JP7654276B2 - BLOOD ANALYZER, BLOOD ANALYZING METHOD, AND PROGRAM FOR BLOOD ANALYZER - Google Patents
BLOOD ANALYZER, BLOOD ANALYZING METHOD, AND PROGRAM FOR BLOOD ANALYZER Download PDFInfo
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- PWPJGUXAGUPAHP-UHFFFAOYSA-N lufenuron Chemical compound C1=C(Cl)C(OC(F)(F)C(C(F)(F)F)F)=CC(Cl)=C1NC(=O)NC(=O)C1=C(F)C=CC=C1F PWPJGUXAGUPAHP-UHFFFAOYSA-N 0.000 title 1
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- 102000001554 Hemoglobins Human genes 0.000 claims description 38
- 108010054147 Hemoglobins Proteins 0.000 claims description 38
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- Investigating Or Analysing Materials By Optical Means (AREA)
- Measurement Of The Respiration, Hearing Ability, Form, And Blood Characteristics Of Living Organisms (AREA)
Description
本発明は、チューブ内の血液を通過した透過光の強度に基づいてヘマトクリット値又はヘモグロビン濃度を算出する血液分析装置に関するものである。 The present invention relates to a blood analyzer that calculates the hematocrit value or hemoglobin concentration based on the intensity of light transmitted through blood in a tube.
例えば人工透析システムでは、患者の体内から取り出される血液の流量や浄化されて患者の体内に戻される血液の流量を適切な量に管理し、患者に負担をかけないようにする必要がある。このため、人工透析システムを構成する血液回路中を流れる血液の流量を正確に測定する必要がある。 For example, in an artificial dialysis system, the flow rate of blood taken from the patient's body and the flow rate of purified blood returned to the patient's body must be appropriately controlled to avoid placing a burden on the patient. For this reason, it is necessary to accurately measure the flow rate of blood flowing through the blood circuit that makes up the artificial dialysis system.
特許文献１では、血液の流量を算出するために必要となるヘマトクリット値やヘモグロビン濃度を測定するために血液の流れるチューブに対して血液分析装置が取り付けられている。この血液分析装置は、チューブを半径方向に対して横切るように光を射出する発光部と、チューブ及び血液を通過した透過光を受光する受光部と、受光部の出力する例えば電流値から透過光強度を算出するとともに、この透過光強度からヘマトクリット値やヘモグロビン濃度へ換算する分析部と、を備えている。 In Patent Document 1, a blood analyzer is attached to a tube through which blood flows in order to measure the hematocrit value and hemoglobin concentration required to calculate the blood flow rate. This blood analyzer includes a light emitting unit that emits light across the tube in the radial direction, a light receiving unit that receives the transmitted light that has passed through the tube and blood, and an analysis unit that calculates the transmitted light intensity from, for example, a current value output by the light receiving unit and converts this transmitted light intensity into the hematocrit value and hemoglobin concentration.
しかしながら、上述したような透過光強度だけに基づいて測定されるヘマトクリット値やヘモグロビン濃度は、血液自体の特性やその懸濁状態等の影響を受けるため、個人間や同一人であっても血液検体間で測定誤差が発生してしまう。 However, the hematocrit value and hemoglobin concentration measured based solely on the transmitted light intensity as described above are affected by the characteristics of the blood itself and its suspension state, resulting in measurement errors between individuals and between blood samples from the same person.
このような問題について本願発明者らが鋭意検討を行ったところ、以下のような現象に起因して測定誤差が発生していることが見いだされた。すなわち、例えば赤血球に凝集が生じている場合とそうではない場合には血液中において血球の存在しない領域の大きさが異なる。また、赤血球の凝集度合いは生理食塩水か血漿で血液を懸濁しているかによっても影響を受ける。この結果、同じ血液濃度（ヘモグロビン濃度）の血液検体があったとしても、赤血球の存在している領域と存在していない領域の大きさが異なってしまい、ひいては検出される透過光の強度も異なってしまう。したがって、透過光の強度だけに基づいてヘマトクリット値やヘモグロビン濃度を算出すると、赤血球の凝集状態の影響を受けてばらつきが大きく発生してしまう。 The inventors of the present application conducted extensive research into this problem and found that measurement errors occur due to the following phenomenon. That is, for example, the size of the area in the blood where no blood cells are present differs between cases where red blood cells have aggregated and cases where they have not. The degree of red blood cell aggregation is also affected by whether the blood is suspended in saline or plasma. As a result, even if there is a blood sample with the same blood concentration (hemoglobin concentration), the size of the area where red blood cells are present and the area where they are not present will differ, and the intensity of the detected transmitted light will also differ. Therefore, if the hematocrit value or hemoglobin concentration is calculated based only on the intensity of the transmitted light, there will be a large variation due to the effect of the state of red blood cell aggregation.
本発明は上述したような問題に鑑みてなされたものであり、血液検体の懸濁条件や赤血球の凝集状態に違いがあったとしても、測定誤差が発生するのを抑えて、より正確にヘマトクリット値やヘモグロビン濃度を算出することができる血液分析装置を提供することを目的とする。 The present invention has been made in consideration of the above-mentioned problems, and aims to provide a blood analyzer that can reduce the occurrence of measurement errors and more accurately calculate hematocrit values and hemoglobin concentrations, even if there are differences in the suspension conditions of the blood sample or the aggregation state of red blood cells.
すなわち、本発明に係る血液分析装置は、透光性を有するチューブ内にある少なくとも血液を含む分析対象液に対して光を照射して、前記チューブを透過した光に基づいて血液を分析する血液分析装置であって、前記チューブを半径方向に対して横切るように光を射出する発光素子と、前記チューブ及び前記分析対象液を透過した光を受光する第１受光素子と、前記チューブ又は前記分析対象液で前記発光素子側へ反射又は散乱された光を受光する第２受光素子と、前記第１受光素子の出力、及び、前記第２受光素子の出力に基づいて、少なくともヘマトクリット値又はヘモグロビン濃度を含む血液分析値を算出する分析器と、を備えたことを特徴とする。 That is, the blood analysis device according to the present invention is a blood analysis device that irradiates light onto an analysis target liquid containing at least blood in a light-transmitting tube and analyzes blood based on the light transmitted through the tube, and is characterized by comprising a light-emitting element that emits light across the tube in the radial direction, a first light-receiving element that receives the light transmitted through the tube and the analysis target liquid, a second light-receiving element that receives light reflected or scattered by the tube or the analysis target liquid toward the light-emitting element, and an analyzer that calculates blood analysis values including at least a hematocrit value or a hemoglobin concentration based on the output of the first light-receiving element and the output of the second light-receiving element.
