JP6963793B2 - Pulmonary function test device - Google Patents

Description

The present invention relates to a respiratory function test device capable of measuring respiratory capacity.

Conventionally, as shown in Patent Document 1, a respiratory function test device has been proposed in which a piston in a cylinder moves according to the breathing of a subject and the respiratory capacity of the subject is measured based on the movement amount.

Further, in Patent Document 2, in order to calibrate the flow sensor type respiration flow rate measuring device, the fan is rotated to supply the gas to be measured to the flow sensor, and a rotation speed signal indicating the rotation speed of the fan is output. A technique using a calibration device including a fan motor is disclosed.

Japanese Unexamined Patent Publication No. 2016-106946 Japanese Patent No. 5886060

Although medical institutions require a simple calibration method using a simple calibration device, in the conventional technique, the calibration device itself is not simple and the calibration method is also complicated.

An object of the present invention is to simplify the calibration of a respiratory function testing device.

The problem is solved by the following means.

The invention of means 1 is
A respiratory function testing device (1) provided with a respiratory capacity measuring means (rolling seal type spirometer 12) capable of measuring respiratory capacity (volume).
Based on the comparative capacity (measured volume at the time of calibration) measured by the breathing capacity measuring means with the operation of the calibration pump (300) of the reference capacity (3L), the breathing capacity measured by the breathing capacity measuring means is calculated. It is a respiratory function test apparatus including a calibratorable volume calibration means (CPU 140 that calculates a volume calibration coefficient based on a measured volume at the time of calibration and a known volume of a calibration pump 300).

The invention of means 2 is
A respiratory function testing device (1) provided with a respiratory capacity measuring means (rolling seal type spirometer 12) capable of measuring respiratory capacity (volume).
Respiratory flow rate measuring means (differentiating circuit 131, amplifier 132, ADC 133b, and CPU 140, or rotary encoder and CPU 140) capable of measuring respiratory flow rate (flow), and
Calculated capacity (measured flow integrated value at the time of calibration) calculated based on the flow rate (measured flow at the time of calibration) measured by the breathing flow rate measuring means with the operation of the calibration pump (300) of the reference capacity (3 L). Based on, the flow calibration coefficient is calculated based on the flow rate calibrating means (measured flow integrated value at the time of calibration and the capacity of the known calibration pump 300) capable of calibrating the respiratory flow rate measured by the breathing flow rate measuring means. CPU140) and
It is a respiratory function test device provided with.

The invention of means 3 is
A respiratory function testing device (1) provided with a respiratory capacity measuring means (rolling seal type spirometer 12) capable of measuring respiratory capacity (volume).
Respiratory flow rate measuring means (differentiating circuit 131, amplifier 132, ADC 133b, and CPU 140, or rotary encoder and CPU 140) capable of measuring respiratory flow rate (flow), and
A capacity calibration means (capacity calibration means) capable of calibrating the respiratory capacity measured by the respiratory capacity measuring means based on the comparative capacity measured by the respiratory capacity measuring means with the operation of the reference capacity (3 L) calibration pump (300). CPU140), which calculates the volume calibration coefficient based on the measured volume at the time of calibration and the known capacity of the calibration pump 300,
Calculated capacity (measured flow integrated value at the time of calibration) calculated based on the flow rate (measured flow at the time of calibration) measured by the breathing flow rate measuring means with the operation of the calibration pump (300) of the reference capacity (3 L). Based on, the flow calibration coefficient is calculated based on the flow rate calibrating means (measured flow integrated value at the time of calibration and the capacity of the known calibration pump 300) capable of calibrating the respiratory flow rate measured by the breathing flow rate measuring means. CPU140) and
It is a respiratory function test device provided with.

The invention of means 4 is
Means 2 or 3 respiratory function testing device
The calculated capacity (measured flow integral value at the time of calibration) is a respiratory function test device calculated based on the integral of the respiratory flow rate (measured flow) measured by the respiratory flow rate measuring means.

The invention of means 5 is
A respiratory function testing device (1) provided with a respiratory capacity measuring means (rolling seal type spirometer 12) capable of measuring respiratory capacity (volume).
Respiratory flow rate measuring means (differentiating circuit 131, amplifier 132, ADC 133b, and CPU 140, or rotary encoder and CPU 140) capable of measuring respiratory flow rate (flow), and
Calculated flow rate (measured volume differential value at the time of calibration) calculated based on the capacity (measured volume at the time of calibration) measured by the breathing capacity measuring means with the operation of the calibration pump (300) of the reference capacity (3 L). Based on the above, a flow rate calibrating means capable of calibrating the respiration flow rate measured by the respiration flow rate measuring means (CPU140 that calculates a flow calibration coefficient based on a measured flow at the time of calibration and a measured volume differential value at the time of calibration).
It is a respiratory function test device provided with.

The invention of means 6 is
It is a respiratory function test device of means 5, and is
The calculated flow rate (differential value of the measured volume) is a respiratory function test device calculated based on the derivative of the respiratory capacity (measured volume at the time of calibration) measured by the respiratory capacity measuring means.

The invention of means 7 is
Any respiratory function testing device selected from means 2-6.
The respiratory flow measuring means (differentiating circuit 131, amplifier 132, ADC 133b, and CPU 140) is set to the moving distance of the moving unit (piston 123) according to the breathing of the subject (moving distance of the piston 123 detected by the potentiometer 125). It is a respiratory function test device that can measure the respiratory flow rate (actual measurement flow) based on the above.

The invention of means 8 is
It is a respiratory function test device of means 7, and is
The respiratory flow measuring means (differentiating circuit 131, amplifier 132, ADC 133b, and CPU 140) includes a differentiating circuit (131) in which a signal corresponding to the moving distance of the moving unit (piston 123) is input. It is a device.

The invention of means 9 is
Any respiratory function testing device selected from means 2-8.
The respiration flow rate measuring means (rotary encoder and CPU 140) has a pulse interval (pulse interval) output from the rotary encoder if the moving speed of the moving portion according to the breathing of the subject (if the moving speed of the piston 123 in the central axis direction is slow). If the output cycle) is long and the moving speed of the piston 123 in the central axis direction is fast, the respiratory flow rate (actual measurement flow) is measured based on the pulse interval (pulse output cycle) output from the rotary encoder. It is a possible respiratory function tester.

