NZ765006B2 - Ex vivo organ care system - Google Patents

Abstract

The invention generally relates to systems, apparatuses, methods, and devices for ex vivo organ care. More particularly, in various embodiments, the invention relates to caring for a liver ex vivo at physiologic or near-physiologic conditions. The below summary is exemplary only, and not limiting. Other embodiments of the disclosed subject matter are possible. Embodiments of the disclosed subject matter can provide techniques relating to portable ex vivo organ care, such as ex vivo liver organ care. In some embodiments, the liver care system can maintain the liver at, or near, normal physiological conditions. To this end, the system can circulate an oxygenated, nutrient enriched perfusion fluid to the liver at or near a physiological temperature, pressure, and flow rate. The technique that can extend the time during which an organ such as a liver can be preserved in a healthy state ex-vivo and enable assessment capabilities. ther embodiments of the disclosed subject matter are possible. Embodiments of the disclosed subject matter can provide techniques relating to portable ex vivo organ care, such as ex vivo liver organ care. In some embodiments, the liver care system can maintain the liver at, or near, normal physiological conditions. To this end, the system can circulate an oxygenated, nutrient enriched perfusion fluid to the liver at or near a physiological temperature, pressure, and flow rate. The technique that can extend the time during which an organ such as a liver can be preserved in a healthy state ex-vivo and enable assessment capabilities.

Description

EX VIVO ORGAN CARE SYSTEM CROSS-REFERENCE TO RELATED APPLICATIONS The present application is a divisional application of New Zealand Application No. 726895, which is incorporated in its entirety herein by reference.

This application claims the t under 35 U.S.C. § 119(e), of provisional application U.S. Serial No. 62/006,871, filed June 2, 2014, entitled, “EX VIVO ORGAN CARE SYSTEM”, and U.S. Serial No. 62/006,878, filed June 2, 2014, ed, “EX VIVO ORGAN CARE SYSTEM”, the entire subjects of which are incorporated herein by nce.

FIELD OF THE INVENTION The invention generally relates to systems, methods, and devices for ex vivo organ care.

More particularly, in various embodiments, the invention relates to caring for an organ ex vivo at physiologic or hysiologic conditions.

BACKGROUND t organ preservation techniques typically involve hypothermic storage of the organ packed in ice along with a chemical ate solution. In the case of a liver transplant, tissue damage resulting from ischemia can occur when hypothermic techniques are used to preserve the liver ex vivo. The severity of these injuries can increase as a function of the length of time the organ is maintained o. For example, continuing the liver example, lly it may be maintained ex-vivo for about seven hours before it becomes unusable for transplantation. This relatively brief time period limits the number of recipients who can be reached from a given donor site, y restricting the recipient pool for a harvested liver. Even within this time limit, the liver may nevertheless be significantly damaged. A significant issue is that there may not be any e indication of the damage. e of this, less-than-optimal organs may be lanted, resulting in post-transplant organ dysfunction or other injuries. Thus, it is desirable to develop techniques that can extend the time during which an organ such a liver can be preserved in a healthy state ex-vivo and enable assessment capabilities. Such techniques would reduce the risk of transplantation failure and enlarge potential donor and recipient pools.

SUMMARY According to a first aspect, the present invention provides a perfusion circuit for perfusing a liver ex vivo, the perfusion circuit comprising: a pump for providing fluid flow of a perfusion fluid through the perfusion t; a gas exchanger; a on pump configured to infuse a solution into the perfusion fluid; a divider in fluid communication with the pump and configured to divide the fluid flow of the perfusion fluid into a first portion of the perfusion fluid flowing through a first branch and a second portion of the perfusion fluid flowing h a second branch, a volume of the second portion of the perfusion fluid being greater than a volume of the first portion of the perfusion fluid; wherein the first branch comprises a hepatic artery interface configured to provide the first portion of the perfusion fluid to a hepatic artery of the liver, the first n of the perfusion fluid having a first pressure and a first flow rate at the hepatic artery ace, and the second branch comprises a portal vein interface configured to provide the second portion of the ion fluid to a portal vein of the liver, the second portion of the perfusion fluid having a second pressure and a second flow rate at the portal vein interface; one or more drains configured to receive the perfusion fluid from an inferior vena cava of the liver; a oir positioned between the one or more drains and the pump, the reservoir configured to receive the perfusion fluid from the one or more drains and store a volume of the perfusion fluid; a bile container configured to receive bile produced by the liver.

According to a second aspect, the present invention provides a system for perfusing an ex vivo liver at near physiologic conditions, the system sing: a perfusion circuit comprising: a pump configured to provide a fluid flow of a perfusion fluid through the perfusion circuit; a gas exchanger; a divider in fluid communication with the pump, the divider configured to divide the perfusion fluid into: a first portion of the perfusion fluid flowing to a hepatic artery interface configured to provide the first portion of the perfusion fluid to a hepatic artery of the liver at a first pressure and a first flow rate, and a second portion of the perfusion fluid flowing to a portal vein interface configured to provide the second portion of the perfusion fluid to a portal vein of the liver at a second pressure and a second flow rate; a heating subsystem for maintaining a temperature of the perfusion fluid at a hermic ature; a solution pump configured to infuse a solution into the perfusion fluid; and a bile container configured to receive bile produced by the liver.

According to a third aspect, the present ion provides a system for ving a liver ex vivo at physiological conditions, the system comprising: a multiple-use module comprising a pump; and a single-use module comprising: an organ-chamber assembly configured to hold an ex vivo organ, the organ-chamber assembly including: a housing; a flexible support surface suspended within the organ-chamber assembly; and a perfusion circuit configured to e fluid flow of a perfusion fluid to the liver, the perfusion circuit comprising: a pump interface assembly for translating pumping from the pump to the perfusion fluid; a hepatic artery interface configured to provide a first portion of the perfusion fluid to a hepatic artery of the liver; a portal vein interface configured to provide a second portion of the ion fluid to a portal vein of the liver; and a divider configured to e the first portion of the ion fluid from the pump interface assembly to the hepatic artery interface at a pressure between 25-150 mmHg and a flow rate between 0.25-1 Liters/minute and the second portion of the perfusion fluid to the portal vein interface at a pressure n 1-25 mmHg and a flow rate between 0.75-2 /minute. 1b followed by 2 The below summary is exemplary only, and not limiting. Other embodiments of the disclosed subject matter are possible.

Embodiments of the disclosed subject matter can provide ques relating to portable ex vivo organ care, such as ex vivo liver organ care. In some ments, the liver care system can maintain the liver at, or near, normal physiological conditions. To this end, the system can circulate an oxygenated, nutrient enriched perfiJsion fluid to the liver at or near physiological temperature, pressure, and flow rate. In some embodiments, the system employs a blood product— based perfusion fluid to more accurately mimic normal physiologic ions. In IO other embodiments, the system uses a synthetic blood substitute solution, while in still other embodiments, the solution can contain a blood product in combination with a blood tute product.

Some embodiments of the disclosed subject matter relate to a method for using lactate and liver enzyme ements to evaluate the: i) overall perfusion status of an isolated liver, ii) metabolic status of an isolated liver, and/or iii) the overall vascular patency of an ed donor liver. This aspect of the disclosed subject matter is based on the ability of liver cells to produce/generate lactate when they are starved for oxygen and metabolize/utilize lactate for energy production when they are well perfused with oxygen.

Some embodiments of the organ care system can include a module that has a chassis, and an organ chamber assembly that is mounted to the chassis and is adapted to contain a liver during perfusion. The organ care system can include a fluid conduit with a first interface for connecting to an c artery of the liver, a second interface for connecting to the portal vein, a third interface for connecting to the inferior vena cava and a fourth interface to connect to the bile duct. The organ care system can include a lactate sensor for sensing lactate in the fluid being provided to and/or flowing from the liver. The organ care system can also include sensors for ing the pressures and flows of the hepatic artery, portal vein, and/or inferior vena cava.

Some embodiments can relate to a method of determining liver ion status. For example, a method for evaluating liver ion status can include the steps of g a liver in a protective chamber of an organ care system, g a perfusion fluid into the liver, providing a flow of the perfusion fluid away from the liver, measuring the lactate value of the fluid leading away from the liver, measuring the amount of bile produced by the liver, and evaluating the status of the liver using the measured lactate values, oxygen saturation level, and/or the quantity and quality ofbile ed.

Some embodiments can relate to a method for providing a physiologic rate of flow and a physiologic pressure for both the hepatic artery and for the portal vein. In some embodiments the flow is sourced by a single pump. In particular, the system can include a mechanism for the user to manually divide a single source of perfusate to the hepatic artery and portal vein, and to adjust the division for physiologic flow rates and pressures. In other ments the system automatically divides the single IO source of perfusate flow to the hepatic artery and portal vein to result in physiologic pressures and rates of flow using, for e, an automatic control thm.

Some embodiments of the organ care system can include a nutritional subsystem that infuses the perfusion fluid with a supply of maintenance solutions as the perfusion fluid flows through the system, and in some embodiments, while it is in the reservoir. According to one feature, the maintenance solutions include nutrients.

According to another feature, the maintenance solutions include a supply of therapeutics and/or ves to support ed preservation (e.g., vasodilators, heparin, bile salts, etc.) for reducing ischemia and/or other reperfusion d injuries to the liver.

In some ments, the perfusion fluid es blood removed from the donor h a process of exsanguination during harvesting of the liver. Initially, the blood from the donor is loaded into the reservoir and the cannulation locations in the organ chamber assembly are bypassed with a bypass conduit to enable normal mode flow of perfilsion fluid through the system without a liver being present, aka “priming tube”. Prior to cannulating the harvested liver, the system can be primed by circulating the exsanguinated donor blood through the system to warm, oxygenate and/or filter it. Nutrients, vatives, and/or other therapeutics may also be provided during priming via the infiision pump of the nutritional subsystem. During priming, various parameters may also be initialized and ated Via the operator interface. Once primed and running appropriately, the pump flow can be reduced or cycled off, the bypass conduit can be removed from the organ chamber assembly, and the liver can be cannulated into the organ chamber assembly. The pump flow can be restored or increased, as the case may be.

In some embodiments, the system can include a plurality of compliance chambers. The compliance chambers are effectively small inline fluid accumulators with flexible, resilient walls for simulating the human body's vascular ance. As such, they can aid the system in more accurately mimicking blood flow in the human body, for e, by filtering/reducing fluid pressure spikes due, for e, to flow rate changes. In one configuration, compliance chambers are located in the perfiJsate path to the portal vein and on the output of the perfusion fluid pump.

According to one embodiment, a compliance chamber is located next to a clamp used for regulating pressure to effect physiologic hepatic artery and portal vein flows.

In some embodiments, the organ r assembly includes a pad or a sac assembly sized and shaped for interfitting within a bottom of the housing. Preferably, the pad assembly includes a pad formed from a material resilient enough to n the organ from mechanical vibrations and shocks during transport. In the case of the organ chamber assembly being configured to receive a liver, according to one feature, the pad of the invention includes a mechanism to m the pad to ently sized and shaped livers so as to ain them from the effects of shock and vibration encountered during transport.

Some embodiments of the organ care system are divided into a multiple use module and a single use module. The single use module can be sized and shaped for interlocking with the portable chassis of the multiple use module for electrical, mechanical, gas and fluid interoperation with the multiple use module. According to one embodiment, the multiple and single use modules can communicate with each other via an optical interface, which comes into optical ent automatically upon the single use able module being led into the portable multiple use module. According to another feature, the portable multiple use module can provide power to the single use disposable module Via spring loaded connections, which also automatically connect upon the single use disposable module being installed into the portable multiple use module. According to one feature, the optical interface and spring loaded connections can ensure that connection between the single and multiple modules is not lost due to jostling, for example, during transport over rough terrain.

In some embodiments, the disposable single-use module includes a ity of ports for sampling fluids from the ate paths. The ports can be interlocked such that sampling fluid from a first of the plurality of ports prohibits simultaneously sampling fluids from a second port of the plurality. This safety feature reduces the hood of mixing fluid samples and inadvertently opening the ports. In one embodiment, the single use module includes ports for ng from one or more of the hepatic artery, portal vein, and/or IVC interfaces.

Some embodiments of the disclosed subject matter are directed at a method of providing therapy to a liver. Exemplary methods can e placing a liver in a protective chamber of a portable organ care system, pumping a perfusion fluid into the liver via a hepatic artery and portal vein, providing a flow of the perfiision fluid away from the liver via the vena cava, operating a flow control to alter a flow of the perfusion fluid such that the perfiision fluid is pumped into the liver via a hepatic artery and portal vein and flows away from the liver via a vena cava, and administering a therapeutic treatment to the liver. The treatments can include, for example, administering one or more of immunosuppressive treatment, chemotherapy, gene therapy and irradiation y to the liver. Other treatments may include surgical applications including split transplant and cancer ion.

In some embodiments, the disclosed t matter can include a perfiision circuit for perfiising a liver ex-vivo, the perfusion circuit ing a single pump for ing ile fluid flow of a perfusion fluid h the circuit; a gas exchanger; a divider configured to divide the perfusion fluid flow into a first branch and a second branch; wherein the first branch is configured to provide a first portion of the perfusion fluid to a hepatic artery of the liver at a high pressure and low flow rate, wherein the first branch is in fluid pressure communication with the pump; wherein the second branch is configured to provide the remainder of the perfusion fluid to a portal vein of the liver at a relatively low pressure and high flow rate, wherein the second branch is in fluid pressure communication with the pump; the second branch further comprising a clamp located between the divider and the liver for selectively controlling the flow of perfusion fluid to the portal vein; the second branch further comprising a compliance chamber between the divider and the liver configured to reduce the ile flow teristics of the perfusion fluid from the pump to the portal vein; wherein the pump is configured to communicate fluid pressure through the first and second branches to the liver; a drain configured to receive ion fluid from an uncannulated inferior vena cava of the liver; and a reservoir positioned entirely below the liver and located between drain and the pump, configured to WO 87737 receive the perfiasion fluid from the drain and store a volume of fluid. Other embodiments are possible.

In some embodiments, the disclosed subject matter can include a solution pump including a stepper motor in communication with a ed rod; a carriage that is ted to the rod and configured to move along a linear axis as the rod rotates, the carriage being configured to compress a plunger of a syringe when moved in a first direction and being red to retract the plunger of the syringe when moved in a second direction; a clamp configured to connect to the r; a connection assembly including a port configured to couple to a tip of the syringe; a first one way IO valve configured to allow fluid to flow into the syringe h the port as the syringe is retracted; a second one way valve configured to allow fluid to flow away from the syringe through the port as the syringe is compressed; a pressure sensor coupled to the connection assembly for determining a pressure of the fluid within the connection assembly; a controller configured to control operation of the r motor; and a sensor configured to determine when the syringe is fully retracted. Other embodiments are possible.

In some embodiments, the disclosed subject matter can include a method including ng a rod to cause a carriage connected to the rod to move along a linear axis of the rod, ssing a plunger of a syringe as the carriage moves in a first direction along the linear axis, delivering fluid from the syringe into a port of a connection assembly and through a first one-way valve as the plunger is compressed, retracting a plunger of a syringe as the carriage moves in a second direction along the linear axis, delivering fluid to the syringe through a second one-way valve, and through the port of the connection assembly as the plunger is retracted, sensing a pressure of fluid in the connection assembly, and sensing a location of the r when the syringe is retracted. Other embodiments are possible.

In some embodiments, the disclosed subject matter can include an ex-vivo perfusion liquid for machine perfusion of donor livers sing an energy—rich component, a bile salt, an olyte, and a buffering component. The liquid can include a blood product. The energy-rich component can be one or more compounds selected from the group consisting of a carbohydrate, pyruvate, flavin adenine dinucleotide (FAD), B-nicotinamide adenine dinucleotide (NAD), B—nicotinamide adenine dinucleotide phosphate (NADPH), a phosphate tive of nucleoside, a coenzyme, and metabolite and precursor thereof. The liquid further includes one or more components selected from the group consisting of an lotting agent, a lipid, terol, a fatty acid, oxygen, an amino acid, a hormone, a vitamin, and a steroid.

The perfusion solution is essentially free of carbon dioxide. Other embodiments are possible.

These and other embodiments of the disclosed subject matter will be more fully understood after a review of the following figures, and detailed description.

BRIEF PTION OF THE FIGURES IO The following drawings are intended show non-limiting examples of the disclosed subject matter. Other embodiments are possible. is an exemplary diagram of a liver. is a photograph of an exemplary single use module.

FIGS. 3A-3I show s views of an exemplary organ care system and ents thereof. shows an exemplary system that can be used within an ment of the organ care system. shows an exemplary system that can be used within an embodiment of the organ care .

FIGS. 6A-6E show an ary pump configuration that can be used within an embodiment of the organ care system.

FIGS. 7A-7Q show an exemplary solution infusion pump that can be used within an embodiment of the organ care system. shows an exemplary system that can be used within an embodiment of the organ care system. shows an exemplary system that can be used within an embodiment of the organ care system. shows an exemplary system that can be used within an embodiment of the organ care system.

FIG. ll shows an exemplary system that can be used within an embodiment of the organ care system.

FIGS. 12A—12G show exemplary graphical user interfaces that can be used within an embodiment of the organ care system.

H shows an exemplary system that can be used within an embodiment of the organ care system.

FIGS. l3A—13R show exemplary ments of a single use module and components thereof that can be used in an embodiment of the organ care system.

FIGS. l4A—l4S show exemplary embodiments of an organ chamber and components thereof that can be used in an embodiment of the organ care system.

FIGS. lSA—lSD show an exemplary embodiment of a support structure that can be used in an ment of the organ care system.

FIGS. l6A—l6J show an exemplary pad and components thereof and a flexible IO material support surface that can be used in embodiments of the organ care system. shows an exemplary system that can be used within an embodiment of the organ care system.

A-18G show an exemplary heater assembly and components f that can be used within an embodiment of the organ care system.

FIG. l9A-19C show an exemplary sensor system that can be used within an embodiment of the organ care system.

FIGS. 20A—20C show an exemplary system that can be used within an embodiment of the organ care system.

FIGS. 21A-21K show exemplary hepatic artery cannulas that can be used within an embodiment of the organ care system.

FIGS. 22A-22G show exemplary portal vein cannulas that can be used within an embodiment ofthe organ care system.

FIGS. N show an ary connector that can be used within an embodiment of the organ care system.

FIGS. 24A-24L show an exemplary tor that can be used within an embodiment of the organ care system.

FIGS. 25A-24D show exemplary clamps that can be used within an embodiment of the organ care system.

FIGS. 26-27 show exemplary processes that can be used in embodiments of an organ care . shows exemplary test results from an embodiment of an organ care system.

FIGS. 29 shows an exemplary s that can be used in ments of an organ care system. shows exemplary systems that can be used within an embodiment of the organ care system. shows the hepatic artery flow (HAF) trend throughout the course of 8 hours preservation on OCS. shows the portal vein flow (PVF) trend throughout the course of 8 hours preservation on OCS. shows a graphical depiction of hepatic artery pressure versus portal IO vein pressure throughout the 8 hour OCS-liver ion. is a graphical depiction of arterial lactate levels over the 8 hour OCS liver perfusion. is a graphical depiction of total bile production over the 8 hour OCS liver perfusion. is a graphical depiction ofAST level over the 8 hour OCS liver perfusion. is a cal depiction ofACT level over the 8 hour OCS liver perfusion. is a graphical depiction of oncotic pressure throughout the course of 8 hours vation on OCS. is a graphical depiction of bicarb levels over the 8 hour OCS liver perfusion. is a depiction of the detected pH levels hout the course of 8 hours preservation on OCS. shows images of s taken from samples in Phase I, Group A. depicts Hepatic Artery Flow of a 12hr OCS Liver Perfusion. depicts Portal Vein Flow of al2hr OCS Liver Perfusion. depicts Hepatic Artery Pressure vs. Portal Vein Pressure in a l2hr OCS-Liver Perfusion. depicts Arterial Lactate in a 12hr OCS-Liver Perfusion. depicts Bile Production in a 12hr OCS-Liver Perfiasion. depicts AST Level of a 12hr OCS-Liver Perfusion. depicts ACT Levels in a 12hr OCS-Liver Perfusion. s Hepatic Artery Flow on a simulated transplant OCS-Liver preservation arm vs. a simulated transplant control cold preservation arm. depicts Portal Vein Flow on a ted transplant OCS-Liver preservation arm vs. a simulated transplant control cold preservation arm. depicts Hepatic Artery Pressure vs. Portal Vein Pressure in a simulated transplant OCS—Liver vation arm vs. a simulated transplant control cold preservation arm. depicts Arterial Lactate on a simulated transplant OCS-Liver preservation arm vs. a simulated transplant control cold preservation arm.

IO depicts bile tion of a simulated transplant OCS-Liver vation arm vs. a simulated transplant control cold preservation arm. depicts a AST Level of simulated transplant OCS-Liver preservation arm vs. a ted transplant control cold preservation arm. depicts ACT Levels of a simulated transplant OCS-Liver preservation arm vs. a simulated transplant control cold preservation arm. depicts oncotic pressure of a simulated transplant OCS-Liver preservation arm vs. a simulated transplant control cold vation arm. depicts the Bicarb Level of a simulated lant OCS-Liver preservation arm vs. a simulated transplant control cold preservation arm. depicts pH Levels of a simulated transplant OCS-Liver preservation arm vs. a simulated transplant control cold vation arm. shows the histological examination of Parenchymal tissue and Bile duct tissue. shows the histological examination of Parenchymal tissue and Bile duct tissue. is a m illustrating locations of samples from a liver of a pig. illustrates the Hepatic Artery Pressure (HAP) trend over the course of 24 hours perfusion on the OCS. illustrates the Portal Vein Pressure in an OCS-Liver Preservation arm vs the control Cold preservation arm. rates a Hepatic Artery Flow in a OCS-Liver vation arm vs. control Cold preservation arm. illustrates a Portal Vein Flow in an OCS-Liver Preservation arm vs. control Cold preservation arm. s Arterial Lactate in an OCS-Liver Preservation arm vs. a control Cold preservation arm. illustrates an AST Level OCS-Liver Preservation arm vs. control Cold Preservation arm.

FIG 68 illustrates an ALT Level OCS-Liver Preservation arm vs. control Cold preservation arm. depicts a GGT Level of an ver Preservation arm vs. control IO Cold preservation arm. depicts a PH level of an OCS-Liver Preservation arm vs. a control Cold vation arm. depicts a HCO3 level in an OCS-Liver Preservation arm vs. a Control Cold preservation arm. s a bile production OCS-Liver Preservation arm vs. control Cold preservation arm. demonstrates that both arms maintained bile production rate of >10ml/hr. DETAILED DESCRIPTION While the following description uses section gs, these are included only as a convenience to the reader. The section gs are not intended to be limiting or impose any restriction on the subject matter herein. For example, components described in one section of the description can be included in other sections additionally or alternatively. The embodiments disclosed herein are exemplary only and it is within the scope of the present disclosure that the disclosed embodiments and various features may be interchanged with one another.

I. Introduction A. General Summary Embodiments of the sed subject matter can provide techniques for maintaining a liver ex vivo, such as during a transplant procedure. The system can in a liver in conditions mimicking the human body. For e, the system can supply a blood substitute to an ex vivo liver in a manner that simulates the blood flow provided by the body. More specifically, the system can provide a flow of blood tute to a hepatic artery and portal vein of a liver having flow and pressure characteristics similar to the human body. In some embodiments, the desired flows can be achieved using a pumping system that employs a single pump. The system can also warm the blood substitute to a hermic temperature that simulates the human body and can provide nutrients to the blood substitute to maintain the liver and to promote the normal generation of bile by the liver. By ming these techniques, the length of time that a liver can be maintained outside the body can be extended, thereby making the phical distance n donors and recipients less important than it previously was. Also, some of the embodiments sed herein that are used to maintain the liver ex vivo can also be used to assess the IO condition of the liver pre-transplant. In some embodiments, the techniques described herein can also be used to treat an injured and/or diseased liver ex vivo using treatments that would otherwise be harmful to the body if performed in vivo. Other embodiments are within the scope of the disclosed subject matter.

While the disclosure herein focuses on embodiments that are intended to maintain or treat a liver, the disclosure is not limited as such. For example, techniques described herein can also be used, or can be adapted for use with other organs such as lungs, a heart, intestines, a pancreas, a kidney, a spleen, a bladder, a gallbladder, a stomach, skin, and a brain. 11. Liver compared with other organs While the liver is one of many organs in the human body, the liver can present challenges during ex vivo maintenance and transport that do not exist with other organs such as the heart and lungs. Some exemplary differences and considerations are described next.

A. Liver uses two ate inflow supplies Importantly, the liver uses two unique input paths for perfusate as compared with only one for other . Hepatic circulation is unique as featured by its dual vascular blood supply, each having different flow teristics. Referring to FIG 1, which is an exemplary conceptual drawing of a liver 100, the liver uses two blood supplies, the portal vein 10 and the hepatic artery 12. In particular, the hepatic artery delivers blood to the liver having high pressure, pulsatile flow, but of relatively low flow rate. Hepatic blood flow typically accounts for about ird of the total liver blood flow. The portal vein delivers blood to the liver having a low pressure and minimal ility at a higher flow rate. Portal vein flow typically accounts for about two-thirds of the total blood flow to the liver.

The dual blood supply expected by the liver can present challenges when one tries to artificially supply physiologic blood flow thereto when the organ is in an ex Vivo system. While the challenges can be difficult when using a dual-pump design, they can be intensified when using a single-pump design. Some embodiments of the subject matter disclosed herein can address these challenges.

B. Assisted drainage of blood In Vivo, the liver is positioned beneath the diaphragm. Due to this oning, liver blood flow and venous drainage Via the inferior vena cava 14 is typically enhanced by diaphragmatic contraction as a result of pressure exerted on the liver.

When the diaphragm moves in tandem with the lungs as air is drawn in and ed by the lungs, the movement of the agm can act on the liver by applying pressure to the organ, thereby pushing blood out of the tissue. It is ble to mimic this phenomenon in an ex-vivo liver to help encourage blood flow out ofthe liver and prevent blood buildup in the organ.

C. Oncotic re To minimize edema formation in an ex vivo liver, the ate should have high oncotic pressure, for example, dextran, 25% albumin, and/or fresh frozen plasma. In some embodiments, oncotic pressure ofthe circulating perfusate is maintained between 5 — 35 mmHg, and more specifically between 15 — 25 mmHg.

Non-limiting examples ofpossible oncotic pressures are 15, l6, 17, 18, 19, 20, 21, 22, 23, 24, and 25 mmHg, or any ranges bounded by the values noted here.

D. Metabolism and C02 levels The liver is a metabolic hub in the body and is in a constant state of metabolism. Most compounds absorbed by the intestine first pass h the liver, which is thus able to regulate the level of many metabolites in the blood. For example, the conversion of sugars into fat and other energy stores (e.g., gluconeogenesis and glycolysis) results in production of C02. The liver consumes about 20% of the total body . As a result, the liver produces higher levels of C02 than most other organs. In vivo, the organ is able to self-regulate to remove excess carbon dioxide from the organ. However, for an ex-vivo organ, it can be ble to remove excess carbon dioxide from the organ to maintain physiologic levels of oxygen and carbon dioxide and thus pH. The system described in this application can facilitate establishment of blood chemistry equilibrium suitable for organ preservation ex vivo.

E. Bile production The liver is an excrement producing organ. The excrement, bile, is usually produced and excreted by the organ in vivo. Bile is produced in the liver by cytes. In vivo, the liver utilizes bile salts to create bile, and bile salts are recycled through the enterohepatic circulation system back to the liver to be reused.

The bile salts in turn ate the hepatocytes to produce more bile. Ex vivo, bile salts are not ed back to the liver. As a result, it can be desirable to supplement perfusate with bile salts to aid the organ in producing bile. onally, in some instances, the bile produced by the liver can e an indication (e.g., quantity, color and consistency) of the suitability of the organ for transplant.

F. Supporting a liver The liver is the largest solid organ in the body, but it is delicate and fragile. In the body, it is protected by the rib cage and other . Unlike many other organs, the liver does not include protective elements and is not defined by a rigid ure.

Therefore, when the liver is removed from the body and maintained ex-vivo, it should be treated more delicately than other organs. For example, it can be desirable to e proper support for the liver, place the liver on a low friction surface, and/or cover the organ with a wrap to protect the organ from damage during transport and while being maintained ex vivo.

G. Perfusate Given the liver’s wide range of vital functions when compared with other organs (e.g., detoxification, protein synthesis, glycogen storage, and production of biochemicals necessary for digestion), the perfusion fluid used in the organ care system described herein can be lly designed to maintain the liver in close to its physiological state to maintain its regular functions. For instance, because the liver is 2015/033839 in a constant state of metabolism consuming energy, the oxygen t in the perfusion fluid can be maintained at close to or more than the physiological level to meet its high demand as a metabolic warehouse. rly, the perfusion fluid can also be designed to include sufficient concentration of energy-rich components, such as carbohydrates and electrolytes, to provide the liver with an energy source to carry out its functions.

The flow rate of the perfusion fluid can be also properly adjusted to ensure that oxygen and nts are delivered to an ex vivo liver at a suitable rate.

Furthermore, the carbon dioxide content in the perfusion liquid can be lower than the level in physiological state, thus further driving the equilibrium of the liver’s biological reactions to lism and oxidation. In some embodiments, the perfusion fluid used herein does not contain significant amount of carbon e or is free from all carbon dioxide. In some embodiments, the perfusion fluid used herein also contains sufficient amount of bile salt to sustain the need of the liver to produce bile. Thus, the perfusion fluid for the organ care system described herein can be designed to maintain the liver’s regular cellular fiinctions to maintain the liver in a viable state.

III. Description of exemplary system components A. General architecture shows an exemplary organ care system 600 that can be used to preserve an organ such as a liver when the organ is ex vivo during, for example, a transplant operation or medical procedure. At a general level, the organ care system 600 is configured to provide conditions to an ex Vivo organ that mimic the ions the organ experiences when in vivo. For example, in the case of a liver, the organ care system 600 can provide a ate flow to the organ in a manner that mimics blood flow in a human body (e.g., flow, pressure, and temperature) and provide similar environmental characteristics (e. g., temperature).

In some embodiments, the organ care system 600 can be d into two parts: a disposable single-use portion (e. g., 634) and a sposable multiple-use portion (e.g., 650) (also referred to herein as a single-use module and a multiple-use module). As the names imply, the single—use portion can be replaced after a liver is transported and the multiple-use portion can be reused. At a general level, though not required, the single-use portion includes those ns of the system that come into direct contact with biological al whereas the multiple-use portion es those components that do not come into contact with biological al. In some embodiments, all of the components in the single-use portion are sterilized before use, whereas the components in the multiple-use portion are not. Each of the portions are bed in detail below. This configuration allows a method of operation where, after use, the entire single-use module 634 can be discarded and replaced with a new single-use . This can allow the system 600 to be available for use again after a short turnaround time.

Typically the single and multiple use portions can be configured to be removably connected to one another Via a mechanical interface. Additionally, the single and multiple use portions can include mechanical, gas, optical, and/or electrical connections to allow the two ns to interact with one another. In some embodiments, the connections between the portions are designed to be connected/unconnected from one another in a modular fashion.

The disposable module 634 and the le use module 650 can be constructed at least in part of material that is durable yet light-weight such as polycarbonate c, carbon fiber epoxy composites, polycarbonate astic blend, glass reinforced nylon, acetal, straight ABS, aluminum, and/or magnesium. In some embodiments, the weight of the entire system 600, is less than 100 pounds, including the multiple use module, organ, batteries, gas tank, and priming, nutritional, preservative and perfusion fluids, and less than about 50 pounds, excluding such items. In some embodiments, the weight of the single use module 634 is less than 12 pounds, excluding any solutions. In some embodiments, the multiple use module, excluding all fluids, batteries, and gas supply, weighs less than 50 pounds.

With the cover removed and the front panel open, an operator can have easy access to many of the components of the disposable 634 and multiple use 650 modules. For example, the or can access the various components of the single and multiple use modules and can install and/or remove the single use module from to/from the le use module.

While certain components are described herein as being in the single—use portion or the multiple-use n of the system 600, this is exemplary only. That is, components identified herein as being located in the single-use portion can also be located in the multiple-use portion and vice-versa.

B. Exemplary multiple use module Referring to FIGS. 3A-3I, the multiple use module can include several components including a housing, a cart, a battery, a gas supply, at least part of a perfusion fluid pump, an infusion pump, and a control system. 1. Cart/Housing Referring to FIGS. 3A-3I, an exemplary embodiment of the organ care system is shown as organ care system 600 can include a housing 602 and a cart 604. The cart 604 can include a platform and wheels for transporting the system 600 from place to place. A latch 603 can secure the housing 602 to the cart 604. To further aid in portability, the system 600 can also include a handle hinge d to the left side of the housing 602, along with two rigidly mounted handles 612a and 6l2b mounted on the left and right sides of the housing 602. The housing 602 can filrther include a removable top lid (not shown) and a front panel 615 hinged to a lower panel by hinges 616a and 616b. The cover can include handles for aiding with removal.

The system 600 can e an AC power cable 618, along with a frame for securing the power cable, both which can be located on the lower n of the left side of the housing 602. A power switch 622, which can also located on the lower section of the left side, can enable an operator to restart the system software and onics. shows a front perspective View of the multiple use module 650 with the single use module 634 removed. As shown, the multiple use module 650 can include the cart 604 and the housing 602, along with all of the components mounted to/in it. The multiple use module 650 also es a bracket assembly 638 for receiving and locking into place the single use module 634. An exemplary bracket assembly 638 is shown in .

In some embodiments, the housing 602 can include a fluid tight basin, which is configured to capture any ion fluid and/or any other fluid that may inadvertently leak from the upper portion of the g 602 and prevent it from reaching the lower section of the housing 602. Thus, in some embodiments, the basin can shield the electronic components of the system 600 from leaked fluid. In some embodiments, the basin 652 can be sized to accommodate the entire volume of fluids used in the system 600 at any particular time.

The system 600 can also include the operator interface module 146, along with a cradle 623 for holding the operator interface module 146. The operator ace module 146 can include a display 624 for displaying information to an operator. The operator interface module 146 can also include a ble and depressible knob 626 for selecting n multiple parameters and display screens. The knob 626 can also be used to set parameters for automatic control of the system 600, as well as to provide manual control over the operation of the system 600. In some embodiments, the operator interface module 146 can include its own battery and may be d from the cradle 623 and used in a wireless mode. While in the cradle 623, power connections can enable the operator interface module 146 to be charged. The operator interface module can also include control buttons for controlling the pump, silencing or disabling alarms, entering or exiting standby mode, and ng the perfusion clock, which initiates the display of data obtained during organ care.

Referring also to FIGS, the system 600 can also e a plurality of interconnected circuit boards for facilitating power distribution and data transmission to, from and within the system 600. For example, the multiple use module 650 can include a front end interface circuit board 636, which lly and electromechanically couples to the front end circuit board 637 of the single use module 650. The system 600 can further include a main board 718, a power circuit board 720, and a battery interface board 711 located on the multiple use module 650.

The main board 718 can be configured to allow the system 600 to be fault tolerant, in that if a fault arises in the operation of a given circuit board, the main board 718 can save one or more operational parameters (e.g., pumping parameters) in non-volatile memory. When the system 600 reboots, it can then re-capture and continue to m according to such parameters. Additionally, the system 600 can divide critical ns among multiple processors so that if one sor fails the remaining critical functions can ue to be served by the other processors. 2. Power system Referring also to the multiple-use portion of the system 600 can include a power subsystem 148 that is configured to provide power to the system 600.

The power tem 148 can provide power to the system 600 using swappable batteries and/or an external power . In some embodiments, the power subsystem 148 can be configured to switch between external power and an onboard battery, without interruption of system operation. The power subsystem 148 can also be configured to automatically allocate externally supplied power between powering the system 600, charging the batteries, and ng internal batteries of the or interface module 146. The batteries in the power system can be used as the primary power source and/or as a backup power source in the event the external power source fails or becomes insufficient. Additionally, the power system 148 can be configured to be compatible with multiple types of al power sources. For example, the power system can be configured to receive le input voltages (e.g., 100V — 230V), multiple frequencies (e.g., 50-60 Hz), single phase power, three-phase power, AC, and/or DC power. Additionally, in some embodiments the operator interface module 146 can have its own y 368.

The housing 602 can include a battery bay 628 that is configured to hold one or more batteries 352. In embodiments with more than one battery, the battery bay 628 can also include a t mechanism 632 that is configured to prevent more than one battery from being removed from the battery bay 628 at any given time while the system 600 is operating. This feature can provide an additional level of fault tolerance to help ensure that a source of power is always available. The system 600 can also include a tank bay 630 that can be configured to receive one or more tanks of gas.

Referring to the conceptual drawing of g 731 can bring power (such as AC power 351) from a power source 350 to the power circuit board 720 by way of connectors 744 and 730. The power supply 350 can convert the AC power to DC power and distribute the DC power as described above. The power circuit board 720 can couple DC power and a data signal 358 via respective cables 727 and 729 from the connectors 726 and 728 to corresponding connectors 713 and 715 on the front end interface circuit board 636. Cable 729 can carry both power and a data signal to the front end interface board 636. Cable 727 can carry power to the heater 110 via the front-end interface board 636. The connectors 713 and 715 can interfit with ponding connectors 712 and 714 on the front end circuit board 637 on the single use module 634 to provide power to the single use module 634. 7The power circuit board 720 can also provide DC power 358 and a data signal from the connectors 732 and 734, respectively, on the power circuit board 720 to corresponding connectors 736 and 738 on the main t board 718 by way of the cables 733 and 735. The cable 737 can couple DC power 358 and a data signal from a connector 740 on the main circuit board 718 to the operator interface module 146 by way of a connector 742 on the operator interface module cradle 623. The power circuit board 720 can also provide DC power 358 and a data signal from connectors 745 and 747 via cables 741 and 743 to connectors 749 and 751 on a battery interface board 711. Cable 741 can carry the DC power signal and cable 743 can carry the data signal. Battery interface board 711 can distribute DC power and data to the one or more batteries 352 (in batteries 352a, 352b, and 352c), which can contain electronic ts that allow them to communicate the respective charges so that the controller 150 can monitor and l the charging and discharging of the one a more batteries 352. 3. ion fluid pump The system 600 can include a pump 106 that is configured to pump perfusate h the organ care system. The perfusate is typically a blood product-based perfusion fluid that can mimic normal physiologic conditions. In some embodiments, the perfusate can be a synthetic blood substitute solution and/or the perfusate can be a blood product in combination with a blood substitute product. In the ments where the perfusion fluid is blood-product based, it typically contains red blood cells (e.g., oxygen ng cells). The perfusate is described more fiJlly below.

In some embodiments, the pump 106 can have a systolic phase and a diastolic phase. The amount of perfiisate pumped by the pump 106 can be varied by changing one or more characteristics of the pump itself. For e, the number of strokes per minute and/or the stroke displacement can be changed to achieve the desired flow rate and pressure characteristics. In some ments, the pump 106 can be configured to use a stroke rate of 1 — 150 st/min and a displacement of 0.1 — 1.5”.

More specifically, however, a nominal stroke rate of 60 st/min :: 5 st/min can be used 2015/033839 with a displacement of 0.5”. These values are exemplary only and values outside of these ranges can also be used. By varying the characteristics of the pump 106 flow rates of between 0.0 and 10 L/min can be ed.