また、本発明に係る血液分析方法は、透光性を有するチューブ内にある少なくとも血液を含む分析対象液に対して光を照射して、前記チューブを透過した光に基づいて血液を分析する血液分析装置を用いた血液分析方法であって、前記血液分析装置が、前記チューブを半径方向に対して横切るように光を射出する発光素子と、前記チューブ及び前記分析対象液を透過した光を受光する第１受光素子と、前記チューブ又は前記分析対象液で前記発光素子側へ反射又は散乱された光を受光する第２受光素子と、を備え、前記第１受光素子の出力、及び、前記第２受光素子の出力に基づいて、少なくともヘマトクリット値又はヘモグロビン濃度を含む血液分析値を算出することを特徴とする。 The blood analysis method according to the present invention is a blood analysis method using a blood analysis device that irradiates light onto an analysis target liquid containing at least blood in a light-transmitting tube and analyzes the blood based on the light transmitted through the tube, and is characterized in that the blood analysis device includes a light-emitting element that emits light across the tube in the radial direction, a first light-receiving element that receives the light transmitted through the tube and the analysis target liquid, and a second light-receiving element that receives light reflected or scattered by the tube or the analysis target liquid toward the light-emitting element, and calculates blood analysis values including at least a hematocrit value or a hemoglobin concentration based on the output of the first light-receiving element and the output of the second light-receiving element.
このようなものであれば、前記発光素子から射出された光のうち、赤血球によって吸収されず透過した光だけでなく、赤血球において反射又は散乱された光も用いてヘマトクリット値やヘモグロビン濃度といった前記血液分析値を算出しているので、以下のような理由で測定誤差をできると考えられる。 In such a case, the blood analysis values such as the hematocrit value and hemoglobin concentration are calculated using not only the light emitted from the light-emitting element that is not absorbed by the red blood cells and is transmitted through them, but also the light that is reflected or scattered by the red blood cells, so it is thought that measurement errors can occur for the following reasons.
例えば、赤血球が凝集している場合には、前記発光素子により光が照射されている領域において赤血球の存在しない領域が大きくなるため、透過光の量が多くなるため、前記第１受光素子の出力は大きくなる。これに対して、赤血球が凝集しているほど前記発光素子側に反射又は散乱される光の少なくなるので、前記第２受光素子の出力は小さくなる。 For example, when red blood cells are aggregated, the area where no red blood cells are present becomes larger in the area irradiated with light by the light-emitting element, and the amount of transmitted light increases, so the output of the first light-receiving element becomes larger. In contrast, the more red blood cells are aggregated, the less light is reflected or scattered toward the light-emitting element, so the output of the second light-receiving element becomes smaller.
逆に赤血球があまり凝集しておらず、均一に分散している場合には赤血球が凝集している状態を基準とすると透過光の強度は少なくなって前記第１受光素子の出力が小さくなる。これに対して前記発光素子側へ反射又は散乱される光の量は多くなるため前記第２受光素子の出力は大きくなる。 Conversely, when the red blood cells are not significantly aggregated and are uniformly dispersed, the intensity of the transmitted light is reduced and the output of the first light receiving element is reduced when compared to the state in which the red blood cells are aggregated. In contrast, the amount of light reflected or scattered toward the light emitting element is increased, and the output of the second light receiving element is increased.
したがって、前記第１受光素子の出力と前記第２受光素子の出力は赤血球の凝集度合いに対して逆の変化特性を有しているので、例えばこれらの出力の線形和は赤血球における光の吸収だけを反映させやすくなると考えられる。すなわち、透過光の強度が反映された前記第１受光素子の出力だけでなく、前記発光素子側への反射光や散乱光の強度が反映された前記第２受光素子の出力も用いることによって、赤血球の凝集度によらず、ヘマトクリット値やヘモグロビン濃度といった血液分析値と対応する吸光度を正確に測定できるようになる。このため、前記分析部は前記第１受光素子及び前記第２受光素子の出力に基づいて、正確に前記血液分析値を算出することができると考えられる。 Therefore, since the output of the first light receiving element and the output of the second light receiving element have inverse change characteristics with respect to the degree of red blood cell aggregation, it is considered that, for example, the linear sum of these outputs is likely to reflect only the absorption of light in red blood cells. In other words, by using not only the output of the first light receiving element reflecting the intensity of transmitted light, but also the output of the second light receiving element reflecting the intensity of reflected light and scattered light toward the light emitting element, it becomes possible to accurately measure the absorbance corresponding to blood analysis values such as hematocrit value and hemoglobin concentration, regardless of the degree of red blood cell aggregation. Therefore, it is considered that the analysis unit can accurately calculate the blood analysis value based on the output of the first light receiving element and the second light receiving element.
例えば赤血球の凝集度合いや懸濁条件の違いによらず、赤血球において生じている吸光現象を正確に反映した吸光度を得られるようにして、前記血液分析値を正確に算出したり、測定誤差のばらつきを従来よりも低減したりするには、前記分析器が、前記第１受光素子の出力に基づいて第１吸光度を算出する第１吸光度算出部と、前記第２受光素子の出力に基づいて第２吸光度を算出する第２吸光度算出部と、前記第１吸光度と前記第２吸光度の線形和を前記血液分析値に換算する換算部と、を具備するものであればよい。このようなものであれば線形和を用いているので、前記第１受光素子の出力と前記第２受光素子の出力の重み付けを変更して、前記血液分析値を正確に算出できるように調整するといったことも可能となる。 For example, in order to obtain an absorbance that accurately reflects the absorption phenomenon occurring in red blood cells regardless of the degree of aggregation of red blood cells or differences in suspension conditions, and to accurately calculate the blood analysis value and reduce the variation in measurement error more than ever before, the analyzer needs to include a first absorbance calculation unit that calculates the first absorbance based on the output of the first light receiving element, a second absorbance calculation unit that calculates the second absorbance based on the output of the second light receiving element, and a conversion unit that converts the linear sum of the first absorbance and the second absorbance into the blood analysis value. In such a case, since a linear sum is used, it is also possible to change the weighting of the output of the first light receiving element and the output of the second light receiving element to adjust the blood analysis value so that it can be calculated accurately.
調整作業等の手間を省く事が可能となる簡単な構成でありながらも従来よりも正確にヘマトクリット値やヘモグロビン濃度といった前記血液分析値を算出できるようにするための具体例としては、値前記換算部が、前記第１吸光度と前記第２吸光度の和を前記血液分析値に換算するように構成されたものが挙げられる。 As a specific example of a device that can calculate the blood analysis values such as hematocrit value and hemoglobin concentration more accurately than before while having a simple configuration that can eliminate the trouble of adjustment work, etc., the value conversion unit is configured to convert the sum of the first absorbance and the second absorbance into the blood analysis value.
前記分析器が、前記第１受光素子の出力と前記第２受光素子の出力の線形和に基づいて補正吸光度を算出する補正吸光度算出部と、前記補正吸光度を前記血液分析値に換算する換算部と、を具備するものが挙げられる。 The analyzer may include a corrected absorbance calculation unit that calculates a corrected absorbance based on the linear sum of the output of the first light receiving element and the output of the second light receiving element, and a conversion unit that converts the corrected absorbance into the blood analysis value.