The invention of means 10
Any respiratory function testing device selected from means 1-9.
The respiratory capacity measuring means (rolling seal type spirometer 12) has a respiratory capacity (actual measurement) based on the moving distance of the moving portion (piston 123) according to the breathing of the subject (moving distance of the piston 123 detected by the potentiometer 125). It is a respiratory function test device that can measure volume).

The invention of means 11 is
Any respiratory function testing device selected from means 1-10.
A first respiratory path (X1) in which a storage case (5) containing an absorbent that absorbs carbon dioxide gas contained in the subject's exhaled breath is installed.
Including a second breathing path (X2) in which the storage case is not installed,
The calibration pump can be connected to the second breathing path.
It is a respiratory function test device.

The invention of means 12 is
It is a respiratory function test device of means 11, and is
A connection notification means (display 14) for notifying the connection of the calibration pump to the second breathing path (X2) is provided.
It is a respiratory function test device.

The invention of means 13 is
Any respiratory function testing device selected from means 1-12.
The calibration pump (300) manually moves the operating portion (grip portion 332) in the first direction (forward (pushing direction)) to obtain a volume of air (3L) corresponding to the moving distance of the operating portion. Can be supplied to the respiratory function test device (cylinder chamber 211).
A first movement notification means (display 14) for notifying a first speed (how many seconds the rod 330 is pushed from the 0L position to the 3L position) for moving the operation unit in the first direction is provided.
It is a respiratory function test device.

The invention of means 14
It is a respiratory function test device of means 13, and is
The first movement notification means (display 14) makes the first speed (the speed at which the rod 330 is pushed from the 0L position to the 3L position) different, and presses the operation unit a plurality of times (for example, 5 times). Notify to move in one direction,
It is a respiratory function test device.

The invention of means 15
Any respiratory function testing device selected from means 1-14.
The calibration pump (300) manually moves the operating portion (grip portion 332) in the second direction (rearward (pulling direction)) to obtain a volume of air (3L) corresponding to the moving distance of the operating portion. Can be discharged from the respiratory function test device (cylinder chamber 211).
A second movement notification means (display 14) for notifying a second speed (how many seconds the rod 330 is pulled from the 3L position to the 0L position) for moving the operation unit in the second direction is provided.
It is a respiratory function test device.

The invention of means 16
The respiratory function test device of means 15.
The second movement notification means (display 14) performs the operation unit a plurality of times (for example, 5 times) by varying the second speed (the speed at which the rod 330 is pulled from the 3L position to the 0L position). Notify to move in two directions,
It is a respiratory function test device.

The invention of means 17 is
Any respiratory function testing device selected from means 1-16.
A calibration coefficient storage means (ROM) for storing the calibration coefficient (volume calibration coefficient calculated by the CPU 140, flow calibration coefficient calculated by the CPU 140), and
Calibration coefficient display means (display 14) for displaying the time transition of the calibration coefficient (time transition graph of the volume calibration coefficient, transition graph of the flow calibration coefficient), and
To prepare
It is a respiratory function test device.

According to the present invention, it becomes possible to simplify the calibration of the respiratory function test device.

1A and 1B show the appearance of the respiratory function test apparatus of the present embodiment, where FIG. 1A is a front view and FIG. 1B is a plan view. FIG. 2 is a perspective view showing a state in which the opening / closing door of the respiratory function testing device of FIG. 1 is opened. FIG. 3 is an explanatory diagram showing the configuration of a rolling seal type spirometer. FIG. 4 is an explanatory diagram showing a configuration for measuring volume and flow. 5A and 5B are side views of the calibration pump, FIG. 5A is a view showing a state in which the rod is extended to the maximum with respect to the main body, and FIG. 5B is a view showing a state in which the rod is maximally contracted with respect to the main body. It is a figure which shows the state. FIG. 6 is an explanatory diagram showing the relationship between the operation of the calibration pump and the flow volume curve at the time of volume calibration. FIG. 7 is a flowchart showing an example of guide information displayed on the display when performing volume calibration. FIG. 8 is an explanatory diagram showing an example of determining the volume calibration coefficient based on a plurality of flow volume curves. FIG. 9 is an explanatory diagram showing the relationship between the operation of the calibration pump and the flow volume curve during flow calibration. FIG. 10 is a flowchart showing an example of guide information displayed on the display when performing flow calibration. FIG. 11 is an explanatory diagram showing an example of determining a flow calibration coefficient based on a plurality of flow volume curves. FIG. 12 is an explanatory diagram showing a comparative example of the flow volume curve before the flow calibration and the flow volume curve after the flow calibration. FIG. 13 is an explanatory diagram showing a comparative example of a flow volume curve based on the measured flow and a flow volume curve based on the measured volume differential value.

Hereinafter, the respiratory function test apparatus of this embodiment will be described with reference to the drawings. FIG. 1 shows the appearance of the respiratory function test apparatus of the present embodiment, (a) is a front view, and (b) is a plan view of (a). FIG. 2 is a perspective view showing a state in which the opening / closing door of the respiratory function testing device of FIG. 1 is opened. As shown in FIGS. 1 and 2, the respiratory function test device 1 of the present invention is composed of a main body 11 which is a housing, a rolling seal type spirometer 12 built in the main body 11, and the like. A keyboard 13, a display 14, a printer 15, and a mouse 16 are placed on the upper surface of the main body 11, and a control unit (not shown) is provided inside the main body 11. An opening / closing door 17 is attached to the left side surface of the main body 11 so as to be openable / closable by a hinge, and the opening / closing door 17 is closed to shield the rolling seal type spirometer 12.

As shown in FIG. 1, a recess 18 long in the vertical direction is formed on the side surface of the opening / closing door 17, and a storage case 5 containing an absorbent that absorbs carbon dioxide gas is detachably attached to the recess 18. .. Further, as shown in FIGS. 1 and 3, the outer wall 17b of the opening / closing door 17 is provided with an intake tube connection port 38b, an exhalation tube connection port 39b, and a breathing tube connection port 40b at positions facing the recess 18. Has been done. Further, as shown in FIG. 2, the inner wall 17a of the opening / closing door 17 is provided with an intake port 38a, an exhalation port 39a, and a breathing air port 40a, respectively.

FIG. 3 is an explanatory diagram showing a schematic structure around a rolling seal type spirometer 12 of the respiratory function test device 1 of the present embodiment. As shown in FIG. 3, the rolling seal type spirometer 12 includes a cylindrical cylinder 121 and a piston 123 supported by a slide bearing 122 for bearings, and a silicon rolling between the cylinder 121 and the piston 123 is provided. It is sealed with a seal 124. One end of the rolling seal 124 is joined to the inner wall surface of the cylinder 121, and the other end is joined to the side surface of the piston 123. By bending the rolling seal 124 in accordance with the movement of the piston 123, the closed state of the gap between the cylinder 121 and the piston 123 is maintained. When the piston 123 moves, the potentiometer 125 detects the moving distance of the central axis 126 of the piston 123 in the axial direction.