In some embodiments, a perfusion fluid pump 106 is split into two separable portions: a pump driver portion located in the multiple-use portion 650 and a pump ace assembly in the single-use portion 634. This interface assembly of the single-use n can isolate the pump driver of the multiple-use n from direct blood biologic contact.

FIGS. 6A-6D show an exemplary embodiment of the pump 106. FIGS. 6A- 6C show various Views of a pump interface assembly 300 according to an exemplary ment. shows a perspective view of an exemplary pump-driver n 107 of the perfusion fluid pump 106. shows the pump interface assembly 300 mated with the pump—driver portion 107 of the perfiasion fluid pump assembly 300, according to one exemplary embodiment.

The pump interface assembly 300 includes a housing 302 having an outer side 304 and an inner side 306. The interface assembly 300 includes an inlet 308 and an outlet 310. The pump interface assembly 300 can also include inner 312 and outer 314 O-ring seals, two deformable membranes 316 and 318, a doughnut-shaped bracket 320, and ings 319a and 31% that fit between the o-ring 314 and the bracket 320. The half-rings 319a and 3 19b can be made of foam, plastic, or other suitable material.

The inner O-ring 312 can fit into an annular track along a periphery of the inner side 306. The first deformable membrane 316 can mount over the inner O-ring 312 in fluid tight interconnection with the inner side 306 of the housing 302 to form a chamber between an interior side of the first deformable membrane 316 and the inner side 306 of the housing 302. A second deformable membrane 318 can fit on top of the first deformable membrane 316 to provide fault tolerance in the event that the first deformable membrane 316 rips or tears. Illustratively, the able membranes 316 and 318 can be formed from a thin polyurethane film (about 0.002 inches thick).

However, any suitable material of any suitable thickness may be employed. Referring to FIGS. 6A and 6B, the bracket 320 can mount over the second deformable membrane 318 and the rings 319a and 3 19b and can affix to the g 302 along a ery of the inner side 306. Threaded fasteners 322a-322i can attach the bracket 320 to the housing 302 by way of respective threaded apertures 324a-324i in the bracket 320. The outer O—ring 314 can interfit into an annular groove in the bracket 320 for providing fluid tight seal with the pump assembly 106. Prior to inserting O- ring 314 into the annular groove in bracket 320, the half-rings 319a and 31% are typically placed in the groove. The O-ring 314 can then be compressed and positioned within the annular groove in bracket 320. After being oned within the annular groove, the O-ring 314 can expand within the groove to secure itself and the half- rings 319a and 31% in place.

The pump interface assembly 300 can also include heat stake points 321a- 321c, which project from its outer side 304. The points 321a-321c can receive hot glue to take the pump interface assembly 300 to a C-shaped bracket 656 of the single use portion of the system 300.

As shown in , the fluid outlet 310 includes an outlet housing 310a, an outlet fitting 310b, a flow regulator ball 310c and an outlet port 310d. The ball 310c is sized to fit within the outlet port 310d but not to pass through an inner re 326 of the outlet 310. The fitting 310b is bonded to the outlet port 310d (e.g., via epoxy or another adhesive) to capture the ball 3100 between the inner aperture 326 and the fitting 310b. The outlet g 310a is similarly bonded onto the fitting 310b.

In operation, the pump interface assembly 300 is configured and aligned to e a pumping force from a pump driver 334 ofthe perfusion fluid pump assembly 106 and translate the pumping force to the perfiJsion fluid 108, y circulating the perfusion fluid 108 to the organ chamber assembly 104. According to the exemplary embodiment, the perfusion fluid pump ly 106 can e a pulsatile pump having a driver 334, which can contact the membrane 318. The fluid inlet 308 can draw perfusion fluid 108, for example, from the reservoir 160, and provide the fluid into the chamber formed between the inner membrane 316 and the inner side 306 of the housing 302 in response to the pump driver moving in a direction away fiom the deformable membranes 316 and 318, thus ing the membranes 316 and 318 in the same direction.

As the pump driver moves away from the deformable membranes 316 and 318, the pressure head of the fluid 108 inside the reservoir 160 causes the perfusion fluid 108 to flow from the reservoir 160 into the pump assembly 106. In this respect, the pump assembly 106, the inlet valve 191 and the reservoir 160 are oriented to provide a gravity feed of perfusion fluid 108 into the pump ly 106. At the same time, the flow tor ball 310c is drawn into the aperture 326 to prevent perfusion fluid 108 from also being drawn into the chamber through the outlet 310. It should be noted that the outlet valve 310 and the inlet valve 191 are one way valves in the rated embodiment, but in alternative embodiments the valves 310 and/or 191 are two-way valves. In response to the pump driver 334 moving in a direction toward the deformable membranes 316 and 318, the flow regulator ball 310c moves toward the fitting 310b to open the inner aperture 326, which enables the outlet 310 to expel perfusion fluid 108 out of the chamber formed n the inner side 306 of the g 302 and the inner side of the deformable membrane 316. A separate one-way inlet valve 191, shown between the reservoir 160 and the inlet 308 in stops any perfirsion fluid from being expelled out of the inlet 308 and flowing back into the oir 160.

In embodiments of the system 600 that are split into the single use module 634 and the multiple use module 650, the pump assembly 107 can rigidly mount to the multiple use module 650, and the pump interface assembly 300 can rigidly mount to the able single use module 634. The pump assembly 106 and the pump interface assembly 300 can have ponding interlocking connections, which mate together to form a fluid tight seal between the two assemblies 107 and 300.

More particularly, as shown in the ctive view of , the perfusion fluid pump assembly 107 can include a pump driver housing 338 having a top surface 340, and a pump driver 334 housed within a cylinder 336 of the housing 338. The pump driver housing 338 can also include a docking port 342, which includes a slot 332 sized and shaped for mating with a flange 328 projecting from the pump interface assembly 300. The top surface 340 of the pump driver housing 338 can mount to a bracket 346 on the non-disposable multiple use module 650. The bracket 346 can include features 344a and 344b for abutting the tapered projections 323a and 323b, respectively, of the pump interface assembly 300. The bracket 346 can also include a cutout 330 sized and shaped for aligning with the docking port 342 and the slot 332 on the pump driver housing 338.

Operationally, the seal between the pump interface assembly 300 and the fluid pump assembly 107 can be formed in two steps, illustrated with reference to FIGS. 6D and 6E. In a first step, the flange 328 is positioned within the docking port 342, while the tapered projections 323a and 323b are positioned on the clockwise side next to corresponding features 344a and 344b on the bracket 346. In a second step, as shown by the arrows 345, 347 and 349, the pump interface assembly 300 and the fluid pump assembly 106 are rotated in opposite directions (e.g., rotating the pump interface ly 300 in a counter clockwise direction while holding the pump assembly 106 fixed) to slide the flange 328 into the slot 332 of the docking port 342.

At the same time, the tapered projections 323a and 323b slide under the bracket features 344a and 344b, respectively, engaging inner surfaces of the bracket es 344a and 344b with tapered outer surfaces of the tapered projections 323a and 323b to IO draw the inner side 306 of the pump interface assembly 300 toward the pump driver 334 and to interlock the flange 328 with the docking ports 342, and the d projections 323a and 323b with the bracket es 344a and 344b to form the fluid tight seal between the two assemblies 300 and 106.

In some embodiments, the system 100 can be configured such that the flow characteristics including pressure and flow volume of the perfusion fluid provided to the hepatic artery and the portal vein are directly controlled and under pressure generated by the pump 106 (e. g., the hepatic artery and portal veins can be in fluid pressure communication with the pump 106). This embodiment is ent from an embodiment where a pump provides ion fluid to a reservoir (e.g., a reservoir located above the liver) and then uses gravity to e fluid pressure to the liver. 4. Solution infusion pump The system 600 can include a solution pump 631 that can be configured to inject one or more solutions into the perfusion module circuit. In some embodiments of the organ care system 600, the on pump 631 can be an e-shelfpump such as a MedSystem III from CareFusion Corporation of San Diego, CA, and/or can be a solution pump as described below with respect to FIGS. 7A-7P. The infusion solutions provided by the solution pump 631 can be used to, for example provide g management of the organ such as inotropic support, e control, pH control. Additionally, while the solution pump 631 is generally considered part of the multiple use module 650, parts of the solution pump 631 can be single use and replaced each time the system is used. 2015/033839 The solution pump 631 can be red to provide one or more solutions simultaneously (also referred to has having one or more ls). In some embodiments, the solution pump 631 can provide three solutions: a maintenance solution, bile salts, and a vasodilator such as epoprostenol sodium. Each of these solutions are described more fully below. The solution pump 631 can support multiple infusion rates (e. g., from 1 to 200 ml/hr, although higher/lower rates are also possible). The infusion rate can be adjustable in time increments (e.g., 1 ml/hour increment, although higher/lower rates are possible) and changes to the infusion rate typically take effect within five seconds, although this is not required. At infusion rates of 10 ml/hr and below, the infused volume can be accurate to within +/- 10% of the on rate set point, although this is not required. At infusion rates above 10 ml/hr, the infused volume can be accurate to within +/- 5% of the infiasion rate set point, although this is not required.

The solution pump can be configured to maintain any required accuracy with input pressures (static pressures relative to the solution pump line connection) of 0 to — 50 mmHg on the on side and 0 to +220 mmHg on the organ side. Preferably, infusions should not have any flow discontinuities greater than three seconds. After the solution pump has been ed, air bubbles larger than 50 uL are typically not injected into the perfusion module. In some embodiments, the portion of the line between the solution pump 631 and the organ can e a valve (e.g., a pinch valve) to further control the flow of solution to the organ. The solution pump 631 can provide status information for each channel such as on state and error.

The solution pump 631 can be used with one or more disposable cartridges that provide the solution. For example, the portion of the line between the solution supply and the solution pump 631 can include a spike to t to an IV bag. In embodiments that include a disposable cartridge to supply the solution, the cartridge should be capable of operating for at least 24 hours.

The solution pump 631 can be red to be lled via one or more communication ports. For example, the solution pump 631 can be controlled via commands received over via a serial port, a network (e.g., Ethernet, WiFi), and/or cellular ications. Various aspects of the solution pump 631 can be controlled such as initial available volume of solution for each channel, infusion state (e.g., infiising or paused). A l and/or alarm status for each channel can also be accessible via the communication port. The status for each channel can include an indication of: whether a disposable cartridge is present, an l volume is available, an infusing state, an infilsing rate, time remaining until empty, and total volume infiised. Additionally, the solution pump 631 can be configured so that each channel has fault-mode infusion rate capable of being written/read via the communication port. In some embodiments sensors disposed throughout the organ care system 600 can be connected (directly or indirectly through the controller 150) to facilitate automatic control the solution pump 631 by the controller 150 using an open or closed feedback loop.

The solution pump 631 can be configured to indicate when failures occur. For example, when a failure or occlusion is detected the solution pump 631 can illuminate a fault indicator associated with the faulted channel and/or send a notification via the communication port. The solution pump 631 can be configured to pause the infusion in a channel that has d and can restart the infusion after the fault or occlusion has been cleared. In embodiments where the infusion rates are set via the communication port, in the event that signals m the communication port are lost, the on pump 631 can be configured to set the infusion rate to a preprogrammed mode infusion rate.

The solution pump 631 can include one or more fault detection algorithms/mechanisms. For example, if a hardware failure is detected the solution pump 631 can alert a device connected to the ication port that a re fault has occurred. If a solution and/or organ side occlusion is detected, the solution pump 631 can alert the device connected via communication port that the occlusion has occurred. The solution pump 631 can be red to carry out self tests including power on and ound self tests. The results of the self tests can be indicated on the solution pump 631 itself and/or communicated via the communication port.

As noted above, the solution pump can be an off-the—shelf solution pump and/or a custom design pump. Referring to FIGS. 7A — 7P, an exemplary embodiment of a custom-designed solution pump 631 is shown and described.

Some embodiments of the on pump sed herein can use a syringe connected to a motor to control the delivery of an infusion solution. By increasing the diameter of the syringe, the capacity of the syringe to hold fluid can be increased.

This increased fluid capacity can reduce the number of times the syringe is exchanged for a new, pre-loaded e. However, syringes with an increased er can result in the loss of precision during the delivery of solution because as the diameter increases, the amount of on delivered when the plunger is depressed one unit also increases. Another exemplary ment of the solution pump uses a relatively small diameter syringe that can allow for greater precision in the delivery of solution.

However, the solution can quickly run out due to the syringe’s low fluid capacity.

Exchanging the syringe with a new, aded syringe can create problems such as introducing air bubbles, interrupting the solution delivery, causing an inconvenience for users, and creating accessibility challenges. Thus, in some embodiments, a relatively small er e can be connected to an external source of fluid solution and the perfusion circuit via fluid lines and a series of one-way valves. In these embodiments, as the syringe is depressed, solution can flow through a one-way valve and into the perfiision circuit. When the syringe is retracted, the solution can flow through another one-way valve from the external fluid source into the syringe to refill it with solution. Thus, some embodiments of this design can allow fine precision control of solution delivery (e.g., by using a smaller diameter syringe) while eliminating the need to replace a ded syringe with another. ing to FIGS. 7A — 7P, an exemplary embodiment of a solution pump 9000 is shown. In this ment, the solution pump 9000 can use a removable/replaceable cassette 9020 to provide infusion solutions. Figures 7C and 7D show an exploded view of the solution pump 9000 and an infusion cassette 9020, respectively. In this embodiment, the solution pump 9000 includes three ls, and thus, is configured to provide up to three different solutions. Other embodiments can include more or fewer channels.

The solution pump 9000 can be a syringe pump driven by a stepper motors 9002a, 9002b, 90020. The stepper motors 9002 can rotate respective lead screws 9005. Carriages 9042 with ge covers 9004 communicate with the lead screw 9005 and can move back and forth along the screw 9005. The inside of carriages 9042 can also be threaded with ng threads to facilitate movement along the lead screw 9005 as the lead screw 9005 rotates. Additionally, the carriages 9042 can also move along linear rails 9041 that facilitate movement back and forth along the lead screws 9005. Pins 9003 can be attached to the carriage covers 9004 and to a carrier 9036 that is red to hold a syringe plunger 9017 so that as the carriages 9042 move back and forth along the lead screws 9005, the plunger can be sed and retracted. The pins 9003 can be threaded to facilitate attachment to the carrier 9036, although this is not required. In the embodiment shown in FIGS. 7E, 7F, 7G, 7H, the carrier 9036 can be shaped to fit around and hold the plunger 9017. The r 9036 can be manufactured in two pieces that can press fit together using protrusions 9045, fit together via screws, and/or any other fastener to clamp the syringe plunger.

In some embodiments, the stepper motor 9002 can be configured to operate at different speeds depending on whether the syringe is being extended or compressed.

For example, when the syringe is being compressed (e.g. during on) the motor can move at a low speed such as four steps per second, whereas when the syringe is being extended (e.g., during refill) the motor can be moved at high speed such as 16,000 steps per second. Other speeds are possible. Additionally, each stepper motor 9002 can include an optical encoder on a motor shaft enclosed therein (or elsewhere) that can be used to track the on and/or speed of the motor 9002. Accordingly, the position of the plunger of the syringe can be calculated.

In the embodiment shown in , the stepper motors 9002a, 9002b, 9002c are positioned in parallel to one another, although other configurations are possible.

The pins 9003 pass through slots 9008 in a top cover 9001 and can attach to the carrier 9036 that ts to a plunger 9017 of e 9016. The connection between the carriage 9042 and the plunger 9017 via the pins 9003 and the carrier 9036 can be used to depress and retract the syringe, which can cause the syringe to provide fluid, or refill itself with fluid when ly connected. For example, as the stepper motor 9002 rotates the lead screw 9005 in a clockwise , the carriage 9042 and the carriage cover 9004 with pin 9003 connected to carrier 9036 and plunger 9017 can move in a direction to cause the plunger 9017 to depress and release fluid on from the syringe 9016. When stepper motor rotates in a counterclockwise manner, the carriage 9042 can move in an opposite direction and the r 9017 can be caused to retract, thereby refilling the syringe 9016 with fluid from a fluid source, such as an external IV bag.

The solution pump 9000 can include optical switch 9007 that can be used to detect when the syringe is in a “home” or other position. In some embodiments, the home on can be a position when the syringe is extended and filled with solution, although other home positions are possible. The optical switch 9007 can be U—shaped and can be configured to transmit an optical beam between the two upper portions of the U (e.g., by having a transmitter on one side and a receiver on the other). In some embodiments, when the carriage 9042 is in its home position, a flag 9006 on the carriage cover 9004 can interrupt the optical beam from the optical switch 9007, thus providing information on the position of the syringe. The flag 9006 can be made of any material that interrupts the optical beam such as opaque plastic and/or metal. In some instances it can be possible that the solution pump 9000 loses track of the position of the carriage 9042 because of, for example, a malfunction. If this occurs, the carriage 9042 can return to the home position, leaving the e 9016 filled and the plunger 9017 extended. This can allow the pump 9000 reattain the position of the syringe t accidentally providing any additional solution. In some embodiments ofthe on pump 9000, an additional optical switch 9007 can be included to ine when the syringe is nearly or tely empty.

The solution pump 9000 can also include pressure sensors 9009 to detect blockages in the delivery line 9010 or output line 9011. An alarm can indicate when the pressure sensors 9009 detect a blockage by sensing a pressure over or under predetermined olds. The pressure sensor can be any cially available sensor suitable for this purpose. In one embodiment, the sensor can be a MEMSCAP SP854 transducer with hydraulic fluid and a diaphragm. The pressure sensors 9009 can extend through the gs 9012 in the top cover 9001.

The stepper motor 9002, linear rails 9041, and pressure sensors 9009 can be mounted to the structural plate 9013. A printed circuit board (“PCB”) 9015 can be mounted to the opposite side of the structural plate 9013 and include electronics used to operate the solution pump 9000. The plate 9013 can be made out of aluminum or any other suitable al and can contain a flange 9014 to provide increased stiffiiess. The plate can also contain a series of mounting holes to provide a connection point to the top cover and bottom cover.

The top cover 9001 can engage a bottom cover 9018 to e the solution pump 9000. The two parts can engage along the edges and can be secured with screws or another fastener. A ng plate 9019 can attach to the bottom cover 9018 (labeled as 9015 in some drawings) and to, for example, the inner wall of the system 600. The top cover 9001 can also e an g 9025 for connector cables that can connect elsewhere in the system 600, such as to the controller 150.

The solution pump 9000 can engage an infusion cassette 9020 that contains the syringe 9016. In one embodiment the top cover 9001 can include a boss 9023 with a pin. As shown in FIGS. 7A, 7B, a tab 9021 on the infusion cassette 9020 can engage the pin on the boss 9023 to provide a connection between the solution pump 9000 and the infusion cassette 9020. Additionally, the solution pump 9000 can engage the infusion cassette 9020 Via a circumferential groove on the pressure sensors 9009 that can be received by a pinch release portion 9022 of the infusion cassette 9020.

The on cassette 9020 can include the delivery line 9010 with an IV bag spike 9024 at one end that can be connected to an IV bag or other external source of solution. The other end of the delivery line 9010 can be ted to a one-way check valve 9026 that is designed to allow fluid to only flow away from the IV bag and toward the syringe 9016. The one-way check valve 9026 can be connected to a connector 9027. An output line 9011 can be ted to a second one-way check valve 9032 that is ed to allow fluid to only flow away from the syringe 9016 and towards a port 9034. The one-way check valve 9032 can also be connected to the connector 9027. The output line 9011 can include a filter 9033 that filters particulate and air from the solution. The filter 9033 can be any filter with hydrophobic properties that are suitable for this purpose. The output line 9011 can also be coupled to the port 9034 that connects to the perfusion . Port 9034 can include a luer fitting. The output line 9011 can also include a roller clamp 9035 that can close the output line 9011. During use, the roller clamp 9035 can be kept open to allow fluid to pass through the output line 9011.

Referring to FIGS. 7I-7K, the connector 9027 can be, for example, a Y- connector. The tor 9027 can include tors 9043, 9044. Connector 9043 can be connected to the delivery line 9010 and connector 9044 can be connected to the output line 9011. tor 9027 can also include vertical infusion line. The vertical infusion line can connect to a connector mount. The connector 9027 can also include an alignment tab 9028.

Referring to FIGS. 7L-7P, an exemplary connector mount 9029 is shown.

Connector mount 9029 can include a connection port 9031 that can be coupled to the tor 9027 and a syringe mount 9030 that can be coupled to the syringe 9016. A pressure membrane (not shown) can be placed in the connector mount 9029 to monitor the pressure in the fluid circuit n the syringe 9016, the delivery line 9010, and the output line 9011 (e. g., using the pressure sensor 9009). The pressure membrane can be ed to the connector mount 9029 at a on opposite the connection port 9031. The connector mount 9029 can also be used to removably attach the cassette 9020 to the top cover 9001 using a snap tor. For e, wings 9055 can extend through openings in the top cover 9037. By squeezing the wings 9055 together a bottom portion 9056 can be flexed outwards releasing it from a corresponding connector portion on, for example, the pressure sensor 9009.

In one embodiment, the syringe 9016 can deliver fluid as the plunger 9017 is compressed by the nt of the carriage 9042 along the lead screw 9005 by the stepper motor 9002. The fluid from the syringe can pass into the vertical infusion line, past the y check valve 9032, into the output line 9011, through the filter 9033, and into the perfusion fluid being circulated in the system 600. Once the plunger 9017 is nearly or fully compressed so that there is little or no fluid to deliver from the syringe, the syringe can be retracted, allowing fluid to pass from the IV bag (not , through delivery line 9010, past the one-way check valve 9026, into the vertical infusion line, and into the syringe 9016, thus refilling the syringe.

The on cassette can include a top cover 9037 that can engage a bottom cover 9038, thus enclosing the syringe 9016. A gasket 9039 can provide a seal around slots 9008 in top cover 9001 to keep fluid from entering the solution pump 9000 through the slots 9008. The gasket can be made of any suitable sealing material, including foam. A shipping lock 9040 can retain the plunger 9017 and carrier in the fully retracted position so that carriage 9042 can be engaged in the home position.

One purpose of the shipping lock 9040 can be to ensure that the hole 9092 in carrier 9036 is at the correct location so that the drive pin 9003 protrudes into the hole 9092 when the user installs the cassette 9020. The shipping lock 9040 can be d before use.

As will be appreciated, the type and configuration of syringe used in the cassette 9020 can affect how the system is controlled. For example, as the bore of the syringe increases, less travel of the plunger is needed to provide a given amount of solution. Additionally, syringes can have different capacities which can affect how often the syringe needs to be refilled. Thus, it can be beneficial for the solution pump 9000 to know what kind of syringe is installed in cassette 9020. ingly, in some embodiments the system 9000 es a mechanism by which it can determine what type of syringe is included in the cassette 9020. For example, in an embodiment of the solution pump 9000 is configured to work with two different types of syringes, the pump can include a magnet and Hall effect sensor that can be configured to determine which of the two types of syringes is being used. For example, the cassette 9020 can e a magnet having N and S poles. The magnet can be oriented so that only one ofthe two poles interacts with the Hall effect sensor. When the first type of syringe is used, the N pole can be configured to interact with the Hall effect sensor and, likewise, when the second type of e is used, the S pole can be configured to interact with the Hall effect sensor. By determining which of the two poles is interacting with the Hall effect , the solution pump 9000 can determine which type of syringe is being used in the cassette 9020. The sensor configuration is exemplary only, and other sensors can be used to determine which type of syringes being used in the cassette 9020.

The solution pump 9000 can be controlled by one or more l systems.

For example, the solution pump 9000 can be controlled by the controller 150 and/or can include an internal l system. Regardless of the location of the ller, the ller can be configured to know how many partial or full rotations of the stepper motor 9002 are required to provide the necessary amount of solution and/or to refill the syringe. Thus, for example, the controller can know that it takes 40 steps of the stepper motor to provide 1 mL of solution. In some embodiments, the amount of solution provided by the solution pump 9000 can be manually controlled and/or can be controlled automatically by the controller 150.

The solution pump 631 can be red to provide solution flow rates that vary between 0.5 and 200 mL/hr, although other rates are le.

Some embodiments of the solution pump 631 can include a priming cycle that can be used to prime and eliminate air within the lines of the pump 631. For example, a user can assemble a complete line set dry and perform priming cycle until air is eliminated. For example, each priming cycle can advance 3 mL of air (or solution) using a special fast-forward and fast refill movement. In some embodiments, the prime cycle is under user control and/or can be performed automatically.

In some embodiments, when the motor 9002 is operated at a high speed (e. g., during refill and/or priming), the high-speed cycle can include a ramp-up and ramp down periods going into and coming out of peed operation. These ramp-up and ramp down s can be used to overcome the rotational inertia of the motor 9002.

This function can be implemented by the firmware and/or controller is controlling the pump 63] using, for example lookup tables that have been calculated to adjust the pulse rates of the motors 9002 for constant acceleration and/or deceleration. The ramp-up and ramp down periods can also be used during low-speed operation.

In some embodiments, the solution pump 631 can be configured to compensate for inherent backlash that can be caused when the direction of travel of the syringe is reversed. For example, fluid flow can be particularly affected by the backlash inherent in the motor 9002 and lead screw 9005. Errors caused by sh can affect the resumption of infusion flow after a refill cycle. To offset these possible errors, firmware within the pump and/or the controller can capture the pressure in the syringe chamber at the end of all on strokes. The fast refill cycle can then be executed and the firmware and/or controller can advance the plunger at a moderately fast rate until the re in the syringe chamber is equal to the re captured during the last on strokes. When that pressure is reached, all system backlash has typically been resolved and the pump can continue infusing at the desired rate.

While stepper motors typically provide the t torque for a given motor size, and can be easy to drive, they can also consume high amounts of power and can generate large amounts ofmechanical noise. Thus, in some embodiments ofthe pump 631, firmware and/or the controller can include a dynamic torque fimction that can operate the motors 9002 at the minimal torque required at any given time. This can be accomplished using l to analog converters that control the current limit of each stepper motor driver, which can in turn control the torque provided by the motor.

Accordingly, stepper motor torque can be adjusted to efficiently provide the required motion. At rest, a small current can be ed to the motor to maintain its static position without slipping. At the start of each forward infiJsion stroke, the stepper motor can be run at the selected infusion rate with a predefined minimal torque. If the encoder indicates that the stepper is not moving as desired, the torque can be increased until the proper movement is achieved. In this way, the forward on stroke can be performed at the l torque required to do the job.

The solution pump 631 can also be configured to make up for slippage between the actual position and the desired position of the syringe plunger. For example, when firmware and/or the controller determines that the syringe position (e.g. provided by an encoder) has slipped behind the desired profile, it can double the rate until the syringe position s up. This process of ng, torque increase, and/or rate doubling can happen quickly enough to provide uninterrupted on at the selected rate. shows an exemplary embodiment of a microcontroller architecture that can be included in the on pump 631, although this is not required and other configurations are possible. In this embodiment, the microcontroller architecture includes a processor (e. g. PIC 18F8722 processor) that receives inputs from, for example, the controller 150, pressure input sensors, motor current and diagnostic voltage sensors, Hall magnetic sensors, photo interrupters, and/or encoder inputs.

Using the information it es, the processor can provide feedback to the controller 150 and/or can l the stepper motor drive to actuate the syringes in the respective channels.

. Gas system, including variable delivery rate control The multiple use module 650 can include an on-board gas supply such as one or more common gas ers that can fit into the gas tank bay 630 and/or an oxygen trator. The gas supply system can include: i) one or more regulators to reduce the pressure of the gas provided by one or more gas cylinders, ii) pressure sensors that are configured to measure the pressure in the gas supply, and ii) gas pressure gauge that can provide a visual indication of the fullness of the gas supply. Each of these components can be ly lled and/or can be connected and automatically controlled by the ller 150. For example, the controller 150 can automatically regulate the gas flow into the gas exchanger 114. While the gas provided by the gas provided by the gas source can vary, in some ments, the gas supply can provide a gas comprised of 85% 02, 1% C02, and the balance N2 with a blend process accuracy of 0.030%, while in some embodiments the gas supply can be between 50% 02 and 95% 02 and the balance N2 and/or Ar. In some embodiments the multiple gasses can be supplied premixed from a single cylinder or can be provided from multiple gas cylinders and mixed within the system 600. In some embodiments gas can be supplied from a portable oxygen concentrator, such as the Oxus Portable Oxygen Concentrator from Oxus, Inc. of Rochester Hills, M1, or a Freestyle series portable oxygen concentrator ble from AirSep, or Buffalo, NY.

In some embodiments the system 600 can support a gas flow rate of 0 — 1000 mL/min and can have a set point resolution of 50 ml/min With a gas flow delivery accuracy of :: 20% in the range from 200 — 1000 mL/min. The system 600 and the gas supply 172 can be red to provide a gas flow in the event of a circulatory pump fault. The ranges listed above are ary, and values outside of those specifically identified can also be used. , in some embodiments the system 600 and the gas supply 172 can be configured to provide an indicator of the pressure in the gas supply 172 Via multiple interfaces (e. g., Via a gauge on the gas supply 172 and/or the operator interface module 146). 6. Controller and user interface The system 600 can include a control system (e. g., controller 150) that controls the overall operation of the system 600 and the components used therein. At a general level, the control system can include an d computer system that is ted to one or more of the components in the system 600 and to one or more sensors, network connections, and/or user inputs. Using the information obtained from the sensors, network connections, and/or user inputs, the control system can control the s components in the system 600. For example, the control system can be used to implement one or more open or closed feedback systems to control operation of the system 600. The control system can be a common off-the-shelf computer and/or a specially designed computer system. It should be noted that although the system 600 is described conceptually with reference to a single controller, the control of the system 600 can be distributed in a plurality of controllers or processors. For e, any or all of the described subsystems may include a dedicated processor/controller. ally, the dedicated processors/controllers of the various subsystems may communicate with and Via a l controller/processor. For example, in some embodiments, a single controller located in the multiple-use module 650 can control the entire system 600, in other embodiments a single controller located in the single-use module 634 can control the entire system 600, and in still other embodiments, the controller can be split between the single-use module 634 and the le-use module 650.

As a fiarther example, in some embodiments, the controller 150 can be located on the main circuit board 718 and can perform all control and processing required by the system 600. However, in other embodiments, the controller 150 can distributed, locating some processing functionality on the front end interface circuit board 636, some on the power circuit board 720, and/or some in the operator interface module 146. Suitable cabling can be provided between the various circuit boards, ing on whether and the degree to which the controller 150 is distributed within the system 600. depicts an exemplary block diagram of an illustrative control scheme for the system 600. For example, the system 600 can include a controller 150 for controlling operation of the system 600. As shown, the controller 150 can connect interoperationally several subsystems: an operator interface 146 that can assist an operator in ring and controlling the system 600 and in monitoring the condition ofthe organ; a data acquisition subsystem 147 that can include various sensors for obtaining data relating to the organ and to the system 600, and for conveying the data to the controller 150; a power management subsystem 148 for providing fault tolerant power to the system 600; a heating subsystem 149 for providing controlled energy to the heater 110 for g the perfiision fluid 108; a data management subsystem 151 for storing and maintaining data relating to operation of the system 600 and with respect to the liver; and a pumping subsystem 153 for controlling the pumping of the perfusion fluid 108 through the system 600.

An exemplary embodiment of the data acquisition subsystem 147 will now be described with reference to In this ment, the data acquisition subsystem 147 e sensors for obtaining information pertaining to how the system 600 and the liver is functioning. The data acquisition subsystem 147 can provide this information to the ller 150 for sing. For example, the data ition subsystem 147 can be d to the following sensors: ature s 120, 122, 124; pressure sensors 126, 128, 130 (which can be the pressure sensors 130a, 130b referred to elsewhere herein); flow rate sensors 134, 136, 138; the oxygenation/hematocrit/temperature sensor 140; Hall sensors 388; shaft encoder 390; battery sensors 362a, 362b, 362c; external power available sensor 354; and operator WO 87737 interface module battery sensor 370; a gas pressure sensor 132. How the system 600 uses the ation from the data acquisition subsystem 147 will now be described with regard to the heating 149, power management 148, pumping 153, data management 151, and operator ace 146 subsystems. ing to , this figure depicts an exemplary block diagram of the power management system 148 for providing fault nt power to the system 600.

The system 600 can be powered by one of multiple sources such as an external power source (e.g., 60 Hz, 120 VAC in North America or 50 Hz, 230 VAC in Europe) or by any of the one or more ies 352. While the remainder of this description refers to an AC power source as the external power source, it is to be understood that a DC power source can also be used. The controller 150 can receive data from an AC line voltage availability sensor 354, which can indicate whether the AC voltage 351 is available and/or sufficient for use by the system 600.

In response to the controller 150 detecting that external power is not available, the controller 150 can signal the power ing try 356 to provide system power from the one or more batteries 352. The ller 150 can determine from the battery charge sensors 362 which of the one or more batteries 352 is most fully charged, and can then switch that y into ion by way of the switching network 356. The system can be designed to prevent interruptions in the operation of the system 600 as the power is switched from one source to another.

Alternatively, in response to the controller 150 detecting that suitable external power is available, the controller 150 can determine whether to use the external power for providing system power and for providing power to the user interface module 146, for charging the one or more batteries 352, and/or for charging the internal battery of user interface module 146, which can also have its own internal r and charging controller. To use available external power (e. g., AC power 141) the controller 150 can draw the external power into the power management system 148 by signaling through the switching system 164. In the event that the external power source is AC, the power management system 148 can also receive the external AC and convert it to a DC for providing power to the system 600. The power management system 148 can be universal and can handle any line frequencies or line voltages commonly used throughout the world. According to the illustrative embodiment, in response to a low battery indication from one or more of the battery sensors 362, the controller 150 can also direct power via the switching network 364 and the ng circuit 366 to the appropriate battery. In response to the controller 150 receiving a low battery signal from the sensor 370 (which can r a battery in the user interface module 146), it can also or alternatively direct a charging voltage 367 to the user ace battery 368. In some embodiments, the power ment subsystem 148 can select batteries to power the system 600 using an algorithm to best provide for battery longevity, including selecting in order of least-charged first as well as other factors, such as least number of charge cycles. If the battery that is currently being used to power the system 600 is removed by the user, the power management subsystem 148 can automatically switch to the next battery per the algorithm to continue powering the system 600. ing to , an exemplary ment of the heating subsystem 149 is shown. The heating tem 149 can control the temperature of the perfusion fluid 108 within the system 600 through, for example, a dual feedback loop approach.

In the first loop 251 (the perfusion fluid temperature loop), the perfusion fluid temperature thermistor sensor 124 provides two (fault tolerant) signals 125 and 127 to the controller 150. The s 125 and 127 are typically indicative of the temperature of the perfusion fluid 108 as it exits the heater assembly 110. The controller 150 can regulate the drive signals 285 and 287 to the drivers 247 and 249, respectively. The drivers 247 and 249 can convert corresponding digital level signals 285 and 287 from the ller 150 to heater drive signals 281 and 283, respectively, having sufficient current levels to drive the first 246 and second 248 heaters to heat the perfusion fluid 108 to within a desired temperature range. In response to the controller 150 detecting that the perfusion fluid temperatures 125 and 127 are below the desired temperature range, it can set the drive signals 281 and 283 to the first 246 and second 248 heaters, respectively, to a sufficient level to continue to heat the perfusion fluid 108. Conversely, in response to the controller 150 detecting that the perfusion fluid temperatures 125 and 127 are above the desired temperature range, it can decrease the drive signals 281 and 283 to the first 246 and second 248 heaters, respectively. In response to detecting that the temperature of the perfusion fluid 108 is within the desired temperature range, the controller 150 can maintain the drive signals 281 and 283 at constant or ntially constant . The temperature control system can be lled to warm the perfusate to a temperature range between 0 — 50° C, and more cally between 32 — 42° C, and even more specifically between 32 — 37° C. These ranges are ary only and the temperature control system can be controlled to warm the perfusate to any temperature range falling within 0 — 50° C. The desired temperature can be user- selectable and/or automatically controlled by the controller 150. As used herein and in the claims, “normothermic” is defined a temperature between 34-37° C.

In some embodiments, the controller 150 can vary the drive signals 281 and 283, which can control the first and second heaters, in substantially the same manner. r, this is not required. For e, each heater 246 and 248 may respond differently to a particular current or voltage level drive signal. In such a case, the controller 150 can drive each heater 246 and 248 at a slightly different level to obtain the same temperature from each. In some embodiments, the heaters 246 and 248 can each have an associated calibration factor, which the controller 150 stores and employs when ining the level of a particular drive signal to provide to a particular heater to achieve a particular temperature result. In certain configurations, the controller 150 can set one of the stors in dual sensor 124 as the default thermistor, and will use the temperature reading from the default thermistor in ces where the thermistors give two different temperature readings. In some embodiments, where the temperature readings are within a pre—defined range, the controller 150 can use the higher of the two readings. The drivers 247 and 249 can apply the heater drive signals 28] and 283 to corresponding drive leads 282a and 282b on the heater assembly 110.

In the second loop 253 (the heater temperature loop), the heater ature sensors 120 and 122 can provide signals 121 and 123, indicative of the temperatures of the heaters 246 and 248, respectively, to the controller 150. According to the illustrated embodiment, a temperature ceiling can be established for the heaters 246 and 248 (e.g., by default, operator selection, or automatically determined by the controller 150), above which the temperatures of the s 246 and 248 are not allowed to rise. As the temperatures of the heaters 246 and 248 rise and approach the temperature ceiling, the sensors 121 and 123 can indicate the same to the controller 150, which can then lower the drive signals 281 and 283 to the heaters 246 and 248 to reduce or stop the supply of power to the heaters 246 and 248. Thus, while a low ature signal 125 or 127 from the perfusion fluid temperature sensor 124 can cause the controller 150 to increase power to the heaters 246 and 248, the heater temperature sensors 120 and 122 ensure that the heaters 246 and 248 are not driven to a degree that would cause their respective heater plates 250 and 252 to become hot enough to damage the perfusion fluid 108.

In some embodiments, the controller 150 can be configured to maintain the perfusion fluid temperature between 0-50° C. In some embodiments the perfiJsate is ined within a temperature range of 32-42° C, or in some more specific embodiments in the rage of 35-3 7° C. In some embodiments, the controller can be configured to limit the temperature of the heater plates 250 and 252 to 38° C, 39° C, 40° C, 41° C, or 42° C. All of the ranges and numbers identified herein are ary and values outside of these ranges can also be used. Lastly, to the extent that the claims recite “substantially” in connection with a specific ature value or range, this means that the ature is to be within the operational temperature swing range of the heater/control system used. For example, if the claimed temperature is “substantially 32° C,” and a heater/control system is used in an accused product that maintains the temperature within :: 5% of a desired value, then any temperature that is i 5% of 32° C is “substantially 32° C.” As can be seen, the second loop 253 can be configured to override the first loop 251, if necessary, such that temperature readings from temperature sensors 120 and 122 indicating that the s 246 and 248 are approaching the maximum allowable temperature override the effect of any low temperature signal from the perfusion fluid temperature sensor 124. In this respect, the subsystem 149 can ensure that the temperature of the heater plates 250 and 252 do not rise above the maximum ble temperature, even if the temperature of the-perfilsion fluid 108 has not reached the desired temperature value. This override feature can be particularly ant during failure situations. For example, if the perfusion fluid ature sensors 124 both fail, the second loop 253 can stop the heater assembly 110 from overheating and damaging the perfiision fluid 108 by ing control exclusively to the heater temperature sensors 120 and 122 and ng the temperature set point to a fixed value. In some embodiments, the controller 150 can take into t two time constants assigned to the delays associated with the temperature measurements from the heaters 246 and 248 and perfilsion fluid 108 to optimize the dynamic response of the temperature controls.