前記第１受光素子及び前記第２受光素子からの信号処理を簡素化しつつ、正確な前記血液分析値を算出できるようにするには、補正吸光度算出部が、前記第１受光素子の出力と前記第２受光素子の出力の和に基づいて補正吸光度を算出するように構成されたものであればよい。 In order to simplify the signal processing from the first light receiving element and the second light receiving element while being able to accurately calculate the blood analysis value, the corrected absorbance calculation unit may be configured to calculate the corrected absorbance based on the sum of the output of the first light receiving element and the output of the second light receiving element.
例えば人工透析装置を構成するチューブの一部に後付できるようにしつつ、前記第１受光素子及び前記第２受光素子には前記発光素子以外の光源から射出された光が迷光として入射しにくくして、測定精度を担保できるようにするには、前記発光素子、前記第１受光素子、及び、前記第２受光素子が設けられるボディをさらに備え、前記ボディが、前記チューブが嵌め込まれる収容溝と、前記発光素子から射出された光を前記収容溝内へ入射させる入射光窓と、前記入射光窓と対向するように設けられ、前記チューブ及び前記分析対象液を通過した光を前記収容溝から前記第１受光素子へ入射させる透過光窓と、前記チューブの延伸方向に対して前記入射光窓と並べて設けれ、前記チューブ又は前記分析対象液で反射又は散乱された光を前記収容溝から前記第２受光素子へ入射させる反射散乱光窓と、を具備するものであればよい。 For example, in order to ensure measurement accuracy by making it possible to retrofit a part of a tube constituting an artificial dialysis device while making it difficult for light emitted from a light source other than the light-emitting element to enter the first light-receiving element and the second light-receiving element as stray light, it is sufficient if the body further includes the light-emitting element, the first light-receiving element, and the second light-receiving element, and the body includes a storage groove into which the tube is fitted, an incident light window that allows light emitted from the light-emitting element to enter the storage groove, a transmitted light window that is arranged opposite the incident light window and allows light that has passed through the tube and the liquid to be analyzed to enter the first light-receiving element from the storage groove, and a reflected and scattered light window that is arranged side by side with the incident light window in the extension direction of the tube and allows light reflected or scattered by the tube or the liquid to be analyzed to enter the second light-receiving element from the storage groove.
前記ボディの外部から前記チューブ内へ迷光が入射するのをさらに防ぐことができるようにするには、前記入射光窓、前記透過光窓、及び、前記反射散乱光窓が前記収容溝のいずれかの側面に形成されており、前記ボディが、前記収容溝が底面部に形成されているとともに、前記収容溝の延伸方向に沿って延びる凹部をさらに備えたものであればよい。 In order to further prevent stray light from entering the tube from outside the body, the incident light window, the transmitted light window, and the reflected and scattered light window may be formed on any side of the storage groove, and the body may further include a recess extending along the extension direction of the storage groove, with the storage groove formed on the bottom surface.
例えば既存の血液分析装置に前記第２受光素子を追加するとともに、プログラムを更新することによって本発明に係る血液分析装置と同等の効果を発揮できるようにするには、透光性を有するチューブ内にある少なくとも血液を含む分析対象液に対して光を照射して、前記チューブを透過した光に基づいて血液を分析する血液分析装置に用いられるプログラムであって、前記血液分析装置が、前記チューブを半径方向に対して横切るように光を射出する発光素子と、前記チューブ及び前記分析対象液を透過した光を受光する第１受光素子と、前記チューブ又は前記分析対象液で前記発光素子側へ反射又は散乱された光を受光する第２受光素子と、を備え、前記第１受光素子の出力、及び、前記第２受光素子の出力に基づいて、少なくともヘマトクリット値又はヘモグロビン濃度を含む血液分析値を算出する分析器としての機能をコンピュータに発揮させる血液分析装置用プログラムを用いれば良い。 For example, in order to achieve the same effect as the blood analysis device of the present invention by adding the second light receiving element to an existing blood analysis device and updating the program, a program for a blood analysis device that irradiates light onto an analysis target liquid containing at least blood in a light-transmitting tube and analyzes blood based on the light transmitted through the tube, the blood analysis device includes a light-emitting element that emits light across the tube in the radial direction, a first light-receiving element that receives the light transmitted through the tube and the analysis target liquid, and a second light-receiving element that receives light reflected or scattered by the tube or the analysis target liquid toward the light-emitting element, and the program for the blood analysis device causes a computer to function as an analyzer that calculates blood analysis values including at least a hematocrit value or a hemoglobin concentration based on the output of the first light-receiving element and the output of the second light-receiving element.
このように本発明に係る血液分析装置によれば、チューブ及び分析対象液を通過した透過光を第１受光素子で検出するとともに、前記チューブ又は分析対象液で反射又は散乱された光を前記第２受光素子で検出して、各受光素子の出力に基づいてヘマトクリット値やヘモグロビン濃度といった血液分析値を算出しているので、赤血球の凝集の程度や懸濁条件の違いがあったとしても血液分析値を正確に測定することが可能となる。 In this way, with the blood analyzer of the present invention, the first light receiving element detects the transmitted light that passes through the tube and the liquid being analyzed, and the second light receiving element detects the light reflected or scattered by the tube or the liquid being analyzed. Blood analysis values such as hematocrit value and hemoglobin concentration are calculated based on the output of each light receiving element, making it possible to accurately measure blood analysis values even if there are differences in the degree of red blood cell aggregation or suspension conditions.
本発明の第１実施形態に係る血液分析装置１００について図１乃至図４を参照しながら説明する。 The blood analysis device 100 according to the first embodiment of the present invention will be described with reference to Figures 1 to 4.
第１実施形態の血液分析装置１００は、例えば人工透析システム２００において用いられるものであって、血液循環回路の一部を構成するチューブＴに対して後付可能に構成されている。人工透析システム２００は、図１に示すように血液と透析液とが透析膜を介して接触する透析部Ｄと、透析部Ｄの入り口側と患者のアクセス血管Ａにおいて上流側とを接続する動脈側回路Ｃ１と、透析部Ｄの出口側と患者のアクセス血管Ａにおいて下流側とを接続する静脈側回路Ｃ２と、を備えている。動脈側回路Ｃ１上には血液を循環させるポンプＣ１１と、血液中の気泡を除去するための動脈側チャンバＣ１２等が設けられている。また、静脈側回路Ｃ２上にも、気泡を除去するための静脈側チャンバＣ２２が設けられている。第１実施形態では静脈側回路Ｃ２において静脈側チャンバＣ２２の出口側とアクセス血管Ａとの間を接続し、浄化された血液の流れるチューブＴに対して血液分析装置１００が別途外付けされている。 The blood analyzer 100 of the first embodiment is used in, for example, an artificial dialysis system 200, and is configured to be retrofittable to a tube T that constitutes a part of a blood circulation circuit. As shown in FIG. 1, the artificial dialysis system 200 includes a dialysis section D where blood and dialysis fluid come into contact with each other through a dialysis membrane, an arterial circuit C1 that connects the inlet side of the dialysis section D to the upstream side of the patient's access blood vessel A, and a venous circuit C2 that connects the outlet side of the dialysis section D to the downstream side of the patient's access blood vessel A. The arterial circuit C1 is provided with a pump C11 for circulating blood, an arterial chamber C12 for removing bubbles in the blood, and the like. The venous circuit C2 is also provided with a venous chamber C22 for removing bubbles. In the first embodiment, the blood analyzer 100 is separately attached externally to the tube T through which purified blood flows, which connects the outlet side of the venous chamber C22 to the access blood vessel A in the venous circuit C2.