As shown in FIGS. 2 and 3, a silicon cushion member 212 is joined to the wall surface around the opening of the cylinder 121, and the opening of the cylinder 121 is surrounded by the annular cushion member 212. It has become. As shown in FIG. 3, when the opening / closing door 17 is closed, the cushion member 212 is deformed in contact with the inner wall 17a of the opening / closing door 17 to alleviate the impact when the opening / closing door 17 is closed. Further, the cushion member 212 fills the gap between the inner wall 17a of the opening / closing door 17 and the wall surface around the opening of the cylinder 121 by being in close contact with the inner wall 17a of the opening / closing door 17. As a result, the cylinder chamber 211 in the cylinder 121 is sealed by the inner wall 17a of the opening / closing door 17 and the cushion member 212. When the subject inhales, the gas in the cylinder chamber 211 is supplied to the subject (the subject inhales the gas in the cylinder chamber 211), and when the subject exhales, the subject's exhaled air is discharged to the cylinder chamber 211. That is, the cylinder chamber 211 when the opening / closing door 17 is closed functions as a breathing space for the subject.

As shown in FIG. 3, the inner wall 17a of the opening / closing door 17 is provided with an intake port 38a and an exhalation port 39a. Further, the outer wall 17b of the opening / closing door 17 is provided with an intake tube connection port 38b and an exhalation tube connection port 39b.

One end of the rubber tube 73C is connected to the intake port 38a, and the other end of the rubber tube 73C is connected to the intake tube connection port 38b. That is, the rubber tube 73C forms an intake path that connects the intake port 38a to the intake tube connection port 38b for passing the intake air from the cylinder chamber 211 to the outside of the main body.

Further, one end of the rubber tube 73A is connected to the exhalation port 39a, and the other end of the rubber tube 73A is connected to the exhalation outlet 5A of the storage case 5 attached to the recess 18. Further, one end of the rubber tube 73B is connected to the exhalation inlet 5B of the storage case 5, and the other end of the rubber tube 73B is connected to the exhalation tube connection port 39b. In this way, when the storage case 5 is connected to the recess 18, the exhalation port 39a and the exhalation tube connection port 39b are fluidly connected via the storage case 5 (carbon dioxide gas absorber in the storage case 5). Will be connected. That is, the rubber tubes 73A and 73B, and the storage case 5 connected to these, form an exhalation path connecting the exhalation tube connection port 39b to the exhalation port 39a for passing the exhalation from the outside of the main body to the cylinder chamber 211. There is.

A mouthpiece (MP) is connected to a breathing tube 80 branched into an inspiratory tube 81 through which the subject's inspiration passes and an expiratory tube 82 through which the subject's exhaled air passes via a three-way valve 85 provided at a branch. One end of the intake pipe 81 is connected to the intake tube connection port 38b, and the other end of the intake pipe 81 is fluidly connected to the intake valve (not shown) of the three-way valve 85. Further, one end of the exhalation tube 82 is connected to the exhalation tube connection port 39b, and the other end of the exhalation tube 82 is fluidly connected to the exhalation valve (not shown) of the three-way valve 85.

When the subject inhales through the mouthpiece connected to the breathing tube 80, the intake valve of the three-way valve 85 is opened, the piston 123 moves toward the front (opening direction), and the capacity of the cylinder chamber 211 (breathing). As the volume of the space decreases), the gas in the cylinder chamber 211 flows out from the intake port 38a, passes through the rubber tube 73C and the intake pipe 81, and is supplied to the subject. When the potentiometer 125 detects the moving distance of the piston 123 at this time, the intake air amount is converted into an electric signal.

When the subject exhales through the mouthpiece connected to the breathing tube 80, the exhalation valve of the three-way valve 85 is opened, the subject's exhalation passes through the exhalation tube 82, and passes through the rubber tube 73B from the exhalation tube connection port 39b. Then, when it reaches the storage case 5 and passes through the storage case 5, carbon dioxide gas is absorbed by the absorbent, further passes through the rubber tube 73A, and is discharged from the exhalation port 39a to the cylinder chamber 211. Along with this, the piston 123 moves in the back direction (direction opposite to the opening), and the capacity (volume of the breathing space) of the cylinder chamber 211 increases. When the potentiometer 125 detects the moving distance of the piston 123 at this time, the expiratory amount is converted into an electric signal.

As described above, the rubber tube 73C that fluidly connects the intake port 38a and the intake tube connection port 38b, and the rubber tube 73A that fluidly connects the exhalation port 39a and the storage case 5, the storage case 5, and the storage. The respiratory path including the rubber tube 73B that fluidly connects the case 5 and the expiratory tube connection port 39b is referred to as a respiratory path X1.

For example, when measuring functional resident capacity (FRC), minute volume (MV), and basal metabolic rate (BMR), respiratory pathway X1 is used. .. Respiratory pathway X1 is also used when measuring vital capacity (VC), forced vital capacity (FVC), and minute ventilation (MV) while supplying high-concentration oxygen to the cylinder chamber 211. To use.

Further, as shown in FIG. 3, a breathing air port 40a is provided on the inner wall 17a of the opening / closing door 17. Further, a breathing tube connection port 40b is provided on the outer wall 17b of the opening / closing door 17. One end of the rubber tube 74 is connected to the breathing air port 40a via a two-way valve 75, and the other end of the rubber tube 74 is connected to the breathing tube connection port 40b. That is, the rubber tube 74 allows the intake air to pass from the cylinder chamber 211 to the outside of the main body, forms an intake path connecting the breathing air port 40a to the breathing tube connection port 40b, and allows the exhaled air to pass from the outside of the main body to the cylinder chamber 211. For this purpose, an expiratory path connecting the breathing tube connection port 40b to the breathing air port 40a is formed.