In some embodiments, the user can be provided with the option to disable the blood warming feature of the system 600. In this manner, the system can more efficiently support cooling of the liver during the post-preservation chilling procedure.

In some embodiments, the heater ly 110 (or a separate device, such as a gas ger with integrated cooling interface) can function as a chiller to cool the temperature of the perfusion fluid. g now to the operator interface subsystem 146, FIGS. 12A-12G show various exemplary display screens of the operator interface subsystem 146. The display screens can enable the operator to receive information from and provide commands to the system 600. A depicts an exemplary top level "home page" screen 400. From the screen 400 an operator can typically access most if not all of the data available from the data acquisition subsystem 147, and can typically provide any d commands to the controller 150. For example, a user can monitor and adjust the pumping subsystem 153 via the screen 400. As described in more detail in reference to FIGS. G, the screen 400 can also allow the operator to access more detailed display screens for obtaining information, ing commands and setting operator selectable parameters.

In this exemplary embodiment, the screen 400 includes various portions each displaying ent pieces of information and/or ing different inputs. However, screen 400 is exemplary only and the information displayed by the screen 400 can be customized by the user (e.g., using dialog 590 described below in F). The values displayed on the screen 400 can be updated at regular als such as once every second. In this particular example, the screen 400 includes the ing 0 Portion 402 that displays the hepatic artery flow rate. This value can be an indication of the flow at the flow sensor 138b. o Portion 404 that ys the portal vein flow rate. This value can be an indication of the flow at the flow sensor 138a. o Portion 406 that displays the oxygen saturation (SvOz) of the perfusion fluid leaving the liver as measured by, for example, the sensor 140. o Portion 408 that displays the hematocrit (HCT) level of the perfilsion fluid leaving the liver as measured by, for example, the sensor 140. o Portion 410 that displays the desired and measured temperature of the perfiisate. In this embodiment, the , top number represents the measured temperature whereas the smaller number listed below represents the temperature at which the desired perfusate temperature is set. The temperature can be ed from one ofmore locations such as at the output of the heater assembly 110 using the temperature sensors 120 and 122, and in some ments sensor 140. o Portion 412 that displays the flow rate as measured by flow sensor 136. o Portion 414 that displays ic/diastolic pressure in the hepatic artery. The number in parentheses below the systolic/diastolic pressures is an arithmetic mean of the pressure waveform. This systolic/diastolic/mean pressure in the hepatic artery can be determined by the pressure sensor 130a. o Portion 416 that ys a waveform of the hepatic artery pressure over time. o Portion 418 that displays systolic/diastolic pressure in the portal vein.

Number in parentheses below the systolic/diastolic pressures is an arithmetic mean of the two. The systolic/diastolic pressure in the portal vein can be determined by the pressure sensor 13%. o Portion 420 that displays a waveform of the portal vein pressure over time. o Portion 422 that ys the hepatic artery pressure ed over time (e.g., two minutes). 0 Portion 424 that displays the hepatic artery flow rate averaged over time (e.g., two minutes). 0 Portion 426 that a graphical representation of the values from portion 422 and 424 over time. In this embodiment, the graph represents a 3 1/2 hour time window. In some embodiments, the portion 426 can be controlled by the user to show different periods of time. o n 428 that displays an icon showing that the perfusion pump is running. 0 Portion 429 (which is not illuminated in this e) can show an organ type indicator that indicates which organ is being perfused and which mode of operation is being used. For example, an “M” can be used to indicate that the system 600 is in a maintenance mode. 0 Portion 430 that displays the status of a storage medium included in the system 600 (e.g., an SD card). o Portion 432 that displays the flow rate from the onboard gas .

This portion can also display the amount of time remaining before the onboard gas supply runs out. o Portion 434 that displays the status of the power supply system. In this ment, the system 600 includes three batteries, where each battery has a corresponding status indicator showing the degree to which the battery is charged. This portion also tes whether the system 600 is connected to an external power source (by showing a plug icon). In some embodiments, this portion can also include a numerical indication of the amount of time that the batteries can run the system 600 in the current mode of ion. 0 Portion 436 that displays the status and charge remaining of the battery included in the operator interface module 146. This portion can also include an indication of the amount of time remaining for which the battery in the operator interface module 146 can support it in a wireless mode of operation. 0 Portion 438 that displays the status of a network and/or ar connection. This portion can also identify r the operator interface module 146 is operating in a wireless 464 fashion, along with a graphical representation 463 of the th of the wireless connection between the operator interface module 146 and the remainder of the system 600. 0 Additional portions can be displayed to show when one or more alarms and/or ns of the system 600 have been disabled by the user.

As can be seen in A—12G some ns can also include alarm range indicators (e.g., indicator 440) that indicates where the current value falls within an allowable range. Each portion can also e an alarm indicator (not shown) indicating that the respective values are outside of the range indicated by the corresponding range indicator. The range indicator for each tive value can be tied to the alarm values set in dialog 512 or independently set by the user. The screen 400 can be implemented on a touch screen interface. In portions that accept user input, the user can touch a specific portion to change the value therein using the knob 626.

Referring to FIGS. 12B, 12C, and 12D, a user can select to enter a configuration menu 484. In some embodiments of the system, the configuration menu 484 can be limited to a n of the screen so that the user can continue to monitor the ation displayed on the screen. Using the configuration menu, the user can program desired operational parameters for the system 600. In this embodiment of the ration menu 484, the menu has three tabbed pages 484a, 484b, 484C (“Liver,” “System,” and “Actions”).

In tabbed page 484a, the Liver tab is shown. In this tab the user is able to enter alarm dialog 512 (described below with respect to E), select the data shown in the middle graphic frame, select the data shown in the bottom graphic frame, set the desired gas flow rate, and set the desired temperature. Changes made in the tabbed page 484a can be reflected in the screen 400.

In tabbed page 484b, the System tab is shown. In this tab, the user can adjust one or more display features of the system 600. For example, the user can select which units are used to display the various measurements (e.g., pascal versus mmHg), can restore factory defaults, can store new default settings, and can e saved default settings. From this tab a service technician can also enable a wireless connection from a service laptop to the system 600. Changes made in the tabbed page 484b can be reflected in the screen 400.

In tabbed page 4840, the Actions tab is shown. In this menu, the user can display the status of the machine, display a summary of all of the alarms, can adjust the scale of displayed measurements, and/or can interact with the data stored by the system 600. For example, in some embodiments the user can withdraw a sample of the perfiasion fluid and perform an external test on it. The user can then manually enter the value obtained by the external test into the data stream being maintained by the system 600. In this , system 600 can e all data relevant to the organ being transplanted, regardless of whether that data was ted externally from the system 600.

Referring to E, alarm dialog 512 displays the ters associated with the operation of the system 600. In this embodiment, there are alarms for hepatic artery flow (HAF), portal vein pressure (PVP), hepatic artery pressure (HAP), inferior vena cava pressure (IVCP), perfiasion fluid temperature (Temp), oxygen saturation (SvOz), hematocrit (HCT). More of fewer ters can be included in the dialog 512. Row 514 indicates an upper alarm limit (e.g., a value above this number will cause an alarm) and row 516 indicates a lower alarm limit (e.g., a value below this number will cause an alarm). The user can also enable/disable individual alarms by selecting the ated alarm icon in row 518. The icons in row 518 can indicate whether an individual alarm is enabled or disabled (e. g., in E the alarm for IVCP is disabled). The alarm limits can be predetermined, user le, and/or determined in real-time by the ller 150. In some ments, the system 600 can be red to automatically switch between sets of alarm limits for a given flow mode upon changing the flow mode. Changes made in the dialog 512 can be reflected in the screen 400.

F shows an exemplary user interface (dialog 590) in which a user can select what the various portions of screen 400 display. For example, in F, the user can choose to display the realtime waveform of the hepatic artery pressure, portal vein pressure or IVC pressure, or choose to y trend graphs for those or other measured parameters in a portion of the screen 400. Other waveforms can also be calculated and displayed by the controller 150.

G shows an exemplary user interface (dialog 592) in which a user can adjust parameters of the g subsystem 153. In this example, the user can adjust the pump flow and turn the pump on/off.

The data management subsystem 151 can receive and store data and system information from the various other subsystems. The data and other information can be downloaded to a portable memory device and organized within a database, as desired by an operator. The stored data and information can be accessed by an operator and displayed through the operator interface subsystem 146. The data management system 151 can be configured to store in the information in one or more places. For example, the data management subsystem 151 can be configured to store data in storage that is internal to the system 600 (e.g., a hard drive, a flash drive, an SD card, a compact flash card, RAM, ROM, CD, DVD) and/or external to the system (e.g., a remote storage memory or Cloud storage).

In embodiments using external storage, the data management subsystem 151 (or another part of the controller 150) can communicate with the al storage over various communication connections such as point-to-point network connections, intranets, and the Internet. For example, the data ment subsystem 151 can communicate with a remote storage medium or “the Cloud” (e.g., data s and storage devices on a shared and/or private network) via a WiFi network (e.g., 802.11), a cellular connection (e. g., LTE), a Bluetooth (e. g., 802.15), infrared tion, a satellite-based connection, and/or a hard-wired network connection (e.g., Ethernet).

In some embodiments, the data ment subsystem can be configured to automatically detect the best network connection to communicate with the remote storage device and/or Cloud. For example, the data management subsystem can be red to default to known WiFi networks and automatically switch to a cellular network when no known WiFi networks are available. Remote and Cloud based embodiments are discussed more fully below.

Referring to H, the pumping subsystem 153 will now be described in further detail. The controller 150 can operate the pumping subsystem 153 by sending a drive signal 339 to a brushless three—phase pump motor 360 using Hall Sensor feedback. The drive signal 339 can cause the pump motor shaft 337 to , thereby causing the pump screw 341 to extent and retract the pump driver 334. According to the illustrative embodiment, the drive signal 339 is controlled to change a rotational direction and rotational velocity of the motor shaft 337 to cause the pump driver 334 to extract and retract cyclically. This cyclical motion can pump the perfilsion fluid through the system 600.

The controller 150 can receive a first signal 387 from the Hall s 388 positioned integrally within the pump motor shaft 337 to te the position of the pump motor shaft 337 for purposes of commutating the motor winding currents. The controller 150 can receive a second higher resolution signal 389 from a shaft r sensor 390 indicating a precise onal position of the pump screw 341. From the current motor commutation phase position 387 and the current onal position 389, the ller 150 can calculate the appropriate drive signal 339 (both magnitude and polarity) to cause the necessary rotational change in the motor shaft 337 to cause the 2015/033839 riate position change in the pump screw 341 to achieve the desired pumping action. By varying the magnitude of the drive signal 339, the controller 150 can vary the pumping rate (i.e., how often the pumping cycle repeats) and by varying the rotational ion changes, the controller 150 can vary the pumping stroke volume (e. g., by varying how far the pump driver 334 moves during a cycle). Generally speaking, the cyclical pumping rate regulates the pulsatile rate at which the ion fluid 108 is provided to the liver, while (for a given rate) the pumping stroke regulates the volume of perfusion fluid provided to the liver.

Both the rate and stroke volume affect the flow rate, and indirectly the pressure, of the perfusion fluid 108 to the liver. As described herein, the system 600 can e three flow rate s 134, 136 and 138, and three pressure sensors 126, 128, and 130. The sensors 134, 136, and 138 can provide corresponding flow rate signals 135, 137 and 139 to the controller 150. Similarly, the sensors 126, 128 and 130 can provide corresponding pressure signals 129, 131 and 133 to the controller 150. The controller 150 can use all of these signals in feedback to ensure that the commands that it is providing to the perfusion pump 106 have the desired effect on the system 600. In some instances, the controller 150 can generate various alarms in response to a signal indicating that a ular flow rate or fluid pressure is e an acceptable range. Additionally, employing multiple sensors enables the controller 150 to distinguish between a ical issue (e.g., a conduit blockage) with the system 600 and a biological issue with the liver.

While the above discloses the use of three pressure sensors, this is not required. In many of the ments described herein only two pressure sensors are used (e. g., pressure s 130a, 130b). In this instance, the input for the third pressure sensor can be ignored. However, in some ments of the system disclosed herein a third pressure sensor can be used to measure the pressure in the perfusion fluid flowing from the inferior vena cava (or elsewhere in the system 100).

In this instance, the controller 150 can process the pressure signal from the sensor as described above.

The pumping system 153 can be configured to control the position of the pump driver 334 during each moment of the pumping cycle to allow for finely tuned pumping rate and volumetric profiles. This can enable the pumping system 153 to supply perfusion fluid 108 to the liver with any desired pulsatile pattern. According to one illustrative ment, the onal position of the shaft 337 can be sensed by the shaft encoder 390 and adjusted by the controller 150 at least about 100 increments per revolution. In another illustrative embodiment, the rotational position of the shaft 337 is sensed by the shaft r 390 and adjusted by the controller 150 at least about 1000 increments per revolution. According to a further illustrative embodiment, the rotational position of the shaft 337 is sensed by the shaft encoder 390 and adjusted by the controller 150 at least about 2000 increments per revolution. The position of the pump screw 341 and thus the pump driver 334 can be calibrated initially to a nce position of the pump screw 341.

As described above, the system 600 can be manually controlled using the controller 150. r, some or all of the control of the system can be ted and performed by the controller 150. For example, the controller 150 can be configured to automatically control the pump 106 flow of the perfusion fluid (e.g., re flow rate), the solution pump 63], the pump 106, the gas exchanger 114, the heater 110, and/or the flow clamp 190. Control of the system 600 can be accomplished using minimal, or even no intervention by the user. For example, the controller 150 can be mmed with one or more predetermined routines and/or can use information from the various sensors in the system 600 to implement open and/or closed feedback loops. For e, if the controller determines that the oxygenation level of the perfusion fluid flowing out of the IVC is too low or the C02 level is too high, the controller 150 can adjust the supply of gas to the gas exchanger 114 accordingly. As another example, the controller 150 can control the infiision of one or more solutions based on the sensor 140 and/or any other sensor in the system 600. As a still further example, if the ller senses that the liver is producing too much C02, the controller can reduce the temperature of the liver to 35° C (assuming it was previously being maintained as a higher temperature) to reduce the metabolic rate, and accordingly the rate of C02 production or 02 consumption. As yet another example, the controller 150 can modulate gas flow to the gas exchanger 114 based on measurements from one or more sensors in the system 600.

In some embodiments, the controller 150 can be configured to control aspects of the system 600 as a flinction of lactate value in the perfusion fluid. In one embodiment, le perfusion fluid lactate values can be obtained over time. For example, a user can withdraw a perfusion fluid sample and use an external blood gas analyzer to ine a lactate value and/or the system 600 can use an onboard lactate sensor (e.g., a lactate sensor d in the measurement drain 2804). The lactate value can be ed in the IVC or elsewhere and can be repeated at predetermined time intervals (e.g., every 30 minutes). The controller 150 can e the trend of the lactate values over time. If the lactate is trending down or staying relatively even, this can be an indication that the liver is being properly perfiised. If the lactate is trending upwards, this can be in indication of improper perfusion, which can result in the controller 150 increasing pump flow, adjusting the rate of infused vasodilator, and/or IO ing the gas flow to the gas exchanger ll4.

Automating the control s can provide many benefits ing providing finer control over the parameters of the system, which can result in a healthier liver and/or reducing the burden on the user.

In some embodiments, the system 600 can include a global positioning device to track the geographic location of the system.

C. Exemplary single use module g now to the single use module, an exemplary embodiment is described herein as the single-use module 634, although other embodiments are possible. As noted above, this portion of the system 600 typically contains at least all of the ents of the system 600 that come into t with biological material such as the perfusate along with various peripheral components, flow conduits, sensors, and support electronics used in connection with the same. After the system 600 is used to transport an organ, the single-use module can be removed from the system 600 and discarded. A new (and sterile) single-use module can be installed into the system 600 to transport a new organ. In some embodiments, the module 634 does not include a processor, instead relying on the controller 150, which can be distributed between the front end interface circuit board 636, the power circuit board 720, the operator interface module 146, and the main t board 718, for control. However, in some embodiments, the single-use module can include its own ller/processor (e.g., on the front end circuit board 637).

Referring to FIGS. l3A-13H, an exemplary single use module 634 is shown.

FIGS. l3M-R show another exemplary single use module 634 with an alternatively WO 87737 shaped organ chamber 104. Note, however, in some of the views certain components have been omitted to clarify the drawings (e.g., some of the tubing connectors, ports, and/or clamps have been omitted).

The single-use module 634 can include a chassis 635 having upper 750a and lower 750b sections. The upper section 750a can include a platform 752 for supporting various components. The lower section 750b can support the platform 752 and can include structures for pivotably connecting with the multiple use module 650.

The lower chassis section 750b can include a C-shaped mount 656 for rigidly mounting the perfusion fluid pump interface assembly 300, and the tion 662 for sliding into and snap fitting with the slot 660. In some embodiments, the lower chassis section 750b can also provide structures for ng parts of the perfusion circuit including the following components: gas exchanger 114, heater assembly 110, reservoir 160, perfusate flow compliance chambers 184, 186. In some embodiments, the lower chassis section 750b can also contain, via appropriate mounting hardware, various sensors such as the sensor 140, the flow rate sensors 136, 138a, 138b, and the pressure sensors 130a, l30b. The lower chassis section 750b can also mount the front end circuit board 637. This embodiment is exemplary only, and components listed above as being part of the lower s section 750b can be located elsewhere such as in the upper section 750a (e. g., the re sensors 130a, 130b).

The upper chassis section 750a can include the rm 752. The platform 752 can include handles 753a and 753b formed therein to assist in installing and removing the single use module 634 from the le use module 650, although the handles can be located ere in the single use module 634. The platform 752 can include one or more orifices (e.g., 717) to allow tubing and/or other components to pass therethrough. The platform 752 can also include one or more integrally formed brackets (e.g., 716) to hold components in place atop the platform 752, such as the fluid injection and/or sampling ports described more fully below. The upper chassis section 750a can also include a flow clamp 190 for regulating the flow of perfusion fluid to the portal vein, as described more fully below. The organ chamber assembly 104 can be configured to mount to the platform 752 via one or more supports 719.

Referring specifically to 1, the organ r ly 104 can be mounted so that the left and right sides ive to the main drain) are at approximately a 15° angle with respect to the platform 752. Doing so can help perfusion fluid drain from the organ chamber assembly 104, especially during ent conditions that can be encountered during transport (e.g., takeoff and landing in an ne). 1. Organ chamber The system 600 can include an organ chamber that is red to hold an ex vivo organ. The design of the organ chamber can vary depending on the type of organ. For example, the design of the organ chamber can vary depending on whether, for example, it is being used to transport a liver, a heart, and/or lungs. While the following description focuses on an organ chamber 104 that is configured to transport a liver, this ment is exemplary only, and other configurations are possible. For e, other configurations of the organ chamber 104 can also be used to ort a liver. 21) Shape/drain structure Referring to FIGS. 14A — 14H, an exemplary embodiment of the organ chamber 104 is shown from multiple views. In this embodiment, the organ chamber 104 includes a base 2802, a front piece 2816, a removable lid 2820, and a support surface 2810 (which is described in detail with respect to FIGS. 15A — 15D). In some embodiments, the organ chamber 104 can also include a pad 4500 to support the liver. The bottom of the organ r 104 can be configured with a quasi-funnel shape where the sides of the funnel are angled at approximately 15° relative to the platform 752, this is illustrated more clearly in 1.

The general level, the base member 2802 can include one or more drains (e.g., 2804, 2806), one more orifices (e. g., 2830) for tubing, connectors, and/or instruments to be ed inside of the organ chamber 104 while the lid (e.g., 2820) is closed, one or more hinge portions (e.g., 2832), and one or more ng brackets (e. g., 2834).

In some embodiments, as shown in 1, the mounting brackets 2834 are molded.

In some embodiments, the base member 2802 is red to fit and support the support surface 2810, on which the liver typically rests. The organ chamber 104 and the support surface 2810 can be made from any suitable polymer plastic, for example, polycarbonate.

The base 2802 of chamber 2204 can be shaped and positioned within the system 600 to facilitate the drainage of the perfusion medium from the liver 101. The organ chamber 104 can have two drains: measurement drain 2804, and main drain 2806, which can e overflow from the measurement drain. The measurement drain 2804 can drain perfusate at a rate of about 0.5 L/min, considerably less than ion fluid 250 flow rate through liver 101 of between and 1-3 L/min. The measurement drain 2804 can lead to sensor 140, which can e SaOz, hematocrit values, and/or temperature, and then leads on to reservoir 160. The main drain 2806 can lead directly to the defoamer/fllter 161 without passing through the sensor 140.

In some embodiments, the sensor 140 cannot obtain te measurements unless perfusion fluid 108 is substantially free of air s. In order to achieve a bubble- free column of perfusate, base 2802 is shaped to collect ion fluid 108 draining from liver 101 into a pool that collects above the measurement drain 2804. The perfusate pool typically allows air bubbles to dissipate before the perfusate enters drain 2804. The formation of a pool above drain 2804 can be promoted by optional wall 2808, which can partially block the flow of perfiisate from measurement drain 2804 to main drain 2806 until the perfusate pool is large enough to ensure the dissipation of s from the flow. Main drain 2806 can be lower than measurement drain 2804, so once perfusate overflows the depression surrounding drain 2804, it flows around and/or over wall 2808, to drain from main drain 2806.

In an alternate embodiment of the dual drain system, other systems are used to collect perfusion fluid into a pool that feeds the measurement drain. In some embodiments, the flow from the liver is directed to a vessel, such as a small cup 2838, which feeds the measurement drain. The cup 2838 fills with perfiision fluid, and excess blood overflows the cup and is directed to the main drain and thus to the reservoir pool. In this ment, the cup 2838 performs a fianction similar to that of wall 2808 in the embodiment described above by forming a small pool of perfusion fluid from which bubbles can dissipate before the perfusate flows into the ement drain on its way to the oxygen sensor. In still other ments of the measurement drain, a gradual depression can be formed in the bottom of the base 2802 around the measurement drain 2804 that performs the same fiJnction as the cup described above.

The top of organ chamber 104 can be covered with a sealable lid that includes front piece 2816, removable lid 2820, inner lid with sterile drape (not shown), and sealing piece 2818. The removable lid 2820 can be hingedely and removably coupled to the base member 2802 via hinge portions 2832. The sealing piece 28 l 8 can seal the front piece 2816 and/or base 2802 to lid 2820 to create a fluid and/or airtight seal.

The sealing piece 2818 can be made out of, for example, rubber and/or foam. In some embodiments, the front piece 2816 and lid 2820 is rigid enough to protect the liver 101 from physical contact, indirect or direct.

An alternative embodiment of the organ chamber is shown from multiple views in FIGS. l4I—S. In this embodiment, the base 2802 of the organ chamber 104 has a different shape. FIGS. K show a top views, FIGS. l4L-l4O show side views, FIGS. l4P-14R show bottom views, and S shows a break out of the IO alternative embodiment. The organ chamber 104 es a base 2802, an organ support surface 2810, and a removable lid 2820.

For example, the top of the organ chamber can be covered with a single sealable lid 2820. The removable lid can be hingedly and bly coupled to the organ r base member via hinge ns 2832. The lid is fastened to the base through a series of latches 2836 or other isms. The sealing piece 2818 of the lid can be made ofrubber and/or foam, and it can seal the lid to the base to create a fluid or airtight seal. The combination of the lid and base is rigid enough to protect the liver from direct or indirect physical contact. The organ chamber contains orifices (e. g., 2830) for conduit connections for cannulated vessels, including the HA, PV and bile duct. The organ chamber contains a structure 2840 positioned above the measurement drain 2804 that holds the end of the IVC in place during ort of the organ. This structure directs the perfusate exiting from the IVC cannula to the ement drain.

In an alternate embodiment (not shown), the organ chamber 104 can include a double lid system that includes an inner lid and an outer lid. More particularly, in one ment, the organ chamber assembly can e a housing, an outer lid and an intermediate lid. The housing can e a bottom and one or more walls for containing the organ. The intermediate lid can cover an opening to the housing for substantially enclosing the organ within the housing, and can include a frame and a flexible membrane suspended within the frame. The flexible membrane can be transparent, opaque, translucent, or substantially transparent. In some embodiments, the flexible membrane includes sufficient excess membrane material to contact an organ contained within the chamber. This feature can enable a medical operator to 2015/033839 touch/examine the organ indirectly through the membrane while still maintaining sterility of the system and the organ. For example, the area of the membrane in the intermediate lid can be 100-300% larger than the area defined by the intermediate lid frame or have an area that is 100-300% larger than a two-dimensional area occupied by the liver. In some embodiments, the flexible membrane can be selected so that an operator can perform an ultrasound of the liver through the ne while maintaining the sterility and/or nment of the r.

In some embodiments, the intermediate lid can be hinged to the housing. The intermediate lid can also include a latch for securing the intermediate lid closed over the opening of the organ chamber. The outer lid may be similarly hinged and latched or completely ble. In some configurations, gaskets are provided for forming a fluid and/or airtight seal between the intermediate lid frame and the one or more organ chamber walls, and/or for forming a fluid and/or airtight seal between the periphery of the outer lid and the frame of the intermediate lid. In this manner, the environment nding the liver 10] can be maintained regardless of whether the outer lid is open.

Covering the organ r 104 can serve to minimize the exchange of gases between perfusion fluid 108 and ambient air, can help ensure that the oxygen probes measure the desired oxygen values (e.g., values corresponding to perfusate exiting the liver 101), and can help maintain sterility. The closing of organ chamber 2204 can also serve to reduce heat loss from the liver. Heat loss can be considerable because of the large surface area of the liver. Heat loss can be an important issue during transport of the liver when the system 600 may be placed into relatively low temperature environments, such as a vehicle, or the rs when moving the system 600 into and out of a vehicle. Furthermore, prior to transplantation, system 600 may be temporarily placed in a hospital holding area or in an operating theater, both of which lly have atures in the range of 15-220 C. At such ambient temperatures, it is important to reduce heat loss from organ chamber 2204 in order to allow heater 230 to maintain the desired ate and liver temperature. Sealing the liver 101 in the organ chamber 2204 can also help to maintain uniformity of the temperature h liver lOl .

Referring also to FIGS. lSA-lSD shows an exemplary embodiment of support surface 2810 that is configured to support the liver 101. This embodiment includes drainage ls 2812, drain 2814, and orifices 2815. The drainage channels 2812 are configured to channel perfusate draining from the liver 101 and guide it toward the drain 2814. In some ments, when the t surface 2810 is led in the base 2802, the drain 2814 is located above and/or in the proximity of measurement drain 2804 thereby ensuring that a substantial amount of the perfusate 108 drains from the support surface 2810 into the measurement drain 2804. The orifices 2815 are configured to provide supplemental areas for the perfiision to drain from the support surface 2810. Additionally, the support surface 2810 can be configured to be used with the pad 4500 (described below). The support surface 2810 can also include orifices 2813 that can be used to secure the pad 4500 using, for e, screws or rivets. In some embodiments, when the support surface 2810 is installed in the organ chamber 104, it is installed so that it rests at approximately a 5— degree angle relative to horizontal, although other angles can be used (e.g., 0—60 degrees).

Referring to FIGS. 16F-16J, in an alternate embodiment, the support surface 4700 is a e material that supports and cushions the organ, and support e 2810 is omitted. The material is of a composition such that is provides a compliant, smooth surface on which the sensitive liver tissue can rest. The surface can be perforated in a manner, i.e. the , arrangement and er of the perforations, to allow for drainage from the liver while providing an atic surface for the liver tissue. In this or other embodiments, the support 4700 is a layer of materials, including a top layer 4706 and a bottom layer 4708 of a compliant material 4706 and an inner layer that is a frame 4702 of malleable metal substrate (e. g., aluminum). In some embodiments, the top layer 4706 and bottom layer 4708 can be made out of polyurethane foam and/or a cellular silicone foam.

The assembly is supported by the organ chamber base 2802, suspending the support surface 4700 above the bottom of the organ chamber base2802 at an appropriate height to provide displacement by the weight of the organ. The frame 4702 of the support surface 4700 can be held in place to the organ chamber base 2802 through the use of fasteners 4704, such as molded pins, rivets, screws, or other hardware, that are inserted through openings 4610 in the frame 4702.

In some embodiments, the malleable metal frame 4702 s into projections 4712. The projections 4712 may also be enclosed by the top layer 4706 and bottom layer 4708. The projections 4712 can be formed into positions to surround the liver to stabilize the position of the liver in the x, y and z axes. By bending the projections 4712, the user can selectively t the liver in a manner that mimics how the liver is supported in the human body. In some embodiments, portions of the frame 4702 can be tapered and terminated with a circle, as shown in G. The tapering of the portions of the frame 4702 can: i) allow the projections 4712 to be curled more easier and reduce, or even eliminate, the possibility of creasing, and ii) reduce weight of the support surface 4700. The circle can provide a e that is easily held by the user. The tapered shape of the portions ofthe frame 4702 can be specifically selected to facilitate its rolling to conform to a natural arc rather than a fold or bend. The projections 4712 can be of any shape desired to surround the liver. In use, the liver is placed on the top layer 4706 of the support surface 4700, allowing the support surface 4700 to depress. Then, the projections 4712 may be formed into positions to surround the liver. b) ization of liver In some embodiments, the liver can be stabilized during transport by one or more systems that are ed to support and keep the liver in place without damaging the liver by applying undue pressure o. For example, in some ments the system 600 can use a soft stabilizing liver pad (e. g., 4500) to t the liver along with a wrap/tarp (e.g., 4600). In some embodiments, the stabilization system can allow some movement of liver up to a predetermined limit (e.g., the system can allow the liver to move up to 2 inches in any direction). In some ments the surface on which the liver rests can have a low friction surface, which can also help reduce damage to the liver. The side of the pad in contact with the support surface 2810 can have a high friction surface to help hold the pad in place.

The pad can be designed to form a cradle that selectively and controllably ts the liver 101 without applying undue re to the liver 101. That is, were the liver 101 merely placed on the support surface 2810 without anything more, physical damage could result to the portions of the liver on which the liver is resting during transport. For example, the pad can be formed from a material resilient enough to cushion the liver from mechanical vibrations and shocks during transport.

An exemplary embodiment of the stabilizing liver pad and wrap is shown as pad 4500 in FIGS. 16A-16E and wrap 4600 in D. The pad 4500 can include two layers: a top layer 4502 and a bottom layer 4504. In some embodiments, the top layer 4502 can be made out of polyurethane foam and the bottom layer 4504 can be made out of cellular silicone foam. In this embodiment, the top layer 4502 can be 6 mm thick and the bottom layer 4504 can be 3/16” thick, although other thicknesses and materials can be used. The top layer 4502 and the bottom layer 4504 can be bonded to one another using adhesive such as MOMENTIVE Silicone RTV 118 silicone. The shape of the pad 4500 can be optimized for the liver (e. g., as shown in A). For example, the shape of the pad 4500 can include curved comers and one or more fingers (e.g., 4506, 4508, 4510, 4512, 4514, and 4516). The pad 4500 can also include one or more holes 4520 through which the pad 4500 can be secured to the support surface 2810 using, for example, rivets and/or . In some embodiments, the pad 4500 can be approximately 16 x 12 inches in size, gh other sizes are possible.

Sandwiched between the top layer 4502 and the bottom layer 4504 can be a deformable metal substrate 4518. The deformable substrate 4518 can be constructed out of a rigid yet pliable material such as metal, although other materials can be used.

In some ments, the deformable ate 4518 is aluminum 1100-0 that is 0.04” thick. The substrate 4518 can be configured so that it is manipulated easily by the user, but resists changes to its positioning due to Vibration or impact of the liver.

The deformable substrate 4518 can include fingers 4522, 4524, 4526, 4528, 4530, 4532 that pond to the fingers 4506, 4508, 4510, 4512, 4514, 4516, respectively.

By bending the various fingers in the pad 4500, the user can selectively support the liver in a manner that mimics how the liver supported in the human body. An exemplary embodiment ofthe pad 4500 with the fingers in a curled position is shown in D. In some embodiments, each of the fingers in the deformable substrate 4518 can be tapered (e. g., as shown by 4534) and terminated with a circle. The tapering of the fingers in the ate 4518 can i) allow the fingers to be curled easier and reduce, or even eliminate the possibility of the finger ng while being bent, and ii) reduce weight of the pad 4500. The circle can provide a surface that is easily held by the user. The tapered shape of the fingers can be specifically selected to facilitate a rolling of the pad finger to conform to a natural are rather than a fold or bend.

Referring to FIGS. J, in an alternate ment, the stabilizer may be comprised of three layers. The top layer 4706 and the bottom layer 4708 may be made of cellular silicone foam. Each foam layer can be 3/16” thick, although other thicknesses and materials can be used. The inner layer is a frame 4702 of a deformable metal substrate in the form of a narrow frame. The frame 4702 can be constructed out of a rigid yet pliable material such as metal, although other materials can be used. In some embodiments, the frame 4702 is aluminum 1100-0 that is 0.04” thick. The frame 4702 can be configured so that it is manipulated easily by the user, but resists changes to its positioning due to vibration or impact of the liver.

The top layer 4706 and the bottom layer 4708 can be bonded to one another and to the frame 4702 using adhesive such as MOMENTIVE Silicone RTV 118 silicone. The top and bottom layers 4706, 4708 cover the area inside the frame 4702, thereby ng a compliant support surface 4700 on which the liver is d for ort. The shape of the support surface 4700 can be optimized for the liver. For example, the shape of the support surface 4700 can include curved comers and one or more projections 4712 to constrain the movement of the liver during transport. In some embodiments, a wrap 4600 can be placed over the liver to hold it in place during transport and maintain moisture in the liver. For example, as shown in D, the wrap 4600 can be attached to the pad on one side (e.g., the right side in D) and the ing portion of the wrap can be draped over the liver. In other embodiments, the wrap can be secured on multiple edges or all edges. The wrap 4600 may also be used with flexible support surface 4700. In some embodiments, the wrap can perform one or more functions such as securing the liver during lant, helping maintain sterility, and preserving the moisture in the liver by acting as a vapor barrier. The wrap can be made out of a polyurethane sheet and can be opaque or clear to facilitate visual inspection of the liver. The size of the wrap 4600 can vary. For example, it can have a length that is between 0.5 and 24 inches and a width that is n 0.5 and 24 inches. 2. General description of perfusion circuit As described above, the liver has two blood supply sources: the hepatic artery and the portal vein, which e approximately 1/3 and 2/3 of the blood supply to the liver, respectively. Typically, when comparing the blood supply provided by the hepatic artery and the portal vein, the hepatic artery provides a blood supply with a higher pressure yet low flow rate and the portal vein provides a blood supply with a lower-pressure yet high flow rate. Also, typically, the hepatic artery provides a pulsatile flow of blood to the liver whereas the portal vein does not.

The system 600 can be red to supply perfusion solution to the liver in a manner that simulates the human body (e.g., the proper pressures, volumes, and pulsatile flows) using a single pump. For e, in a normal flow mode, the system 600 can circulate the perfusion fluid to the liver in the same manner as blood would circulate in the human body. More particularly, the perfusion fluid enters the liver through the hepatic artery and the portal vein and flows away from the liver via the IVC. In normal flow mode, the system 100 pumps the perfusion fluid to the liver 102 at a near physiological rate of between about 1-3 L/min, although in some embodiments the range can be 1.1 — 1.75 L/min (although the system can also be configured to provide flow rates outside of this range, e. g., 0—10 L/min). Each of the foregoing numbers is the total flow per minute provided to the hepatic artery and portal vein.

Referring to , an exemplary embodiment of a perfusion set 100 is shown. The perfusion set 100 can include a reservoir 160, a one-way valve 191, a pump 106, a one-way valve 310, compliance rs 184, 186, a gas exchanger 114, a heater 110, flow meters 136, 138a, 138b, a r 105, a flow clamp 190 re sensors 130a, 130b, organ chamber 104, a sensor 140, defoamer/filter 161, and tubing/interfaces to connect the same. The liver can also be connected to a bag 187 the collects bile ed therefrom. In some ments, the perfiJsion set 100 is contained entirely within the single use module 634, although this is not required.

In some embodiments, the inferior vena cava (IVC) is cannulated so that flow from the IVC can be directed to a conduit in which the IVC pressure, flow, and oxygen saturation can be measured. In other embodiments, the IVC is not cannulated and perfusate flows freely from the IVC into the organ chamber 104 (and ultimately into the drain(s) in the organ chamber 104).

In one embodiment, perfusion fluid flows from the reservoir 160 to valve 191 and then to the pump 106. After pump 106, the perfusion can flow to one-way valve 310 to compliance r 184. After ance r 184, the perfilsion fluid can flow to the gas exchanger 114 and on to the heater 110. After the heater 110 the perfusion fluid can flow to the flow meter 136 which is configured to measure the flow rate at that part of the perfiision circuit. After the flow meter 136 the perfusion fluid flows to the r 105, which can divide the flow of the perfusion fluid into branches 313 and 315. In some ments, the divider 105 can split the flow between the c artery and the portal vein at a ratio of between 1:2 and 1:3.

Branch 313 is ultimately provided to the portal vein of the liver s branch 315 is ultimately provided to the hepatic artery of the liver. The branch 313 can include flow meter 138a and the compliance chamber 186 which provides perfusion fluid to the flow clamp 190. From the flow clamp 190 the perfusion fluid can flow to the pressure sensor 130a before being provided to the portal vein of the liver. The branch 315 can include a flow meter 138b which provides perfiJsion fluid to the pressure meter 130b before being provided to the hepatic artery of the liver. After perfusion fluid exits the liver, some of the perfiision fluid is collected by the measurement drain 2804 and the remainder is collected by the main drain 2806. The perfusion fluid collected by the measurement drain 2804 can be ed to the sensor 140. Perfusion fluid exiting the sensor 140 can be provided to the defoamer/filter 161. The perfusion fluid collected by the drain 2806 can be provided directly to the defoamer/filter 161.

Perfusion fluid exiting the defoamer/filter 161 can be provided to the oir 160.

Additionally, bile produced by the liver can be collected in a bag 187.

In some embodiments, the system 100 has at least 1.6 L of perfusion fluid (or other fluid) in it when operating. 3. Reservoir The single use module 634 can include a perfusate reservoir 160 that is mounted below the organ chamber 104. The reservoir 160 can be configured to store and filter perfusion fluid 108 as it circulates through the perfusion set 100. Reservoir 160 can include one or more one-way valves (not shown) that prevent the flow of ion fluid in the wrong direction. In some ments, the reservoir 160 has a minimum capacity of 2 L, although smaller capacities can be used. In some embodiments, the reservoir 160 can include a filter (shown separately in as defoamer/filter 161) that is designed to trap particles in the perfiision fluid 108. In some embodiments, the filter is red to trap particles in the perfusion fluid 108 2015/033839 that are greater than 20 microns. In some embodiments, the reservoir 160 includes a defoamer (shown tely in as defoamer/filter 161) that reduces and/or eliminates foam generated from the perfiasion fluid 108. In some embodiments, the reservoir 160 can be made of a clear material and can include level markings so that a user may estimate the volume of the perfusion fluid in the reservoir 160. In some embodiments, the reservoir 160 can be red to allow for a minimum of 4.5 L per minute a fluid ingress from the organ chamber 104, although other flow rates are possible. In some embodiments, the reservoir 160 includes a vent to the atmosphere that es a sterile barrier (not shown).