血液分析装置１００は、チューブＴを流れる血液もしくは血液と生理食塩水等が混合した状態の分析対象液とは非接触で少なくともヘマトクリット値又はヘモグロビン濃度を含む血液分析値を測定するように構成されている。具体的には図２及び図３に示すように血液分析装置１００はチューブＴの外側から光を照射し、チューブＴ及び分析対象液を通過した光と、チューブＴ又は分析対象液で反射又は散乱された光とを検出するように構成されている。また、各検出結果に基づいてヘマトクリット値又はヘモグロビン濃度は算出される。 The blood analyzer 100 is configured to measure blood analysis values including at least the hematocrit value or hemoglobin concentration without contacting the blood flowing through the tube T or the analysis target liquid, which is a mixture of blood and physiological saline or the like. Specifically, as shown in Figures 2 and 3, the blood analyzer 100 is configured to irradiate light from the outside of the tube T and detect the light that has passed through the tube T and the analysis target liquid and the light that has been reflected or scattered by the tube T or the analysis target liquid. The hematocrit value or hemoglobin concentration is calculated based on each detection result.
より具体的には血液分析装置１００は、発光素子２、第１受光素子３１、及び、第２受光素子３２が設けられたボディ１、第１受光素子３１と第２受光素子３２の出力に基づいて血液分析値を算出する分析器４と、を備えている。 More specifically, the blood analysis device 100 includes a body 1 in which a light-emitting element 2, a first light-receiving element 31, and a second light-receiving element 32 are provided, and an analyzer 4 that calculates blood analysis values based on the outputs of the first light-receiving element 31 and the second light-receiving element 32.
発光素子２は、例えば近赤外領域の波長の光を射出するＬＥＤであって、光軸に沿って所定の分布で光を射出するものである。すなわち、発光素子２から射出される光は光軸上だけでなく、光軸に対して所定角度をなす方向に対して光線が射出されている。第１実施形態では発光素子２の光軸はチューブＴの半径方向に沿うように構成されている。 The light-emitting element 2 is, for example, an LED that emits light with a wavelength in the near-infrared region, and emits light with a predetermined distribution along the optical axis. In other words, the light emitted from the light-emitting element 2 is not only emitted on the optical axis, but also in a direction that forms a predetermined angle with respect to the optical axis. In the first embodiment, the optical axis of the light-emitting element 2 is configured to be aligned along the radial direction of the tube T.
第１受光素子３１は、チューブＴ及び分析対象液を透過した光を受光し、その強度に応じた電流又は電圧を出力するフォトダイオードである。第１実施形態では第１受光素子３１は発光素子２に対してチューブＴを挟んで対向するように設けられている。 The first light receiving element 31 is a photodiode that receives light that has passed through the tube T and the liquid to be analyzed, and outputs a current or voltage according to the intensity of the light. In the first embodiment, the first light receiving element 31 is disposed opposite the light emitting element 2 across the tube T.
第２受光素子３２は、チューブＴ又は分析対象液によって発光素子２側へと反射又は散乱された光を受講し、その強度に応じた電流又は電圧を出力するフォトダイオードである。第１実施形態では第１受光素子３１と第２受光素子３２はほぼ同じ出力特性を有するものが用いられている。また、第２受光素子３２はチューブＴを基準として発光素子２と同じ側に設けられているとともに、チューブＴの軸方向に沿って発光素子２から所定距離離隔した位置に配置されている。すなわち、第２受光素子３２については発光素子２から射出された光が直接入射しないように構成されている。 The second light receiving element 32 is a photodiode that receives light reflected or scattered by the tube T or the liquid to be analyzed toward the light emitting element 2 and outputs a current or voltage according to the intensity of the light. In the first embodiment, the first light receiving element 31 and the second light receiving element 32 have approximately the same output characteristics. The second light receiving element 32 is provided on the same side as the light emitting element 2 with respect to the tube T as a reference, and is located at a predetermined distance from the light emitting element 2 along the axial direction of the tube T. In other words, the second light receiving element 32 is configured so that the light emitted from the light emitting element 2 does not directly enter it.
ボディ１は、図２に示すように概略直方体状をなすものであって、内部に発光素子２、第１受光素子３１、第２受光素子３２が設けられる。このボディ１には軸方向でもある長手方向に沿って概略直方体状をなす凹部１２が一方の端面から他方の端面まで形成されている。さらに、この凹部１２の底面部には凹部１２と同様に長手方向に沿ってまっすぐに延びる収容溝１１が形成されており、この収容溝１１内に血液回路の一部を構成している可撓性を有するチューブＴが嵌め込まれる。この収容溝１１の横幅及び深さは例えばチューブＴの外径とほぼ同じに設定されており、収容溝１１の横幅は凹部１２の横幅よりも小さい。また、発光素子２、第１受光素子３１、及び、第２受光素子３２は、それぞれの光軸が収容溝１１の側面と交差するようにボディ１内に設けられている。また、収容溝１１の側面には、３つの窓が形成されており、発光素子２、第１受光素子３１、及び、第２受光素子３２において対象となる光が出射又は入射するようにしてある。より具体的には、収容溝１１の側面には、発光素子２から射出された光を収容溝１１内へ入射させる入射光窓Ｗ２と、入射光窓Ｗ２と対向するように設けられ、チューブＴ及び分析対象液を通過した光を収容溝１１から前記第１受光素子３１へ入射させる透過光窓Ｗ３１と、チューブＴの延伸方向（ボディ１の長手方向）に対して入射光窓Ｗ２と並べて設けれ、チューブＴ又は分析対象液で反射又は散乱された光を収容溝１１から第２受光素子３２へ入射させる反射散乱光窓Ｗ３２が形成されている。このように各窓が形成されているので、第１受光素子３１はほぼ透過光のみを検出し、第２受光素子３２は発光素子２側へ反射又は散乱された光を検出するようにできる。 2, the body 1 is generally rectangular parallelepiped-shaped, and has the light-emitting element 2, the first light-receiving element 31, and the second light-receiving element 32 inside. The body 1 has a generally rectangular parallelepiped recess 12 formed from one end face to the other end face along the longitudinal direction, which is also the axial direction. Furthermore, the bottom surface of the recess 12 has a storage groove 11 that extends straight along the longitudinal direction, similar to the recess 12, and a flexible tube T that constitutes a part of the blood circuit is fitted into the storage groove 11. The width and depth of the storage groove 11 are set to be approximately the same as the outer diameter of the tube T, for example, and the width of the storage groove 11 is smaller than the width of the recess 12. The light-emitting element 2, the first light-receiving element 31, and the second light-receiving element 32 are provided in the body 1 so that their optical axes intersect with the side surfaces of the storage groove 11. In addition, three windows are formed on the side of the storage groove 11, so that light targeted by the light emitting element 2, the first light receiving element 31, and the second light receiving element 32 can be emitted or received. More specifically, on the side of the storage groove 11, there are an incident light window W2 that allows the light emitted from the light emitting element 2 to enter the storage groove 11, a transmitted light window W31 that is provided opposite the incident light window W2 and allows the light that has passed through the tube T and the liquid to be analyzed to enter the first light receiving element 31 from the storage groove 11, and a reflected and scattered light window W32 that is provided in line with the incident light window W2 in the extension direction of the tube T (the longitudinal direction of the body 1) and allows the light reflected or scattered by the tube T or the liquid to be analyzed to enter the second light receiving element 32 from the storage groove 11. Since each window is formed in this way, the first light receiving element 31 can detect almost only transmitted light, and the second light receiving element 32 can detect light reflected or scattered toward the light emitting element 2 side.