One end of the breathing tube 90 is connected to the breathing tube connection port 40b, and a mouthpiece (MP) is connected to the other end of the breathing tube 90. When the subject inhales through the mouthpiece connected to the breathing tube 90, the intake valve of the two-way valve 75 is opened, the piston 123 moves toward the front (opening direction), and the capacity of the cylinder chamber 211 (the capacity of the cylinder chamber 211 (opening direction)). As the volume of the breathing space decreases), the gas in the cylinder chamber 211 flows out from the breathing air opening 40a, passes through the rubber tube 74 and the breathing tube 90, and is supplied to the subject. When the potentiometer 125 detects the moving distance of the piston 123 at this time, the intake air amount is converted into an electric signal.

When the subject exhales through the mouthpiece connected to the breathing tube 90, the exhalation valve of the two-way valve 75 is opened, the subject's exhaled air passes through the breathing tube 90, and further, the rubber tube 74 from the breathing tube connection port 40b. Is discharged from the breathing air port 40a to the cylinder chamber 211. Along with this, the piston 123 moves in the back direction (direction opposite to the opening), and the capacity (volume of the breathing space) of the cylinder chamber 211 increases. When the potentiometer 125 detects the moving distance of the piston 123 at this time, the expiratory amount is converted into an electric signal.

As described above, the respiratory path including the rubber tube 74 that fluidly connects the breathing air port 40a and the breathing tube connecting port 40b is referred to as a respiratory path X2. For example, when measuring the vital capacity (VC), forced vital capacity (FVC), and maximum ventilation volume (MVV) in a normal state where high-concentration oxygen is not supplied to the cylinder chamber 211, the respiratory pathway X2 is used. The respiratory path X2 is also used when calibrating the volume or flow using the calibration pump 300 described later.

Next, the method of measuring the volume and the flow in the present embodiment will be described with reference to FIG. As described above, when the potentiometer 125 detects the moving distance of the piston 123 in the central axis direction, a signal corresponding to the detected moving distance is output and amplified by the amplifier 130. The signal amplified by the amplifier 130 is converted from an analog signal to a digital signal by the A / D converter 133a (hereinafter referred to as ADC 133a), and then read by the CPU 140. The signal output from the ADC 133a in this way (the signal corresponding to the moving distance in the central axis direction of the piston 123) is referred to as a volume output.

Further, the DC component of the signal amplified by the amplifier 130 is cut by the differentiating circuit 131, and the signal is amplified by the amplifier 132. The signal amplified by the amplifier 132 is converted from an analog signal to a digital signal by the A / D converter 133b (hereinafter referred to as ADC 133b) and read by the CPU 140. The signal output from the ADC 133b in this way (the signal corresponding to the time change of the moving distance of the piston 123 in the central axis direction) is referred to as a flow output.

The CPU 140 is connected to a RAM, a ROM, a display control unit, etc. (not shown), reads a measurement program stored in the ROM into the RAM, executes the measurement program, calculates a volume and a flow, and further calculates the volume and the flow. Calculate the value for each measurement item based on the calculation result of. These volumes, flows, and values related to each measurement item can be displayed on the display 14 by the display control unit, and printed out by the printer 15 so that doctors, inspection technicians, and the like can check them.

For example, the CPU 140 can calculate the volume (L) based on the volume output and the known diameter (area of a circle) of the piston 123. The volume measured based on the volume output in this way is also referred to as an actually measured volume. Further, the CPU 140 can calculate the flow (L / sec) based on the time average of the flow output in a predetermined period (for example, 1 second) and the known diameter (area of a circle) of the piston 123. The flow measured based on the flow output in this way is also referred to as an actual measurement flow. As described above, the measured volume is a measured value based on the output signal (volume output) from the potentiometer 125, and the measured flow is a measured value based on the output signal (flow output) from the potentiometer 125 and the differentiating circuit 131.

(Calibration pump 300)
In this way, the piston 123, which is a moving portion, moves according to the respiration of the subject, and the measured volume and the measured flow can be measured based on the amount of movement at that time. With respect to the actually measured volume and the actually measured flow measured in this way, more accurate values can be obtained by calibration using the calibration pump 300 shown in FIG.

FIG. 5 is a diagram showing the appearance of the calibration pump 300. The calibration pump 300 is composed of a cylindrical main body 310 and an elongated rod-shaped rod 330. The front surface 310a of the main body 310 is provided with a substantially cylindrical connecting portion 320 for connecting the above-mentioned breathing tube 90 (breathing tube connection port 40b) and the main body 310. An air hole 321 that communicates with the space inside the main body 310 is formed at the tip of the connecting portion 320.

Further, to the lower part of the main body 310, the legs 311, 311 are joined to the front side, and the legs 312 are joined to the rear side. The hemispherical legs 311, 311, and 312 are all made of an elastic material such as silicone rubber. The legs 311, 311 are provided at positions facing each other about the lower end of the cylinder (the lowest point in the circular cross section) of the main body 310. The leg portion 312 is provided at the lower end of the cylinder (the lowest point in the circular cross section) of the main body portion 310. Therefore, when the main body 310 is placed on a flat place, the main body 310 is supported by the three points of the legs 311, 311 and the legs 312.

An insertion hole for inserting the rod 330 is formed in the center of the rear surface 310b of the main body 310, and the rod 330 is slid in a state where the wall surface of the insertion hole and the outer peripheral surface of the rod 330 are in contact with each other. It is possible to make it. One end side (front side) of the rod 330 is fixed to the rubber stopper in the main body 310, and the grip portion 332 is joined to the other end side (rear surface side) of the rod 330. Further, a scale is indicated every 0.5 L from 0 L to 3.0 L in the longitudinal direction of the rod 330 (axial direction of the main body 310), and the flange 331 is fixed at the position of 3.0 L.

The front surface 310a and the rear surface 310b of the main body 310 are provided with strap fixing portions 313 and 314 for fixing through the strap 315, respectively. By fixing one end side of the strap 315 to the strap fixing portion 313 and fixing the other end side to the strap fixing portion 314, the calibration pump 300 can be easily held by holding the strap 315 instead of the cylindrical main body 310 which is difficult to hold. Can be moved.

The example of FIG. 5A shows a state in which the rod 330 is most extended with respect to the main body 310 (a state in which the rubber stopper (not shown) in the main body 310 can no longer move to the rear surface 310b side). .. In this state, since the scale of "0L" written on the outer circumference of the rod 330 is visible, the air inside the main body 310 is not supplied to the outside (cylinder chamber 211) at all, and more than this. Is in a state where external air cannot be sucked into the main body 310.