The reservoir 160 can be positioned within the system 600 in various locations. For example, the reservoir 160 can be located above the liver, completely below the liver, partially below the liver, next to the liver, etc. Thus, one potential benefit some embodiments described herein is that the oir can be positioned below the liver since a gravity-induced re head in the perfiasion fluid is not required. 4. Valves In some embodiments, the valves 191 and 310 are one-way valves configured to ensure that the perfiasion fluid in the system 100 flows in the correct direction through the system 100. Exemplary embodiments of the valves 191 and 310 are described above with respect to the pump 106.

. Perfusion fluid pump An exemplary embodiments of the pump 106 is described more fully above with respect to FIGS. 6A-6E. As described above, in some embodiments, the pump is split between the multiple use module 650 and the single use module 634. For example, the single use module 634 can include the pump interface ly while the multiple use module 650 includes the pump driver portion. 6. Compliance chamber While the pump 106 provides a lly pulsatile output, the characteristics of that flow are typically adapted to match the flow typically provided by the human body to the liver. For example, the portal vein typically does not provide a pulsatile flow of blood to a liver when the liver is in vivo. Thus, in some embodiments, in order WO 87737 to provide a lsatile flow of perfusion fluid to the portal vein of the liver, one or more compliance chambers can be used to mitigate the pulsatile flow generated by the pump 106. In some embodiments, the compliance chambers are essentially small in- line fluid accumulators with flexible, resilient walls for simulating the human body’s vascular compliance. The compliance chambers can aid the system 600 by more accurately mimicking blood flow in the human body, for example, by filtering/reducing fluid pressure spikes due, for example, to the flow profile from the pump 106. In the embodiment of system 600 described herein, two compliance chambers are used: compliance chamber 184 and 186. Various teristics of the compliance chambers can be varied to achieve the desired result. For example, the combination i) a pressure versus volume relationship, and ii) the overall volume of the compliance chamber can affect the performance of the ance chamber.

Preferably the characteristics of the respective ance rs are chosen to achieve the desired effect.

In some embodiments, the compliance chamber 184 is located between the valve 310 and the gas exchanger 114 and operates to partially smooth the pulsatile output of the pump 106. For example, the compliance chamber 184 can be configured such that the flow of perfusion fluid ultimately provided to the hepatic artery of the liver mimics that of the human body. In some embodiments, the compliance chamber 184 can be omitted if the output of the pump 106 results in a perfusate flow to the c artery that y mimics that of the human body.

In some embodiments, the compliance chamber 186 is located between the divider 105 and the flow clamp 190. The ance chamber 186 can operate to substantially reduce, or even ate the pulsatile nature of the flow of perfiision fluid ultimately provided to the portal vein. Additionally, while the compliance chamber 186 is positioned before the flow clamp 190 in the branch 313, this is not ed. For example, flow clamp 190 can come before the compliance chamber 186.

In this embodiment, r, it may be desirable to adjust the parameters of the compliance chamber 186. 7. Gas exchanger The system 600 can also include a gas exchanger 114 (also referred to herein as an oxygenator) that is configured to, for example, remove C02 from the perfusion fluid and add 02. The gas exchanger 114 can receive input gas from an external or onboard source (e.g., gas supply 172 or oxygen concentrator) through a gas regulator and/or a gas flow r which can be a pulse-width modulated solenoid valve that ls gas flow, or any other gas control device that allows for precise control of gas flow rate. In some embodiments, the gas exchanger 114 is a standard membrane ator, such as the interventional lung assist membrane ventilator from NOVALUNG or member of the Quadrox series from Maquet of Wayne, NJ. In the illustrative embodiment, the gas can be a blend of oxygen, carbon dioxide, and nitrogen. An exemplary blend of gas is: 80% 02, 0.1% C02, and the e N2 with a blend process accuracy of 0.030%. In some embodiments, the ion of the gas exchanger, regulator, and/or gas flow chamber can be controlled by the controller 150 using the output of the sensor 140.

In some embodiments, the oxygenator 114 can have an oxygen transfer rate of 27.5 mme/LPM minute at a blood flow of 500 mme at standard ions. The oxygenator 114 can also have a carbon dioxide transfer rate of 20 mme at a blood flow rate of 500 mme at standard conditions. Standard conditions can be, for example: gas = 100% 02, blood temp = 37.0 i 0.5° C, hemoglobin = 12 i 1 mg%, SVOQ = 65 :: 5 %, pCO2 = 45 :: 5mmHg, and gas to blood ratio of 1:1). The above values are exemplary only and not limiting. Transfer rates higher and/or lower than the rate fied above can be used. 8. Heater/cooler The perfusion set 100 can include one or more heaters that are configured to maintain the temperature of the perfusion fluid 108 at a desired level. By warming the perfusion fluid, and the flowing the warmed liquid through the liver, the liver itself can also be warmed. While the heater can be capable of warming the perfusion fluid to a wide range of temperatures (e. g., 0 — 50° C), typically, the heater warms the perfusion fluid to a ature of 30 — 37° C. In some more c embodiments, the heater can be configured warm the perfusion fluid to a temperature of 34 — 37° C, 35 — 37° C, or any other range that falls within 0 — 50° C. In some embodiments, the ranges described herein can also extend to 42° C.

Referring to FIGS. 18A-18G, an exemplary embodiment of a heater assembly 110 is shown. FIGS. 18A-18F depict various views of the perfusion fluid heater assembly 1 10. The heater assembly 110 can include a housing 234 having an inlet 110a and an outlet 110b, As shown in both the longitudinal cross-sectional and the lateral cross-sectional views, the heater assembly 110 can include a flow channel 240 extending between the inlet 110a and the outlet 11%. The heater assembly 110 can be conceptualized as having upper 236 and lower 238 symmetrical halves. Accordingly, only the upper half is shown in an exploded view in F.

The flow channel 240 can be formed between first 242 and second 244 flow channel plates. The inlet 110a can flow the perfiision fluid into the flow channel 240 and the outlet 11% can flow the perfusion fluid out of the heater 110. The first 242 and second 244 flow channel plates can have substantially bioinert perfusion fluid 108 contacting es for providing direct contact with the perfusion fluid flowing through the channel 240. The fluid contacting surfaces can be formed from a treatment or coating on the plate or may be the plate surface itself. The heater assembly 110 can include first and second ic heaters 246 and 248, respectively.

The first heater 246 can be located adjacent to and can couple heat to a first heater plate 250. The first heater plate 250, in turn, can couple the heat to the first flow l plate 242. Similarly, the second heater 248 can be located adjacent to and can couple heat to a second heater plate 252. The second heater plate 252 can couple the heat to the second flow channel plate 244. According to the illustrative ment, the first 250 and second 252 heater plates can be formed fiom a al, such as aluminum, that conducts and distributes heat from the first 246 and second 248 electric heaters, respectively, relatively uniformly. The uniform heat distribution of the heater plates 250 and 252 can enable the flow channel plates to be formed from a rt material, such as titanium, reducing concern regarding its heat distribution characteristic. The heater assembly 110 can also include s 254 and 256 for fluid sealing tive flow channel plates 242 and 244 to the g 234 to form the flow channel 240. In some embodiments the function of the heater plate and flow channel plate are ed in a single plate.

The heater assembly 110 can further include first assembly brackets 258 and 260. The assembly bracket 258 can mount on the top side 236 of the heater assembly 110 over a periphery of the electric heater 246 to sandwich the heater 246, the heater plate 250 and the flow channel plate 242 between the assembly bracket 258 and the housing 234. The bolts 262a-262j can fit through ponding through holes in the bracket 258, electric heater 246, heater plate 250 and flow channel plate 242, and thread into ponding nuts 264a—264j to affix all of those components to the housing 234. The assembly bracket 260 can mount on the bottom side 238 of the heater assembly 110 in a similar n to affix the heater 248, the heater plate 252 and the flow channel plate 244 to the housing 234. A resilient pad 268 can interfit within a periphery of the bracket 258. Similarly, a resilient pad 270 can interfit within a periphery of the bracket 260. A bracket 272 can fit over the pad 268. The bolts 278a-278f can interfit through the holes 276a-276f, respectively, in the bracket 272 and thread into the nuts 80f to compress the resilient pad 268 against the heater 246 to provide a more efficient heat transfer to the heater plate 250. The resilient pad 270 can be compressed against the heater 248 in a similar fashion by the bracket 274.

The illustrative heater assembly 110 can include temperature sensors 120 and 122 and dual-sensor 124. The dual sensor 124, which in practice can include a dual thermistor sensor for providing fault tolerance, can measure the temperature of the perfusion fluid 108 exiting the heater assembly 110, and can provide these temperatures to the controller 150. As described in fiarther detail with respect to the heating subsystem 149, the signals from the sensors 120, 122 and 124 can be employed in a ck loop to control drive signals to the first 246 and/or second 248 s to control the temperature of the heaters 256 and 248. Additionally, to ensure that heater plates 250 and 252 and, therefore, the blood contacting surfaces 242 and 244 of the heater plates 250 and 252 do not reach a temperature that might damage the perfiision fluid, the illustrative heater assembly 110 can also include temperature sensors/lead wires 120 and 122 for monitoring the temperature of the heaters 246 and 248, respectively, and providing these temperatures to the controller 150. In practice, the sensors attached to sensors/lead wires 120 and 122 can be RTD (resistance temperature device) based. The signals from the sensors attached to sensors/lead wires 120 and 122 can be employed in a ck loop to further control the drive signals to the first 246 and/or second 248 s to limit the maximum ature of the heater plates 250 and 252. As a fault protection, there can be sensors for each of the s 246 and 248, so that if one should fail, the system can ue to operate with the ature at the other sensor.

The heater 246 of the heater assembly 110 can receive from the controller 150 drive signals 281a and 281b ctively 281) onto corresponding drive lead 282a.

Similarly, the heater 248 receives from the controller 150 drive signals 283a and 283b (collectively 283) onto drive lead 282b. The drive signals 281 and 283 control the current to, and thus the heat generated by, the respective heaters 246 and 248. More particularly, as shown in G, the drive leads 282a includes a high and a low pair, which connect across a resistive element 286 of the heater 246. The greater the current provided h the resistive element 286, the hotter the resistive element 286 gets. The heater 248 operates in the same fashion with regard to the drive lead 282b. According to the illustrative embodiments, the element 286 has a resistance of about 5 ohms. However, in other illustrative embodiments, the element may have a resistance of between about 3 ohms and about 10 ohms. The heaters 246 and 248 can be controlled independently by the processor 150.

The heater assembly 110 housing components can be formed from a molded plastic, for example, polycarbonate, and can weigh less than about one pound. More ularly, the housing 234 and the brackets 258, 260, 272 and 274 can all be formed from a molded c, for e, polycarbonate. According to another feature, the heater assembly can be a single use able assembly.

In operation, the rative heater assembly 110 can use between about 1 Watt and about 200 Watts of power, and can be sized and shaped to transition perfusion fluid 108 flowing through the channel 240 at a rate of between about 300 ml/min and about 5 L/min from a temperature of less than about 30° C to a ature of at least 37° C in less than about 30 minutes, less than 25 minutes, less than about 20 minutes, less than about 15 minutes, or even less than about 10 minutes, t substantially causing hemolysis of cells, or ring proteins or otherwise damaging any blood product portions of the perfusion fluid.

The heater assembly 110 can include housing components, such as the housing 234 and the brackets 258, 260, 272 and 274, that are formed from a polycarbonate and weighs less than about 5 lb. In some ments, the heater assembly can weigh less than 4 pounds. In the illustrative embodiment, the heater assembly 110 can have a length 288 of about 6.6 inches, not including the inlet 110a and outlet 110b ports, and a width 290 of about 2.7 inches. The heater assembly 110 can have a height 292 of about 2.6 inches. The flow l 240 of the heater assembly 110 can have a nominal width 296 of about 1.5 inches, a nominal length 294 of about 3.5 inches, and a nominal height 298 of about 0.070 inches. The height 298 and width 296 can be WO 87737 selected to provide for uniform heating of the perfusion fluid 108 as it passes h the channel 240. The height 298 and width 296 are also selected to provide a cross- sectional area within the channel 240 that is approximately equal to the inside cross- sectional area of fluid conduits that carry the ion fluid 108 into and/or away from the heater assembly 110. In one embodiment, the height 298 and width 296 are selected to provide a cross-sectional area within the channel 240 that is approximately equal to the inside cross-sectional area of the inlet fluid conduit 792 and/or substantially equal to the inside cross-sectional area of the outlet fluid conduit 794.

Projections 257a-257d and 259a-259d can be included in the heater assembly 110 and can be used to receive a heat-activated adhesive for binding the heating ly to the multiple-use unit 650.

In addition to the heater 110, the system 100 can also include an additional heater (not shown) that is placed inside the organ chamber 110 to provide heat (e.g., a resistance heater). 9. Pressure/flow probes In some embodiments, the system 600 can include pressure sensors 130a, 130b and flow sensors 138a, 138b. The probes and/or sensors can be obtained from standard commercial sources. For example, the flow rate s 136, 138a, and 138b can be onic flow sensors, such as those available from Transonic Systems Inc., Ithaca, NY. The fluid pressure probes 130a, 13% can be conventional, strain gauge pressure sensors available from M81 or G.E. Thermometrics. Alternatively, a pre- calibrated pressure transducer chip can be embedded into organ chamber connectors and connected to the controller 150. In some embodiments, the sensors can be configured to measure mean, instantaneous, and/or peak values flow/pressure values.

In embodiments where a mean value is calculated, the system can be configured to ate the mean pressure using a running average sampled values. The sensors can also be configured to provide systolic and diastolic ements. While these are shown as separate devices in , in some embodiments, a single device can measure both pressure and flow. In some embodiments, the sensors can be configured to e pressures between 0 — 225 mmHg with an cy ofi (7% + mmHg) for each transducer. In some embodiments the flow sensor can be configured to measure flow rates between 0-10 L/min with an accuracy ofi 12% + 0.140 L/min. In some embodiments the pressure and flow sensors can be red to sample the pressure/flow within the cannula tip, within the vessel, or in the tubing prior to the cannula.

While there is a single sensor 130b and a single sensor 130a, these sensors can include more than one pressure sensor. For example, in some embodiments, the sensor 130a can include two pressure sensors for redundancy. In such an ment, when both sensors are working the controller 150 can average the output of both to determine the actual pressure. In embodiments where one of the two pressure sensors in sensor 130a fails, the controller can ignore the malfunctioning sensor.

As described more fully below with respect to FIGS. 23A-23K, the pressure sensors can be contained in a housing 3010 of the connector 3000 (and rly on the connector 3050). 10. Flow control The system 600 can be configured to provide perfusate flow rates varying from 0-10 L/min at the flow sensor 136 (e.g., before the divider 105). In some embodiments, the system can be configured to provide a flow rate of 0.6 — 4 L/min at the flow sensor 136, or even more specifically, 1.1 — 1.75 L/min at the flow sensor 136. These ranges are exemplary only and the flow rate at the sensor 136 can be provided within any range that falls within 0 — 10 L/min. The system 600 can be configured to provide perfusate flow rates varying from 0 — 10 L/min, and more cally 0.25 — 1 L/min to the hepatic artery of the liver (e. g., as measured by the flow sensor 130b). These ranges are exemplary only and the flow rate at hepatic artery can be provided within any range that falls within 0 — 10 L/min. The system 600 can be configured to provide ate flow rates varying from 0 — 10 L/min, and more cally 0.75 to 2 L/min to the portal vein of the liver (e. g., as ed by the flow sensor 130a). These ranges are exemplary only and the flow rate at the portal vein can be provided within any range that falls within 0 — 10 L/min.

In some embodiments, the system 100 can be capable of generating perfusate flow through the perfusion module at rates of 0.3 — 3.5 L/min with at least 1.8 Liters of perfiJsion fluid therein. In some embodiments, the re provided to the hepatic artery via the branch 315 can be between 25-150 mmHg and more specifically between 50-120 mmHg, and the pressure provided to the portal vein via the branch 313 can be between 1-25 mmHg and more specifically 5-15 mmHg. These ranges are exemplary only and the respective pressures can be provided within any range that falls within 5 — 150 mmHg. 11. Perfusate sensors The sensor 140 can sense one or more characteristics of the perfusion fluid flowing from the liver by measuring the amount of light absorbed or reflected by the perfusion fluid 108 when applied at multi-wavelengths. For example, the sensor 140 can be an 02 saturation, hematocrit, and/or temperature sensor. FIGS. 19A—19C depict an ary ment of the sensor 140. The sensor 140 can include an in-line cuvette shaped section of tube 812 connected to the conduit 798, which can have at least one optically clear window through which an ed sensor can provide ed light. Exemplary embodiments of the sensor 140 can be the BLOP4 and/or BLOP4 Plus probes from DATAMED SRL. The cuvette 812 can be a one-piece molded part having connectors 801a and 801b. The connectors 801a and 801b can be red to adjoin to connecting receptacles 803a and 803b, respectively, of conduit ends 798a and 798b. This interconnection between cuvette 812 and conduit ends 798a and 798b can be configured so as to provide a substantially nt cross-sectional flow area inside conduit 798 and cuvette 812. The configuration can thereby reduce, and in some embodiments substantially s, discontinuities at the interfaces 814a and 814b between the cuvette 812 and the conduit 798. Reduction/removal of the discontinuities can enable the blood based perfusion fluid 108 to flow through the e with reduced lysing of red blood cells and reduced turbulence, which can enable a more accurate reading of perfusion fluid oxygen levels. This can also reduce damage to the perfusion fluid 108 by the system 600, which can ultimately reduce damage done to the organ being transplanted.

The cuvette 812 can be formed from a light transmissive material, such as any suitable light transmissive glass or polymer. As shown in A, the sensor 140 can also include an optical transceiver 816 for directing light waves at perfusion fluid 108 passing through the cuvette 812 and for measuring light transmission and/or light reflectance to determine the amount of oxygen in the perfiasion fluid 108. In some ments a light itter can be d on one side of the cuvette 812 and a detector for measuring light transmission through the perfusion fluid 108 can be located on an opposite side of the cuvette 812. C depicts a top cross-sectional view of the cuvette 812 and the eiver 816. The transceiver 816 can fit around cuvette 812 such that transceiver interior flat surfaces 811 and 813 mate against cuvette flat surfaces 821 and 823, respectively, while the interior convex surface 815 of transceiver 816 mates with the cuvette 812 convex surface 819. In operation, when UV light is transmitted fiom the transceiver 816, it travels from flat surface 811 through the fluid 108 inside cuvette 812, and is received by flat surface 813. The flat surface 813 can be configured with a or for measuring the light transmission through the fluid 108.

In some embodiments, the sensor 140 can be configured to measure SvOz in the range of 0-99%, although in some embodiments this can be limited to . To the extent that the sensor 140 also measures hematocrit, the measurement range can be from 0 — 99%, although in some embodiments this can be limited to 15 — 50%. In some embodiments, the cy of the measurements made by the sensor 140 can be i 5 units and measurements can occur at least once every 10 seconds. In embodiments of the sensor 140 that also e temperature, the measurement range can be from 0 — 500 C.

In some embodiments, the system 600 can also include one or more lactate sensors (not shown) that are configured to measure lactate in the perfusion fluid. For example, a lactate sensor can be placed between the measurement drain 2804 and the er/filter 161 in branch 315, and/or in branch 313. In this configuration, the system 600 can be configured to measure lactate values of the perfusion fluid before and/or after processing by the liver. In some ments, the lactate sensor can be an in-line lactate analyzer probe. In some embodiments the lactate sensor can also be external to the system 600 and use samples of the perfiision fluid withdrawn from a sampling port.

In some embodiments the system 600 can also include one or more sensors (e.g., the sensor 140 and/or other sensors such as a disposable blood gas analysis probe) to measure pH, HCO3, p02, pC02, e, , potassium, and/or lactate. Exemplary sensors that can be used to e the foregoing values include e-shelf probes made by Sphere Medical of Cambridge, United Kingdom. As described above, the sensor can be coupled to the measurement drain 2804.

Alternatively, a piece of tubing can be used to route perfusion fluid to/from the . Some ments of the sensor use calibration fluid before and/or after ming a measurement. In embodiments using such sensors, the system can include a valve that can be used to control the flow of calibration fluid to the sensor.

In some embodiments, the valve can be manually actuated and/or automatically ed by the controller 150. In some ments of the sensor, calibration fluid is not used, which can result in a continuous sampling of the perfusion fluid.

In addition to using the foregoing s in a feedback loop to control the system 600, some or all of the sensors can also be used to determine the viability of the liver for lant.

In some embodiments, external blood analyzer sensors can also be used. In these embodiments, blood samples can be drawn from ports in the branches 313, 315 (the ports are described more fully below). The blood samples can be provided for analysis using standard hospital equipment (e.g. radiometer) or via point of care blood gas analysis (e.g., I—STATl from Abbott Laboratories or the Epoc from Alere). 12. Sampling/infusion ports The system 600 can include one or more ports that can be used to sample the perfusion fluid and/or infuse fluid into the perfusion fluid. In some embodiments, the ports can be configured to work with standard syringes and/or can be configured with controllable valves. In some embodiments, the ports can be luer ports. Essentially, the system 100 can include infiision/sampling ports at any on therein and the following examples are not limiting.

Referring to , the system 100 can include ports 4301, 4302, 4303, 4304, 4305, 4306, 4307, and 4308. The port 4301 can be used to provide a bolus ion and/or flush (e.g., a post-preservation flush) to the hepatic artery. The port 4302 can be used to provide a bolus injection and/or flush (e. g., post-preservation flush) to the portal vein. The ports 4303, 4304, 4305 can be coupled to the respective channels of the solution pump 631 and can provide infusion to the portal vein (in the case of 4303 and 4304) and to the hepatic artery (in the case of 4305). The ports 4306 and 4307 can be used to obtain a sample of the ion fluid flowing into the hepatic artery and portal vein, respectively. The port 4308 can be used to sample the perfusion fluid in the IVC (or hepatic veins, depending on how the liver was harvested). In some embodiments, each of the ports can include a valve that the user operates to obtain a flow from the ports.

The port configuration shown in is exemplary, and more or fewer ports can be used. onally, ports can be located in additional locations such as between the pump 106 and the divider 105, between the organ chamber and bile bag 187, in the bile bag 187, between the main drain 2806 and the defoamer/fllter 161.

The single use module 634 can also include a tube 774 for loading g solution and the uinated blood from the donor or blood products from a blood bank into the reservoir 160. The priming tube 774 can be provided directly to the reservoir 160 and/or it can be located so that an end of it empties directly above the drain 2806 in the organ chamber 104. The single use module 634 can also include non-vented caps for replacing vented caps on selected fluid ports that are used, for example, while running a sterilization gas through the single use module 634.

Some embodiments the system 100 can also include vents and/or air purge ports to eliminate air from the hepatic artery interface, the portal vein ace, or elsewhere in the system 100.

In some ments an extra infusion port can be included for the user to provide an imaging contrast medium to the perfiision fluid so that imaging of the liver can be enhanced. For example, an ultrasound contrast medium can be infused to perform a contrast-enhanced ultrasound. 13. Organ assist While ion fluid can drain naturally from the liver as a result of the re applied to the c artery and portal vein, the system 600 can also e additional features that help the perfusion fluid drain from the liver in a manner that mimics the human body. That is, in the human body the diaphragm typically applies pressure to the liver as the person breathes. This pressure can help expel blood from the ’s liver. The system 600 can include one or more systems that are designed to mimic the pressure applied by the diaphragm to the liver. Exemplary embodiments include contact and contactless embodiments. In some embodiments, the amount of pressure applied to the liver can be less than the pressure in the portal vein and/or hepatic artery of the liver. Sketches of exemplary embodiments of the organ assist systems are shown in .

One embodiment of a contactless pressure system is a system that varies the air pressure in the organ chamber 104 to simulate pressure applied by the diaphragm to the liver. In this embodiment, the organ chamber 104 can be red to provide a substantially ht environment such that the air re inside the organ chamber 104 can be maintained at an elevated (or lowered) state when compared to the outside atmosphere. As the air pressure in the organ chamber 104 rises, it can apply pressure to the liver that simulates the pressure applied by the diaphragm y increasing the rate at which the liver expels ion fluid. In some embodiments, the air pressure can be varied in a manner that mimics a human breathing rate (e. g., 12-15 times per minute), or at other rates (e. g., 0.5 to 50 times per minute). The air pressure in the organ chamber 104 can be varied by various s including, for example, a dedicated air pump (not shown) and/or the d gas supply 172. In some embodiments, the air pressure inside the organ chamber 104 can be controlled by the controller 150. In these embodiments, the controller can also be coupled to an air pressure sensor measuring the pressure inside the organ chamber 104 that is used as part of a ck control loop.

One embodiment of a contact pressure system is a system that that uses a wrap and/or r to apply pressure to the liver. For example, a wrap can be placed over some or all of the liver within the organ chamber 104. The edges of the wrap can then be mechanically tightened to apply re to the portion of the liver covered by the wrap. In this example, one or more small motors attached to various points around the periphery of the wrap can be used to tighten the edges of the wrap. In r example of a contact pressure system, a removable bladder can be used (not shown).

In this embodiment, an inflatable bladder can be placed between the liver and the top surface (or some other portion) of the organ chamber 104. A pump can then be used to inflate/deflate the bladder. As the bladder inflates, it can press against the top surface (or other portion) of the organ chamber 104 thereby exerting pressure on the liver contained therein. As with the contactless system described above, the pressure applied to the liver can be applied ically to mimic the l pressure provided by the diaphragm. In some embodiments, the pressure applied to the liver can be varied in a manner that mimics human breathing rate (e.g., 12-15 times per minute), or at other rates (e. g., 0.5 to 50 times per minute). Regardless of whether the pressure is applied to the liver using a wrap or a bladder, the pressure can be controlled by the controller 150. In some embodiments, one or more s that e the pressure applied to the liver can be included in the organ chamber 104 as part of a feedback control loop. Other s of ing contact pressure to the liver are also possible. 14. Cannulation Operationally, in one embodiment, a liver can be harvested from a donor and coupled to the system 600 by a process of cannulation. For example, interface 162 can be cannulated to vascular tissue of the hepatic artery via a conduit located within the organ chamber assembly. Interface 166 can be cannulated to vascular tissue of the portal vein via a conduit located within the organ chamber assembly. The liver emits the perfiasate through the inferior vena cava (IVC). In some embodiments, the IVC can be cannulated by interface 170 (not shown) so that the flow can be directed to a conduit in which the IVC pressure, flow and oxygen saturation can be measured. In another embodiment, the IVC can be cannulated by the interface 170 to direct the flow within the organ chamber. In still another embodiment, the IVC is not cannulated and the organ chamber provides a means to direct the perfusate flow for efficient collection to the reservoir.

Each of the interfaces 162, 166 and 170 can be cannulated to the liver by pulling vascular tissue over the end of the ace, then tying or otherwise securing the tissue to the interface. The vascular tissue is preferably a short segment of a blood vessel that remains connected to the liver after the liver is severed and explanted from the donor. In some embodiments, the short vessel segments can be 0.25 — 5 inches, although other lengths are possible.

Referring to FIGS. 21A-21D, an exemplary embodiment of a hepatic artery a 2600 is shown. The cannula 2600 is generally tubular in shape and includes a first n 2604 that is configured to be inserted into tubing used in the system 100 and includes a first orifice 2612. The first portion 2604 can also include a ring 2602 that can be used to help secure the first portion 2604 inside of the tubing of the system 100 by friction. The cannula 2600 can also include a second portion 2608 that can have a r er than the first portion 2604 and that forms a second orifice 2614. The second portion 2608 can also include a channel 2610 that is ed from the surface of the second portion 2608. In some embodiments, when the user ties the hepatic artery to the second portion 2608, the user can place the suture in the channel 2610 to help secure the hepatic artery. Between the first and second portions can be a collar 2606. The outside diameter of the collar can have a slightly larger diameter than the first portion 2604 to prevent the tubing of the system 100 from extending over the second portion 2608 when inserted. Viewing the cross-section shown in D, the inside diameter of the cannula 2600 can vary, with a taper 2616 therebetween. The cannula 2600 can be formed in s sizes, lengths, inside diameters, and outside ers. In some embodiments of the system 600, it can be advantageous to have a substantially large inside diameter in the first portion 2604 and a much smaller inside diameter in the second portion 2608 to offset pressure and flow changes caused by the cannula 2600.

Referring to FIGS. 2lH-21K, in an alternative embodiment the cannula 2600 has a beveled cut end 2618.

The outside diameter of the first portion 2604 can be configmred to be press-fit inside of silicone or ethane tubing. Thus, while the e diameter of the first portion 2604 can vary, one exemplary range of possible diameters is 0.280 — 0.380”.

The outside er of the second portion 2608 can range between 4 — 50 Fr, but more specifically between 12-20 Fr. Additionally, the cannula 2600 can be made from s biocompatible als, such as stainless steel, titanium, and/or plastic (the dimensions of the cannula 2600 can be adapted to be manufacturable using different materials).

Additionally 10-20% ofthe population have a genetic variation where the liver includes an accessory hepatic artery. For these instances, the hepatic artery cannula described above can be a double-headed (e.g., Y-shaped) cannula. An exemplary embodiment of a Y-shaped hepatic artery cannula 2642, is shown in FIGS. 21E-21G, where like numbers are used to denote corresponding features in the cannula 2600.

The bifurcated design of hepatic artery cannula 2642 can allow the system 100 to treat both vessels as one input for hepatic artery flow without changing the configuration of the system 100 and/or the controller 150.

In an alternative ment, when the liver includes an accessory hepatic , two hepatic artery as 2600 may be attached to a section of Y-shaped tubing at one end, and the other end may be connected to the organ chamber.

WO 87737 Referring to FIGS. D, an exemplary embodiment of a portal vein cannula 2650 is shown. The cannula 2650 is generally tubular in shape and includes a first portion 2654 that is configured to be inserted into tubing used in the system 100 and includes a first orifice 2660. The first portion 2654 can also e a ring 2652 that can be used to help secure the first portion 2654 inside of the tubing of the system 100 by friction. The cannula 2650 can also include a second portion 2656 that can have a larger diameter than the first portion 2654 and that forms a second orifice 2662. The second portion 2656 can also include a channel 2658 that is recessed from the surface of the second portion 2656. In some embodiments, when the user ties the portal vein to the second portion 5626, the user can place the suture in the channel 2658 to help secure the portal vein. Viewing the cross-section shown in D, the inside diameter of the cannula 2600 can vary, with a taper 2664 therebetween.

The cannula 2650 can be formed in various sizes, lengths, inside diameters, and outside diameters. In some embodiments of the system 600, it can be advantageous to have a substantially large inside diameter in the first portion 2654 and an even larger inside diameter in the second portion 2656 to offset pressure and flow changes caused by the cannula 2650.

Referring to FIGS. 22E-22G. in an alternative embodiment the cannula 2650 has a collar 2666 between the first and second portions. The e diameter of the collar can have a slightly larger diameter than the first portion 2654 to t the tubing of the system 100 from extending over the second portion 2656 when inserted.

The cannula 2650 may also have a beveled cut end 2668.

The outside diameter of the first n 2654 can be configured to be press-fit inside of silicone or polyurethane tubing. Thus, while the outside diameter of the first n 2654 can vary, one exemplary range of possible diameters is 0.410 — .

The e diameter of the second portion 2656 can range between 25-75 Fr, but more specifically between 40-48 Fr. Additionally, the cannula 2650 can be made from various biocompatible materials, such as stainless steel, titanium, and/or plastic (the ions of the cannula 2600 can be adapted to be manufacturable using different materials).

Referring to FIGS 23A-23N, an exemplary hepatic artery connector 3000 is shown. The connector 3000 can be part of the branch 315 leading to the hepatic artery of the liver. For e, the connector 3000 can be inserted into and secured to the wall of the organ chamber 104. The connector 3000 can include a first portion 3006 that includes a circumferential channel 3007 and defines an opening 3008. In some embodiments, the outside er of the first portion 3006 is sized to couple to 1A1” tubing, although other diameters are possible. In some embodiments, tubing coupled to the first portion 3006 can coupled using friction and/or a common zip tie (or other similar fastener) can be tied around the channel 3007 to secure the tubing connected thereto. The connector 3000 can also include a second portion 3002 that defines an opening 3003. In some embodiments, the outside diameter ofthe second portion 3002 can be configured to couple to 1A1” tubing using a press/friction connection, although other sizes are possible. In some embodiments, perfiasion fluid flows from the opening 3008 toward the opening 3003.

The connector 3000 can include an interface that is configured to mate with an opening in a wall of the organ chamber 104. For example, tor 3000 can e a ridge 3003 that is sized to fit within a corresponding opening in a wall of the organ r 104. A backstop 3004 can be larger than the opening to prevent the connector from being inserted too far, and can also provide a surface on which adhesive can be applied to bond the connector 3000 to the organ chamber 104. In some embodiments, the ridge 3003 can include a protrusion 3011 that is red to rotationally align the connector 3000 within the organ chamber 104. For example, in some embodiments, the protrusion 3011 and corresponding opening in the organ r 104 can be configured so that the connector 3000 is rotated about a udinal axis of the second portion 3003. In some embodiments, the rotation can be optimized to prevent air bubbles.

The connector 3010 can also including a housing 3010 that is configured to house the pressure sensor 130b. In this embodiment the two re sensors make up the pressure sensor 13%. In such an embodiment, the re sensors can be mounted in the openings 3009, which can provide direct access to the fluid within the connector 3000. Additionally, some embodiments of the connector 3000 can include an air vent 3005 that can be connected to a valve which can be opened to vent air bubbles trapped within the connector 3000. In operation, a user can attach one end of a tube to the second portion 3002 and the other end of the tube to the hepatic artery cannula 2600 (which can be connected to the hepatic artery). In some embodiments, the user can place a liver into the organ chamber 104, connect a cannula 2600 to an end of a piece of tubing, which can be connected to the hepatic artery using a suture.

Next, because the size of the liver can vary, the user can then trim the tubing to the proper length and attach it to the second portion 3003.

Referring to FIGS 24A-23 L, an ary portal vein connector 3050 is shown. In some ments the portal vein connector 3050 is configured and functions in the same manner as the connector 3000, except that the first and second portions can be coupled to connect to 3/8” or 1/2” tubing d of W’, although it can be configured to work with other size tubing as well. Also, as should be clear by the name, the portal vein connector can be configured to couple the branch 313 to the portal vein of the liver.

While some dimensions are provided above, these dimensions are exemplary only and each of the foregoing components can sized as necessary to achieve the desired flow characteristics. For example, in some embodiments, it can be beneficial to use the largest diameter cannula to avoid introducing undesirable pressure or flow changes. Additionally, in practice, the diameter of the cannula can be chosen by the surgeon such that the largest a is used that will ally fit in the vessel.

It is noted herein that some consider the “Fr” scale to end at “34.” Thus, to the extent that a Fr size larger than 34 is fied (or an Fr. number that does not exist in the traditional Fr. scale), the size in mm can be calculated by dividing the identified Fr number by 3.

. Flow clamp Referring to FIGS. 25A-25B, an exemplary embodiment of the flow clamp 190 is shown. The flow clamp 190 can be used to l the flow and/or pressure of the perfusion fluid to the portal vein of the liver. The flow clamp 190 can include a cover 4001, a knob 4002, a pivot 4003, a pin 4004 a screw 4005, a bearing 4006, a slide 4007, an axle 4008, and a body 4009. The slide 4007 can include a groove 4010 and detent 4012 and can be configured to move up and down within the body 4009.

In some embodiments, a tube carrying perfusion fluid is placed within the body 4009 under the slide 4007. FIGS. 25C-25D show the flow clamp 190 with molded components.

The flow clamp 190 can be configured to allow a user to y engage and disengage the clamp 190, while still having precise control over the amount of clamping force applied. In this embodiment, the cover 4001, the knob 4002, the pivot 4003, the pin 4004, the screw 4005, and the bearing 4006 make up a switch unit 401 1.

The pivot 4003 of the switch unit 4011 can rotate about a longitudinal axis formed by the axle 4008 (which can be made up of two separate screws). In this , when the switch unit 4011 is engaged (e.g., the screw 4005 is vertical), as shown in A, the g 4006 forces the slide 4007 downward in the body 4009 (which can compress the tube carrying the perfusion fluid, if present, and restricts flow therein).

How far down the slide is forced is a function of how extended the screw 4005 is relative to the pivot 4003. When the switch unit 4011 is disengaged, it is pivoted sideways so that the screw is no longer vertical and does not restrict the movement of the slide 4007. When the switch unit 4011 is pivoted, the bearing can slide along the grove 4010. In some embodiments, the switch unit 4011 can “lock” into place when the bearing 4006 comes to rest in the detent 4012. The user can adjust the amount of flow restriction is imposed by the flow clamp 190 when engaged by rotating the knob 4002, thereby extending/retracting the screw 4005. In some embodiments, the pitch ofthe screw can be 4-40 thread, gh other pitches can be used adjust the precision of the flow clamp 190. 16. Priming In some embodiments, the perfusion fluid includes packed red blood cells also known as “bank blood.” Alternatively, the perfusion fluid includes blood removed from the donor through a process of uination during harvesting of the liver.

Initially, the blood is loaded into the reservoir 160 and the cannulation locations in the organ r assembly are connected with a bypass conduit to enable normal mode flow of perfusion fluid through the system without a liver being t, aka “priming tube.” Prior to cannulating the harvested liver, the system may be primed by circulating the exsanguinated donor blood through the system to heat, oxygenate, and/or filter it. Nutrients, preservatives, and/or other therapeutics may also be provided during priming via the on pump of the nutritional subsystem. During priming, various parameters may also be initialized and calibrated via the operator interface during g. Once primed and running appropriately, the pump flow can be reduced or cycled off, the bypass t is removed from the organ chamber assembly, and the liver can be cannulated into the organ chamber assembly. The pump flow can then be restored or increased, as the case may be. The priming process is described more fully below. 17. IVC cannulation In some embodiments, the inferior vena cava (IVC) can be cannulated, though not required. In these embodiments, additional pressure and/or flow s can be used to determine the pressure and/or flow of the perfusion fluid flowing from the liver. In some ments, the cannulated IVC can be coupled directly to the sensor 140 and/or oir. In other embodiments, the IVC can be cannulated for the purpose of directing the drainage of the perfusion fluid (e.g., directed free draining).

For example, the uncannulated end of a short tube connected to the IVC can be held in place by a clip so that perfiision fluid drains directly over the measurement drain 2804. In other embodiments, the IVC is not cannulated and perfusion fluid can drain freely therefrom. In still other embodiments, the IVC can be partially tied off.