分析器４は、ＣＰＵ、メモリ、Ａ／Ｄコンバータ、Ｄ／Ａコンバータ、各種入出力機器を備えたいわゆるコンピュータによってその機能を実現されるものである。メモリに格納されている血液分析装置１００用のプログラムが実行され、各機器が協業することによって図３に示すように第１吸光度算出部４１、第２吸光度算出部４２、換算部４３としての機能を発揮する。以下では各部について詳述する。 The analyzer 4 realizes its functions using a so-called computer equipped with a CPU, memory, A/D converter, D/A converter, and various input/output devices. A program for the blood analyzer 100 stored in the memory is executed, and the devices work together to perform the functions of a first absorbance calculation unit 41, a second absorbance calculation unit 42, and a conversion unit 43, as shown in FIG. 3. Each unit will be described in detail below.
第１吸光度算出部４１は、第１受光素子３１の出力に基づいて第１吸光度を算出する。例えば第１吸光度算出部４１は、第１受光素子３１から出力される電流値から検出されている透過光の強度を算出し、発光素子２から出射されている入射光の強度とから第１吸光度を算出する。ここで、発光素子２から出射される入射光の強度については、チューブＴ内に血液が流れていない状態で発光素子２から射出された光を第１受光素子３１で検出した場合の強度を用いてもよいし、発光素子２から出射される入射光の理論的な強度を用いてもよい。 The first absorbance calculation unit 41 calculates the first absorbance based on the output of the first light receiving element 31. For example, the first absorbance calculation unit 41 calculates the intensity of the transmitted light detected from the current value output from the first light receiving element 31, and calculates the first absorbance from the intensity of the incident light emitted from the light emitting element 2. Here, the intensity of the incident light emitted from the light emitting element 2 may be the intensity detected by the first light receiving element 31 when no blood is flowing in the tube T, or the theoretical intensity of the incident light emitted from the light emitting element 2.
第２吸光度算出部４２は、第２受光素子３２の出力に基づいて第２吸光度を算出する。例えば第２吸光度算出部４２は、第２受光素子３２から出力される電流値から検出されている発光素子２側へ反射又は散乱されている光の強度を算出し、発光素子２から出射されている入射光の強度とから第２吸光度を算出する。ここで、第２吸光度算出部４２で使用されている入射光の強度は第１吸光度算出部４１で使用されているのと同じ値が一例として挙げられる。 The second absorbance calculation unit 42 calculates the second absorbance based on the output of the second light receiving element 32. For example, the second absorbance calculation unit 42 calculates the intensity of light reflected or scattered toward the light emitting element 2 detected from the current value output from the second light receiving element 32, and calculates the second absorbance from the intensity of the incident light emitted from the light emitting element 2. Here, the intensity of the incident light used in the second absorbance calculation unit 42 is, for example, the same value as that used in the first absorbance calculation unit 41.
換算部４３は、算出された第１吸光度と第２吸光度の線形和を血液分析値に換算する。第１実施形態では例えば測定対象であるヘマトクリット値又はヘモグロビン濃度が既知の分析対象液が流れている場合の第１吸光度と第２吸光度との測定値の組み合わせが予め実験によって測定されている。複数の血液分析値に対する第１吸光度及び第２吸光度の組み合わせを実測し、それらの組に基づいて関係式が予め求められている。例えば、第１吸光度に対する重み付け係数と第２吸光度に対する重み付け係数が実験によって求められた血液分析値、第１吸光度、第２吸光度の複数の組から最小二乗法等によって決定される。換算部４３は、実験によって定められた第１吸光度及び第２吸光度を入力変数とし、血液分析値を出力変数とする関係式に測定されている第１吸光度及び第２吸光度を代入して血液分析値を出力する。なお、血液分析値として出力されたヘマトクリット値やヘモグロビン濃度はその時点の数値が外部表示されたり、時刻ととともに変化するグラフとして表示されたりしてもよい。また、人工透析システム２００内において血液回路を流れる血液の流量や流速を制御するために、ヘマトクリット値やヘモグロビン濃度を使用しても構わない。 The conversion unit 43 converts the linear sum of the calculated first absorbance and second absorbance into a blood analysis value. In the first embodiment, for example, a combination of the measured values of the first absorbance and the second absorbance when a liquid to be analyzed, whose hematocrit value or hemoglobin concentration is known, is flowing is measured in advance by an experiment. Combinations of the first absorbance and the second absorbance for a plurality of blood analysis values are actually measured, and a relational equation is determined in advance based on these combinations. For example, a weighting coefficient for the first absorbance and a weighting coefficient for the second absorbance are determined by the least squares method or the like from a plurality of combinations of the blood analysis value, the first absorbance, and the second absorbance determined by an experiment. The conversion unit 43 substitutes the measured first absorbance and second absorbance into a relational equation in which the first absorbance and the second absorbance determined by an experiment are input variables and the blood analysis value is an output variable, and outputs the blood analysis value. The hematocrit value and hemoglobin concentration output as blood analysis values may be displayed externally as numerical values at that time, or may be displayed as a graph that changes over time. The hematocrit value and hemoglobin concentration may also be used to control the flow rate and flow speed of blood flowing through the blood circuit in the artificial dialysis system 200.