From the state of FIG. 5A, when the grip portion 332 is grasped and the rod 330 is pushed forward and the flange 331 is brought into contact with the rear surface 310b, the rod 330 cannot be pushed any further (rubber in the main body 310). The stopper (not shown) is in a state where it cannot be moved to the front surface 310a side any more). At this time, as shown in FIG. 5 (b), only the scale of "3.0 L" indicated on the outer circumference of the rod 330 is visible, and 3.0 L from the state shown in FIG. 5 (a). This means that air has been supplied to the outside (cylinder chamber 211).

Further, from the state of FIG. 5 (b), when the grip portion 332 is grasped and the rod 330 is pulled rearward to return to the state of FIG. 5 (a), the scale of "0L" written on the outer circumference of the rod 330 is displayed again. Is visible. At this time, 3.0 L of air is sucked from the outside (cylinder chamber 211) from the state shown in FIG. 5 (b).

(Volume calibration)
Next, a method of calibrating the volume measured by the respiratory function test device 1 including the rolling seal type spirometer 12 will be described using the calibration pump 300 shown in FIG. First, as shown in FIG. 6 (1), the inspector connects the connection portion 320 of the calibration pump 300 to the other end of the breathing tube 90. At this time, the rod 330 is set to the maximum extended state (the state where the scale of "0L" is seen). Further, the CPU 140 displays a graph on the display 14 in which the horizontal axis is the actual measurement volume and the vertical axis is the actual measurement flow.

Then, as shown in FIG. 6 (2), the inspector pushes the rod 330 forward. At this time, the CPU 140 displays the measured flow and the flow volume curve based on the measured volume on the graph. At this stage, as the measured volume increases, the measured flow also increases in the positive direction (expiratory direction). Next, as shown in FIG. 6 (3), the rod 330 is pushed to the maximum (the flange 331 is in contact with the rear surface 310b, and only the scale of "3.0L" is visible). When this happens, the increase in the measured volume stops and the measured flow becomes 0 L / s. The CPU 140 stores the final value of the measured volume at this time in the RAM as the measured volume (exhalation) at the time of calibration.

The inspector then pulls the rod 330 backwards, as shown in FIG. 6 (4). At this time, the CPU 140 displays the measured flow and the flow volume curve based on the measured volume on the graph. At this stage, as the measured volume increases, the measured flow also increases in the negative direction (intake direction). Next, as shown in FIG. 6 (5), when the rod 330 is set to the maximum extended state (the state where the scale of "0L" is seen), the increase in the measured volume stops and the measured flow is 0L. It becomes / s. The CPU 140 stores the final value of the measured volume at this time in the RAM as the measured volume (intake) at the time of calibration.

The CPU 140 calculates the volume calibration coefficient based on the known capacity (3.0 L) of the calibration pump 300 and the measured volume (exhalation and inspiration) at the time of calibration which is the comparison data. Specifically, the volume calibration coefficient is calculated based on [3.0 (L) ÷ average value of comparison data]. Then, in the subsequent respiratory function test, [measured measured volume × volume calibration coefficient] is stored as the calibrated volume and displayed on the display 14.

In this way, when the volume is calibrated using the calibration pump 300, the speeds at which the rods 330 are operated (flows to be generated) are different, flow volume curves related to a plurality of actually measured flows are acquired, and they are obtained. It is preferable to calibrate the volume based on a plurality of flow volume curves. In the example shown below, 5 sets of ± 0.5 L / s, ± 1.0 L / s, ± 1.5 L / s, ± 3.0 L / s, and ± 6.0 L / s (10 ways in total). The flow volume curve for the flow of is obtained and the volume is calibrated.

In the present embodiment, the CPU 140 is an operation for the inspector to perform volume calibration on an input device such as the keyboard 13 or the mouse 16 (for example, the mouse pointer is placed on the icon displayed as "volume calibration" and clicked. Execute the volume calibration program based on what you have done.

When the volume calibration program is executed, the message "Volume calibration is performed. Connect the 3L calibration pump to the respiratory path X2." Is displayed on the display 14, as shown in S100 of FIG. At this time, an image showing how the connection portion 320 of the calibration pump 300 is connected to the breathing tube 90 may be displayed on the display 14 together with the image of the breathing path X2. With such a display, the tester can easily grasp the respiratory path (and the connection point) to which the calibration pump 300 should be connected, and appropriately connect the respiratory function test device 1 and the calibration pump 300. Can be done.

Then, as shown in S111, the message "Push the rod of the calibration pump for 6 seconds" is displayed on the display 14. That is, an operation for generating a flow corresponding to an exhaled breath of 0.5 L / s (flow of + 0.5 L / s) is instructed. When the inspector pushes the rod 330 from the 0L position to the 3L position according to the instructed speed, the measured volume (expiration 1) at the time of calibration is stored as comparison data.

Then, as shown in S112, the message "Pull the rod of the calibration pump over 6 seconds" is displayed on the display 14. That is, an operation for generating a flow corresponding to an intake of 0.5 L / s (flow of −0.5 L / s) is instructed. When the inspector pulls the rod 330 from the position of 3L to the position of 0L according to the instructed speed, the measured volume (intake 1) at the time of calibration is stored as comparison data. Further, as shown in FIG. 8, the first set of flow volume curves 1 is acquired and displayed on the display 14 according to the operation of the calibration pump 300.

Then, as shown in S121, the message "Push the rod of the calibration pump for 3 seconds" is displayed on the display 14. That is, an operation for generating a flow corresponding to a breath of 1.0 L / s (flow of + 1.0 L / s) is instructed. When the inspector pushes the rod 330 from the 0L position to the 3L position according to the instructed speed, the measured volume (exhalation 2) at the time of calibration is stored as comparison data.

Then, as shown in S122, the message "Pull the rod of the calibration pump over 3 seconds" is displayed on the display 14. That is, an operation for generating a flow corresponding to an intake of 1.0 L / s (flow of −1.0 L / s) is instructed. When the inspector pulls the rod 330 from the position of 3L to the position of 0L according to the instructed speed, the measured volume (intake 2) at the time of calibration is stored as comparison data. Further, as shown in FIG. 8, the second set of flow volume curves 2 is acquired and displayed on the display 14 according to the operation of the calibration pump 300.

Then, as shown in S131, the message "Push the rod of the calibration pump for 2 seconds." Is displayed on the display 14. That is, an operation for generating a flow corresponding to an exhaled breath of 1.5 L / s (a flow of + 1.5 L / s) is instructed. When the inspector pushes the rod 330 from the 0L position to the 3L position according to the instructed speed, the measured volume (exhalation 3) at the time of calibration is stored as comparison data.