In embodiments where the IVC is cannulated and connected to tubing, it can be desirable to keep the length of tubing as short as possible to achieve the desired result. That is, because physiologic IVC pressure is low, even a length of narrow tube can result in an elevated IVC pressure. In embodiments of the system 600 that include pressure exertion on the liver to encourage draining (e.g., pressurizing the chamber 104 as discussed above), the liver may be able to tolerate a longer a/tubing. 18. Bile duct cannulation In some embodiments of the system 600, the bile duct of the liver can be cannulated using an off the shelf and/or custom a. For example, a bile duct a of 14 Fr can be used. Additionally, the bile bag 187 can be configured to collect bile produced by the liver. In some embodiments, the bag 187 is clear so the user can visually e the color of the bile. In some ments, the bag 187 can collect up to 0.5 L of bile, although other amounts are possible. In some embodiments, the bag 187 can include graduations that te how much bile has been collected. While the system 600 is described as including a soft shell (e. g., the bag 187) to collect bile, a hard shell container can also be used. Some embodiments of the system 600 can include a sensor (e.g., capacitive, onic, and/or cumulative flow rate) to measure the volume of bile collected. This information can then be displayed to the user and/or sent to the Cloud. 19. Blood collection/filter Some embodiments of the system 600 using whole blood from a donor can e leukocyte filter (not shown). In these embodiments, the leukocyte filter can be used when priming the system to filter blood received from a donor body via a blood collection line connected to a donor’s artery and/or vein. In some ments, the yte filter can be configured to filter at least 1500 mL of blood in 6 minutes or less (although other rates are possible). In some embodiments, the leukocyte filter can be configured to remove 30% or more of all leukocytes in up to 1500 mL of whole blood.

. Final Flush Administration Kit At times during operation, it can be ble to remove all of the perfusion solution from the liver vasculature (e.g., before the liver is implanted into a ent) without necting the liver from the system 100. Thus, embodiments ofthe system 600 can be used with a final flush administration kit. The kit can include a bag (or other container) to collect a volume of liquid (e.g., flush solution and/or perfusate) so that when the flushing solution is administered to the liver (e.g., via ports 4301, 4302), the system 100 is not overwhelmed by the additional volume of fluid. Thus, in some embodiments, the system 100 can include a drain line (not shown) that can be used to drain fluid from the reservoir 160 and/or elsewhere in the system 100 in such a manner that the liver need not be disconnected from the system 100 before adding onal fluid. In some embodiments, the system can also be setup in a bypass ion where the liver is temporarily isolated from the system 100 using one or more valves. For example, in this embodiment, valves can be used before the ports 4301, 4302 to stop fluid flow within the system 100. Additional drainage ports can then be included between the drains 2804, 2806 and the valves. In this embodiment, the flush solution (or any other solution) can be provided via the ports 4301, 4302 and drain out of the additional drainage ports without being circulated in the rest of the system 100. In some embodiments, the drain line can hold at least 3 L of liquid, although this is not required.

WO 87737 D. Interface between single/multi use modules As shown in and described in r detail below, the multiple use module 650 can e a front-end interface circuit board 636 for interfacing with a front-end circuit board (shown in ] at 637) of the disposable module 634. As described more fiilly below, power and drive signal connections between the multiple use module 650 and the disposable module 634 can be made by way of corresponding electromechanical tors 640 and 647 on the front end interface circuit board 636 and the front end circuit board 63 7, respectively. By way of example, the front-end circuit board 637 can receive power for the disposable module 634 from the front-end interface circuit board 636 via the electromechanical connectors 640 and 647. The front end circuit board 637 can also receive drive signals for various components (e.g., the heater assembly 110, the flow clamp 190, and the oxygenator 114) from the controller 150 via the end interface circuit board 636 and the electromechanical tors 640 and 647. The front-end circuit board 637 and the front-end ace circuit board 636 can exchange control and data signals (e. g., between the controller 150 and the single use module 634) by way of optical connectors (shown in B at 648). As described in more detail below, the connector configuration employed between the front-end 637 and front-end interface 636 circuit boards can ensure that critical power and data interconnections between the single and le use s 634 and 650, tively, continue to operate even during transport over rough terrain, such as may be experienced during organ transport.

Turning now to the installation of the single use module 634 into the multiple use module 650, shows a detailed View of the above-mentioned bracket assembly 638 located on the multiple use module 650 for receiving and locking into place the single use module 634. shows a side perspective view of the single use module 634 being installed onto the bracket assembly 638 and into the multiple use module 650, and shows a side view of the single use module 634 installed within the multiple use module 650. The bracket assembly 638 includes two mounting brackets 642a and 642b, which can mount to an internal side of a back panel of the housing 602 via mounting holes 644a-644d and 646a-646d, respectively.

A cross bar 641 extends between and rotatably attaches to the mounting brackets 642a and 642b. Locking arms 643 and 645 are spaced apart along and radially extend from the cross bar 641. Each locking arm 643 and 645 includes a respective downward extending locking tion 643a and 645b. A lever 639 attaches to and extends radially upward from the cross bar 641. Actuating the lever 639 in the direction of the arrow 65] rotates the locking arms 643 and 645 toward the back 606b of the housing 602. Actuating the lever 639 in the direction of the arrow 653 rotates the locking arms 643 and 645 toward the front of the housing 602.

As described above with t to , the perfusion pump interface assembly 300 includes four projecting heat staking points 321a-321d. During assembly, the projections 32la-321d are aligned with corresponding res (e.g., 657a, 657b in B) and heat staked through the apertures to rigidly mount the IO outer side 304 of the pump interface assembly 300 onto the C-shaped t 656 of the single use module chassis 635.

During installation, in a first step, the single use module 634 is d into the multiple use module 650 while tilting the single use module 634 forward (shown in ). This process slides the projection 662 into the slot 660. As shown in 6E, it also positions the flange 328 of the pump interface assembly 300 within the docking port 342 of the perfusion pump ly 106, and the tapered projections 323a and 323b of the pump ace assembly 300 on the clockwise side of corresponding ones of the features 344a and 344b of the pump assembly bracket 346.

In a second step, the single use module 634 is rotated backwards until locking arm cradles of the single use module chassis 635 engage projections 643 and 645 of spring-loaded locking arm 638, forcing the projections 643 and 645 to rotate upward, until locking projections 643a and 645a clear the height of the locking arm cradles, at which point the springs cause the g arm 638 to rotate downward, allowing locking projections 643a and 645a to releasably lock with locking arm s of the disposable module chassis 635. This motion causes the curved surface of 668 of the single use module projection 662 of B to rotate and engage with a flat side 670 of the basin slot 660 of B. Lever 639 can be used to rotate the locking arm 638 upwards to release the single use module 635.

As shown in , this motion also causes the pump interface assembly 300 to rotate in a counterclockwise direction relative to the pump assembly 106 to slide the flange 328 into the slot 332 of the docking port 342, and at the same time, to slide the tapered projections 323a and 323b under the respective bracket es 344a and 344b. As the tapered projections 323a and 323b slide under the respective bracket features 344a and 344b, the inner es of the bracket features 344a and 344b engage with the tapered outer surfaces of the tapered projections 323a and 323b to draw the inner side 306 of the pump interface assembly 300 toward the pump driver 334 to form the fluid tight seal between the pump interface ly 300 and the pump assembly 106. The lever 639 may lock in place to hold the disposable module 634 securely within the multiple use module 650.

Interlocking the single use module 374 into the multiple use module 650 can form both electrical and optical interconnections between the front end ace circuit board 636 on the multiple use module 650 and the front end circuit board 637 on the single use module 634. The ical and optical connections enable the multiple use module 650 to power, control and collect information from the single module 634. A is an exemplary conceptual drawing g various l couplers and omechanical connectors on the front end circuit board 637 of the single-use disposable module 634 used to communicate with corresponding optical couplers and electromechanical connectors on the front end interface circuit board 636 of the multiple use module 650. Since this correspondence is one for one, the various optical couplers and electromechanical connectors are described only with reference to the front end t board 63 7, rather than also depicting the front end circuit board 650.

According to the exemplary embodiment, the front end circuit board 637 receives signals from the front end interface circuit board 636 Via both optical couplers and electromechanical tors. For example, the front end circuit board 637 receives power 358 from the front end interface circuit board 636 Via the electromechanical connectors 712 and 714. The front end circuit board 637 applies the power to the components of the single use module 634, such as the various sensors and transducers of the single use module 634. Optionally, the front end circuit board 637 converts the power to suitable levels prior to distribution. The front end interface circuit board 636 can also provide the heater drive signals 281a and 28 lb to the applicable connections 282a on the heater 246 of via the electromechanical connectors 704 and 706. Similarly, the electromechanical tors 708 and 710 can couple the heater drive signals 283a and 283b to the applicable connections in 282b of the heater 248. ing to the exemplary embodiment, the front end circuit board 637 can receive signals from temperature, pressure, fluid te, and oxygenation/hematocrit sensors, amplify the signals, convert the signals to a digital format, and provide them to the front-end interface circuit board 636 by way of electrical and/or optical couplers. For example, the front end circuit board 637 can e the temperature signal 121 from the sensor 120 on the heater plate 250 to the front end interface circuit board 636 by way of the optical coupler 676. Similarly, the front end circuit board 637 can provide the temperature signal 123 from the sensor 122 on the heater plate 252 to the front end interface circuit board 636 by way of the optical coupler 678. The front end—circuit board 637 can also e the perfusion fluid temperature signals 125 and 127 from the thermistor sensor 124 to the front end ace circuit board 636 via respective l couplers 680 and 682. Perfusion fluid pressure signals 129, 131 and 133 can be provided from respective re transducers 126, 128 and 130 to the front end interface circuit board 636 via respective optical couplers 688, 690 and 692. The front end circuit board 637 can also provide perfusion fluid flow rate signals 135, 137 and 139 from respective flow rate sensors 134, 136 and 138 to the front end interface circuit board 636 by way of respective optical couplers 694, 696 and 698. Additionally, the front end circuit board 637 can provide the oxygen saturation 141 and hematocrit 145 signals from the sensor 140 to the front end interface circuit board 636 by way of respective optical couplers 700 and 702. In another implementation, the front end circuit receives signals from integrated blood gas analysis probes. In another implementation the front end board passes control signals to a fluid path restrictor to facilitate real time control of the division of perfusate flow between the portal vein and hepatic artery conduits. The ller 150 can employ the signals provided to the front end interface circuit board 636, along with other signals, to transmit data and otherwise control operation of the system 600.

While the front end circuit board 637 is described with the foregoing couplers, more or fewer couplers can be used based on the number of connections necessary.

In some exemplary embodiments, one or more of the foregoing s can be wired directly to the main system board 718 for processing and is, thus by- passing the front-end interface board 636 and front-end board 637 ther. Such embodiments can be desirable where the user prefers to re—use one or more of the sensors prior to disposal. In one such e, the flow rate sensors 134, 136 and 138 and the oxygen and hematocrit sensor 140 are electrically coupled directly to the system main board 718 through electrical coupler 611 shown in C, thus by- passing any tion with the circuit boards 636 and 637.

B rates the operation of an exemplary electromechanical connector pair of the type employed for the electrical interconnections between the circuit boards 636 and 63 7. Similarly, C illustrates the ion of an optical coupler pair of the type ed for the optically coupled interconnections between the circuit boards 636 and 637. One advantage of both the electrical connectors and l couplers employed is that they ensure connection integrity, even when the system 600 is being transported over rough terrain, for example, such as being wheeled along a tarmac at an t, being transported in an aircraft during bad weather conditions, or being transported in an ambulance over rough roadways. The power for the front end board 637 is isolated in a DC power supply located on the front end interface board 636.

As shown in B, the electromechanical connectors, such as the connector 704, include a portion, such as the portion 703, located on the front end interface circuit board 636 and a portion, such as the portion 705, located on the front end circuit board 637. The portion 703 includes an ed head 703a mounted on a substantially straight and rigid stem 703b. The head 703 includes an outwardly facing ntially flat surface 708. The portion 705 includes a substantially straight and rigid pin 705 including an end 705a for contacting the surface 708 and a spring-loaded end 705b. Pin 705 can move axially in and out as shown by the directional arrow 721 while still maintaining electrical contact with the surface 708 of the enlarged head 703a. This feature enables the single use module 634 to in electrical contact with the multiple use module 650 even when experiencing mechanical disturbances associated with ort over rough terrain. An advantage of the flat surface 708 is that it allows for easy cleaning of the interior surface of the multiple use module 650.

According to the illustrative embodiment, the system 600 employs a connector for the electrical interconnection between the single use disposable 634 and multiple use 650 s. An exemplary connector is part no. 101342 made by Interconnect Devices. r, any suitable connector may be used.

Optical couplers, such as the optical couplers 684 and 687 of the front end t board 637, are used and include ponding counterparts, such as the optical couplers 683 and 685 of the front end interface circuit board 636. The optical transmitters and optical receiver portions of the optical couplers may be d on either circuit board 636 or 637.

As in the case of the electromechanical connectors ed, allowable nce in the optical alignment between the optical transmitters and corresponding optical receivers enables the circuit boards 636 and 637 to remain in optical communication even during transport over rough terrain. According to the rative embodiment, the system 100 uses optical couplers made under part nos. 5FH485P and/or 5FH203 PFA by Osram. However, any suitable coupler may be used.

The couplers and connectors can facilitate the transmission of data within the system 600. The front-end interface circuit board 636 and the front-end board 637 transmit data pertaining to the system 600 in a paced fashion. As shown in C, circuit board 636 transmits to the front-end board 637 a clock signal that is synchronized to the clock on the controller 150. The front-end circuit board 637 receives this clock signal and uses it to synchronize its transmission of system data (such as temperatures, pressures, or other desired information) with the clock cycle of the controller 150. This data is zed by a processor on the front—end circuit board 637 according to the clock signal and a pre-set sequence of data type and source address (i.e. type and location of the sensor providing the data). The front-end interface circuit board 636 receives the data from the front-end board 637 and transmits the data set to the main board 618 for use by the ller 150 in evaluation, display, and system control. Additional optical rs can be added between the multiple use module and single use module for ission of control data from the multiple use module to the single use module, such data including heater control signals or clamp/flow restrictor controls.

IV. Description of exemplary system operation A. Generally As described below, the system 600 can be configured to operate in multiple modes such as: perfusion circuit priming mode, organ stabilization mode, nance mode, chilling mode, and self-test/diagnostic mode. During each mode the system (vis-a-vis the controller 150) can be configured to operate in different manners. For example, as described more fully below, during the different modes of operation characteristics of, for example, perfusion fluid flow rates, perfilsion fluid pressure, perfusion fluid temperature, etc. can vary.

Additionally, some embodiments of the system 600 can include a self-test mode in which diagnostics can be performed. For example, the system 600 can tically test circuits and sensors in the single use and multiple use modules before the organ is instrumented on the system. The system 600 can also check to ensure that the single use module is installed properly in the multiple use module (e.g., all connections are secure and functioning). In the event of a failure, the system can inform the user and inhibit further operation of the system until the issue is resolved.

B. Temperature monitoring and l In general, the temperature of an organ contained in the system 600 can be controlled by circulating warmed or cooled perfiasion fluid therethrough. Thus, the perfusion fluid itself can be used to control the temperature of the organ without using a ted heater/cooler within the organ chamber 104.

In some embodiments of the system 600, the controller 150 can be configured to receive signals from one or more temperature sensors such as temperature sensors 120, 122, 124. While these sensors are described as being located at or near the heater 110, this is not required. For example, temperature sensors that measure the temperature of the perfusion fluid can be placed hout the system 100 such as in the es 313, 315, in the measurement drain 2804, in the drain 2806, and/or in the reservoir 160. Additional temperature sensors can also be ed to e other temperature aspects of the system 600. For example, the system 600 can include ambient air temperature sensors that measure the ature of the environment around the system 600, temperature sensors that measure the temperature of the environment within the organ chamber 104, and/or sensors that e the temperature of a e and/or internal portion of the organ contained therein.

The controller 150 can use information from the various temperature sensors in the system 600 in order to control the ature of the environment and/or perfusion fluid therein. For example, in some embodiments the controller 150 can in the perfusion fluid exiting the heater at a desired temperature. In some embodiments, the controller 150 can determine a ature differential between the perfusion fluid flowing into and out of the organ. If the temperature differential is large, the controller 150 can indirectly determine the temperature of the organ and adjust the temperature of the perfiasion fluid flowing into the organ to achieve the desired organ temperature. Additionally, in some embodiments the organ chamber 104 can include a heater/cooler that heats/cools the environment within the organ chamber 104, such as a resistive heater or a thermoelectric cooler. Such a /cooler can be controlled by the controller 150.

While much of the disclosure herein s on heating an organ to a desired temperature, this is not intended to be ng. In some embodiments, the system 600 can include a cooling unit (not shown) in on to and/or instead of the heater 110.

In such embodiments, the cooling unit can be used to cool the perfusion fluid and ultimately cool the organ itself. This can be useful during, for example, post- preservation ng procedures used with a heart, lung, kidney, and/or liver. In some embodiments, the cooling unit can be comprised of a gas exchanger with an integrated water cooled feature, although other configurations are possible.

C. Blood flow monitoring and control Many organs in the human body receive a blood supply with a single set of pressure and flow characteristics (e. g., kidney, lung). To the extent that these organs are maintained ex vivo in an organ care system, a single pump and a single supply line can be used to provide perfusion fluid thereto. The liver, however, is different from other organs in that it has two blood supplies, each with different pressure and flow characteristics. As noted above, the liver es imately 1/3 of its blood supply from the hepatic artery and imately 2/3 of its blood supply from the portal vein. The hepatic artery provides a pulsatile blood flow at a relatively high pressure, but low flow rate. In contrast, the portal vein provides a substantially nonpulsatile blood flow at a relatively low pressure, but high flow rate. Because of these different flow characteristics, providing perfusion fluid to an ex vivo liver can present challenges when a single pump is used. Thus, some embodiments of the organ care system 600 include a system that is configured to provide a dual flow of perfusion fluid in a manner that mimics the human body. Specifically, the branch 315 of the system 100 can provide ion fluid to the c artery in a pulsatile, high- pressure, low flow . The branch 313 of the system 100 can provide perfusion fluid to the portal vein in a non-pulsatile, low re, high flow manner.

As noted above, the pump 106 can provide a flow ofperfiasion fluid at a predetermined flow rate, which can be split at the divider 105. In some ments, the fluid flow can be split between the c artery and the portal vein at a ratio of between 1:2 and 1:3. In some embodiments, the divider is configured such that the branch 313 uses 3/8” tubing and the branch 315 uses 1A” tubing. In some embodiments, a portal vein clamp can be used to help attain this split ratio and/or can be used to restrict the resulting flow in the portal vein leg of the circuit (e.g., branch 313) so as to create higher pressure flow in the hepatic artery leg of the circuit (e.g., branch 315) and lower pressure flow in the parallel portal vein leg of the circuit. In some embodiments, a user can manually adjust the portal vein clamp (e.g., such as the flow clamp 190) to effect a hepatic re in the acceptable range and adjust the pump flow rate to provide an acceptable hepatic artery flow rate. The combination of these two adjustments (portal vein clamp and pump flow rate) can result in acceptable hepatic artery flow and pressure and correspondingly acceptable portal vein pressure and flow rate.

In some embodiments, the portal vein clamp can be implemented as mechanism controlled by the system, such as an electromechanical or pneumatically controlled clamp. The system can adjust the pump flow and portal vein clamp in response to pressure and flow values measured on the hepatic artery and portal vein branches to effect pressures and flows in acceptable ranges for these paths. For example, in embodiments that use an automated portal vein clamp, if the controller 150 detects that the flow in the hepatic artery branch 315 is too low, the controller 150 can increase the flow rate provided by the pump 106. Likewise, if the controller detects that the pressure in the hepatic artery branch 315 is too low, the controller 150 can cause the portal vein clamp to close slightly in order to increase the pressure in hepatic artery branch 315.

In some embodiments, the controller 150 can monitor the level of perfusion fluid in the system 600. In the event that the amount of ion fluid is below recommended levels, the controller 150 can alert the user to this fact so that they may take recommended action such as ing pump flow and/or adding additional perfusion fluid to the . onally, if the level is below a critical level, the controller 150 can automatically reduce the pump flow to a reduced or minimal level while alerting the user.

D. Gas monitoring and control In some ments, the system 600 can be configured to automatically control pressure within the system by varying the flow rate of the pump 106 and/or by controlling the infiision of a vasodilator. For example, one ofthe infiasions provided by the solution pump 631 can be, or can contain a vasodilator. When a vasodilator is IO administered, the ion fluid pressure for a given flow rate within the system 100 can drop (due to the dilation of the vasculature in the . Thus, for example, reducing the infusion rate of a vasodilator can result in increased perfiasate pressure.

An optimal balance can be achieved at the least amount of vasodilator that results in adequate liver perfusion.

The system 600 can be configured to control the gas content in the perfusion fluid in such a manner that it mimics the human body. Accordingly, in some ments, the system 600 includes a gas exchanger (e. g., gas exchanger 114) that is configured to provide 02 and/or other desirable gases to the perfiasion fluid. In principle, a gas exchanger works by facilitating the flow of a high concentration of gas to an area of low concentration of gas. In this way, the O2 in the maintenance gas (e.g., the gas provided to the gas exchanger) can be diffused to the O2 depleted perfusion fluid and the relatively high level of CO2 in the perfusion fluid can be diffused to the maintenance gas before it is exhausted from the gas ger. The maintenance gas provided to the gas exchanger can be comprised ofthe appropriate e of 02, N2, and CO2, where the tration of O2 is higher, and the concentration of CO2 is lower than that in the perfusion solution exiting a metabolically-active liver. In some instances the gas is sed of only 02 and N2.

Some embodiments of the system 600 include an oxygenation sensor (e.g., sensor 140) that can be used to provide information about the oxygenation of the perfusion fluid. If the oxygenation level is too low, the rate of gas supplied to the gas ger can be increased to raise the level of oxygen in the perfusion fluid.

Likewise, if the level is too high, the rate of gas supplied to the gas exchanger can be decreased. Control of the gas supply to the gas exchanger can be performed manually by the user (e.g., through the operator ace module 146) and/or automatically. In an automated embodiment, the controller 150 can automatically increase or decrease the gas flow from the d gas supply to the gas ger to effect the desired change in ation level.

The liver, however, can present an additional challenge providing the proper perfusion fluid gas content. Because of its inherent metabolism, the liver produces CO2 that replaces 02 contained in the perfusate. In some embodiments, measuring the 02 levels alone is not sufficient to determine the amount of CO2 present in the perfusion fluid. Thus, some embodiments the system 600 can be configured to IO separately monitor the level of CO2 in the perfusion fluid to ensure that it stays within an acceptable range. In these embodiments, the gas exchanger can also be used to reduce or even eliminate CO2 from the perfiision fluid as it passes therethrough.

In order to determine the carbon dioxide level in the perfusate, some embodiments of the system 600 orate blood sample ports so that the user can withdraw blood samples to assess the levels of carbon e in the perfusate via a third party blood gas analyzer. Based on this is, the user can assign a gas flow rate into the gas exchanger in order to effect an acceptable carbon dioxide level in the perfusate. For example, higher than acceptable levels of carbon dioxide can require a higher gas flow rate to the gas exchanger to reduce the resulting level of carbon dioxide. However, it can be ageous to keep the gas flow to the gas exchanger as low as possible in order to maximize the life of the onboard gas supply—an ant factor in extended transport scenarios.

Some embodiments of the system 600 can incorporate a blood gas analysis system (not shown). In these embodiments, the blood gas is system can be configured to sample perfusion fluid flowing within the system 100. For example, the blood gas analysis system can be configured to take samples of perfusion fluid at one or more locations in the system 100 such as in es 313, 315, in the measurement drain 2804, and/or in the main drain 2806. By measuring the concentration of oxygen and/or carbon dioxide in the perfusate, the controller 150 can automatically increase or decrease, as the case may be, the flow of gas to the gas exchanger to obtain the desired gas levels in the perfusion fluid.

E. Solution delivery and control As noted above, some embodiments of the system 600 can include a solution pump that is configured to provide one or more solutions. In some specific embodiments, the runtime perfusion solution comprises three solutions. The first solution can comprise one or more energy—rich component (e.g., one or more carbohydrates); and/or one or more amino acids; and/or one or more electrolytes; and/or one or more ing agents (e.g., onate). In some particular embodiments, the first solution can comprise TPN (Clinimix E), buffering agents (e.g., sodium bicarbonate and phosphates), heparin and insulin. The second solution can comprise one or more vasodilators. In some particular embodiments, the IO vasodilator used is Flolan®. The third solution can comprise bile acid or salts (e.g., Na Taurocholic acid salt). In some ments, the three solutions are kept separate from one another and administered separately (e.g., using the three channels of the solution pump 631). In other embodiments, the three solutions, optionally all aqueous solutions, can be mixed er to form the runtime perfiJsion solutions. In n embodiments, a sufficient amount of heparin can be ed (e.g., amount sufficient to maintain activated clotting time (ACT) for about or more than 400 seconds ACT).

V. Solutions Exemplary solutions that can be used in the organ care system 600 according to one or more embodiments are now described. Various solutions can be used at different times in the vation/treatment s.

A. Donor Flush If the organ being harvested is an abdominal organ, the surgeon performing the harvest can perform a donor flush in vivo or ex vivo to remove donor blood and/or other matter from the organ. The flush used during the donor flush can be an intracellular or extracellular solution such as the University of Wisconsin Solution, a modified University of Wisconsin Solution, or a histidine-tryptophan-ketoglutarate (HTK) solution.

B. Initial flush solution In some ments, after the donor flush (regardless of r the donor flush was done in vivo or ex vivo) and before it is placed in the vation chamber of the organ care system 600, an initial flush solution can be used to flush the liver in vivo or ex vivo in order to remove the residual blood and any solution used in the WO 87737 2015/033839 donor flush. This flush solution is referred to herein as the initial flush solution, which is optionally a sterile solution. In some ments, the main components of the l flush solution can include a buffered isotonic electrolyte solution, such as Plasmalyte, and an ti-inflammatory, such as SoluMedrol. In some embodiments, the initial flush can be used to remove the fluid used during the donor flush. In some embodiments, the main components of the initial flush solution can include electrolytes and buffering agents. Non-limiting examples of the electrolytes include s salts of sodium, potassium, calcium, magnesium, chloride, en phosphate, and hydrogen carbonate. A proper combination of the electrolytes in suitable concentrations can help maintain the physiological c pressure of the intracellular and extracellar environment in liver. Non-limiting examples of the ing agents include bicarbonate ions. The buffering agents in the initial flush solution can serve to maintain the pH value inside the liver organ to be at or close to the physiological state, e. g., about 7.3 to 7.6, 7.4 to 7.6, or 7.4 to 7.5. Preferably, after the liver is ted to the initial flush and cooled according to one more embodiments described herein, the harvested liver can be placed into the organ care system 600 according to one more embodiments.

C. Priming solution and additives In certain embodiments, prior to the placement of the liver into the organ care system 600, the organ care system 600 can be primed with a priming solution. The g solution can be sterile and can be used to evaluate the physical integrity of the system and/or to help remove the air in the system. The composition of the priming solution can be similar or identical to that of the runtime perfusion solution, described in more detail below. The priming solution can include certain additives to render the system compatible with liver preservation. For instance, the liver regularly produces coagulation factors promoting blood coagulation. In order to t the blood (e.g., donor’s blood used as part of the perfusion fluid for preserving the liver on the organ care system 600) from clotting during preservation, anti-clotting agents can be added to the priming solution as additives. Non-limiting examples of anti- clotting agents include heparin. Heparin can be administered throughout the vation session to maintain ACT ated clotting time) of Z 400 s, although other ACT values can be used. Depending on the liver being maintained, the amount of n needed to achieve the desired ACT can vary. In some embodiments, the heparin can be provided continuously or at intervals such as at 0, 3, and 6 hours post-instrumentation on the system 600. In certain embodiments, the organ care system 600 can be primed by a blood product (e.g., donor’s blood) or synthetic blood product prior to the placement of the liver into the organ care system 600. In certain embodiments, the system 600 can be primed by the g solution and/or the blood or synthetic blood product. The system 600 can be primed by the mixture ofthe priming on and the blood or synthetic blood product, or by the priming solution and the blood or synthetic blood product sequentially. In some IO embodiments, the organ care system 600 is primed with the perfusion fluid described herein (e. g., the perfusion fluid used to ve the organ). Alternatively or additionally, any one of the following combined with either albumen or dextran can also be used: donor blood, red blood cells (RBC), or RBCs plus fresh frozen plasma plus Table 1 sets forth components that can be used in an exemplary priming solution.

TABLE 1. ition of Exemplary Priming Solution Component Amount Specification pRBCs 1200-1500 : about 10% % Albumin : about 10% PlasmaLyte : about 10% Cefazoline or 2 about 10% equivalent antibiotic (gram positive and gram negative) Cipro or equivalent : about 10%. antibiotic (gram positive and gram negative) Soiwl‘viedrol or i about 10%. equivalent anti» inflammatory 50 mmoi : about 10%. itamin Calcium ate : about 10%.

Heparin (Optional) 10000 Units : about 10%.

The exemplary priming solution can be added to the organ care system 600 through the priming step 5024, as more fully described with reference to (described more fillly below).

D. Runtime perfusion solution During the preservation of the harvested liver in the organ care system 600 (e.g., during transport), a perfusion fluid or perfusate, can be used to perfuse the liver and maintain the liver function at or near physiological conditions. In certain embodiments, the perfusion fluid comprises a runtime ion on (also ed to as a maintenance solution) and/or a blood product, e.g., donor’s blood, other individual’s compatible blood, or synthetic blood. The perfusion fluid can be periodically/continuously infused by, for example, the solution pump 631 in order to provide nutrients that can maintain the liver during preservation. In some embodiments, the runtime perfusion solution and/or the blood product are sterile.

The compositions of the runtime perfusion solution and the priming solution are now described in more detail. According to certain ments, the runtime perfusion solution with particular solutes and concentration is ed and proportioned to enable the organ to fianction at physiologic or near physiologic conditions. For example, such conditions e maintaining organ function at or near a logical temperature and/or preserving the liver in a state that permits normal cellular metabolism, such as protein synthesis, e storage, lipid metabolism, and bile production. In some embodiments, the priming solution and runtime solution can be selected to be similar or even identical to one another.

In certain embodiments, the runtime perfiasion solution is formed from compositions by combining ents with a fluid, from more concentrated solutions by dilution, or from more dilute solutions by tration. In exemplary embodiments, suitable runtime perfusion solutions include an energy source, and/or one or more stimulants to assist the organ in continuing its normal physiologic function prior to and during transplantation, and/or one or more amino acids selected and proportioned so that the organ continues its cellular metabolism during perfusion.

The runtime perfusion solution can include any therapeutic agents bed in more detail below. Cellular lism includes, for example conducting protein synthesis while functioning during perfusion. Some illustrative solutions are s based, while other illustrative solutions are ueous, for example organic solvent-based, ionic-liquid-based, or fatty-acid-based.

The runtime perfiasion solution can include one or more energy-rich components to assist the liver in conducting its normal physiologic function. These components can include energy rich materials that are metabolizable, and/or components of such materials that an organ, e.g., liver, can use to synthesize energy sources during perfusion. Exemplary sources of energy-rich molecules include, for e, one or more carbohydrates. Examples of carbohydrates include ccharides, disaccharides, oligosaccharides, polysaccharides, or combinations thereof, or sors or metabolites thereof. While not meant to be ng, examples of ccharides suitable for the solutions include octoses; heptoses; hexoses, such as fructose, allose, altrose, glucose, mannose, gulose, idose, galactose, and talose; pentoses such as ribose, arabinose, xylose, and ; tetroses such as erythrose and threose; and trioses such as glyceraldehyde. While not meant to be limiting, examples of disaccharides suitable for the solutions include ltose (4- O-(OL-D-glucopyranosyl)—0t-D-glucopyranose), (+)-cellobiose (4-O-(B-D- glucopyranosyl)-D—glucopyranose), (+)-lactose (4-O-(B-D-galactopyranosyl)—B-D- glucopyranose), sucrose (2-O-(0t-D-glucopyranosyl)-B-D-fructofuranoside). While not meant to be limiting, examples of polysaccharides suitable for the solutions include ose, , amylose, amylopectin, sulfomucopolysaccharides (such as dermatane sulfate, chondroitin sulfate, sulodexide, mesoglycans, heparan sulfates, idosanes, heparins and heparinoids), dextrin, and glycogen. In some embodiments, monossacharides, disaccharides, and polysaccharides of both s, ketoses, or a combination thereof are used. One or more isomers, including enantiomers, diastereomers, and/or tautomers of monosacharides, disaccharides, and/or polysaccharides, ing those described and not described herein, can be employed in the e ion solution described herein. In some embodiments, one or more monossacharides, disaccharides, and/or polysaccharides can have been chemically modified, for example, by derivatization and/or protection (with protecting groups) of one or more functional groups. In certain ments, ydrates, such as dextrose or other forms of glucose are preferred.

Other possible energy sources include, co-enzyme A, pyruvate, flavin adenine dinucleotide (FAD), thiamine pyrophosphate chloride (co—carboxylase), [3- nicotinamide adenine dinucleotide (NAD), B-nicotinamide adenine dinucleotide phosphate ), and phosphate derivatives of nucleosides, i.e. nucleotides, including mono-, di-, and tri-phosphates (e.g., UTP, GTP, GDP, and UDP), coenzymes, or other bio-molecules having similar cellular metabolic functions, and/or metabolites or precursors thereof. For example, phosphate derivatives of adenosine, guanosine, thymidine (5 -Me-uridine), cytidine, and uridine, as well as other lly and chemically modified nucleosides are contemplated.

In n embodiments, one or more carbohydrates can be provided along with a phosphate , such as a nucleotide. The carbohydrate can help enable the organ to produce ATP or other energy sources during perfusion. The phosphate source can be ed directly through ATP, ADP, AMP or other sources. In other rative embodiments, a phosphate is provided through a phosphate salt, such as glycerophosphate, sodium phosphate or other phosphate ions. A phosphate can include any form thereof in any ionic state, including protonated forms and forms with one or more counter ions. The energy source used can depend on the type of organ being perfused (e.g., ine can be omitted when perfusing a liver).

One of the liver’s important functions is to produce bile liquid. In some embodiments, the runtime ion solution comprises one or more compounds supporting the production of bile by the liver. Non—limiting examples of such compounds include cholesterol, y bile acids, secondary bile acids, glycine, taurine, and bile acids (bile salts) to promote production of bile by the liver ex vivo, IO all of which can be used by the liver to produce bile. In some specific embodiments, the bile salt is Na Taurocholic acid salt.

Because ofthe liver’s function as the lism powerhouse of the body, it is typically in constant need of energy source and . Thus, in addition to maintaining the proper concentration of the energy source compounds in the perfiJsion liquid, the organ care system 600 described herein can also red to provide constant oxygen supply to the preserved liver. In some embodiments, the oxygen is provided by ing an oxygen gas flow through the perfusion liquid (e.g., in the gas exchanger 114) or the blood product to dissolve or saturate oxygen in the liquid medium, e.g, by binding oxygen to the hemoglobin in the blood product. In certain embodiments, the perfusion liquid supplied to the liver contains 02 in PaOz 2 200 mmHg (arterial perfusate). In certain embodiments, the perfusion liquid supplied to the liver contains less than PaCOz S 40 mmHg of carbon dioxide y promoting and ining the oxidative metabolic functions of the liver. In certain embodiments, the perfusion liquid contains less than 30 mmHg 5 PAC02 of carbon dioxide thereby maintaining the pH value in the liver to in its biological functions.

The runtime perfiision solution described herein can e one or more amino acids, ably a plurality of amino acids, to support protein synthesis by the organ's cells. Suitable amino acids include, for example, any of the naturally- occurring amino acids. The amino acids can be, in s enantiomeric or diastereomeric forms. For example, solutions can employ either D- or L-amino acids, or a combination thereof, i.e. solutions enantioenriched in more of the D- or L-isomer or racemic solutions. Suitable amino acids can also be non-naturally occurring or modified amino acids, such as line, ornithine, homocystein, homoserine, [3- amino acids such as B-alanine, amino-caproic acid, or combinations thereof Certain exemplary runtime perfusion solutions include some but not all lly-occurring amino acids. In some embodiments, runtime perfusion solutions include essential amino acids. For example, a runtime perfusion solution can be ed with one or more or all of the following amino-acids: Glycine, Alanine, Arginine, Aspartic Acid, Glutamic Acid, Histidine, Isoleucine, Leucine, Methionine, Phenylalanine, Proline, Serine, nine, phan, Tyrosine, Valine, and Lysine acetate.

In n embodiments, non-essential and/or semi-essential amino acids are not included in the runtime perfusion solution. For example, in some embodiments, asparagine, glutamine, and/or cysteine are not included. In other embodiments, the solution contains one or more non-essential and/or semi-essential amino acids.

Accordingly, in some ments, asparagine, glutamine, and/or cysteine are included.

The runtime ion solution can also contain electrolytes, particularly calcium ions for facilitating enzymatic reactions, and/or maintain osmotic pressure within the liver. Other electrolytes can be used, such as sodium, potassium, chloride, sulfate, magnesium and other inorganic and c charged species, or combinations thereof. It should be noted that any component provided hereunder can be provided, where valence and stability , in an ionic form, in a protonated or unprotonated form, in salt or free base form, or as ionic or covalent tuents in ation with other components that hydrolyze and make the component available in aqueous solutions, as suitable and appropriate.

In certain ments, the runtime perfiJsion solution contains buffering components. For example, suitable buffer s include 2- morpholinoethanesulfonic acid monohydrate (MES), cacodylic acid, NaHC03 (pKal), citric acid (pKag), bis(2-hydroxyethyl)-imino-tris-(hydroxymethyl)—methane (Bis-Tris), N—carbamoylmethylimidino acetic acid (ADA), 3- bis[tris(hydroxymethyl)methylamino]propane (Bis-Tris Propane) (pKal), piperazine- I,4-bis(2-ethanesulfonic acid) (PIPES), N-(2-Acetamido)-2—aminoethanesulfonic acid (ACES), imidazole, N,N—bis(2-hydroxyethyl)—2-aminoethanesulfonic acid (BES), 3- (N—morpholino)propanesulphonic acid (MOPS), NaH2P04/Na2HPO4 (pKaz), N- tris(hydroxymethyl)methylaminoethanesulfonic acid (TES), N-(2-hydroxyethyl)- piperazine—N'ethanesulfonic acid (HEPES), N-(2-hydroxyethyl)piperazine-N'-(2— hydroxypropanesulfonic acid) (HEPPSO), triethanolamine, N- [tris(hydroxymethyl)methyl]glycine (Tricine), tris ymethylaminoethane , glycineamide, N,N—bis(2-hydroxyethyl) glycine (Bicine), glycylglycine (pKaz), N- ydroxymethyl)methylaminopropanesulfonic acid (TAPS), or a combination thereof. In some embodiments, the solutions contain sodium bicarbonate, potassium phosphate, or TRIS buffer.

The e perfusion solution can include other components to help maintain IO the liver and t it against ischemia, reperfilsion injury and other ill effects during perfusion. In n exemplary embodiments these components can include hormones (e.g. , insulin), Vitamins (e.g., an adult multi-Vitamin, such as multi-Vitamin MVIAdult ), and/or steroids (e.g, dexamethasone and SoluMedrol).

In another aspect, a blood product can be provided with the runtime ion solution to support the liver during preservation. Exemplary suitable blood products can include whole blood, and/or one or more components thereof such as blood serum, plasma, albumin, and red blood cells. In embodiments where whole blood is used, the blood can be passed through a leukocyte and platelet depleting filter to reduce pyrogens, antibodies and/or other items that can cause inflammation in the organ. Thus, in some embodiments, the perfiision fluid employs whole blood that has been at least partially depleted of leukocytes and/or whole blood that has been at least partially depleted of platelets.

The perfusion fluid comprising the blood product and the runtime perfusion on can be provided at a physiological temperature and maintained thereabout throughout perfusion and recirculation. As used herein, "physiological temperature" is ed to as atures between about 25° C and about 37° C, for example, between about 30° C and about 37° C, such as n about 34° C and about 37° C.