次に従来のように透過光だけでヘモグロビン濃度を測定した場合と、反射又は散乱光のみでヘモグロビン濃度を測定した場合と、第１実施形態の血液分析装置１００によって透過光と反射又は散乱光に基づいてヘモグロビン濃度を測定した場合の比較結果について図４のグラフを参照しながら説明する。なお、濃度をヘモグロビン濃度の調整するために生理食塩水で希釈した場合と、血漿で希釈した場合の２通りで実測を行った。 Next, the results of a comparison of hemoglobin concentration measured using only transmitted light as in the conventional method, hemoglobin concentration measured using only reflected or scattered light, and hemoglobin concentration measured based on transmitted light and reflected or scattered light using the blood analyzer 100 of the first embodiment will be described with reference to the graph in FIG. 4. Note that actual measurements were performed in two ways: when the hemoglobin concentration was adjusted by diluting with saline, and when it was diluted with plasma.
従来のように透過光のみを用いてヘモグロビン濃度を測定すると、ヘモグロビン濃度が上昇するにしたがって、透過光の吸光度の増加量が小さくなる。特にヘモグロビン濃度が大きい領域では透過光のみの吸光度では所望の線形性を得ることは難しく、また分析対象液の個体差によって高濃度側では測定誤差が大きくなる。 When hemoglobin concentration is measured using only transmitted light as in the past, the increase in absorbance of transmitted light decreases as the hemoglobin concentration increases. In particular, in areas with high hemoglobin concentrations, it is difficult to obtain the desired linearity using absorbance from transmitted light alone, and measurement errors increase at high concentrations due to individual differences in the liquid being analyzed.
また、反射又は散乱光のみの吸光度とヘモグロビン濃度との間の関係は特に生理食塩水で希釈した場合には単調増加ではなく、大きな測定誤差が発生することにある。 In addition, the relationship between the absorbance of reflected or scattered light alone and the hemoglobin concentration is not a monotonically increasing relationship, especially when diluted with saline, which can result in large measurement errors.
一方、第１実施形態の血液分析装置１００であれば、透過光に基づいて算出される第１吸光度と反射又は散乱光に基づいて算出される第２吸光度の線形和を用いることによって、透過光のみを用いた場合よりも測定レンジ全体において測定値の個体差間のばらつきを抑えることができる。また、線形性について改善されているとともに、生理食塩水希釈であっても血漿希釈であってもそのヘモグロビン濃度に対する応答特性はほとんど変化していない。 On the other hand, with the blood analyzer 100 of the first embodiment, by using a linear sum of the first absorbance calculated based on transmitted light and the second absorbance calculated based on reflected or scattered light, it is possible to reduce the variation between individual differences in the measured values over the entire measurement range compared to when only transmitted light is used. In addition, while the linearity has been improved, the response characteristics to the hemoglobin concentration are almost unchanged whether the hemoglobin concentration is diluted with saline or plasma.
このように第１実施形態の血液分析装置１００であれば、血液の個体差や血液の希釈条件によらず、正確なヘモグロビン濃度やヘマトクリット値といった血液分析値を算出することができる。例えば、人工透析システム２００であれば、プライミング時に使用されているプライミング液による希釈状態によらず、正確な血液分析値を得ること可能となるので、血液の循環量等の制御をより患者にとって負担が少なくなるように制御することが可能となる。 In this way, the blood analyzer 100 of the first embodiment can calculate accurate blood analysis values such as hemoglobin concentration and hematocrit value regardless of individual differences in blood or blood dilution conditions. For example, the artificial dialysis system 200 can obtain accurate blood analysis values regardless of the dilution state by the priming fluid used during priming, making it possible to control the amount of blood circulation, etc., so as to reduce the burden on the patient.
また、第１実施形態の血液分析装置１００はチューブＴに対して後付可能に構成されているので、例えば既存の血液回路を構成するチューブＴに対して取り付けて、正確なヘマトクリット値やヘモグロビン濃度をシステムに対して提供し、その機能を改良するといったことも可能である。 In addition, since the blood analysis device 100 of the first embodiment is configured to be retrofitted to a tube T, it is possible to attach it to a tube T that constitutes an existing blood circuit, for example, to provide accurate hematocrit values and hemoglobin concentrations to the system and improve its functions.
さらに、ボディ１に形成された凹部１２の底面部にチューブＴが嵌め込まれる収容溝１１が形成されているので、例えばボディ１の外部から室内照明等から射出される光が迷光として第１受光素子３１や第２受光素子３２に入射するのも防ぐことができ、血液分析値における測定誤差をさらに低減できる。 In addition, a storage groove 11 into which the tube T is fitted is formed on the bottom surface of the recess 12 formed in the body 1, so that light emitted from, for example, indoor lighting outside the body 1 can be prevented from entering the first light receiving element 31 or the second light receiving element 32 as stray light, further reducing measurement errors in blood analysis values.
次に第２実施形態の血液分析装置１００について図５を参照しながら説明する。 Next, the second embodiment of the blood analysis device 100 will be described with reference to FIG. 5.
第２実施形態の血液分析装置１００は、第１実施形態と比較して分析器４の構成が異なっている。具体的には、分析器４は、第１受光素子３１の出力、及び、第２受光素子３２の出力から個別に吸光度を算出するのではなく、第１受光素子３１の出力と第２受光素子３２の出力の線形和に基づいて補正吸光度を算出する補正吸光度算出部４４と、その吸光度から血液分析値に換算する換算部４３とを備えている。 The blood analyzer 100 of the second embodiment has a different configuration of the analyzer 4 compared to the first embodiment. Specifically, the analyzer 4 does not calculate the absorbance individually from the output of the first light receiving element 31 and the output of the second light receiving element 32, but includes a corrected absorbance calculation unit 44 that calculates a corrected absorbance based on the linear sum of the output of the first light receiving element 31 and the output of the second light receiving element 32, and a conversion unit 43 that converts the absorbance into a blood analysis value.
補正吸光度算出部４４は、第１受光素子３１から出力される透過光に由来する電流値と、第２受光素子３２から出力される反射又は散乱光に由来する電流値の線形和に基づいて、透過光の強度と反射又は散乱光の強度の線形和に相当する補正強度を算出する。さらに補正吸光度算出部４４は、発光素子２から出射される入射光の強度と補正強度から補正吸光度を算出する。 The corrected absorbance calculation unit 44 calculates a corrected intensity equivalent to the linear sum of the intensity of the transmitted light and the intensity of the reflected or scattered light based on the linear sum of the current value derived from the transmitted light output from the first light receiving element 31 and the current value derived from the reflected or scattered light output from the second light receiving element 32. Furthermore, the corrected absorbance calculation unit 44 calculates the corrected absorbance from the intensity of the incident light emitted from the light emitting element 2 and the corrected intensity.
換算部４３は、補正吸光度からヘマトクリット値やヘモグロビン濃度等を含む血液分析値に換算する。ここで、補正吸光度と血液分析値との間の関係式については例えば既知の値の血液分析値を有する分析対象液を複数種類用いて実測を行った場合の値に基づいて作成すればよい。 The conversion unit 43 converts the corrected absorbance into blood analysis values including hematocrit value, hemoglobin concentration, etc. Here, the relational equation between the corrected absorbance and the blood analysis value may be created based on values obtained by performing actual measurements using multiple types of analysis target liquids having known blood analysis values.