Then, as shown in S132, the message "Pull the rod of the calibration pump over 2 seconds" is displayed on the display 14. That is, an operation for generating a flow corresponding to an intake of 1.5 L / s (flow of −1.5 L / s) is instructed. When the inspector pulls the rod 330 from the position of 3L to the position of 0L according to the instructed speed, the measured volume (intake 3) at the time of calibration is stored as comparison data. Further, as shown in FIG. 8, the third set of flow volume curves 3 is acquired and displayed on the display 14 according to the operation of the calibration pump 300.

Then, as shown in S141, the message "Push the rod of the calibration pump for 1 second." Is displayed on the display 14. That is, an operation for generating a flow corresponding to a breath of 3.0 L / s (flow of + 3.0 L / s) is instructed. When the inspector pushes the rod 330 from the 0L position to the 3L position according to the instructed speed, the measured volume (exhalation 4) at the time of calibration is stored as comparison data.

Then, as shown in S142, the message "Pull the rod of the calibration pump over 1 second." Is displayed on the display 14. That is, an operation for generating a flow corresponding to an intake of 3.0 L / s (flow of −3.0 L / s) is instructed. When the inspector pulls the rod 330 from the position of 3L to the position of 0L according to the instructed speed, the measured volume (intake 4) at the time of calibration is stored as comparison data. Further, as shown in FIG. 8, the fourth set of flow volume curves 4 is acquired and displayed on the display 14 according to the operation of the calibration pump 300.

Then, as shown in S151, the message "Push the rod of the calibration pump for 0.5 seconds" is displayed on the display 14. That is, an operation for generating a flow corresponding to a breath of 6.0 L / s (flow of + 6.0 L / s) is instructed. When the inspector pushes the rod 330 from the 0L position to the 3L position according to the instructed speed, the measured volume (exhalation 5) at the time of calibration is stored as comparison data.

Then, as shown in S152, the message "Pull the rod of the calibration pump over 0.5 seconds" is displayed on the display 14. That is, an operation for generating a flow corresponding to an intake of 6.0 L / s (flow of −6.0 L / s) is instructed. When the inspector pulls the rod 330 from the position of 3L to the position of 0L according to the instructed speed, the measured volume (intake 5) at the time of calibration is stored as comparison data. Further, as shown in FIG. 8, the fifth set of flow volume curves 5 is acquired and displayed on the display 14 according to the operation of the calibration pump 300.

In this way, comparison data of 5 sets (10 in total) of the measured volume at the time of calibration (intake 1 to 5) and the measured volume at the time of calibration (exhalation 1 to exhalation 5) are acquired. The CPU 140 determines the volume calibration coefficient based on the average value of these comparative data and the known capacity (3.0 L) of the calibration pump 300. As shown in FIG. 8, in this example, since [3.0 (L) ÷ average value of comparison data] is 0.983, the volume calibration coefficient is determined to be 0.983. Then, in the subsequent respiratory function test, [measured measured volume × 0.983] is stored as the calibrated volume and displayed on the display 14.

When the volume calibration coefficient is determined as described above, the message "volume calibration is completed" is displayed on the display 14 as shown in S160.

In this way, volume calibration is possible by connecting the calibration pump 300 to the respiratory path X2 of the respiratory function test device 1 and operating the volume calibration, and the volume calibration is realized by a simple device and a simple procedure. .. Further, by providing a function for guiding the operation procedure of the calibration pump 300, it is possible to have the inspector perform an appropriate operation and perform accurate volume calibration.

In the example of FIG. 8, the inspiration and the inspiration are based on a total of 10 comparative data of the actually measured volume at the time of calibration for inspiration (inspiration 1 to intake 5) and the measured volume at the time of calibration for exhalation (expiration 1 to exhalation 5). Although the common (one) volume calibration coefficient is determined for exhalation, the volume calibration coefficient for inspiration and the volume calibration coefficient for exhalation may be determined separately. Specifically, the volume calibration coefficient for intake is determined by [3.0 (L) ÷ average value of comparison data] using only the actually measured volume (intake 1 to intake 5) at the time of calibration for intake as comparison data. Further, the volume calibration coefficient for exhalation is determined by [3.0 (L) ÷ average value of comparison data] using only the actually measured volume (exhalation 1 to exhalation 5) at the time of calibration for exhalation as comparison data.

(Flow calibration)
Next, a method of calibrating the flow measured by the respiratory function test device 1 including the rolling seal type spirometer 12 will be described using the calibration pump 300 shown in FIG. First, as shown in FIG. 9 (1), the inspector connects the connection portion 320 of the calibration pump 300 to the other end of the breathing tube 90. At this time, the rod 330 is set to the maximum extended state (the state where the scale of "0L" is seen). Further, the CPU 140 displays a graph on the display 14 in which the horizontal axis is the integrated value of the measured flow and the vertical axis is the measured flow.

Then, as shown in FIG. 9 (2), the inspector pushes the rod 330 forward. At this time, the CPU 140 displays the measured flow and the flow volume curve based on the integrated value of the measured flow on the graph. At this stage, as the measured flow increases in the positive direction (expiratory direction), the integrated value of the measured flow also increases. Next, as shown in FIG. 9 (3), the rod 330 is pushed to the maximum (the flange 331 is in contact with the rear surface 310b, and only the scale of "3.0L" is visible). At that time, as the measured flow becomes 0 L / s, the increase in the integrated value of the measured flow stops. The CPU 140 stores the final value of the integrated value of the measured flow at this time in the RAM as the measured flow integrated value (exhalation) at the time of calibration.

The inspector then pulls the rod 330 backwards, as shown in FIG. 9 (4). At this time, the CPU 140 displays the measured flow and the flow volume curve based on the integrated value of the measured flow on the graph. At this stage, as the measured flow increases in the negative direction (intake direction), the integrated value of the measured flow also increases. Next, as shown in FIG. 9 (5), when the rod 330 is in the fully extended state (the state in which the scale of "0L" is seen), the actual measurement flow becomes 0 L / s, and the actual measurement is performed. The increase in the integral value of the flow stops. The CPU 140 stores the final value of the integrated value of the measured flow at this time in the RAM as the measured flow integrated value (intake) at the time of calibration.

The CPU 140 calculates the flow calibration coefficient based on the known capacity (3.0 L) of the calibration pump 300 and the measured flow integral values (exhalation and inspiration) at the time of calibration, which are comparative data. Specifically, the flow calibration coefficient is calculated based on [3.0 (L) ÷ average value of comparison data]. Then, in the subsequent respiratory function test, [measured measured flow × flow calibration coefficient] is stored as the flow after calibration and displayed on the display 14.