Other components or additives can be added to the runtime ion solution, including, for example, adenosine, magnesium, phosphate, calcium, and/or sources thereof. In some ments, additional components are provided to assist the liver in conducting its metabolism during perfusion. These components include, for example, forms of adenosine, which can be used for ATP sis, for maintaining endothelial function, and/or for attenuating ischemia and/or reperfiasion injury.

Components can also include other nucleosides, such as guanosine, thymidine (S-Me- e), cytidine, and e, as well as other naturally and chemically modified nucleosides including nucleotides thereof. According to some ments, a magnesium ion source is provided with a phosphate source, and in certain embodiments, with adenosine to further enhance ATP synthesis within the cells of the perfused liver. A plurality of amino acids can also be added to t protein synthesis by the liver cells. Applicable amino acids can include, for example, any of the naturally-occurring amino acids, as well as those mentioned above.

In some embodiments, the runtime perfusion solution further comprises one or more vasodilators (e.g., a vasodilator can be used to increase or decrease vascular tone and thereby the pressure within the vessel). In some particular embodiments, the vasodilator used is Flolan® although other vasodilators can also be used.

Table 2 sets forth components that can be used in a runtime perfusion solution for preserving a liver as described herein. The runtime perfusion solution can include one or more of the components bed in Table 2.

TABLE 2. ent plary Composition for the Runtime Perfusion on Component Exemplary Concentration Ranges in Preservative Solution Alanine about 1 mg/L-about 10 g/L Glutamic Acid about 1 mg/L-about 10 g/L Glutamine about 1 mg/L-about 10 g/L 2015/033839 Leucine about 1 mg/L-about 10 g/L Lysine about 1 mg/L-about 10 g/L Methionine about 1 mg/L-about 10 g/L Phenylalanine about 1 mg/L-about 10 g/L Proline about 1 mg/L-about 10 g/L Serine about 1 mg/L-about 10 g/L AMP about 10 ug/L-about 100 g/L Ascorbic Acid about 1 ug/L-about 10 g/L D-Biotin about 1 ug/L-about 10 g/L Vitamin D-12 about 1 ug/L-about 10 g/L Cholesterol about 1 ug/L-about 10 g/L Dextrose (Glucose) about 1 out 150 g/L Multi-Vitamin Adult about 1 mg/L-about 20 mg/L or 1 unit Vial Epinephrine about 1 ug/L-about 1 g/L Folic Acid about 1 ug/L-about 10 g/L hione about 1 ug/L-about 10 g/L Guanine about 1 ug/L-about 10 g/L ol about 1 g/L-about 100 g/L Riboflavin about 1 ug/L-about 10 g/L Ribose about 1 ug/L-about 10 g/L Thiamine about 1 mg/L-about 10 g/L Uracil about 1 mg/L-about 10 g/L Calcium Chloride about 1 mg/L-about lOO g/L NaHC03 about 1 mg/L-about 100 g/L Magnesium sulfate about 1 mg/L-about 100 g/L Potassium chloride about 1 mg/L-about 100 g/L Sodium about 1 mg/L-about 100 g/L glycerophosphate Sodium Chloride about 1 mg/L-about 100 g/L Sodium Phosphate about 1 mg/L-about 100 g/L Insulin about 1 IU-about 150 IU Serum albumin about 1 g/L-about 100 g/L Pyruvate about 1 mg/L-about 100 g/L Coenzyme A about 1 ug/L-about 10 g/L Serum about 1 ml/L-about 100 ml/L n about 500 U/L-about 1500 U/L Solumedrol about 200 mg/L-about 500 mg/L thasone about 1 mg/L-about 1 g/L FAD about 1 ug/L-about 10 g/L NADP about 1 ug/L-about 10 g/L guanosine about 1 mg/L-about 10 g/L GTP about 10 ug/L-about 100 g/L GDP about 10 ug/L-about 100 g/L GMP about 10 ug/L-about 100 g/L Table 3 sets forth components that can be used in an ary runtime ion solution. The amounts provided in Table 3 describe preferred amounts relative to other components in the table and can be scaled to provide compositions of sufficient quantity. In some embodiments, the amounts listed in Table 3 can vary by i about 10% and still be used in the solutions bed herein.

TABLE 3. Components of Exemplary Runtime Perfiasion Solution Calcium Chloride dihydrate About 2100 mg-About 2600 mg Glycine About 315 mg-About 385 mg L—Alanine About 150 mg-About 200 mg L-Arginine About 600 ut 800 mg rtic Acid About 220 ut 270 mg L-Glutamic Acid About 230 mg-About 290 mg L-Histidine About 200 mg-About 250 mg L-Isoleucine About 100 mg about 130 mg L-Leucine About 300 mg-About 380 mg L—Methionine About 50 mg-About 65 mg L-Phenylalanine About 45 mg-About 60 mg L-Proline About 110 mg-About 140 mg L—Serine About 80 mg-About 105 mg L-Thereonine About 60 mg-About 80 mg L-Tryptophan About 30 mg-About 40 mg sine About 80 mg-About 110 mg L—Valine About 150 mg-About 190 mg Lysine Acetate About 200 mg-About 250 mg Magnesium Sulfate About 350 mg-About 450 mg Heptahydrate ium Chloride About 15 mg-About 25 mg Sodium Chloride About 1500 mg-About 2000 mg Dextrose About 25 gm-About 120 gm Epinephrine About 0.25 mg—About 1.0 mg Insulin About 75 Units—About 150 Units MVI-Adult 1 unit vial SoluMedrol About 200 mg-500 mg Sodium Bicarbonate About 10-25 mEq In the exemplary embodiment of a runtime perfusion solution, the components in Table 3 can be combined in the relative amounts listed therein per about 1 L of aqueous fluid to form the runtime perfusion solution. In some ments, the quantity of aqueous fluid in the e perfusion solution can vary iabout 10%. The pH of the runtime ion solution can be adjusted to be between about 7.0 and about 8.0, for example about 7.3 and about 7.6. The runtime perfusion solution can be sterilized, for example by aving, to provide for improved purity.

Table 4 sets forth another exemplary e perfusion solution, comprising a tissue culture media having the components identified in Table 4 and combined with an s fluid, which can be used in the perfiasion fluid as bed herein. The amounts of components listed in Table 4 are relative to each other and to the quantity of aqueous solution used. In some embodiments, about 500 mL of aqueous fluid is used. In some embodiments, the quantity of aqueous solution can vary :: about 10%.

The component amounts and the quantity of aqueous solution can be scaled as appropriate for use. The pH of the runtime perfilsion solution, in this embodiment, can be adjusted to be about 7.0 to about 8.0, for example about 7.3 to about 7.6.

TABLE 4. Composition of Another Exemplary Runtime Perfusion Solution (about 500 mL s solution) Tissue Culture Amount Specification Component Calcium Chloride 2400 mg : about 10% dihydrate e 350 mg j: about 10% L—Alanine 174 mg 1: about 10% L—Arginine 700 mg : about 10% L-Aspartic Acid 245 mg : about 10% L-Glutamic Acid 258 mg : about 10% L—Histidine 225 mg : about 10% L-Isoleucine 115.5 mg :: about 10% ine j: about 10% L—Methionine 1 about 10% L—Phenylalanine : about 10% L-Proline 126 mg :: about 10% L-Serine 0b.) (IQ :: about 10% L-Thereonine \lO (IQ :: about 10% Lysine e Magnesium Sulfate 400 mg d: about 10% Heptahydrate Potassium Chloride 20 mg : about 10% Sodium Chloride 1750 mg :: about 10% Since amino acids are the building blocks of ns, the unique characteristics of each amino acid impart certain important properties on a protein such as the ability to provide structure and to catalyze biochemical reactions. The selection and concentrations of the amino acids provided in the runtime perfusion solutions can provide support of normal physiologic functions such as metabolism of sugars to provide or store energy, regulation of protein metabolism, transport of minerals, synthesis of nucleic acids (DNA and RNA), regulation of blood sugar and support of electrical activity, in on to providing protein structure. Additionally, the concentrations of specific amino acids found in the runtime perfiision solution can be used to predictably stabilize the pH of the runtime perfiasion solution.

In n embodiments, in order to prevent the blood used as part of the perfusion fluid for preserving the liver on the organ care system 600 from clotting during preservation, anti-clotting agents can be added to the runtime perfusion solution as ves. miting es of anti-clotting agents include heparin.

In some embodiments, heparin can be included in a sufficient amount to prevent clotting for 500-600 seconds, although other times are le.

In certain embodiments, the runtime perfiision solution includes a plurality of amino acids. In certain embodiments, the e perfusion solution includes electrolytes, such as calcium and magnesium.

WO 87737 In one embodiment, a e perfusion solution includes one or more amino acids, and one or more carbohydrates, such as glucose or dextrose. The runtime perfusion solution can also have additives, such as those described herein, administered at the point of use just prior to infusion into the liver perfusion system.

For example, additional additives that can be included with the solution or added at the point of use by the user include hormones and steroids, such as dexamethasone and insulin, as well as vitamins, such as an adult multi-vitamin, for example adult itamins for infusion, such as MVI-Adult. Additional small molecules and large bio-molecules can also be included with the runtime perfusion solution or added at the point of use by the user, including therapeutics and/or components typically associated with blood or blood plasma, such as albumin.

In some embodiments, therapeutics can be added either before or during perfusion of the liver. The therapeutics can also be added directly to the system independently from the runtime perfusion solution, before or during perfusion of the organ.

With fiarther reference to Table 3 or 4, certain components used in the exemplary e perfiusion solution are molecules, such as small organic molecules or large bio-molecules, that would be inactivated, for example through decomposition or denaturing, if passed through sterilization. Thus, these components can be prepared tely from the ing components of the runtime perfilsion solution. The te preparation involves tely ing each component through known techniques. The remaining components of the e perfusion on are sterilized, for example through an autoclave, then combined with the biological components.

Table 5 lists certain biological components that can be separately purified and added to the solutions (runtime perfusion solution and/or priming solution) described herein after sterilization, ing to this two-step process. These additional or supplemental components can be added to runtime perfusion solution, the priming solution or a combination thereof individually, in various ations, all at once as a composition, or as a combined solution. For e, in certain embodiments, the insulin, and MVI-Adult, listed in Table 5, are added to the runtime perfusion solution.

In another example, the SoluMedrol and the sodium bicarbonate, listed in Table 5, are added to the priming on. The additional components can also be combined in one or more combinations or all together and placed in solution before being added to runtime perfusion solution, and/or the priming on. In some embodiments, the additional components are added directly to the perfusion fluid. The component amounts listed in Table 5 are relative to each other and/or to the s of components listed in one or more of Tables l-4 as well as the amount of aqueous solution used in preparing the runtime perfusion solution, and/or the priming solution and can be scaled as appropriate for the amount of solution required.

TABLE 5. Exemplary Biological Components Added to Solutions Prior to Use n about 100 Units Hormone : about 10% MVI-Adult 1 mL unit vial Vitamin : about 10% drol About 250 mg Steroid i about 10% Sodium About 20 mEq Buffer d: about 10% onate In one embodiment, a composition for use in a runtime perfusion on is provided comprising one or more carbohydrates, one or more organ stimulants, and a plurality of amino acids. The composition can also include other substances, such as those used in solutions described herein.

In another embodiment, a system for ing a liver, is provided comprising a liver and a substantially cell-free composition, comprising one or more carbohydrates, one or more organ stimulants, and a plurality of amino acids. The ntially ree composition can include systems that are substantially free from cellular matter; in particular, systems that are not derived from cells. For example, substantially cell-free composition can include compositions and solutions ed from non-cellular sources.

In another aspect, the runtime perfusion solution and/or the priming solution can be provided in the form of a kit that includes one or more organ maintenance 2015/033839 solutions. An exemplary runtime perfusion on can include components identified above in one or more fluid solutions for use in a liver perfusion fluid. In certain embodiments, the runtime perfiision solution can include multiple solutions which, in various combinations, provide the runtime perfiasion solution. atively, the kit can include dry components that can be regenerated in a fluid to form one or more runtime perfiision solution or priming solution. The kit can also comprise components from the runtime perfusion solution or priming solution in one or more trated solutions which, on dilution, provide a preservation, nutritional, and/or supplemental solution as described . The kit can also include a g solution.

In certain embodiments, the kit is provided in a single package, wherein the kit includes one or more solutions (or components necessary to ate the one or more solutions by mixing with an appropriate fluid), and instructions for sterilization, flow and temperature control during perfiision and use and other information necessary or appropriate to apply the kit to organ perfusion. In certain embodiments, a kit is provided with only a single runtime perfusion solution (or set of dry components for use in a solution upon mixing with an appropriate fluid), and along with a set of instructions and other information or materials necessary or useful to operate the runtime perfusion solution or g solution.

In n embodiments, the runtime perfiision solution is a singular solution.

In other embodiments, the runtime perfusion solution can include a main runtime perfusion solution and one or more nutritional supplement solutions. The nutritional ment solution can contain any compound or biological component suitable for the runtime perfiJsion describe above. For instance, the nutritional supplement solution can contain one or more components illustrated in Tables 1-5 above.

Additionally, Table 6 sets forth components that are used in an exemplary nutritional supplement on. In some embodiments, the nutritional solution further includes sodium glycerol phosphate. The amount of ents in Table 6 is relative to the amount of s solvent employed in the solution (about 500 mL) and may be scaled as appropriate. In some embodiments, the quantity of aqueous solvent varies iabout 10%. In these embodiments when a main runtime solution and one or more nutritional solutions are used, these solutions can be separately connected to the ation system of the organ care system 600 and l separately. Thus, when one or more components in a ional solution need to be adjusted, the operator may remake this particular nutritional solution with different concentration for these ents or adjust only the flow rate and/or re for this nutritional solution without affecting the flow rate and/or pressure for the main runtime ion solution and other ional solutions.

TABLE 6. Components of Exemplary Nutritional Solution (about 500 mL) In one embodiment, the runtime perfusion solution and the priming solution have the identical composition which is described in any one of Tables 1-6 or a combination thereof.

In some embodiments, the perfusion liquid comprises 1200—1500ml of pRBCs, 400 ml of 25% Albumin, 700 ml of PlasmaLyte, otic (gram positive and gram negative) lg Cefazoline (or equivalent antibiotic) and 100 mg Cipro (or equivalent antibiotic), 500 mg of Solu—Medrol (or equivalent anti-inflammatory), 50 mmol Hco3, multivitamin, and 10000 unit of Heparin administered at 3hr and 6 hr PT.

In n specific embodiments, the perfusion fluid comprises the liver donor’s blood, or packed red blood cells , or packed RBCs with fresh frozen plasma, and the runtime perfusion solution containing one or more components selected form the group consisting of human albumin or dextran. In certain specific embodiments, the ion fluid comprises the liver s blood, or packed RBCS or packed RBCs with fresh frozen plasma, and the runtime perfusion solution ning one or more components selected form the group consisting of human albumin, dextran, and one or more electrolyte.

E. Final-flush solution After the suitable recipient of the liver transplant is identified and before the liver is removed from the organ care system 600, the liver organ can be subjected to another flush process by a flush solution. This flush solution has the similar function as the initial flush solution, which is to remove the residual blood therein and stabilize the liver. This flush solution is referred to herein as the final flush solution. In some embodiments, the final flush solution has similar or identical compositions as the initial flush solution described above. The main components of the final flush on can include electrolytes (e.g., plasmalyte) and buffering agents described herein. In certain embodiments, one or more commercially—available preservation solutions used in hypothermal organ lant are used as the final flush solution.

After the liver is subjected to the final flush and cooled according to one more ments described herein, the liver can be removed from the organ care system 600 for implantation into a recipient.

VI. Methods Exemplary methods to use the organ care system 600 disclosed herein are now described in more . is a flow diagram 5000 depicting exemplary and non-limiting methodologies for harvesting the donor liver and cannulating it into the organ care system 600 described herein. The process 5000 shown in is exemplary only and can be modified. For e, the stages described therein can be altered, changed, rearranged, and/or d.

A. Harvesting organ As shown in , the process of obtaining and preparing liver for cannulation and transport can begin by providing a suitable liver donor (Stage 5004).

The system 600 can be brought to a donor location, whereupon the process of receiving and preparing the donor liver for cannulation and preservation can d down ys 5006 and 5008. The pathway 5006 principally involves preparing the donor liver for preservation, while the pathway 5008 principally involves preparing the system to receive and preserved the liver, and then transport the liver via the organ care system 600 to the recipient site.

As shown in , the first pathway 5006 can include exsanguinating the donor blood (Stage 5010), explanting the liver (Stage 5014), flushing the liver with initial flush solution (Stage 5016), and preparing and cooling the liver for the system (Stage 5018). In particular, in the exsanguination stage 5010, the donor's blood can be partially and/or wholly removed and set aside so it can be used to as the blood product in the ion liquid to perfuse the liver during preservation on the system.

This stage can be performed by inserting a catheter into either the arterial or venous vasculature of the donor to allow the donor's blood to flow out of the donor and be collected into a blood collection bag. The donor's blood is allowed to flow out until the necessary amount of blood is collected, typically 1.0-2.5 liters, whereupon the catheter is removed. The blood extracted through exsanguination is then optionally filtered and added to a fluid oir of the system in preparation for use with the . atively, the blood can be exsanguinated from the donor and filtered for leukocytes and platelets in a single step that uses an apparatus having a filter integrated with the cannula and blood collection bag. An example of such a filter is a Pall BCZB filter. Alternatively, a blood product can be used instead of the donor’s blood in the perfusion liquid (not shown in ).

After the donor's blood is exsanguinated, the donor liver can be harvested (Stage 5014). Any standard liver harvesting method known in the art can be used.

During liver harvesting, the liver vessels including hepatic , portal vein, or vena cava (IVC), and bile duct are prepared properly and severed, with sufficient vessel length remained for cannulation (e.g., standard practice, suitable for human or animal transplant). In certain embodiments, the gall bladder is removed during the liver harvesting and care is taken to preserve the common bile duct intact to maintain stable bile fluid flow during the liver vation. After the liver is removed in hospital settings, it is often flushed (e. g., donor flush) or placed in saline solutions. In stage 5016, the ted liver can then be flushed by an initial flush solution to remove any residual blood and/or donor flush on to improve the stability of the liver. An exemplary composition of the initial flush solution is described above in detail.

After the liver is harvested and prior to its placement on the organ care system 600, the liver can be cooled down (Stage 5018) to reduce or halt its metabolic functions to avoid damage to the liver which otherwise can occur during transportation or placement of the liver into the organ care system 600. In certain ments, the liver is cooled to about 4° C to 10° C, 5° C to 9° C, 5° C to 8° C, 4° C, ° C, 6° C, 7° C, 8° C, 9° C, or 10° C, or a temperature within any range bounded by the value described . The liver can be cooled by ice or refrigeration. Other temperature ranges below 4° C and above 10 °C are also possible. Alternatively, the initial flush solution can be cooled first and then used to flush the liver to cool the liver. Thus, in these alternative embodiments, Stages 5016 and 5018 can be performed simultaneously. Once the liver is prepared and cooled to a proper temperature, it can be ready to be placed onto the liver care system 600.

With continued nce to , during the preparation of the liver via path 5006, the system can be prepared through the stages ofpath 5008 so it is primed and waiting to receive the liver for cannulation and preservation as soon as the liver is prepared and cooled. By quickly transferring the liver from the donor to the system, and subsequently perfusing the liver with the perfusion fluid, a medical operator can minimize the amount of time the liver is deprived of oxygen and other nutrients, and thus reduce ischemia and other ill effects that arise during current organ care techniques. In certain embodiments, the amount of time between infusing the liver with the l flush solution and beginning flow of the perfusion fluid through the liver via the organ care system 600 is less than about 15 minutes. In other illustrative embodiments, the between—time is less than about 1/2 hour, less than about 1 hour, less than about 2 hours, or even less than about 3 hours. Similarly, the time between transplanting the liver into the organ care system 600 and bringing the liver to a near physiological ature (e.g., between about 34 0C and about 37 0C) can occurs within a brief period of time so as to reduce ia within the liver s. In some illustrative embodiments, the period of time is less than about 5 minutes, while in other applications it can be less than about 1/2 hour, less than about 1 hour, less than about 2 hours, or even less than about 3 hours. Stated differently, when the cooled liver is first placed into the organ care system 600, the temperature of the liver can gradually be raised to the desired temperature over a ermined amount of time to reduce any potential damage that could result of a sudden ature change.

As shown in , the system can be prepared in pathway 5008 through a series of stages, which include preparing the single use module (stage 5022), g the system with g solution (stage 5024), ng the blood from the donor and adding it to the system, e.g., at a reservoir of the system (stage 5012), optionally priming the system with blood and/or perfiision fluids, and connecting the liver into the system (stage 5020). In particular, the step 5022 of preparing the single use module includes assembling the disposable single use module described herein (e. g., single use module 634). After the single use module is assembled, or provided in the appropriate assembly, it is then inserted into and connected to the multiple use module (e.g., multiple use module 650) through the process described herein.

Specifically, in stage 5024, the liver care system 600 can be first primed with a priming solution, the composition of which is described more fully above. In certain embodiments, to aid in priming, the system can provide an organ bypass conduit installed into the organ chamber assembly. For example, in certain specific embodiments, the bypass conduit includes three segments attached to the hepatic artery cannulation interface, the portal vein cannulation interface, and the inferior vena cava (IVC) cannulation ace (if present). Using the bypass conduit attached/cannulated into the liver chamber assembly, an operator can cause the system to circulate the perfusion fluid through all of the paths used during actual operation.

This can enable the system to be thoroughly tested and primed prior to cannulating the liver into place.

In stage 5012, blood from the donor can be filtered and added to the , e.g., in the reservoir 160. The filtering process can help reduce the inflammatory process through the complete or partial removal of ytes and platelets.

Additionally, the donor blood can be used to ally prime the system as described above and/or mixed with one or more priming solution or runtime perfusion solution to further prime the system as bed above. Additionally, the blood and the run time perfiision solution can be mixed together to form the perfilsion fluid used later for infusing and preserving the liver. In stage 5026, the system can be primed with the blood and/or the perfusion fluid by activating the pump and by pumping the blood and/or the perfusion fluid through the system with the bypass conduit (described above) in place. As the perfusion fluid circulates through the system in priming stage 5026, it can optionally be warmed to the d temperature (e.g., normothermic) as it passes h a heater assembly of the . Thus, prior to ating the harvested liver, the system can be primed by circulating the g solution, exsanguinated donor blood, and/or the mixture of the two (e.g, the perfusion fluid) through the system to heat, oxygenate and/or filter it. Nutrients, preservatives, and/or other therapeutics can also be provided during g by addition of the components to the priming solution. During priming, various parameters can also be initialized and calibrated via the operator interface during priming. Once primed and running appropriately, the pump flow can be reduced or cycled off, the bypass conduit can be removed from the organ chamber assembly, and the liver can then be cannulated into the organ chamber assembly. 1. Cannulation In stage 5020, the liver, while cooled as described above, can be cannulated and placed onto the organ care system 600. During liver preservation, the perfusion fluid can flow into the liver through the c artery and portal vein and flow out of the liver through the inferior vena cava (IVC). Thus, the hepatic artery, inferior vena cava (IVC), and portal vein can be correspondingly cannulated and connected with the relevant flow path of the liver care system 600 to ensure proper ion through the liver (as described above). In some embodiments, the IVC is not cannulated and free drains. The bile duct can also be cannulated as well and connected to a reservoir to collect the bile produced by the liver (e. g., bile bag 187).

The system 600 bed herein can be ed to be compatible with the human hepatic artery anatomy. In the majority of the patients, the hepatic artery is the only major artery of the liver and thus the organ care system 600 can a single-port a to be ted with the hepatic artery. In certain cases (i.e., about 10-20% ofthe patient population with genetic difference), however, the donor of the liver also has an accessory hepatic artery in addition to the main hepatic artery. Thus, in certain embodiments, the liver care system 600 provides a dual-port a configuration (e.g., cannula 2642) so that both the main and accessory hepatic arteries can be cannulated and connected to the same perfusion fluid flow path. In certain specific embodiments, the dual-port cannula has a Y shape. Any other le shapes or designs for the dual-port cannula are contemplated.

In certain embodiments, the cannula can be designed to be straight to reduce unnecessary flow pressure drop along the cannula flow path. In other embodiments, the cannula can be designed to be curved or angled as required by the shape, size, or geometry of the organ care system 600’s other components. In some specific embodiments, the a is designed with a proper shape, e.g., straight, angled, or a combination thereof, so that the overall flow re within the cannula is ined at a desired level that mimics physiologic conditions. 2. Instrumentation The liver can then be instrumented on the organ care system 600 (Stage 5020) and more specifically, in the organ chamber 104. Care should be taken to avoid excessive nt of the liver during mentation to reduce injuries to the liver.

As described above in greater detail, the liver r can be specially designed to maintain the liver in a stable position that reduces its movement.

B. Preservation/transport 1. Controlled early perfusion and rewarming In certain embodiments, once the liver is mented on the organ care system 600 with proper cannulation of the vessels, the liver can be subjected to an early perfusion and/or rewarm process to restore the liver to a normothermic temperature (34-370 C) (Stage 5021). In some embodiments, the organ chamber can contain heating circuit to warm the previously cooled liver to normothermic temperature gradually over a predetermined amount of time. In other embodiments, the initial perfusion fluid (for early perfusion) can be heated to close to or to the normothermic temperature (e.g., 34-370 C) and perfuse and warm the liver at the same time. As described , the liver preserved on the organ care system 600 can be kept at conditions near to physiological state, which includes normothermic temperatures, to maintain the liver’s normal biological functions.

After the liver is instrumented onto the system and warmed to normothermic temperature, the pump within the organ care system 600 (e.g., pump 106) can be adjusted to pump perfusion fluid through the liver, e.g, into the hepatic artery and portal vein. The perfusion fluid exiting from the IVC (or hepatic veins, depending on how the liver was harvested) can be collected and subjected to various treatments including genation and carbon dioxide removal. s nutrients can be added to the spent perfusion fluid to increase the nutrient concentrations to required value for recirculation.

In some embodiments, during the liver perfiJsion on the organ care system 600, the in-flow res within the hepatic artery and the portal vein are carefully lled to ensure the proper delivery of nutrients to the liver to maintain its functions. In some embodiments, the flow pressure within the hepatic artery can be, for e, 50 — 120 mmHg and the flow pressure in the portal vein can be 5 — 15 mmHg, although pressures outside these ranges are possible such as l, 2, 20, 25, 30, , 40, 45, 50, 60, 70, 80, 90, 100, 110, 120 mmHg, or a pressure in any range bounded by the values noted here. In some embodiments, the flow rate within the hepatic artery and the portal vein can be ined at about or more than 0.25 — 1.0 L/min, and 0.75 — 2.0 L/min, respectively, or at any range bounded by any of the values noted here. In some embodiments, the flow rate within the hepatic artery and the portal vein can be maintained at about 0.25, 0.30, 0.35, 0.40, 0.45, 0.50, 0.55, 0.60, 0.65, 0.70, 0.75, 0.80, 0.85, 0.90, 0.95, 1.00, 1.10, 1.20, 1.30, 1.40, 1.50, 1.60, 1.70, 1.80, 1.90, 2.1, 2.2, 2.3, 2.4, 2.5 L/min or a rate in any range bounded by the values noted here.

In some embodiments, the fluid flow, e.g., flow rate and/or flow pressure, within the organ care system 600 and hepatic artery and the portal vein can be controlled chemically and/or mechanically. The mechanical or the chemical control ofthe flow can be achieved automatically or ly. 2. Manual/automatic control The mechanical control of the fluid flow within the organ care system 600 and hepatic artery and the portal vein is first described. In some embodiments, the flow pressure or rate within the flow path of the organ care system 600 can be measured by pressure sensors or rate sensors built in the flow path or in other locations of the systems. Similarly, pressure or rate sensors can be located in the cannulas for the hepatic artery and/or the portal vein, or in the connectors connecting the cannulas to these vessels. The re or rate sensors can provide the operator with gs regarding the flow within the flow path and/or within the hepatic artery and/or the portal vein. Any other pressure monitoring methods or techniques known in the art are contemplated. If the pressure or rate reading is deviating from the desired values, the operator can manually adjust the flow pump to increase or decrease the pumping re and, y, the flow rate for the ion fluid. Alternatively, the organ care system 600 can contain a flow control module which has a programmable desired value for flow rate and/or flow pressure and automatically adjusts the pumping pressure of the ion fluid and thereby also ing the flow rate when the flow pressure and/or rate are deviating from the desired values. Manual and/or automatic control is described more fully above. 3. Chemical control In other embodiments, the pressure and/or fluid flow within the organ care system 600 and hepatic artery and the portal vein can be controlled chemically. In some c embodiments, the pressure can be controlled or increased by using one or more vasodilators (e.g., a vasodilator can be used to se or decrease vascular tone and y the pressure within the vessel). Vasodilation refers to the widening d vessels resulting from relaxation of smooth muscle cells within the vessel walls. When blood vessels dilate, the flow of perfusion fluid is increased due to a decrease in vascular ance. Any vasodilators known in the art can be used to IO dilate the hepatic artery and/or the portal vein to increase the fluid flow rate therein.

In some particular embodiments, the vasodilator used is Flolan®. In particular, when the fluid flow is insufficient as indicated by low flow pressure or rate, and/or by any ofthe liver—viability evaluation techniques bed in greater detail below, the operator can manually add vasodilator into the system’s flow module or to the perfusion fluid to increase the fluid flow rate. Alternatively, the organ care system 600 can contain a flow control module which automatically adds one more vasodilators into the flow path or perfusion fluid to increase the flow rate. The amount ofthe vasodilator provided can be n, for example, 1-100 micrograms/hr, and more specifically between 1-5 rams/hr. These ranges are ary only and any range falling within 0-100 rams an hour can be used.

Some embodiments of the foregoing can be adapted for use with a liver that is being preserved in the system 600. For example, in this embodiment, an algorithm can be used to allow closed loop control of the hepatic artery pressure (HAP). The algorithm used can be a proportional-integral-derivative controller (PID controller).

A PID controller can calculate how far away the HAP is from the desired set point and attempt to minimize the error by increasing or decreasing the vasodilator (e.g., Flolan®) flow rate.

Accordingly, in some embodiments, the controller 150 (or other part of the system) can determine the error (e.g., how far the HAP is from the user set—point) and adjust the vasodilator flow rate in an attempt to make the error 0. In embodiments where the algorithm runs once a second the adjustments can be very small. Small, nt adjustments can help to stabilize the control by ensuring that any noise in the system does not result in dramatic changes in vasodilator flow rate. The algorithm can be trying to get the HAP to the user set point. This means that when the HAP is above the set point the algorithm can increase the vasodilator solution flow rate until the HAP reaches the user set point. If the HAP is below the user set point the algorithm can decrease the vasodilator solution flow rate until the HAP reaches the user set point.

In some embodiments, the PID control algorithm does not decrease the vasodilator flow rate until it has gone under the set point. This can result in undershooting the target pressure. To help offset this, some embodiments can use a virtual set point, which is +3 mmHg (or other value) above the user set point. This can be user definable or hard-programmed. When the HAP is higher than 7mmHg above the user set point the software can enable the virtual set point and attempt to te the HAP to +3 mmHg above the user set point. This can allow for some undershoot of the virtual set point. Once the HAP has ized at the virtual set point the software can then regulate the HAP to the user set point. This approach can help “catch” the HAP as it is falling without incurring as dramatic of an undershoot. ing to , a cal representation of the foregoing is shown with respect to ascending aortic pressure in a heart system. In , an exemplary graph 9500 of the ing is shown. The image shows the AOP (e.g., 9505) coming down to a virtual set point (9510), undershooting the Virtual set point and then coming down softly on the user set point (50 mmHg).

Because some embodiments use a drug to control the HAP it can be beneficial to ensure that the system is not flooding the liver with vasodilator when it is not . To accomplish this, the system can analyze how far the HAP is from the set point and when the HAP is above the set point, the system (e.g., the solution pump 631) can add vasodilator at the standard rate. If the HAP is below the set point, the system 600 can decrease the flow rate 4 times faster than if it were adding vasodilator.

This can help the system stay just above the HAP set point (e. g., about +0.5 to +1 mmHg) in the “active ment” area as well as potentially helping minimize undershoot but decreasing vasodilator rate faster.

While the ing description has focused on the liver, the same technique can be adapted for use with the heart by substituting AOP for the HAP. 4. Assessment During stages 5028 and 5030 the operator can evaluate the liver functions to determine liver viability for transplant (then-current or likely future viability). lllustratively, step 5028 involves evaluating liver functions by using any of the evaluation techniques described in more detail below. For instance, the or can monitor the fluid flows, pressures, and temperatures of the system while the liver is cannulated. The operator can also monitor one or more liver fimction biomarkers to assess the liver status. During the evaluation step 5030, based on the data and other ation obtained during testing 5028, the operator can determine whether and how to adjust the system properties (e.g., fluid flows, res, nutrient trations, oxygen concentrations, and temperatures), and whether to provide additional modes of treatment to the liver (e.g., surgeries, medications as described in more detail below). The operator can make any such adjustments in step 5032, can then repeat steps 5028 and 5030 to re-test and re-evaluate the liver and the system. In certain embodiments, the operator can also opt to perform surgical, therapeutic or other procedures on liver (described in more detail below) during the adjustment step 5032 (or at other times). For example, the operator can conduct an evaluation of the liver functions, such as for example, performing an ultrasound or other imaging test on the liver, measuring arterial and venous blood gas levels and other evaluative tests.

Thus, after or while the liver is preserved on the system, the operator can perform surgery on the liver or provide therapeutic or other treatment, such as suppressive treatments, chemotherapy, genetic testing and therapies, or ation therapy. Because the system allows the liver to be perfused under near physiological temperature, fluid flow rate, and oxygen tion levels, the liver can be maintained for a long period of time (e.g. for a period of at least 3 days or more, greater than at least 1 week, at least 3 weeks, or a month or more) to allow for repeated evaluation and treatment.

In some ments, the system allows a medical operator to te the liver for compatibility with an intended ent by identifying suitable recipient (Step 5034). For example, the operator can perform a Human Leukocyte Antigen (HLA) matching test on the liver while the liver is cannulated to the system. Such tests can require 12 hours or longer and are performed to ensure compatibility of the liver with the intended ent. The preservation of a liver using the system WO 87737 described herein can allow for preservation times in excess of the time needed to complete an HLA match, potentially resulting in improved post-transplant outcomes.

In the HLA matching test example, the HLA test can be performed on the liver while a preservation solution is g into the liver. Any other matching test known in the art is contemplated.

According to the illustrative embodiment, the testing 5028, evaluation 5030 and adjustment 5032 stages can be conducted with the system operating in normal flow mode. In normal flow mode, the operator can test the function of the liver under normal or near normal physiologic blood flow conditions. Based on the evaluation IO 5030, the gs of the system can be ed in step 5032, if necessary, to modify the flow, heating and/or other characteristics to stabilize the liver in ation for transport to the recipient site in stage 5036. The system with the preserved liver can be transported to the recipient site at step 5036.

C. Preparation for transplant 1. Final flush/cool liver In certain embodiments, before the liver is removed from the system 600 and/or implanted into a recipient, the liver can be flushed by a final flush solution to, for example, remove any residual blood and/or runtime perfusion solution. The composition of the final flush solution is described in detail above.

In n ments, prior to the removal of the liver from the organ care ° C, 5° C system 600, the liver can be cooled again to a temperature at about 4° C to 10 to 9° C, 50 C to 8° C, 4° C, 5° C, 6° C, 7° C, 80 C, 9° C, or 10° C, or a temperature within any range bounded by the value described herein. The liver can be cooled by contact with ice or refrigeration of the liver preservation chamber. In some embodiments, the system 600 can include a cooling unit that is configmred to cool the liver directly and/or cool the fluid circulating in the system 100. The final flush solution can also be chilled first and then used to flush the liver to cool the liver. Thus, in these embodiments, the liver can be finally flushed and cooled simultaneously. Once the liver is prepared and cooled down to a proper temperature, it can be ready to be transplanted into a suitable ent.

For example, in some embodiments, the liver is cooled and flushed while on the system 600. The user can connect a one liter bag of d flush solution to the flush port of the hepatic artery (e. g., port 4301) but leaves the port closed. The user connects two one liter bags of chilled flush solution to the flush port of the portal vein (e.g., port 4302) but leaves the port closed. The user ts a flush collection bag to the perfiasion module to the perfusate collection port located just after the perfusion module's pump compliance chamber (e. g., port 4309). The user can then apply a standard surgical clamp to the perfiision module tubing just before the split to the hepatic artery and portal vein simultaneous with the turning off of the circulatory pump 106. The hepatic artery and portal vein flush ports can be opened so that the flush solution will enter the hepatic artery and the portal vein. The perfiisate collection bag can be unclamped so that the mixture of perfiisate and flush solution fills the bag rather than filling the organ chamber.

In the event that a decision is made to cool the liver at the end of preservation, then the ing exemplary procedure can be used: 1. Obtain and set-up a Heater Cooler unit d near OCS, electrical line plugged in, power ON, water circuit controls ON, water circuit valve OFF). Do not connect Heater Cooler water lines to Liver Perfusion Module gas exchanger water lines yet. 2. Set Heater Cooler water circuit ature to near the current liver temperature (e.g., approximately 37°C) and allow it to reach temperature. 3. Connect Hansen quick connect equipped Heater Cooler water lines to Liver Perfusion Module oxygenator water lines. 4. Turn the heater 100 OFF.

. Set water circuit temperature of Heater Cooler to a lower temperature than the liver but not more than 10° C lower and open the valve of the water lines to allow flow to the Liver Perfusion Module gas exchanger 114. As the actual temperature of the perfilsion fluid, as ed on the user ace, approaches the Heater Cooler water temperature set point, adjust the Heater Cooler water temperature set point lower, but not more than 10° C lower than the perfusate/liver ature, in increments and keep repeating until the blood/liver have reached the desired temperature. 6. When the liver ature has reached the desired temperature, remove the liver from the system 600.

WO 87737 2015/033839 While the foregoing has focused on final flush and cooling of a liver, a similar or cal procedure can be used when preserving other organs. For example, in some embodiments, the foregoing final flush/cooling technique can be applied to a heart and/or lung that is being preserved by the system 600.

VII. Evaluation In some embodiments of the disclosed subject , various techniques or methods to assess the ity of the liver while the liver is preserved on the organ care system 600 are provided (e.g., viability for transplant). Generally, biomarkers known in the art for evaluating liver functions, e.g, liver enzymes, and known imaging ques can be used to te the biological functions and status of the liver. onally, because the liver preserved on the organ care system 600 is readily accessible to the operator, techniques not easily ble to the health care profession in viva, e.g., visual observation of the liver or palpation of the liver, can also be used. Based on the evaluation results, one or more parameters of the organ care system 600, e.g., nutrients or oxygen content in the perfusion fluid or the flow rate and flow pressure of the perfusion fluid, can be adjusted to improve the Viability ofthe liver.