このような第２実施形態の血液分析装置１００であっても、第１実施形態と同様に従来よりも測定誤差の小さい血液分析値を算出することが可能となる。 Even with the blood analysis device 100 of the second embodiment, it is possible to calculate blood analysis values with smaller measurement errors than in the past, just like the first embodiment.
その他の実施形態について説明する。 Other embodiments will be described.
各実施形態では第１受光素子及び第２受光素子の出力、又は、吸光度の線形和からヘマトクリット値やヘモグロビン濃度といった血液分析値が算出されていたが、例えば単純な和を用いて血液分析値が算出されるようにしてもよい。また、透過光の強度を反映した第１受光素子の出力と、反射又は散乱光の強度を反映した第２受光素子の出力とを入力変数として、出力変数である血液分析値を算出するように分析器は構成されたものであってもよい。すなわち、各実施形態において説明した算出方法に限られず、透過光の強度又はそれを反映した第１受光素子の出力、反射又は散乱光の強度又はそれを反映した第２受光素子の出力を入力変数とする様々な関係式を例えば実験的に決定して、血液分析値が算出されるように構成してもよい。また、出力として電流値を用いて吸光度を算出していたが、電圧を用いて吸光度を算出してもよい。 In each embodiment, blood analysis values such as hematocrit value and hemoglobin concentration are calculated from the linear sum of the output of the first light receiving element and the second light receiving element or the absorbance, but the blood analysis value may be calculated using, for example, a simple sum. The analyzer may be configured to calculate the blood analysis value, which is an output variable, using the output of the first light receiving element reflecting the intensity of the transmitted light and the output of the second light receiving element reflecting the intensity of the reflected or scattered light as input variables. In other words, the calculation method is not limited to those described in each embodiment, and various relational expressions using the intensity of the transmitted light or the output of the first light receiving element reflecting it, and the intensity of the reflected or scattered light or the output of the second light receiving element reflecting it as input variables may be determined experimentally, for example, to calculate the blood analysis value. The absorbance is calculated using a current value as the output, but the absorbance may be calculated using a voltage.
ボディの形状に関しても一例を示したものであり、様々な変形を行っても構わない。例えば収容溝の側面に対して発光素子、及び、各受光素子の光軸が交差するように構成されていたが、例えば各光軸が収容溝の底面に対して交差するようにしてもよい。この場合にはボディはチューブが嵌め込まれた状態の収容溝を覆うカバー体を備え、このカバー体の内部に発光素子又は第１受光素子のいずれか一方が設けられていれば良い。 The shape of the body is also shown as one example, and various modifications may be made. For example, while the optical axes of the light-emitting element and the light-receiving elements are configured to intersect with the side surface of the storage groove, the optical axes may also intersect with the bottom surface of the storage groove. In this case, the body is provided with a cover body that covers the storage groove with the tube fitted in it, and either the light-emitting element or the first light-receiving element is provided inside this cover body.
各実施形態では人工透析システムの一部を構成するために血液分析装置を用いていたが、その他の用途やシステムに本発明に係る血液分析装置を用いても構わない。例えば献血中に体外へ導出されている血液の状態をモニタリングするために献血システムを構成するチューブの一部に血液分析装置を設けても構わない。また、血液製剤の製造ラインを構成するチューブの一部に血液分析装置を設けても構わない。 In each embodiment, a blood analyzer is used to configure part of an artificial dialysis system, but the blood analyzer of the present invention may be used for other purposes or systems. For example, a blood analyzer may be provided in part of the tubes that configure a blood donation system to monitor the condition of blood being drawn out of the body during blood donation. Also, a blood analyzer may be provided in part of the tubes that configure a blood product manufacturing line.
血液分析値としてはヘマトクリット値やヘモグロビン濃度に限られず、その他の値であってもよい。例えばヘマトクリット値やヘモグロビン濃度を用いて換算可能な各種血液指標や、吸光度に関連して算出可能な血液指標を分析器が算出するように構成してもよい。 The blood analysis value is not limited to the hematocrit value or the hemoglobin concentration, but may be other values. For example, the analyzer may be configured to calculate various blood indices that can be converted using the hematocrit value or the hemoglobin concentration, or blood indices that can be calculated in relation to the absorbance.
その他、本発明の趣旨に反しない限りにおいて様々な実施形態の変形や、各実施形態の一部同士の組み合わせを行っても構わない。 In addition, various modifications of the embodiments and combinations of parts of each embodiment may be made without going against the spirit of the present invention.
２００・・・人工透析システム
１００・・・血液分析装置
１ ・・・ボディ
１１ ・・・収容溝
１２ ・・・凹部
２ ・・・発光素子
３１ ・・・第１受光素子
３２ ・・・第２受光素子
４ ・・・分析器
４１ ・・・第１吸光度算出部
４２ ・・・第２吸光度算出部
４３ ・・・換算部
４４ ・・・補正吸光度算出部
200... Artificial dialysis system 100... Blood analysis device 1... Body 11... Storage groove 12... Recess 2... Light emitting element 31... First light receiving element 32... Second light receiving element 4... Analyzer 41... First absorbance calculation unit 42... Second absorbance calculation unit 43... Conversion unit 44... Corrected absorbance calculation unit
Claims (4)
前記チューブを半径方向に対して横切るように光を射出する発光素子と、
前記チューブ及び前記分析対象液を透過した光を受光する第１受光素子と、
前記チューブ又は前記分析対象液で前記発光素子側へ反射又は散乱された光を受光する第２受光素子と、
前記チューブが嵌め込まれる収容溝を有するボディと、
前記第１受光素子の出力、及び、前記第２受光素子の出力に基づいて、少なくともヘマトクリット値又はヘモグロビン濃度を含む血液分析値を算出する分析器とを備え、
前記ボディが、
前記収容溝の一方の側面に設けられ、前記発光素子から射出された光を前記収容溝内へ入射させる入射光窓と、
前記収容溝の他方の側面において前記入射光窓と対向するように設けられ、前記チューブ及び前記分析対象液を通過した光を前記収容溝から前記第１受光素子へ入射させる透過光窓と、
前記収容溝の一方の側面において前記チューブの延伸方向に対して前記入射光窓と並べて設けられ、前記チューブ又は前記分析対象液で反射又は散乱された光を前記収容溝から前記第２受光素子へ入射させる反射散乱光窓とを具備し、
前記分析器が、
前記第１受光素子の出力に基づいて第１吸光度を算出する第１吸光度算出部と、
前記第２受光素子の出力に基づいて第２吸光度を算出する第２吸光度算出部と、
前記第１吸光度と前記第２吸光度との線形和を前記血液分析値に換算する換算部と、を具備し、
前記換算部は、前記血液分析値が既知である複数の分析対象液それぞれを予め測定して得られた、各血液分析値と第１吸光度と第２吸光度との組み合わせに基づいて定められ、前記第１吸光度に対する重み付け係数及び前記第２吸光度に対する重み付け係数を含む関係式に、前記第１吸光度算出部により得られた第１吸光度及び前記第２吸光度算出部により得られた第２吸光度を代入することにより、前記血液分析値を出力するものである、血液分析装置。 A blood analyzer that irradiates light onto an analysis target liquid containing at least blood in a light-transmitting tube and analyzes the blood based on the light transmitted through the tube, comprising:
A light emitting element that emits light in a radial direction across the tube;
a first light receiving element that receives light transmitted through the tube and the liquid to be analyzed;
a second light receiving element that receives light reflected or scattered by the tube or the liquid to be analyzed toward the light emitting element;
a body having a receiving groove into which the tube is fitted;
an analyzer that calculates a blood analysis value including at least a hematocrit value or a hemoglobin concentration based on an output of the first light receiving element and an output of the second light receiving element,
The body,
an incident light window provided on one side surface of the accommodation groove to allow light emitted from the light-emitting element to enter the accommodation groove;
a light transmission window provided on the other side surface of the storage groove so as to face the light incident window, the light transmitting window allowing the light having passed through the tube and the liquid to be analyzed to be incident from the storage groove to the first light receiving element;