In this way, when the flow is calibrated using the calibration pump 300, the speeds at which the rods 330 are operated (flows to be generated) are different, and flow volume curves related to a plurality of actually measured flows are acquired and used. It is preferable to calibrate the flow based on a plurality of flow volume curves. In the example shown below, 5 sets of ± 0.5 L / s, ± 1.0 L / s, ± 1.5 L / s, ± 3.0 L / s, and ± 6.0 L / s (10 ways in total). The flow volume curve for the flow of is obtained and the flow is calibrated.

In the present embodiment, the CPU 140 is an operation for the inspector to perform flow calibration in an input device such as the keyboard 13 or the mouse 16 (for example, the mouse pointer is placed on the icon displayed as "flow calibration" and clicked. Run the flow calibration program based on what you have done.

When the flow calibration program is executed, the message "Perform flow calibration. Connect the 3L calibration pump to the respiratory path X2." Is displayed on the display 14, as shown in S200 of FIG. At this time, an image showing how the connection portion 320 of the calibration pump 300 is connected to the breathing tube 90 may be displayed on the display 14 together with the image of the breathing path X2. With such a display, the tester can easily grasp the respiratory path (and the connection point) to which the calibration pump 300 should be connected, and appropriately connect the respiratory function test device 1 and the calibration pump 300. Can be done.

Then, as shown in S211 the message "Push the rod of the calibration pump for 6 seconds" is displayed on the display 14. That is, an operation for generating a flow corresponding to an exhaled breath of 0.5 L / s (flow of + 0.5 L / s) is instructed. When the inspector pushes the rod 330 from the 0L position to the 3L position according to the instructed speed, the measured flow integral value (expiration 1) at the time of calibration is stored as comparison data.

Then, as shown in S212, the message "Pull the rod of the calibration pump over 6 seconds" is displayed on the display 14. That is, an operation for generating a flow corresponding to an intake of 0.5 L / s (flow of −0.5 L / s) is instructed. When the inspector pulls the rod 330 from the position of 3L to the position of 0L according to the instructed speed, the measured flow integral value (intake 1) at the time of calibration is stored as comparison data. Further, as shown in FIG. 11, the first set of flow volume curves 1 is acquired and displayed on the display 14 according to the operation of the calibration pump 300.

Then, as shown in S221, the message "Push the rod of the calibration pump for 3 seconds" is displayed on the display 14. That is, an operation for generating a flow corresponding to a breath of 1.0 L / s (flow of + 1.0 L / s) is instructed. When the inspector pushes the rod 330 from the 0L position to the 3L position according to the instructed speed, the measured flow integral value (exhalation 2) at the time of calibration is stored as comparison data.

Then, as shown in S222, the message "Pull the rod of the calibration pump over 3 seconds" is displayed on the display 14. That is, an operation for generating a flow corresponding to an intake of 1.0 L / s (flow of −1.0 L / s) is instructed. When the inspector pulls the rod 330 from the position of 3L to the position of 0L according to the instructed speed, the measured flow integral value (intake 2) at the time of calibration is stored as comparison data. Further, as shown in FIG. 11, the second set of flow volume curves 2 is acquired and displayed on the display 14 according to the operation of the calibration pump 300.

Then, as shown in S231, the message "Push the rod of the calibration pump for 2 seconds." Is displayed on the display 14. That is, an operation for generating a flow corresponding to an exhaled breath of 1.5 L / s (a flow of + 1.5 L / s) is instructed. When the inspector pushes the rod 330 from the 0L position to the 3L position according to the instructed speed, the measured flow integral value (exhalation 3) at the time of calibration is stored as comparison data.

Then, as shown in S232, the message "Pull the rod of the calibration pump over 2 seconds" is displayed on the display 14. That is, an operation for generating a flow corresponding to an intake of 1.5 L / s (flow of −1.5 L / s) is instructed. When the inspector pulls the rod 330 from the position of 3L to the position of 0L according to the instructed speed, the measured flow integral value (intake 3) at the time of calibration is stored as comparison data. Further, as shown in FIG. 11, the third set of flow volume curves 3 is acquired and displayed on the display 14 according to the operation of the calibration pump 300.

Then, as shown in S241, the message "Push the rod of the calibration pump for 1 second" is displayed on the display 14. That is, an operation for generating a flow corresponding to a breath of 3.0 L / s (flow of + 3.0 L / s) is instructed. When the inspector pushes the rod 330 from the 0L position to the 3L position according to the instructed speed, the measured flow integral value (exhalation 4) at the time of calibration is stored as comparison data.

Then, as shown in S242, the message "Pull the rod of the calibration pump over 1 second" is displayed on the display 14. That is, an operation for generating a flow corresponding to an intake of 3.0 L / s (flow of −3.0 L / s) is instructed. When the inspector pulls the rod 330 from the position of 3L to the position of 0L according to the instructed speed, the measured flow integral value (intake 4) at the time of calibration is stored as comparison data. Further, as shown in FIG. 11, the fourth set of flow volume curves 4 is acquired and displayed on the display 14 according to the operation of the calibration pump 300.

Then, as shown in S251, the message "Push the rod of the calibration pump for 0.5 seconds" is displayed on the display 14. That is, an operation for generating a flow corresponding to a breath of 6.0 L / s (flow of + 6.0 L / s) is instructed. When the inspector pushes the rod 330 from the 0L position to the 3L position according to the instructed speed, the measured flow integral value (exhalation 5) at the time of calibration is stored as comparison data.

Then, as shown in S252, the message "Pull the rod of the calibration pump over 0.5 seconds" is displayed on the display 14. That is, an operation for generating a flow corresponding to an intake of 6.0 L / s (flow of −6.0 L / s) is instructed. When the inspector pulls the rod 330 from the position of 3L to the position of 0L according to the instructed speed, the measured flow integral value (intake 5) at the time of calibration is stored as comparison data. Further, as shown in FIG. 11, the fifth set of flow volume curves 5 is acquired and displayed on the display 14 according to the operation of the calibration pump 300.

In this way, comparison data of 5 sets (10 in total) of the measured flow integral value at the time of calibration (intake 1 to intake 5) and the measured flow integral value at the time of calibration (exhalation 1 to exhalation 5) are acquired. The CPU 140 determines the flow calibration coefficient based on the average value of these comparative data and the known capacity (3.0 L) of the calibration pump 300. As shown in FIG. 11, in this example, since [3.0 (L) ÷ average value of comparison data] is 0.921, the flow calibration coefficient is determined to be 0.921. Then, in the subsequent respiratory function test, [measured measured flow × 0.921] is stored as the flow after calibration and displayed on the display 14.