In some embodiments, the perfusion parameters of the organ care system 600 can be used to evaluate the viability of the liver. Specifically, in certain embodiments, the perfusion liquid flow pressures in the cannulated hepatic artery and/or portal vein can be measured as an indicator of the liver ity. In some embodiments, a stable flow pressure in the range of 50 — 120 mmHg in the hepatic artery line can indicate that the preserved liver is receiving sufficient essential nutrient supply. For example, in some embodiments, a stable flow pressure of about 50, 60, 70, 80, 90, 100, 110, 120 mmHg, or a pressure in any range bounded by the values noted here can indicate that the preserved liver is receiving sufficient essential nutrient supply. A flow pressure e this range can indicate a leak or blockage in the system, or suggest to the operator to adjust the flow pressure to ensure proper nutrient supply to the liver. In other embodiments, the perfusion liquid flow rate in the cannulated hepatic artery and/or portal vein can be measured as an indicator of the liver viability. In other embodiments, a flow rate in the range of 0.25 — 1 L/min for the hepatic artery can indicate that the preserved liver is ing sufficient essential nutrient supply. For example, in some embodiments, a flow rate of about 0.25, 0.30, 0.35, 0.40, 0.45, 0.50, 0.55, 0.60, 0.65, 0.70, 0.75, 0.80, 0.85, 0.90, 0.95, 1.00 L/min or a rate in any range bounded by the values noted here for the hepatic artery can indicate that the preserved liver is ing sufficient essential nutrient supply. A flow rate outside this range can indicate a leak or blockage in the system, or suggest to the or to adjust the flow rate to ensure proper nutrient supply to the liver.

The flow rate and pressure can be measured using the pressure and/or flow sensors described herein.

In some embodiments, visual observation or ation of the liver can be used to assess the liver viability. For instance, a pink or red color of the liver can indicate that the liver is functioning normally, While a dark or blueish color of the liver can indicate that the liver is fimctioning abnormally or deteriorating (e.g., is being rfused). In other embodiments, palpation of the liver is used to assess its viability. When the liver feels soft and elastic, the liver is likely oning normally. On the other hand, if liver feels tense or stiff, the liver is likely functioning abnormally or deteriorating (e.g., is being hypoperfused).

A. Bile production In some embodiments, e the bile duct is cannulated and connected to a reservoir of the organ care system 600, the color and amount of bile produced by the liver can be easily examined to evaluate the liver ity. In certain embodiments, black or dark green color bile can indicate normal liver function While a light or clear color of the bile can indicate that the liver is not functioning properly or orating.

In still other embodiments, the amount of the bile production can be used to evaluate the liver viability as well (and/or the determination that the liver is producing bile at all can be a good tor). While any bile production can be a sign of a healthy liver, generally, the more the bile produced, the better the liver function. In certain embodiments, a bile production of from about 250 mL to l L, 500 mL to lL, 500 mL to 750 mL, 500 mL, 750, or 1 L per day or in any ranges bounded by the values noted herein suggests that the liver preserved on the organ care system 600 is fianctioning normally and viable.

B. Blood gas, liver enzymes, and lactate measurements/trends In some ments, various biomarkers or compounds in the perfusion liquid can be used to evaluate the liver viability. For instance, metabolic assessment ofthe liver can be conducted by calculating oxygen delivery, oxygen consumption, and oxygen demand. Specifically, the amount of oxygen and carbon dioxide dissolved in the perfusion liquid can be monitored as indicators of the liver function.

The concentrations of these gases in the ion liquid (or the blood product) before and after liver ion can be measured and compared. In certain specific embodiments, the concentrations of the oxygen and carbon dioxide can be measured by s sensors within the organ care system 600’s flow module or subsystem.

IO In some embodiments, the perfusion fluid before and after liver perfiision (e.g. , the perfilsion fluid entering the hepatic artery and exiting the IVC) can be sampled using respective oxygen concentration (or other) sensors and the relevant concentrations of the oxygen and carbon dioxide can be measured. A significant increase of the carbon dioxide concentration in the perfilsion liquid after liver perfusion, and/or a significant decrease of the oxygen tration after the liver perfusion, can indicate that the liver is performing its oxidative metabolic fianctions well. On the other hand, a minor or no increase of the carbon dioxide tration in the perfiJsion liquid after liver perfusion, and/or minor or no decrease of the oxygen tration after the liver perfusion, can indicate that the liver is not performing its oxidative metabolic functions properly. The difference of PvOz and PaOz can indicate metabolically active, aerobically active metabolism, oxygen consumption.

In some embodiments, liver fianction blood test (LEFTs) can be conducted to assess the liver Viability. Specifically, in some ments, aspartate aminotransferase (AST), alanine aminotransferase (ALT), alkaline phosphates, albumin, bilirubin t and indirect) can be measured to evaluate the liver ons. In other embodiments, the fibrinogen blood level can be ed as well as an tion of the liver cells’ ability to produce clotting factors.

AST, ALT are liver enzymes and are well-accepted al liver biomarkers used for assessing the liver functions and/or suitability for transplant. However, the measurements of AST and ALT are usually complicated and onsuming, and are typically conducted in hospital or lab settings. Thus, there exists a need for a sensitive and simple indicator for determining the status of the preserved liver.

Lactate, also called lactic acid, is a byproduct/end product of anaerobic metabolism in living cells/tissues/organs. Lactate is generated when there is no or low oxygen in the cell to metabolize glucose for basic energy production through the glycolysis pathway. Applicant has discovered that the level of the lactate in the perfusion liquid, e.g., the perfusion liquid exiting from the IVC, can be measured as a surrogate for measuring the AST levels. The lactate concentration can be ed quickly and simply, which provides significant advantages over the onsuming liver enzyme measurement. Based on the quick feedback ed by lactate measurements, one or more parameters of the organ care system 600, e.g, flow rate, pressure, and nutrient concentrations, can be adjusted to preserve or improve the liver viability quickly.

Stated differently, lactate values (e.g., al lactate trends) can be correlated to and be indicative ofAST levels. For example, a series (over time) of e measurements trending lower can correlate and/or be indicative of a trending lower AST. In some embodiments, lactate measurements can be taken in the measurement drain 2804, gh this is not required and can occur at any other location in the system 100. Additionally, in some embodiments, the system 600 can be configured to obtain e measurements over time from a single location, a differential between a e value entering and exiting the liver, and over time at multiple locations.

C. Imaging In still other embodiments, s other methods known in the art can be used to assess the liver ity. In some specific embodiments, ultrasound analysis of the liver can be conducted to assess liver parenchyma, intra- and extra-hepatic biliary tree. Other non-limiting examples of imaging techniques include ic Resonance g (MRI), Computed Tomography (CT), Positron Emission Tomography (PET), fiuoroscopy, Transjugular Intrahepatic Portosystemic Shunt (TIPS), all of which can be used to assess the liver and detect abnormalities. For example, when examining an ultrasound ofthe liver, the doctor can examine sinusoidal dimensions, potential obstructions in the bile duct, and/or generalized blood flow.

D. Pathology/biopsy In still other embodiments, liver biopsy can be used to assess the liver viability. In liver , a small piece of liver tissue is removed so it can be examined under a microscope for signs of damage or disease. Because the liver is preserved ex vivo on the organ care system 600, it is readily accessible and the biopsy can be easily conducted.

VIII. The Cloud During operation, the system 600 generates information about the system itself and/or the organ being maintained. In some ments of the system 600, this information can be stored in an internal memory such as RAM or ROM. In some embodiments the information generated by the system 600 can also be transmitted to a remote e location such as in the Cloud. The Cloud can be, for example, a series of remote interconnected computers that are configured to provide data and/or I5 services over the Internet. The Cloud can store the information, perform analysis on the information, and/or provide the ation to one or more third parties and/or stakeholders.

In some embodiments of the system 600, the system can include a multimodal communication link n itself and one of more other locations, such as servers in the Cloud. This communication link can be controlled by the controller 150 (e. g., via the data management subsystem 151), although this is not required and other components can be used to control communication. The controller 150 can be configured to provide real—time information about the system 600 and/or the organ contained therein to one or more remote locations while the system is at the donor hospital, is in transit, and/or is at the ent hospital. In some embodiments, communication can be lished using communication link such as a wired network connection (e.g., Ethernet), a wireless network connection (e.g., IEEE 802.11), a ar connection (e. g., LTE), a Bluetooth connection (e. g., IEEE 802.15), infrared connection, and/or a satellite-based network connection. In some embodiments, the controller 150 can maintain a ty list of connections favoring those connections which are more reliable such as a red Internet connection and/or Wi-Fi over less reliable cellular and/or satellite connections. In other 2015/033839 embodiments, the priority list can be generated with a preference for lower-cost transmission mediums such as Wi-Fi.

The system 600 can be configured to communicate with the Cloud, and ultimately remote parties via one or more techniques. For example, the system 600 can be configured to communicate with a server in the Cloud and/or directly with one or more remote computers. In some ments, the system 600 can be configured to: i) send communications such as emails and/or text messages to predetermined addresses, ii) upload data files to remote storage locations using, for example, FTP, iii) communicate with a dedicated remote server to provide information in a proprietary format, and iv) receive ation downloaded from the Cloud and/or other remote computers. In some embodiments, the ller 150 can transmit/receive the information on a r schedule, which can vary depending on which phase of operation the system is in. For example, the controller 150 can be configured to provide updates every five minutes while the system 600 is located at the donor hospital, every 15 seconds while in transport, and/or every 15 seconds while the system 600 is located at the receiving hospital. The controller 150 can also be configured to it/receive information in a secure manner, such as using tion and/or with a timestamp.

The ller 150 can be configured to provide various types of information to the Cloud and/or remote on such as: an offer for an organ, system readiness information, battery charge level, gas tank level, status of the solution infusion pump, flow rates, pressure rates, oxygenation rates, hematocrit levels, lactate levels, temperature levels, the flow rate at which the pump 106 is set, the temperature at which the heater 110 is set, the position of the flow clamp 190, some or all of the information displayed on the user interface (e.g., circulatory and infiision flow rates, pressures, oxygenation levels, hematocrit levels), geographic location, altitude, a copy of the displayed interface itself, waveforms displayed on the user interface, alarm limits, active alarms, screen captures of the user interface, photographs (e. g. captured using an d camera), HAP/HAF/Lacate trends, historical usage information about the system 600 (e.g., the number of hours it has been used), and/or donor ation. In heart/lung embodiments additional information such as AOP and/or PEEP can be provided. Essentially, any piece of information that is collected, 2015/033839 generated, and/or stored by the system 600 can be transmitted to the Cloud and/or a remote computer.

The controller 150 can be configured to receive various types of information from the Cloud and/or a remote location such as: instructions from a remote user, a “pull” demand for data from a remote location, control inputs, information about the organ recipient, and/or system updates.

In some embodiments, using the information provided by the system 600, a user that is remote from the system 600 can effectively remotely view the same user interface that is displayed on the system 600. Additionally, in some embodiments, a user that is remote to the system 600 can also remotely control the system 600 as if they were there in person. In some embodiments, the remote view can be an enhanced version of what is seen by the attending user. For e, the user interface can be presented in a similar format so that the remote user can visualize what the attending user sees, but the remote view can be enhanced so that it also displays additional information to provide context for the remote viewer. For example donor demographics, phic location, trends, and/or assessment results can also be displayed. A remote user can also be provided with virtual buttons and/or ls, matching those found on the system 600, which can be used to remotely control operation of the system 600.

In some embodiments, one or more technicians can remotely connect to and access the system 600 to m diagnostics, update the system, and/or remotely eshoot issues. In some embodiments, remote technical assistance can be limited to times when the system 600 is not being used to preserve an organ.

In some embodiments, the information provided by the system 600 can be presented to a remote user through a web portal, mobile application, and/or other interface.

In some embodiments, access to the information provided by the system 600 can be limited to one or more registered users such as, al staff at the recipient hospital, a technical support team, and/or administrators. In some ments, access to information ed by the system 600 can be tied to an electronic medical file of the recipient. For example, the based server can access one or more electronic medical files of the recipient to determine, for example: s expressly identified as being able to have access to the recipient’s health data, parties associated with organizations that are identified as being able to have access to the recipient’s health data, and/or individuals g at l facilities that are within a certain geographic distance of the recipient.

As described herein, sometimes during transport samples of perfusion fluid can be withdrawn for external analysis. In these instances, however, the data obtained through the external analysis is disassociated with the ation contained within the system 600. Thus, in some embodiments, the user ace provided by the system 600 can be configured to allow a user to input and store externally generated data about the organ. For example, if the attending user withdraws a sample of the perfilsion fluid in order to perform a lactate measurement in an external analyzer, the attending user can then input and store the result in the system 600 along with the data that is generated by the system 600 itself. Along with the result itself, the user can also provide timestamp information and a description of the information. The information inputted by the user can be , sed, downloaded, and/or transmitted by the system 600 as if it were generated internally. In this manner, the system 600 can keep a complete record of all information relating to the organ while it was ex vivo regardless of whether the information was generated ally in or externally from the system 600.

In operation, referring to , a process 6600 describes an exemplary embodiment of how the system 600 can be used with a Cloud-based communication/storage system. The process 6600 is exemplary only and not limiting.

For example, the stages described therein can be altered, changed, nged, and/or omitted. The process 6600 assumes that the system 600 is in communication with a remote cloud-based server and that the system is being used to transport an organ, although this is not required. This process can be adapted to be used, for example, while an organ is being treated ex vivo for implantation back into the al patient rather than being transplanted into a new recipient.

At stage 6605, an offer for an organ can be presented to the retrieval hospital by the organization that controls organ allocation (e.g., an organ procurement organization). h a web portal to the system 600, the val hospital's staff can query the readiness (e.g. battery charge level, gas level) of the system 600 and can enter information about the donor. The information can be transferred to the system 600 via the server.

At stage 6610, clinical support that have registered with the server as on-call staff can be alerted to the upcoming transport session Via an email, a text e, an ted phone call, and/or any other communication means. The clinical support staff can be, for example, staff employed by the cturer of the system 600.

At stage 6615, which typically occurs during transport, the system 600 can transmit system/organ status information to a Cloud-based server Via a communication link. The information transmitted to the server can be reviewed in an online portal by third parties such as the transplant surgeon, support staff, and/or any other permitted party (all of which can be at different geographic locations). In some embodiments, the server can perform additional processing on the information received from the system 600 to generate new information, which can then be presented back to the system 600 and/or to third parties. The information displayed to the user on the system 600 can be itted (e.g., either the underlying data and/or the image itself) to the server, for example, unsolicited once every 2 minutes. The data can then be stored with a timestamp on the server. For example, in some ments, each time information is received by the server from the system 600, this can be placed in a row of an Excel sheet. Additionally, during the stage 6615, remote users that are Viewing the information through the portal can "pull" (demand) a screen refresh/snapshot of the data from the OCS rather than waiting for the next 2-minute sample to be "pushed." Additionally, in some ments, the remote parties can remotely control the operation of the system 600 Via a remote interface.

The remote View can be an enhanced version of what is displayed on the monitor of the system 600. It can be presented in a similar format so that the remote user can visualize what the attending user sees. In some embodiments, however, the remote View can also be enhanced so that it also displays additional information to provide context for the remote Viewer, such as donor demographics, trends, and assessment results.

The system 600 can assert alerts through the server to remote third s such as the transplant n and/or al support team. The attending user can trigger contact from one ofmore remote third s Via a monitor menu action. For example, the attending user can send a request for assistance to technical support who can receive an alert via, for example, text message and/or email and call or otherwise contact the attending user.

The system 600 can automatically assert alerts in certain critical conditions (e.g. HAP > 120, or PVP > 20 mmHg). The attending user can also snap a photograph using a camera that is integrated into the system 600 (e.g., integrated into the operator ace module 146). The image can automatically be pushed to the server by the system 600.

During stage 6615, the system 600 can tically provide information to the server and/or other remote computer at regular intervals such as every 15 s, every two minutes, every five minutes, or every 10 s. In some embodiments, ation transmitted between the system 600, the server, and/or the third party can occur in real time so that the remote party can have real time access to and/or control over the system 600 as if they were there in person. In some embodiments, the attending user and/or any other remote parties can initiate an unscheduled information transfer. In some embodiments, if the communication link of the system 600 has been disabled or is inoperable (e. g., during air transport), the controller 150 can be configured to continue generating regular status updates and store them for transmission once the communication link has been re-enabled.

At stage 6620, which typically occurs at the end of the transport session, n files from the system 600 can be pushed to the server. The information provided to the server can include, for example, the trend, error, blood sample, and event files. Preference can be given to WiFi before ar link for data transmission, to ze cost.

IX. Possible benefits Some embodiments of the system 600 described herein can provide one or more benefits. For example: Depending on the type of procedure being performed, manually controlling an organ preservation system can be a labor-intensive process that can require specialized training. Additionally, as with any medical procedure, manual control can also be prone to mistakes by those controlling the system. Thus, in some embodiments, the system 600 can automatically l itself in real time. For example, the controller 150 can be configured to automatically control the flow rate of the pump 106, the operation of the gas exchanger 114, the temperature of the heater 110, the operation of the flow clamp 190 (when an automated clamp is used), and/or the ission of information to the Cloud. The controller 150 can be configured to control operation of the system 600 based upon feedback information from, for example, the sensors ned therein.

Providing ted control of the system 600 can result in improved usability, can reduce the possibility of error, and can reduce the labor intensity of transporting an organ. For example, automating the control s can compensate for user variability that can exist when different people control the . For e, even if two users receive the same training, one user’s judgment may differ from another which can result in inconsistent levels of care across the two users. By automating the control process, a level of consistency between operators can be achieved in a manner that is otherwise difficult to do. Additionally, providing automated control can also provide better care for the organ while ex vivo by updating operational parameters of the system 600 more quickly than is possible with manual control.

The techniques described herein can also e the utilization of donor organs that are tly not being utilized due to limitations of cold storage methods.

In ng cold storage methods, many organs go to waste because the organ cannot be transported to a recipient before it suffers damage as a result of cold storage. This results in many organs that are otherwise suitable for transplantation going to waste each year. Using the techniques described herein, the amount of time that an organ can be maintained in a healthy ex vivo state can be greatly extended thereby increasing the potential donor and recipient pool.

The techniques described herein can also help e the assessment of whether an organ is suitable for transplant into a recipient. For example, using a liver example, visual ation or examination of the liver can be used to assess the liver viability. For ce, a pink or red color of the liver can indicate that the liver is functioning normally, while a gray or dark color of the liver can indicate that the liver is functioning abnormally or deteriorating. In other embodiments, palpation of the liver can be used to assess its viability. When the liver feels soft and elastic, the liver is likely fianctioning normally. On the other hand, if liver feels tense or stiff, the liver is likely fimctioning abnormally or deteriorating.

In still other embodiments, because the bile duct is cannulated and connected to a reservoir of the system 600, the color and amount of bile produced by the liver can be easily examined to evaluate the liver viability. In certain embodiments, black or dark green color bile indicates normal liver function while a light or clear color of the bile tes that the liver is not fianctioning properly or deteriorating. In still other embodiments, the amount of the bile production can be used to te the liver viability as well. Generally, the more the bile produced, the better the liver on. In certain embodiments, a bile production of from about 250 mL to l L, 500 mL to lL, 500 mL to 750 mL, 500 mL, 750, or 1 L per day or in any ranges bounded by the values noted herein ts that the liver ved on the organ care system 600 is functioning normally and viable. Many of the foregoing techniques can be difficult, if not impossible when the organ is in vivo.

X. Examples Experimental tests and results relating to the some embodiments are bed below. As described below, experimental tests included multiple studies and phases.

Phase I included studies of 27 liver samples including two groups of organs on the above OCS system for up to 12 hours. Phase II included replicating the al steps of liver retrieval, preservation and simulated transplantation processes for multiple sample livers for 4 hours of simulated transplant. Phase III included replicating clinical steps of liver retrieval, preservation and ted transplantation processes for multiple sample livers for 24 hours of simulated transplant.

A. Phase I Groups A and B of organs were used for Phase I. Objectives for Phase I include: (1) To optimally perfuse and ve Livers on the OCS system for up to 12 hours using oncotic adjusted red blood cells (“RBCs”) based nutrient enriched ate; (2) maintain stable near--physiological heamodynamics (pressure and flow) for both the portal and the hepatic arterial circulation; (3) enable monitoring of organ functionality and stability on the OCS by monitoring bile production rate, liver enzymes trends, stable PH and arterial lactate ; and (4) histopathology assess the organ post OCS.

The animal model used for the test was the swine model, including 70-95 kg Yorkshires swine. The Yorkshires swine was used as a model due to its similarity to human anatomy and size relative to human adult organ size. The perfusate for the test was red blood cell based. Given that the liver is a highly metabolic active organ, a ate with an oxygen carrying capacity and nutrient ed would be ideal for the organ, mimicking it’s in-Vivo environment and satisfying the organ’s high metabolic demand.

Liver is unique by its dual blood supply. As described usly, the liver gets its blood supply through the portal vein (PV) and the hepatic artery (HA). Portal circulation is a low-pressure circulation (5—10 mm Hg) and the hepatic arterial circulation delivers high-pressure ile blood flow (70-120 mm Hg). Stable perfiision parameters and namics indicate stable perfiJsion. Lactate levels were used as a marker of adequate perfiasion because lactate is one of the most sensitive physiologic parameters, and is thus a good indicator of the adequacy of ion. Lactate is produced under anaerobic conditions denoting inadequate perfusion, and the trend of lactate level is a sensitive marker for perfusion adequacy assessment. Aspartate Aminotransferase (“AST”) is a standard marker used clinically to assess livers, and was also used as a marker of viability. The trend ofAST level is another marker and indicator of the organ viability. Bile tion is a unique function of the liver. Bile production ring is another marker for the organ Viability and onality.

Phase I included studies of 27 liver samples. Of those, Group A included 21 samples that were preserved on the OCS for 8 hours using cellular based perfusate.

Group B included 6 samples that were preserved on the OCS for 12 hours using cellular based perfusate.

The following protocol was applied for phase I groups A and B testing.

First, animal prep, organ retrieval, cannulation and Pre-OCS flush is bed. Each 70-95kg Yorkshires Swine was sedated in its cage by injecting a combination of Telazol and Xylazine intramuscularly according to the following dose: 6.6mg/kg Telazol and 2.2 mg/kg Xylazine. The animal was then intubated, an IV line established, then the animal was transferred to the OR table in supine position, then connected to the ventilator and esia machine. The liver was exposed through a right subcostal incision, and the heart through median stemotomy incision. The hepatic artery (HA), portal vein (PV) and the common bile duct were isolated. The right atrium and the superior vena cave were then isolated and cannulated for blood W0 2015/187737 tion. Then 2-3 liters of blood were ted from the animal using a 40 Fr venous a through the right atrium. The collected blood was then processed through a cell saver machine (Haemonetics Cell Saver 5+) to collect washed RBCs.

Topical cooling was applied to the liver during the blood collection time. Then the liver was harvested.

After harvesting the liver, the c artery (HA), portal vein (PV), the common bile duct, supra hepatic cava and infra hepatic cave were isolated and cannulated using the appropriate size for each. Exemplary sized cannulas include 14 Fr, 16 Fr, 18 Fr for the hepatic artery cannula, 40 Fr and 44 Fr for the portal vein cannula, 12 Fr and 14 Fr for the common bile duct cannula, 40 Fr for the supra- hepatic vena cava, and 40 Fr for the infra-hepatic cava.

The liver was then flushed using 3L of cold PlasmaLyte® solution, each liter was supplemented with Sodium bicarbonate (NHCO3) at 10 mml/L, stenol Sodium at 2 mics/L, Methylprednisolone at 160 mg/L. One liter was delivered through the hepatic artery rized at ~50-70 mmHg. Two liters were delivered through the portal vein by gravity.

After cannulation, the organ was preserved on the OCS at 340 C for 12 hours using oncotic adjusted RBCs based perfusate. The OCS-liver system prime perfiisate ed washed red blood cells, albumen 25%, PlasmaLyte ® solution, dexamethasone, sodium bicarbonate (NaHCO3) 8.4%, adult multivitamins for infiJsion (INFUVITE ®), calcium gluconate 10% at (100 mg/ml), gram-positive antibiotic such as cefazolin, and a gram negative antibiotic such as ciprofloxacin.

Table 7 below summarizes the liver prime perfusate composition and dose.

TABLE 7. OCS liver prime perfusate composition and dose {3&3 fiwrF-flfam fem; 6&3? Q fifiQFWfiQflfiQW W0 2015/187737 In addition to OCS-Liver circulating ate ned above, the following were delivered to the perfusate as continuous infusion using an integrated Alaris infusion pump: Total Parenteral Nutrition (TPN): CLINIMIX E (4.25% Amino Acid/ 10% Dextrose); PLUS n (3OIU), Glucose (25g) and 40,000 units of n; Prostacyclin on as needed: (epoprostenol sodium) to optimize the Hepatic Artery Pressure; Bile Salts (Taurocholic acid ): as needed for Bile Salt Supplement. Table 8 below illustrates the liver ate infusions and rate.

TABLE 8. OCS liver perfusate infusions and rate The Liver was perfused on the OCS by delivering blood based, warm, oxygenated and nutrient enriched perfusate through the hepatic artery and the portal vein. Once the liver was instrumented on the OCS and all cannulae were connected, pump flow was increased gradually and very slowly to achieve the target flow over —20 minutes. While the liver was warming up to the temperature set point, the flow control clamp was adjusted to maintain a 1:1 to 1:2 flow ratio between the HA and PV. The vasodilator agent flow rate was adjusted as needed to manage the hepatic artery pressure. An arterial blood sample was collected within the first 15-20 minutes.

The following perfusion parameters were maintained during perfusion on the OCS-liver device: Hepatic Artery Pressure (mean HAP): 75 — 100 mmHg; Hepatic Artery Flow (HAF): 300 - 700 ml/min; Portal Vein Pressure (mean PVP): 4 - 8 mmHg; Portal Vein Flow (PVF): 500 - 900 ml/min; Perfusate ature (Temp): 34C; Oxygen gas flow 400 - 700 ml/min.

WO 87737 Lactate levels on the OCS-Liver PerfiJsion were collected according to the ing sampling scheme. One OCS liver arterial sample was collected within 10- minutes from a start ofperfiJsion on the OCS-Liver device. Samples continued to be collected from the device at approximately hourly intervals until lactate level was trending down, at which point the lactate samples were taken every 2 hours or after any active HAF or HAP adjustments. Baseline Liver Enzyme was measured from the . Liver Enzyme was collected and assessed on the OCS every two hours starting at the second hour.

Post OCS athology Sampling.

At the end of the preservation time, OCS perfusion was terminated. The liver was disconnected from the device and all cannulas were removed. Specimens were collected from the Liver and saved in 10% formalin for Histopathology assessment.

A section of the Liver was collected for the wet/dry ratio. The section weight was recorded before and after 48 hours in an 800 C hot oven. The wet/dry ration was then calculated according to the following formula: Water Content (W/D ratio) = 1 — (Ending Weight/Starting Weight).

A liver was ered acceptable if it met acceptance criteria, ing: stable ion parameters throughout preservation on the OCS for HAF, HAP, PVF and PVP; stable or trending down arterial lactate; continuous bile production with a rate of >10 ml/hr.; stable or trending down liver enzymes (AST); and normal and stable perfusate PH.

The Phase I, Group A, 21 samples successfully met the above identified acceptance criteria. The data for hepatic artery flow over 8 hours of OCS liver perfusion shown in the graph in trates that OCS perfused swine livers demonstrated stable perfusion, as evidenced by the Hepatic Artery Flow (HAF) trend throughout the course of 8 hours preservation on OCS. The data for portal vein flow over 8 hours of OCS liver perfiJsion shown in the graph in , which shows PVF trend throughout the course of the 8 hour preservation on OCS, demonstrated stable perfusion, as evidenced by the stable Portal Vein Flow (PVF) trend throughout the course of 8 hours preservation on OCS. shows a graphical depiction of c artery pressure versus portal vein pressure throughout the 8 hour OCS-liver perfusion. illustrates that OCS perfiJsed swine livers demonstrated stable perfusion pressure, as evidenced by the stable portal vein pressure and the hepatic artery pressure throughout the course of the 8 hour preservation. is a graphical depiction of arterial lactate levels over the 8 hour OCS liver ion. shows that OCS ed swine livers demonstrated excellent metabolic function, as evidenced by their ability to clear lactate and trending down lactate throughout the course of 8 hours preservation on OCS. is a graphical depiction of total bile production over the 8 hour OCS liver perfusion. shows that OCS perfused livers continued to produce bile at a rate of >1 0ml/hr. throughout the course of the 8 hour preservation on OCS ting preserved organ functionality. is a graphical depiction of AST level over the 8 hour OCS liver perfusion. Aspartate Aminotransferase (AST) is a standard marker clinically used to assess livers. graph demonstrates that OCS perfused livers exhibited a trending down AST levels over the course of 8 hours perfusion on the OCS, indicating good liver fianctionality. is a graphical ion ofACT level over the 8 hour OCS liver perfiasion. As shown in , activated clotting time (ACT) was maintained above 300 seconds over the course of 8 hours of perfusion on the OCS. is a cal depiction of oncotic pressure throughout the course of 8 hours vation on OCS. As shown in , oncotic pressure remained stable on the OCS. is a graphical depiction of bicarb levels over the 8 hour OCS liver perfusion. As shown in , Bicarb (HCO3) levels were maintained within normal physiologic ranges over the course of 8 hours perfusion on the OCS with very minimal doses required of HCO3 for correction, indicating a stable liver metabolic profile. is a depiction of the ed pH levels throughout the course of 8 hours preservation on OCS. As shown in , stable and normal pH was maintained over the course of 8 hours perfusion on the OCS with no or l need to add HCO3 for tion, indicating a good fianctioning and adequately perfused organ. shows images of tissues taken from samples in Phase I, Group A.

Histological examination of hymal tissue and bile duct tissue shows normal liver sinusoidal structure with no evidence of necrosis or ischemia and normal bile duct epithelial cells indicating te perfusion and lack of ischemic injury. 2015/033839 The results observed for Phase I Group B, organs maintained for 12 hours, exhibited similar acceptable results to those in Group A.

As in Group A above, in Phase I Group B a liver was considered acceptable if it met acceptance ia, including: stable perfiision parameters throughout preservation on the OCS for HAF, HAP, PVF and PVP; stable or trending down al lactate; continuous bile production with a rate of >10 ml/hr.; stable or trending down liver enzymes (AST); and normal and stable perfusate PH. depicts Hepatic Artery Flow of a 12hr OCS Liver Perfusion. As illustrated, the graph of shows that OCS perfused swine livers trated stable perfusion, as ced by the Hepatic Artery Flow (HAF) trend throughout the course of 8 hours preservation on OCS. depicts Portal Vein Flow of al2hr OCS Liver Perfusion. As illustrated, the graph of illustrates OCS perfused swine livers demonstrated stable perfusion, as evidenced by the stable Portal Vein Flow (PVF) trend throughout the course of 12 hours preservation on OCS. depicts Hepatic Artery Pressure vs. Portal Vein Pressure in a 12hr OCS-Liver Perfusion. The graph of demonstrates that OCS ed swine livers demonstrated stable perfusion re, as evidenced by the stable Portal Vein Flow (PVP) and the Hepatic Artery Pressure (HAP) trend throughout the course of 12 hours preservation on OCS. depicts Arterial Lactate in a 12hr OCS-Liver Perfusion. The graph of shows that OCS perfiased swine livers demonstrated excellent metabolic function, as evidenced by their ability to clear lactate and trending down lactate levels throughout the course of 12 hours preservation on OCS. depicts Bile Production in a 12hr OCS-Liver Perfusion. The graph of demonstrates that the OCS perfused Livers continued to produce bile at a rate of >10ml/hr hout the course of 12 hours preservation on OCS ting well preserved organ function. depicts AST Level of a 12hr OCS—Liver Perfusion. Aspartate Aminotransferase (AST) is a standard marker clinically used to assess . The graph of demonstrates that OCS perfused livers exhibited a trending down AST levels over the course of 12 hours perfusion on the OCS. This indicates good liver fianctions. s ACT Levels in a 12hr OCS—Liver Perfusion. Activated clotting time (ACT) was maintained above 300 sec over the course of 12 hours ion on the OCS, as rated in .

B. Phase 11 Phase II, or Group C, included studies of 12 liver samples. Of those, 6 samples were preserved on the OCS for 8 hours using cellular based perfusate, and were then subjected to simulated transplant on the OCS for 4 hours of preservation using whole blood as perfusate. The other 6 samples were preserved for 8 hours using cold static preservation in UW solution, and were then subjected to simulated transplant on the OCS for 4 hours of preservation using whole blood as perfiisate.

Objectives for Phase 11 include preserving the liver with OCS using warm perfusion for 8 hours using an RBCs based perfusate, followed by 45 minutes of cold ischemia, then another 4 hours of OCS-Liver warm perfiasion using whole blood, (a) to optimally perfuse and preserve Livers on the OCS system for 8 hours using oncotic adjusted RBCs-based nt ed perfusate, (b) maintain stable ysiological heamodynamics (pressure and flow) for both the portal and the hepatic arterial circulation, (c) enable monitoring of organ fiinctionality and stability on the OCS by monitoring bile production rate, liver enzymes trends, stable PH and arterial lactate levels, (d) subject the organ to 45minutes of cold ischemia post the first 8 hours on the OCS, (e) followed by 4 hours of simulated transplant on the OCS using whole blood, while monitoring and ing the organ heamodynamic and ion parameters and monitoring organ functionality.

Simulated transplant on the OCS was used to minimize the nding variables associated with orthotopic transplantation and to e the variables to only the ischemia/reperfusion effects.

This group (C) of pre-clinical simulated transplant testing was expanded to include a control arm of cold stored swine livers using standard of care cold liver preservation solution. Except for the cold preservation phase, the ol for this arm of the group was identical to the OCS simulated transplant arm of the same group (C). The detailed protocol and results are described below.

Like Phase I, 70-95 kg Yorkshires swine were used as a test t for Phase II. For this phase, two animals were used for each study, with the first animal as the organ donor, and a second animal as a blood donor for the simulated phase of perfusion on the OCS.

In this simulated animal transplant model, the donor organ was exposed to the identical conditions of organ retrieval, preservation, and terminal cooling for transplantation as in orthotopic transplant. The only difference was that in the transplant phase the organ was reperfused with another animal’s un-modified whole blood in an o OCS perfusion system to control for all the confounding variables of orthotopic transplants that may shadow the true impact of preservation injury on the donor organ. The donor organ’s function and s of injury monitored during simulated transplant phase were identical to the ones that would be red during opic lantation. The acceptance criteria for Phase 11 samples were the same as those outlined above, and were measured during the 4 hours of simulated transplant.

Phase 11, Simulated Transplant OCS arm, 6 samples (N=6).

This set was achieved by replicating all key clinical steps of liver retrieval, preservation and simulated transplantation processes in the following sequence: Donor Organ Retrieval (30 — 45 minutes): During this phase, the donor organ was retrieved, and cold flushed for 30 - 45minutes to replicate the clinical condition of donor liver retrieval and instrumentation on the OCS Liver system. The same prep, organ retrieval, cannulation and pre-OCS flush were performed as described in Phase Donor Liver Preservation on OCS (8 hours): During this phase, the donor organ ent ex-vivo ion and assessment using OCS Liver system. During this phase, the liver was monitored and assessed hourly for marker of liver injury (AST level), marker for lic function (Lactate level), and bile production rate as a marker for liver function/Viability. The same organ preservation was performed for this group as the 8 hour preservation samples described in Phase I.

Post-OCS Preservation Cold Ischemia (45 minutes): During this phase the donor liver was flushed using cold flush solution as specified in the proposed clinical protocol to ate final cooling of the donor liver required for re-implantation.

Donor livers were maintained cold for 45 minutes to replicate the time required for ming the re-implantation procedure in the recipient. Using the Final Flush line included in the OCS Liver perfusion termination set, the liver was flushed and cooled on the OCS using 3L of Cold PlasmaLyte solution supplemented with Sodium bicarbonate (NHCO3) lO mml/L, Epoprostenol Sodium 2 mcg/L and Methylprednisolone 160 mg/L flush, supplying 1 liter at ~50-70 mmHg to the hepatic artery, and a 2 liter gravity drain to the portal vein. The liver was then disconnected from the OCS and placed in a cold saline bath for 45 minutes.

Final Reperfusion of the Donor Liver (4 : The transplantation was replicated/simulated by the following s to isolate the graft assessment markers of ischemia and reperfusion due to preservation technique from other confounding variables associated with the transplant model ibed above). The liver graft was reperfused eX-vivo in a new OCS liver perfusion module using normothermic fresh whole blood from a different swine at 37°C for 4 hours. For the simulated transplant phase, a new ion module was used to perfuse the organ on the OCS. The perfusion pressures/flows were lled to near physiologic levels and temperature was maintained at 37°C. The liver was monitored hourly for the same markers as in the preservation period. In on, liver tissue samples were evaluated histologically to assess c tissue architecture and any signs of injury in the same way as described above in Phase 1.

Phase 11, Simulated Transplant Cold Preservation Control arm (N=6).

This was achieved by replicating all key al steps of liver retrieval, preservation and simulated transplantation processes in the following sequence: Donor Organ Retrieval (30-45 minutes): During this phase, the donor organ was retrieved, for 30-45 minutes to replicate the clinical condition of donor liver retrieval. The same prep, organ retrieval, cannulation and pre-OCS flush were med as described in Phase I.

Donor liver cold preservation: During this phase, the donor liver was preserved for 8 hours using standard of care cold storage solution Belzer UW® (UW Solution) for liver flush and storage at 2-5°C to mimic the standard of care for liver cold preservation.

Post-cold Preservation, organ flush and preparation (45 minutes): During this phase the donor liver was flushed with cold flush solution using the final flush line included in the OCS liver perfiJsion termination set. The liver was flushed using 3L of cold PlasmaLyte solution supplemented with Sodium onate (NaHCO3) 10 mml/L, Epoprostenol Sodium 2 mcg/L and Methylprednisolone 160 mg/L flush, supplying 1 liter at ~50-70 mmHg to the hepatic artery, and a 2 liter gravity drain to the portal vein. The liver was then disconnected from the OCS and placed in a cold saline bath for 45 minutes.

Final Reperfusion of the Donor Liver (4 hours): The transplantation was replicated/simulated by the following process to isolate the graft assessment s of ischemia and reperfusion due to vation technique from other confounding variables associated with the transplant model (described above). The liver graft was reperfused eX-vivo in a new OCS liver ion module using normothermic fresh whole blood from a different swine for 4 hours. The perfiJsion pressures/flows were controlled to near physiologic levels and temperature was maintained at 37°C. The liver was monitored hourly for the same markers as in the preservation period. In addition, liver tissue samples were evaluated histologically to assess hepatic tissue architecture and any signs of injury in the same way as bed above in Phase I.

The results observed for Phase II, indicate that samples that were perfiised using the OCS system ed better post—perfusion results than samples that were subjected to cold storage. The samples that were subject to cold storage, did not meet the acceptance criteria described usly during the 4 hours of simulated lant, as compared to the OCS arm of the group.