a reflected/scattered light window that is arranged on one side of the storage groove in the extension direction of the tube and is arranged next to the incident light window, and that allows light reflected or scattered by the tube or the liquid to be analyzed to enter the second light receiving element from the storage groove;
The analyzer comprises:
a first absorbance calculation unit that calculates a first absorbance based on an output of the first light receiving element;
a second absorbance calculation unit that calculates a second absorbance based on an output of the second light receiving element;
a conversion unit that converts a linear sum of the first absorbance and the second absorbance into the blood analysis value,
the conversion unit outputs the blood analysis value by substituting the first absorbance obtained by the first absorbance calculation unit and the second absorbance obtained by the second absorbance calculation unit into a relational equation that is determined based on a combination of each blood analysis value, a first absorbance, and a second absorbance obtained by measuring in advance each of a plurality of analysis target liquids whose blood analysis values are known, and that includes a weighting coefficient for the first absorbance and a weighting coefficient for the second absorbance.
前記第１受光素子の出力に基づいて第１吸光度を算出し、
前記第２受光素子の出力に基づいて第２吸光度を算出し、
前記第１吸光度と前記第２吸光度との線形和を、少なくともヘマトクリット値又はヘモグロビン濃度を含む血液分析値に換算するものであり、
前記血液分析値が既知である複数の分析対象液それぞれを予め測定して得られた、各血液分析値と第１吸光度と第２吸光度との組み合わせに基づいて定められ、前記第１吸光度に対する重み付け係数及び前記第２吸光度に対する重み付け係数を含む関係式に、算出された前記第１吸光度及び前記第２吸光度を代入することにより、前記血液分析値を求める、血液分析方法。 A blood analysis method using a blood analysis device that irradiates light onto an analysis target liquid containing at least blood in a light-transmitting tube and analyzes the blood based on the light transmitted through the tube, the blood analysis device comprising: a light-emitting element that emits light so as to cross the tube in a radial direction; a first light-receiving element that receives the light that has transmitted through the tube and the analysis target liquid; a second light-receiving element that receives light reflected or scattered by the tube or the analysis target liquid toward the light-emitting element; a body having a receiving groove into which the tube is fitted; an incident light window provided on one side surface of the storage groove, which allows light emitted from the light-emitting element to enter the storage groove; a transmitted light window provided on the other side surface of the storage groove so as to face the incident light window, which allows light that has passed through the tube and the liquid to be analyzed to enter the first light-receiving element from the storage groove; and a reflected/scattered light window provided on one side surface of the storage groove, aligned with the incident light window in the extension direction of the tube, which allows light reflected or scattered by the tube or the liquid to be analyzed to enter the second light-receiving element from the storage groove ,
Calculating a first absorbance based on an output of the first light receiving element;
Calculating a second absorbance based on the output of the second light receiving element;
a linear sum of the first absorbance and the second absorbance is converted into a blood analysis value including at least a hematocrit value or a hemoglobin concentration ;
a blood analysis method in which the blood analysis value is determined based on a combination of each blood analysis value, a first absorbance, and a second absorbance obtained by previously measuring each of a plurality of analysis target liquids whose blood analysis value is known, and the blood analysis value is determined by substituting the calculated first absorbance and second absorbance into a relational equation including a weighting coefficient for the first absorbance and a weighting coefficient for the second absorbance.
前記第１受光素子の出力に基づいて第１吸光度を算出し、前記第２受光素子の出力に基づいて第２吸光度を算出し、及び、前記第１吸光度と前記第２吸光度との線形和を、少なくともヘマトクリット値又はヘモグロビン濃度を含む血液分析値に換算するものであり、前記血液分析値が既知である複数の分析対象液それぞれを予め測定して得られた、各血液分析値と第１吸光度と第２吸光度との組み合わせに基づいて定められ、前記第１吸光度に対する重み付け係数及び前記第２吸光度に対する重み付け係数を含む関係式に、算出された前記第１吸光度及び前記第２吸光度を代入することにより、前記血液分析値を求める分析器としての機能をコンピュータに発揮させる血液分析装置用プログラム。 A program used in a blood analyzer that irradiates light onto an analysis target liquid, which contains at least blood, in a light-transmitting tube and analyzes the blood based on the light transmitted through the tube, the blood analyzer including a light-emitting element that emits light across the tube in a radial direction, a first light-receiving element that receives the light transmitted through the tube and the analysis target liquid, a second light-receiving element that receives light reflected or scattered by the tube or the analysis target liquid toward the light-emitting element, and a body having a receiving groove into which the tube is fitted. a light receiving element, an incident light window provided on one side surface thereof for allowing light emitted from the light emitting element to enter the storage groove, a transmitted light window provided on the other side surface of the storage groove opposite the incident light window for allowing light that has passed through the tube and the analysis target liquid to enter the first light receiving element from the storage groove, and a reflected/scattered light window provided on one side surface of the storage groove aligned with the incident light window in the extension direction of the tube for allowing light reflected or scattered by the tube or the analysis target liquid to enter the second light receiving element from the storage groove ,
a first absorbance based on an output of the first light receiving element, a second absorbance based on an output of the second light receiving element, and a linear sum of the first absorbance and the second absorbance converted into a blood analysis value including at least a hematocrit value or a hemoglobin concentration, the blood analysis value being determined based on a combination of each blood analysis value, the first absorbance, and the second absorbance obtained by measuring each of a plurality of analysis target liquids in advance, the blood analysis value being known, and the first absorbance and the second absorbance being determined based on a weighting coefficient for the first absorbance and a weighting coefficient for the second absorbance, the blood analysis value being determined based on a combination of each blood analysis value, the first absorbance, and the second absorbance obtained in advance, the blood analysis value being known
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