In the cold storage control arm, the metabolic liver functions demonstrated le and worsening profile over the course of the 4 hours of the simulated transplant as evidenced by the higher and unstable lactate trend, as compared to the OCS arm of the group, which trated much better metabolic function, as ced by trending down arterial lactate. This indicates that the OCS-arm livers had significantly better metabolic function as compared to the cold storage control arm. In the cold storage control arm, the liver enzyme (AST) profile, which is a sensitive marker of liver injury, was unstable and trending up to much higher levels than the OCS arm of the group. This indicates compromised liver functions for liver grafts in the control arm, as compared to the well persevered and good oning liver grafts in the OCS arm, which was demonstrated by much lower level of Liver enzyme (AST) trend in the OCS arm. In the cold storage control arm, the pH trend required much higher doses of HCO3 to achieve and maintain a stable metabolic profile, than the doses ed for the OCS arm of the group. This indicates that the OCS arm was able to maintain a much better metabolic profile than the cold storage control arm. The bile production rate was less in the cold storage l arm than in the OCS arm. This indicates better liver graft functions in the OCS arm as compared to the cold storage control arm. The perfusion parameters were comparable for both arms of the group. Based on the above comparison results, the OCS arm successfully met the protocol pre-specified acceptance criteria while the cold storage control arm did not meet the identical acceptance ia. depicts Hepatic Artery Flow on a simulated transplant OCS-Liver preservation arm vs. a ted transplant l cold preservation arm. As illustrated, the graph of depicts stable Hepatic Artery Flow (HAF) over the course of 4 hours of perfusion on the OCS during the simulated transplant period. depicts Portal Vein Flow on a simulated transplant OCS-Liver preservation arm vs. a simulated transplant control cold preservation arm. As illustrated in , the graph demonstrates Stable Portal Vein Flow (PVF) over the course of 4 hours perfusion on the OCS during the simulated transplant period. depicts c Artery Pressure vs. Portal Vein Pressure in a simulated transplant OCS—Liver preservation arm vs. a simulated transplant control cold preservation arm. The graph of trates a stable Hepatic Artery Pressure (HAP) and Portal Vein Pressure (PVP) trend over the course of 4 hours perfusion on the OCS. depicts Arterial e on a simulated lant OCS-Liver preservation arm vs. a simulated transplant control cold preservation arm. The graph of demonstrate that the OCS-arm perfilsed livers had a much better metabolic function, as ced by trending down al Lactate. This indicates that the OCS-arm livers had significantly better metabolic function as compared to cold stored arm. depicts bile production of a simulated transplant OCS—Liver preservation arm vs. a simulated transplant control cold vation arm. The graph of demonstrates that the OCS arm perfiased livers had a higher bile tion rate as compared to cold stored livers. This indicates better liver graft function in the OCS group vs. a cold stored group. depicts a AST Level of simulated transplant OCS-Liver preservation arm vs. a ted transplant control cold preservation arm. The graph of demonstrates that the OCS perfused livers had a significantly lower AST levels throughout the 4 hour simulated transplant period. This indicates significantly less liver injury to the graft in the OCS group as compared to the cold stored group. depicts ACT Levels of a simulated transplant OCS-Liver preservation arm vs. a simulated transplant control cold preservation arm. Activated clotting time (ACT) was maintained above 300 sec over the course of 8 hours perfusion on the OCS. depicts oncotic pressure of a simulated lant OCS-Liver preservation arm vs. a simulated transplant control cold vation arm. As depicted in , there was stable c pressure on the OCS-Liver preservation arm. depicts the Bicarb Level of a simulated lant OCS-Liver preservation arm vs. a simulated transplant control cold preservation arm. depicts pH Levels of a simulated transplant OCS-Liver preservation arm vs. a simulated transplant control cold preservation arm. The graph of demonstrates that an OCS perfused liver had better pH values over the course of 4 hours of perfusion on the OCS as compared to the cold stored livers. OCS ed livers needed very minimal HCO3 correction as compared to the cold stored group, this is an indication of better oning liver grafts in the OCS arm as ed to the control arm.

As illustrated in , histological examination of hymal tissue and Bile duct tissue shows normal liver sinusoidal structure with no evidence of necrosis or ischemia and normal bile duct epithelial cells indicating adequate perfusion and lack of ischemic injury.

As illustrated in , histological examination of Parenchymal tissue and Bile duct tissue shows significant hemorrhage and congestion within the parenchyma, Interlobular hemorrhage, multifocal wide spread interlobular hemorrhage, and Lobular congestion.

C. Phase III This group of pre-clinical simulated transplant testing was conducted to e OCS preserved livers (3 samples) for 12 hours versus control arm livers preserved cold (3 samples) using the rd of care cold liver preservation solution Belzer UW® (UW on) for 12 hours. Both the OCS arm and the cold storage arm were then ed for 24 hours in a simulated transplant model on the OCS using leukocyte-reduced blood from a different animal. Except for the cold vation phase, the ol for both arms of the group was identical. During the simulated transplant phase, organ function and stability were assessed by monitoring and measuring stable perfusion parameters maintained in pre-specified ranges, bile production, liver biomarkers including AST, ALT, ALP, GGT, and total bilirubin, pH levels, and arterial lactate levels. After the simulated transplant phase, livers were sampled for histopathology assessment. The acceptance criteria for this phase was the same as the acceptance ia ed in phase I.

OCS arm: Donor Organ Retrieval: During this phase, the donor organ was retrieved, and cold flushed to replicate the clinical condition of donor liver retrieval and instrumentation on the OCS Liver system. The same prep, organ retrieval, ation and pre-OCS flush were performed as described in Phase I.

Donor Liver Preservation on OCS (12 hours): During this phase, the donor organ underwent ex-vivo perfusion and assessment using OCS Liver system. Similar organ preservation was performed for this group as the 8 hour preservation samples bed in phase 1. The prime perfusate was composed of l500-2000ml RBCs (Haemonetics Cell Saver), 400 ml Albumin 25%, 700 ml of PlasmaLyte, Antibiotic (gram ve and gram negative) lg Cefazolin anleO mg Levofloxacin, 500mg of Solu-Medrol, 20mg, Dexamethasone, 50 mmol Hco3, l vial of multivitamin, and 10 ml of Ca gluconate (4.65 mEq) During preservation, 80% 02 was used starting at a rate of 450 ml/min starting just before organ instrumentation and was adjusted according to the arterial pC02 and p02. Temperature was maintained at 34°C.

Continuous infusion was delivered using the integrated OCS—SDS. Flolan was added to the HA inflow at 0-20 mic/hr (0—20ml/hr), as needed (0.05mg Flolan in 50 ml of Flolan Diluent “lmic/ml”). CLINIMIX E TPN with 30 IU of insulin, 25g of glucose and 40000 U of Heparin added was continuously infused to the PV at a rate of 30mL/h starting with priming. Na holic Salt, Gama sterilized Bile salt was infilsed at a rate of 3 mL/h (concentration 1 g/50 m1 sterile water) ng with priming.

Target pressures and flows were: Portal Vein pressure 1—8 mmHg; Portal Vein flow 7 L/min; Hepatic Artery pressure 85—1 10 mmHg; and Hepatic artery flow 0.3—0.7 L/min.

Using the Final Flush line included in the OCS Liver ion termination set, the liver was flushed and cooled on the OCS using 3L of Cold Lyte solution, supplying 1 liter at ~50—70 mmHg to the hepatic artery, and a 2 liter gravity drain to the portal vein. The liver was then disconnected from the OCS and placed in a cold saline bath for 45 minutes.

Cold Static preservation storage arm: The same prep, organ retrieval, cannulation and pre-OCS flush were performed as described in Phase 1.

After flushing the organ with 3 Liters ofUW, it was stored cold in UW on at temperature ~5 degree for 12 hours. Using the Final Flush line included in the OCS Liver perfusion termination set, the liver was flushed and cooled on the OCS using 3L of Cold PlasmaLyte solution, supplying 1 liter at ~50--70 mmHg to the hepatic artery, and a 2 liter gravity drain to the portal vein. The liver was then disconnected from the OCS and placed in a cold saline bath for 45 s.

Both sets of livers were ted to the post—transplant phase for 24 hours, where they were instrumented onto an OCS machine and supplied with a post- perfusate solution comprising 1500-3000 ml leukocytes reduced blood, 100 ml Albumin 25%, Antibiotic (gram positive and gram negative) lg Cefazolin and100 mg Levofloxacin, 500 mg of Solu-Medrol, 20mg, Dexamethasone, 50 mmol HCO3, 1 vial of multivitamin, and 10 ml of Ca gluconate (4.65 mEq). During simulated lant, 80% 02 was used starting at a rate of 450 ml/min starting just before organ W0 2015/187737 instrumentation and was adjusted according to the arterial pCO2 and p02.

Temperature was maintained at 37°C.

Continuous infusion was delivered using the ated OCS—SDS. Flolan was added to the HA inflow at 0-20 mic/hr. (0-20ml/hr.), as needed (0.05mg Flolan in 50 ml of Flolan Diluent “1mic/ml”). CLINIMIX E TPN with 30 IU of insulin, 25 g of e and 40000 U of Heparin added was continuously infiased to the PV at a rate of 30mL/h starting with priming. Na Taurocholic Salt, Gama sterilized Bile salt was infused at a rate of 3 mL/h (concentration lg/50 ml sterile water) starting with Target pressures and flows were: Portal Vein pressure 1—8 mmHg; Portal Vein flow 0.7—1.7 L/min; Hepatic Artery pressure 85—1 10 mmHg; and Hepatic artery flow 0.3—0.7 L/min.

Using the Final Flush line included in the OCS Liver perfiision termination set, the liver was flushed and cooled on the OCS using 3L of Cold PlasmaLyte solution, supplying 1 liter at ~50-70 mmHg to the hepatic artery, and a 2 liter gravity drain to the portal vein. Each Liter will be supplemented by 10 mmol HCO3 and 150mg of Solu-Medrol. The liver was then disconnected from the OCS and placed in a cold saline bath for 45 minutes. Table 9 below illustrates the liver perfusate infiisions and rate.

TABLE 9. OCS liver perfusate infusions and rate V ... ‘.' «\c ex ,4. .. \‘ “\.\"~._ \ m 3 MN; }, MAS..- is a samples location diagram illustrating locations of samples from a liver of a pig.

The ing liver histopathology sampling protocol was followed to assess the sample livers.

WO 87737 Samples collection time: At completion of the experiment (at the end of the 24hr simulated transplant phase).

Method and Samples collected: 1. Gross Picture: photographs of capsular and under surface of the OCS and CS livers at the beginning of the gross examination post study. 2. Bile Duct: entire extra-hepatic bile duct and as much adherent nding tissue (not surgically dissected from the surrounding tissue) in a neutral-buffered formalin jar. 3. Electron Microscogy (EM): 0.1 cm (1 mm) fragment of the liver tissue from the peripheral and deep aspect of the Left Lateral Lobe and the Right Medial Lobe.

Place the tissue specimen in electron microscopy fixative. 4. Hegatic Parenchyma (LM): 1 x 1 cm sections obtained from the periphery and deep aspects of each lobe (total of 8), and preserved in Formalin. ns thickness no more than 3-5mm and fixative volume 15 — 20 times higher than the specimen . Any obvious defect was sampled.

Samples Locations: Two samples were collected from each lobe according to the to access the hepatic parenchyma, each sample will be preserved in separate jar filled with 10% formalin and labeled accordingly. 1. Left Lateral Lobe L’eripberal—-M(LLLP--LZW) 2. Left Lateral Lobe L’eripberal— -EM(LLLP--EZW) 3. Left Lateral Lobe Qeep- D- -L]ll) 4. Left l Lobe Qeep- -EM(LLLD- -Elll) . Left Medial Lobe L’eripberal— -M(LMLP--LZW) 6. Left Medial Lobe Qeep— -IM(LMLD--LM) 7. Light Medial Lobe L’eriplzeral—-M(RMLP--LZW) 8. Eight Medial Lobe L’erz’pheral— -EM(RMLP--EZW) 9. flight Medial Lobe Qeep- —LM (RMLD- -L]VI) . Eight Medial Lobe Qeep--EM(RMLD--E]VI) l 1. Eight Lateral Lobe L’eripheral— -M(RLLP--LZW) 12. Li’z'ght l Lobe Qeep- -M(RLLD--LMO 13. Extra- tic Elle Qact (EHBD) Data Collection and Analysis Preservation data was summarized in tabular and graphic form, depending on the variable. Then continuous variables were analyzed with means, medians, standard deviations, and minimum and maximum values. After that, AST, ALT, GGT, ALP test results were collected, recorded and ed. Next, arterial lactate was collected, recorded and attached. pH was then measured, recorded and attached. HCO3 levels were then measured, recorded and attached. Lastly, total bile produced volume was collected and recorded.

Results of Phase III.

The OCS arm (N=3) of this group successfully met all of the acceptance criteria, which was pre-specified in the ol, by demonstrating the following hout the 24 hours of the simulated transplant phase: Stable perfusion parameters throughout preservation on the OCS for HAF, HAP, PVF and PVP, stable or trending down arterial lactate, continuous bile production with a rate of >10 ml/hr., stable or trending down liver enzymes (AST), and normal and stable perfusate PH.

For e, illustrates the Hepatic Artery Pressure (HAP) trend over the course of 24 hours perfusion on the OCS. illustrates the Portal Vein Pressure in an OCS-Liver Preservation arm vs the l Cold preservation arm. demonstrates the Portal Vein Pressure (PVP) trend over the course of 24 hours perfusion on the OCS; the cold preservation arm demonstrated an increase in the PVP over time compared to stable PVP for the OCS preservation arm. illustrates a Hepatic Artery Flow in a OCS-Liver vation arm vs. control Cold vation arm. demonstrates stable Hepatic Artery Flow (HAF) trend over the course of 24 hours perfusion on the OCS. illustrates a Portal Vein Flow in an OCS-Liver Preservation arm vs. control Cold preservation arm. demonstrates stable Portal Vein Flow (PVF) trend over the course of 24 hours ion on the OCS.

In comparison, the ted transplant OCS arm (N=3) performed better than the control arm. The perfusion parameters were comparable for both arms of the group however the control arm vascular resistance was higher compared to the OCS arm. The control arm had a much higher peak of the Lactate level at 7.8 mmol/L compared to 2.4 mmol/L for the OCS arm. Both arms continued to produce bile hout the simulated transplant phase at a rate >10ml/hr. For e, depicts Arterial Lactate in an OCS—Liver Preservation arm vs. a control Cold preservation arm. demonstrates Arterial Lactate in an OCS-Liver Preservation arm vs. l Cold preservation arm. This indicates that the OCS-arm livers had significantly better metabolic function as compared to cold stored arm.

Liver enzymes which is a sensitive ker of Liver injury (AST, ALT, and the GGT) showed a much higher peaks compared to the OCS arm of the group.

Average AST peak was 88.7 in the OCS arm compared to 1188 for the control arm.

Average ALT levels peaked at 31.3 for the OCS arm compared to a peak of 82 for the control arm. Average GGT levels peaked at 28.7 for the OCS arm compared to 97 for the control arm. This indicates well preserved Livers and less cell injury for Liver grafts preserved on the OCS arm as compared to the control arm. For example, rates an AST Level OCS-Liver Preservation arm vs. control Cold Preservation arm. demonstrates that the OCS perfused livers had significantly lower AST levels throughout the 24 hours simulated transplant period.

This indicates significantly less liver injury to the graft in the OCS group as compared to the cold stored group.

FIG 68 illustrates an ALT Level OCS-Liver vation arm vs. control Cold preservation arm. demonstrates that the OCS perfused livers had lower ALT levels with an average peak at 31.3 ed to average peak of 82 for the control group. This indicates less liver injury to the graft in the OCS arm as compared to the control cold stored arm. depicts a GGT Level of an OCS-Liver Preservation arm vs. control Cold preservation arm. demonstrates that the OCS perfused livers had a much lower GGT levels throughout the 24 hr. period. This indicates better hepatobilliary protection of the graft in the OCS arm as compared to the control cold stored arm.

The OCS arm demonstrated better metabolic profile ed to the control arm as manifested by the stable and normal pH levels compared to a lower pH for the control arm. This indicates that the OCS arm was able to maintain a much better metabolic profile than the control arm. For example, depicts a pH level of an OCS-Liver Preservation arm vs. a control Cold preservation arm. As demonstrated by , OCS ed livers had normal and stable pH values over the course of 24 hours of perfusion as compared to the Control cold preservation arm livers.

Also the OCS arm demonstrated better metabolic Liver fianctions as shown by higher HCO3 levels over the course of the 24 hours of the simulated transplant, as compared to the control arm of the group, which trated lower HCO3 throughout the ted transplant phase. This indicates that the OCS-arm livers had better metabolic function as compared to the control arm. For example, depicts a HCO3 level in an OCS-Liver Preservation arm vs. a Control Cold vation arm. As illustrated in , OCS perfused livers had higher HCO3 levels over the course of 24 hours of perfusion as compared to the l cold preservation arm livers. depicts a bile production OCS-Liver Preservation arm vs. control Cold preservation arm. demonstrates that both arms ined bile production rate of >10ml/hr. Based on the above presented data, The OCS has demonstrated stable ion and metabolic profile with well-preserved liver graft functions for up to 12 hours of OCS preservation. In addition, when compared to the control arm of cold static preservation, in the simulated transplant model, the OCS ed swine livers demonstrated a significantly better metabolic function, as evidenced by their ability to metabolize lactate to baseline levels as compared to cold stored livers where lactate continued to rise to significantly higher levels.

Additionally, the OCS perfiised swine livers had significantly lower AST levels as compared to the much higher level of AST in the simulated transplant l arm, which indicates better Liver graft functions in the OCS arm as compared to the control cold stored arm. The results of this pre-clinical OCS Liver device testing demonstrated that the OCS device is safe and effective in preservation of swine livers, as evidenced by meeting the specified acceptance criteria. The differences observed between the control arm and the OCS arm in Phase III were r to the differences observed in Phase 11, indicating that the OCS arm had better results. Additional uses While preservation of a donor organ which is intended for transplantation has been described above, some embodiments of the organ care system 600 described herein can be used for other purposes. For example, the system 600 can also be used for maintaining an organ during reconstructive or other types of surgery, therapy, and/or treatment (e.g., cated, high-risk surgeries and/or treatments). That is, some surgeries, therapies, and/or treatments can be damaging to the human body, if the procedure were performed on an in vivo organ. Thus, it can be beneficial to remove the organ from the patient’s body, perform surgery on and/or treat the organ ex vivo, and then reimplant the organ back into the patient’s body. For example, certain radiation therapies can be damaging to tissue surrounding the organ. Thus, by removing the organ, ive radiation y can be med on the organ t collateral damage to the patient’s body. Other embodiments are possible.

D. Ex-vivo treatment of diseased livers, including cancer, fatty , infection, by delivery of therapeutics to organ In some embodiments, the liver preserved on the organ care system 600 can be subjected to ex-vivo eutic treatment of liver es. Non-limiting examples of liver diseases include cancer, fatty livers, and liver infection. The therapy can be conducted by adding eutic agents to the perfusion fluid circulating through the organ care system 600, thereby providing it to the liver itself. atively, the therapeutic agents can be directly added into one or more nutritional solution described herein. In some embodiments, the temperature of the perfusion fluid and/or liver can be maintained at 400 C or 42° C, which can accelerate the rate of breakdown and dissolution of fatty cells in the liver.

Non-limiting examples of anti-cancer therapeutic agents suitable for ex-vivo therapeutic treatment of liver cancer e ubule binding agents, DNA intercalators or linkers, DNA synthesis inhibitors, DNA and/or RNA transcription inhibitors, antibodies, enzymes, enzyme inhibitors, gene regulators, and/or angiogenesis inhibitors. Anti-cancer "Microtubule binding agent" refers to an agent that interacts with tubulin to stabilize or destabilize microtubule formation thereby inhibiting cell division. Examples of microtubule binding agents include, without limitation, paclitaxel, docetaxel, Vinblastine, vindesine, lbine (navelbine), the epothilones, colchicine, atin 15, nocodazole, podophyllotoxin and rhizoxin. Analogs and tives of such compounds also can be used and will be known to those of ry skill in the art.

Anti-cancer DNA and/or RNA transcription regulators e, without limitation, mycin D, daunorubicin, doxorubicin and derivatives and analogs thereof. DNA intercalators and cross-linking agents include, without limitation, cisplatin, carboplatin, oxaliplatin, mitomycins, such as mitomycin C, bleomycin, chlorambucil, cyclophosphamide and derivatives and analogs thereof. DNA synthesis tors include, without limitation, methotrexate, o-5'-deoxyuridine, 5- fluorouracil and analogs thereof Examples of suitable enzyme inhibitors include, without limitation, camptothecin, etoposide, formestane, trichostatin and tives and analogs thereof. Other anti-tumor agents can include adriamycin, apigenin, rapamycin, zebularine, cimetidine, and derivatives and analogs f. Any other suitable liver cancer eutic agents known in the art are contemplated.

A r advantage of the chemotherapy described above is its specificity: the anticancer agent is specifically delivered to the diseased organ, the liver, without any undesirable toxicity to other healthy organs or tissues.

Non-limiting examples of therapeutic agents suitable for ex vivo therapeutic treatment of fatty liver disease include pioglitazone, rosiglitazone, orlistat, ursodiol, and betaine. Any other suitable fatty liver therapeutic agents known in the art are contemplated.

Non-limiting es of therapeutic agents suitable for o therapeutic treatment of liver infection include on alfa-2b, terferon alfa-2a, ribavirin, telaprevir, boceprevir, simeprevir, and sofobuvir. Any other suitable liver infection therapeutic agents known in the art are contemplated.

E. Regenerative approaches including Stem cell or gene delivery In other embodiments, the organ preserved by the organ care system 600 described herein can be subjected to regenerative treatments. Non-limiting examples of the organ regenerative treatments include stem cell therapy or gene delivery therapy. Stem cells are undifferentiated ical cells that can differentiate into specialized cells, e.g., hepatocytes. Adult stem cells can be harvested from blood, adipose, and bone marrow of the donor of the liver with various types of liver diseases, or of another adult with compatible stem cells (stem cells transplantation).

The isolated stem cells, e.g, bone marrow cells, can be used to infuse the d or diseased liver preserved on the organ care system 600 to repair the liver to a healthier state. For instance, the isolated stem cells can be ed from the donor and included in the blood product in the perfusion fluid.

In some other embodiments, the liver ved by the organ care system 600 described herein can be subjected to gene delivery therapy. Gene delivery is the s of introducing foreign DNA into host cells, e.g., liver cells, to effect treatment of diseases. In certain embodiments, the gene delivery therapy is virus-mediated gene delivery utilizing a virus to inject its DNA inside the liver cells. Non—limiting examples of suitable viruses include retrovirus, adenovirus, adeno-associated virus and herpes simplex virus. In some embodiments, a gene that is used to treat certain liver diseases is packaged into a vector (virus or other) and included as part of the perfusion fluid to perfuse the liver or added to the circulation of the organ care system 600 ly.

F. o immune modulation In other embodiments, the donor’s liver preserved by the organ care system 600 described herein can be subjected to immune regulations. Immune responses and their modulation within the liver can affect the outcome liver transplantation. More importantly, a liver disease can be treated by inducing, enhancing, or suppressing an immune response from the liver. For instance, the liver immune system can be activated to attack malicious tissues to treat liver cancer. On the other hand, the liver immune system can be ssed to treat autoimmune liver disease such as autoimmune hepatitis. Any suppressive agents or immune activating agents known in the art can be used to treat the preserved liver to achieve the desirable effect.

G. EX-vivo surgical treatment of livers In yet other embodiments, the donor’s liver preserved by the organ care system 600 described herein can be subjected to surgical treatment such as liver tumor resection or split transplant where the liver is divided between two ent patients.

In yet other embodiments, the donor’s liver preserved by the organ care system 600 described herein can be subjected to irradiation therapy to treat certain liver diseases such as liver cancer.

XI. Conclusion Other embodiments are within the scope and spirit of the disclosed subject matter. In some embodiments, a perfiision circuit for perfusing a liver eX-vivo is disclosed, which comprises a pump for ing pulsatile fluid flow of a perfusion fluid through the circuit, a gas exchanger, a divider in fluid ication with the pump red to divide the perfusion fluid flow into a first branch and a second branch wherein the first branch comprises a c artery interface wherein the first branch is configured to provide a first portion of the perfilsion fluid to a hepatic artery ofthe liver at a high pressure and low flow rate via the hepatic artery interface n the first branch is in fluid pressure communication with the pump wherein the second branch comprises a portal vein interface wherein the second branch is configured to provide a second portion of the perfusion fluid to a portal vein of the liver at a low pressure and high flow rate via the portal vein interface the second branch r comprising a clamp located between the divider and the portal vein interface for selectively lling the flow rate of perfilsion fluid to the portal vein the second branch fiurther sing a compliance chamber configured to reduce the pulsatile flow teristics of the perfusion fluid from the pump to the portal vein wherein the pump is configured to communicate fluid pressure through the first and second branches to the liver, a drain configured to receive perfusion fluid from an uncannulated inferior vena cava of the liver, and a reservoir positioned below the liver and located between drain and the pump, configured to receive the perfusion fluid from the drain and store a volume of fluid.

In certain embodiments, the second branch of a perfiision t comprises a plurality of compliance chambers. In certain embodiments, a compliance chamber in a ion circuit is located between the divider and the portal vein interface. In certain embodiments, a portal vein interface of a perfirsion circuit has a larger cross sectional area than a hepatic artery interface. In certain embodiments, a perfusion circuit includes at least one flow rate sensor in a second , and at least one pressure . In certain embodiments, a pump comprises a pump driver, and the position of the pump driver is adjustable to control the pattern of pulsatile flow to a liver. In some embodiments a clamp comprises an engaged position and a disengaged position, the clamp may be adjusted to select the desired ng force and corresponding flow rate when the clamp is in the disengaged position, the clamp may be moved to the engaged position to apply the selected clamping force without further ment when in the engaged position, such that a user may quickly engage and disengage the clamp while still having e l over the amount of clamping force applied to the perfusion circuit.

In some embodiments, a system for perfiasing an ex vivo liver at near physiologic conditions is disclosed, the system comprising a perfusion circuit comprising a pump for g perfusion fluid through the circuit, the pump in fluid communication with a hepatic artery interface and a portal vein interface, wherein the pump provides perfusion fluid to a hepatic artery of the liver at a high pressure and low flow rate via the hepatic artery interface; and wherein the pump es ion fluid to the a portal vein of the liver at a low pressure and high flow rate Via the portal vein interface, a gas exchanger, a heating subsystem for ining the temperature of the perfusion fluid at a normothermic temperature, a drain configured to receive the perfusion fluid from an inferior vena cava of the liver, a reservoir configured to receive perfiJsion fluid from the drain and store a volume of fluid. In some embodiments, a heating subsystem is red to maintain the perfusion fluid at a temperature between 34-3 7° C. In some embodiments, a the perfusion circuit comprises an inferior vena cava cannula. In some embodiments, a control system for controlling operation of the system is disclosed, comprising an onboard computer system connected to one or more of the ents in the system, a data acquisition subsystem comprising at least one sensor for obtaining data ng to the organ, and a data management subsystem for storing and maintaining data relating to operation of the system and with respect to the liver. In some embodiments, a heading subsystem comprises a dual feedback loop for controlling the temperature of the perfusion fluid within the system.

In some embodiments, a system for preserving a liver ex vivo at physiologic conditions is disclosed, comprising a multiple use module sing a pulsatile pump, a single use module comprising, a perfusion circuit configured to provide perfusion fluid to the liver, a pump interface assembly for translating pulsatile pumping from the pump to the perfusion fluid, a hepatic artery interface red to deliver perfiasion fluid to a c artery of the liver, a portal vein interface configured to deliver perfusion fluid to a portal vein of the liver, a divider to supply perfusion fluid flow from the pump interface assembly to the hepatic artery interface at a high pressure and low flow rate and to the portal vein interface at a low pressure IO and high flow rate, an organ chamber assembly configured to hold an ex vivo organ, the organ r assembly including a housing, a flexible support surface suspended within the organ chamber assembly, and a bile container configured to collect bile produced by the liver.

In some embodiments, flexible support surface is configured to m to differently sized , and further comprising projections to stabilize the liver in the organ chamber assembly. In some embodiments, a e support surface ses a top layer, a bottom layer, and a deformable metal substrate positioned between the top layer and the bottom layer. In some embodiments, a flexible support surface is configured to cradle and controllably support a liver without applying undue pressure to the liver. In some embodiments, a single use module comprises a wrap configured to cover the liver in the organ chamber ly. In some embodiments, a single use module comprises a sensor to measure the volume of bile ted in the bile container. In some ments, a single use module can be sized and shaped for interlocking with a portable chassis of the multiple use module for electrical, mechanical, gas and fluid interoperation with the multiple use module. In some embodiments, multiple and single use modules can communicate with each other via an optical interface, which comes into l alignment automatically upon the single use disposable module being installed into the portable multiple use module.

The subject matter described herein can be implemented using digital electronic circuitry, or in computer software, firmware, or hardware, including the ural means disclosed in this ication and structural equivalents thereof, or in combinations of them. The subject matter described herein can be implemented as one or more computer program products, such as one or more computer programs tangibly embodied in an ation carrier (e.g., in a machine-readable storage device), or embodied in a ated signal, for execution by, or to control the operation of, data processing apparatus (e.g., a mmable processor, a computer, or multiple computers). A computer program (also known as a program, re, software application, or code) can be written in any form ofprogramming language, including compiled or interpreted languages, and it can be deployed in any form, including as a stand-alone program or as a module, ent, subroutine, or other unit suitable for use in a computing environment. A computer program does not necessarily correspond to a file. A program can be stored in a n of a file that holds other programs or data, in a single file dedicated to the program in question, or in multiple nated files (e.g., files that store one or more modules, sub-programs, or ns of code). A computer program can be deployed to be executed on one computer or on multiple computers at one site or distributed across multiple sites and interconnected by a communication network.

The processes and logic flows described in this specification, including the method steps of the subject matter described , can be med by one or more programmable processors executing one or more computer programs to m functions of the subject matter described herein by operating on input data and generating output. The processes and logic flows can also be performed by, and apparatus of the subject matter described herein can be ented as, special purpose logic circuitry, e.g., an FPGA (field programmable gate array) or an ASIC (application-specific integrated circuit).

Processors suitable for the execution of a er program include, by way of example, both general and special purpose microprocessors, and any one or more sor of any kind of digital computer. Generally, a processor will receive instructions and data from a read-only memory or a random access memory or both.

The essential elements of a computer are a processor for executing instructions and one or more memory devices for g instructions and data. Generally, a computer will also include, or be operatively coupled to receive data from or transfer data to, or both, one or more mass storage devices for storing data, e.g., magnetic, magneto-optical disks, or optical disks. Information carriers suitable for embodying computer program instructions and data include all forms of non-volatile memory, ing by way of example semiconductor memory devices, (e.g., EPROM, EEPROM, and flash memory devices); ic disks, (e.g., internal hard disks or removable disks); magneto-optical disks; and optical disks (e. g., CD and DVD disks).

The processor and the memory can be supplemented by, or incorporated in, special purpose logic try.

To provide for interaction with a user, the subject matter bed herein can be implemented on a computer having a display device, e.g., a CRT (cathode ray tube) or LCD (liquid crystal display) monitor, for displaying information to the user and a rd and a pointing device, (e.g., a mouse or a trackball), by which the user can provide input to the er. Other kinds of devices can be used to provide for interaction with a user as well. For example, feedback provided to the user can be any form of sensory ck, (e.g., visual feedback, auditory feedback, or tactile feedback), and input from the user can be received in any form, including acoustic, speech, or tactile input.

The ques described herein can be ented using one or more modules. As used herein, the term “module” refers to computing software, firmware, hardware, and/or various combinations thereof. At a minimum, r, modules are not to be interpreted as software that is not implemented on re, firmware, or recorded on a non-transitory sor readable recordable storage medium (i.e., modules are not software per se). Indeed “module” is to be reted to always e at least some physical, non-transitory hardware such as a part of a processor or computer. Two different modules can share the same physical hardware (e.g., two different modules can use the same processor and network interface). The modules described herein can be combined, integrated, separated, and/or duplicated to support various applications. Also, a fianction described herein as being performed at a particular module can be performed at one or more other modules and/or by one or more other devices instead of or in addition to the fiinction performed at the particular module. Further, the modules can be implemented across multiple devices and/or other components local or remote to one another. Additionally, the modules can be moved from one device and added to another device, and/or can be included in both s.

The subject matter described herein can be ented in a computing system that includes a back-end component (e.g., a data server), a middleware component (e.g., an application server), or a front-end component (e.g., a client 2015/033839 computer having a graphical user interface or a web browser through which a user can interact with an implementation of the subject matter described herein), or any combination of such back-end, middleware, and front-end components. The components of the system can be interconnected by any form or medium of l data communication, e.g., a ication network. Examples of communication networks include a local area network (“LAN”) and a wide area network (“WAN”), e. g., the Internet.

Claims (26)

1. A perfusion circuit for perfusing a liver ex vivo, the perfusion t comprising: a pump for ing fluid flow of a ion fluid through the perfusion circuit; a gas exchanger; a solution pump configured to infuse a solution into the perfusion fluid; a divider in fluid communication with the pump and configured to divide the fluid flow of the perfusion fluid into a first portion of the perfusion fluid flowing through a first branch and a second portion of the perfusion fluid flowing h a second branch, a volume of the second portion of the perfusion fluid being greater than a volume of the first portion of the perfusion fluid; wherein the first branch comprises a hepatic artery interface configured to provide the first portion of the perfusion fluid to a hepatic artery of the liver, the first portion of the ion fluid having a first pressure and a first flow rate at the hepatic artery interface, and the second branch comprises a portal vein interface configured to provide the second portion of the perfusion fluid to a portal vein of the liver, the second n of the perfusion fluid having a second pressure and a second flow rate at the portal vein interface; one or more drains configured to receive the perfusion fluid from an inferior vena cava of the liver; a reservoir positioned between the one or more drains and the pump, the reservoir configured to receive the perfusion fluid from the one or more drains and store a volume of the perfusion fluid; a bile container configured to receive bile produced by the liver.

2. The ion circuit of claim 1, wherein the bile container ses a soft shell through which light passes and a sensor configured to measure the received bile.

3. The perfusion circuit of claim 1 or claim 2, sing at least one flow rate sensor and at least one pressure sensor.

4. The perfusion circuit of any one of claims 1-3, configured such that the first pressure is between 25-150 mmHg, the first flow rate is between 0.25-1 Liters/minute, the second pressure is between 1-25 mmHg, and the second flow rate is between 0.75-2 /minute.

5. The ion circuit of any one of claims 1-4, wherein the solution pump is configured to periodically infuse the solution into the perfusion fluid.

6. The perfusion circuit of any one of claims 1-4, wherein the solution pump is ured to continuously infuse the solution into the perfusion fluid.

7. The perfusion circuit of any one of claims 1-6, wherein the second branch comprises: a clamp between the divider and the portal vein interface, the clamp configured to selectively control the second flow rate; and a compliance chamber configured to mitigate changes of pressure in the second n of the perfusion fluid from the pump to the portal vein.

8. The perfusion circuit of claim 7, wherein the clamp is configured to be moveable between an engaged position and a disengaged position, when the clamp is in the disengaged position, the clamp is adjustable to select a clamping force and corresponding flow rate, and when the clamp is in the engaged position, the clamp is configured to apply the selected clamping force without r adjustment.

9. The perfusion circuit of claim 7 or claim 8, wherein the compliance chamber is d between the r and the portal vein interface.

10. The perfusion circuit of any one of claims 1-9, n the solution pump is ured to infuse the solution comprising a nd supporting production of bile, the compound selected from a group ting of cholesterol; primary bile acids; secondary bile acids; glycine; taurine; and bile acids or salts.

11. The perfusion circuit of claim 1, wherein the pump comprises a pump driver, and wherein a position of the pump driver is adjustable to control a pattern of the fluid flow to the liver.

12. The perfusion circuit of any one of claims 1-11, wherein the solution comprises one or more compounds supporting production of the bile, a vasodilator, a therapeutic agent, an energy source, or an amino acid.

13. A system for perfusing an ex vivo liver at near physiologic conditions, the system comprising: a perfusion circuit comprising: a pump ured to provide a fluid flow of a ion fluid through the perfusion circuit; a gas exchanger; a divider in fluid communication with the pump, the divider configured to divide the perfusion fluid into: a first portion of the perfusion fluid flowing to a hepatic artery interface configured to provide the first portion of the perfusion fluid to a hepatic artery of the liver at a first re and a first flow rate, and a second n of the perfusion fluid flowing to a portal vein interface configured to provide the second portion of the perfusion fluid to a portal vein of the liver at a second pressure and a second flow rate; a heating subsystem for maintaining a temperature of the perfusion fluid at a normothermic temperature; a solution pump ured to infuse a solution into the perfusion fluid; and a bile container configured to receive bile produced by the liver.

14. The system of claim 13, comprising: a clamp between the divider and the portal vein interface, the clamp configured to selectively control the second flow rate; and a compliance chamber configured to mitigate changes of pressure in the second n of the perfusion fluid from the pump to the portal vein.

15. The system of claim 14, wherein the clamp is configured to be moveable between an engaged position and a disengaged position, when the clamp is in the disengaged position, the clamp is able to select a clamping force and ponding flow rate, and when the clamp is in the engaged position, the clamp is ured to apply the selected clamping force without further adjustment.

16. The system of any one of claims 13-15, comprising: one or more drains configured to receive the perfusion fluid from an or vena cava of the liver, and a reservoir configured to receive the ion fluid from the drain and store a volume of the perfusion fluid.

17. The system of any one of claims claim 13-16, wherein the heating subsystem is configured to maintain the temperature of the perfusion fluid at between 34-37º Celsius.

18. The system of any one of claims 13-17, wherein the perfusion circuit comprises an inferior vena cava cannula.

19. The system of any one of claims 13-18, comprising: a control system for controlling operation of the system; an onboard computer system connected to one or more ents of the system; a data acquisition subsystem comprising at least one sensor for obtaining data relating to the liver; and a data management subsystem for maintaining data relating to an operation of the system.

20. The system of any one of claims 13-19, wherein the g tem comprises a dual ck loop for controlling the temperature of the perfusion fluid.

21. The system of any one of claims 13-20, wherein the solution ses one or more compounds supporting production of the bile, a vasodilator, a therapeutic agent, an energy source, or an amino acid.

22. The system of claim 19, wherein the control system is configured to control the first pressure of the first portion of the ion fluid provided to the hepatic artery automatically.

23. The perfusion circuit of claim 1, wherein the first pressure of the first portion of the perfusion fluid provided to the hepatic artery is configured to be controlled tically.

24. The perfusion circuit of any one of claims 1-12 or 23, substantially as herein described with nce to any one or more of the examples but excluding comparative examples.

25. A system for preserving a liver ex vivo at physiological conditions, the system comprising: a multiple-use module comprising a pump; and a single-use module comprising: an organ-chamber assembly configured to hold an ex vivo organ, the organ-chamber assembly including: a housing; a flexible support surface suspended within the organ-chamber assembly; and a ion circuit configured to provide fluid flow of a perfusion fluid to the liver, the perfusion circuit comprising: a pump interface assembly for translating pumping from the pump to the perfusion fluid; a c artery interface configured to provide a first portion of the perfusion fluid to a hepatic artery of the liver; a portal vein interface configured to provide a second portion of the perfusion fluid to a portal vein of the liver; and a divider ured to provide the first portion of the perfusion fluid from the pump ace assembly to the hepatic artery interface at a re between 25-150 mmHg and a flow rate between 0.25-1 Liters/minute and the second portion of the perfusion fluid to the portal vein interface at a pressure between 1-25 mmHg and a flow rate between 0.75-2 Liters/minute.

26. The system of any one of claims 13-22 or 25, substantially as herein described with reference to any one or more of the examples but excluding comparative examples.