When the flow calibration coefficient is determined as described above, the message "flow calibration is completed" is displayed on the display 14 as shown in S260.

In this way, the flow calibration is possible by connecting the calibration pump 300 to the respiratory path X2 of the respiratory function test device 1 and operating the calibration pump 300, and the flow calibration is realized by a simple device and a simple procedure. .. Further, by providing a function for guiding the operation procedure of the calibration pump 300, it is possible to have the inspector perform an appropriate operation and perform accurate flow calibration.

In the example of FIG. 11, it is based on a total of 10 comparative data of the measured flow integrated value (inspiratory 1 to inspiratory 5) at the time of calibration for inspiration and the measured flow integrated value (exhaled 1 to exhaled 5) at the time of calibration for exhalation. Therefore, the common (one) flow calibration coefficient for inspiration and exhalation is determined, but the flow calibration coefficient for inspiration and the flow calibration coefficient for exhalation may be determined separately. Specifically, the flow calibration coefficient for intake is determined by [3.0 (L) ÷ average value of comparison data] using only the measured flow integral value (intake 1 to intake 5) at the time of calibration for intake as comparison data. do. Further, the flow calibration coefficient for exhalation is determined by [3.0 (L) ÷ average value of comparison data] using only the measured flow integral value (exhalation 1 to exhalation 5) at the time of calibration for exhalation as comparison data.

FIG. 12 is a comparison diagram of a flow volume curve based on the measured flow before calibration and a flow volume curve based on the flow after calibration. After determining the flow calibration coefficient, the calibration pump 300 is connected to the respiratory function test device 1 as shown in FIGS. 10 and 11, and the operation is performed according to the guide. The flow after calibration can be obtained. Then, by integrating the flow after calibration, a value closer to the capacity (3.0 L) of the calibration pump 300 can be obtained as compared with the integrated value of the actually measured flow before calibration.

(Flow calibration using measured volume derivative value)
In the above embodiment, the flow calibration coefficient is determined based on the measured flow integral value at the time of calibration, which is the comparative data, and the capacity (3L) of the known calibration pump. Not limited to such a method, the flow calibration coefficient may be determined based on the measured flow at the time of calibration and the measured volume differential value at the time of calibration. Specifically, as shown in FIGS. 9 and 10, an operation for generating a flow is performed using the calibration pump 300. At this time, the CPU 140 performs a calculation to differentiate the measured volume based on the volume output at the time of calibration. Then, the flow calibration coefficient is determined based on the calculated measured volume differential value and the measured flow measured based on the signal (flow output) output from the differentiating circuit 131.

For example, as shown in FIG. 13, based on the measured volume differential value (peak value) at the time of calibration calculated by the CPU 140 and the measured flow (peak value) measured based on the flow output at the time of calibration, [actual measurement]. Volume differential value (peak value) ÷ measured flow (peak value)] determines the flow calibration coefficient. In the example shown in FIG. 13, when the rod 330 of the calibration pump 300 is pushed from the 0L position to the 3L position over 2 seconds, that is, when a flow corresponding to exhalation of about 1.5 L / s is generated. The flow calibration coefficient for exhalation is shown in. In this case, the peak value of the measured volume differential value was 1.51 L / s, and the peak value of the measured flow was 1.62 L / s. Therefore, [1.51 L / s ÷ 1.62 L / s] ] = 0.932 is the flow calibration coefficient.

In this way, the CPU 140 determines the flow calibration coefficient based on the actual measurement flow at the time of calibration, which is the comparison data, and the actual measurement volume differential value at the time of calibration. As described above, the flow calibration coefficient for exhalation and the flow calibration coefficient for inspiration may be determined separately. Further, the flow to be generated may be different and calibrated a plurality of times, and the average value thereof may be determined as the flow calibration coefficient.

(Measurement of actual measurement flow by rotary encoder)
In the above example, when the potentiometer 125 detects the movement distance of the piston 123 in the central axis direction, an analog signal corresponding to the detected movement distance is output, and the signal is processed by a differentiating circuit (the DC component is cut). Then, after the analog signal corresponding to the time change (flow) of the movement distance in the central axis direction of the piston 123 is obtained, it is further converted into a digital signal by the ADC 133b and read by the CPU 140. Not limited to such a configuration, for example, a rotary encoder whose rotation axis rotates as the piston 123 moves in the central axis direction may be used to obtain an actually measured flow. That is, the rotary encoder detects the rotation speed of the rotation shaft accompanying the movement of the piston 123 in the central axis direction, and the pulse signal corresponding to the rotation speed output from the rotary encoder is the movement distance of the piston 123 in the center axis direction. The CPU 140 may be read as a digital signal corresponding to a time change (flow).

For example, if the moving speed of the piston 123 in the central axis direction is slow, the interval between pulses output from the rotary encoder (pulse output cycle) becomes long, and if the moving speed of the piston 123 in the central axis direction is fast, the rotary encoder By shortening the output pulse interval (pulse output cycle), the CPU 140 can obtain an actually measured flow based on the pulse interval (pulse output cycle). Further, by setting the pulses output from the rotary encoder as two-phase outputs having different phases, it is possible to distinguish between the expiratory (forward) flow and the inspiratory (reverse) flow. For example, when the axis of rotation is rotating in the forward direction, the other pulse is in the ON state when one pulse rises, and when the axis of rotation is rotating in the opposite direction, the other pulse is in the ON state. It is preferable to provide a phase difference so that the other pulse is in the OFF state at the time of rising.

(Time transition of calibration coefficient)
The volume calibration coefficient calculated in the above embodiment is stored in the ROM as time-series data together with the calibration conditions (date and time, temperature, humidity, etc.), and the CPU 140 displays the time transition of the volume calibration coefficient in a graph format. It may be displayed on 14. For example, by displaying the time-series data of the volume calibration coefficient for one year (365 days) on the display 14 in a graph format, how the volume calibration coefficient fluctuates due to factors such as temperature and humidity (volume). It is possible to grasp the output stability and the stability of the measured volume before calibration).

Similarly, the flow calibration coefficient calculated in the above embodiment is stored in the ROM as time-series data together with the conditions at the time of calibration (date and time, temperature, humidity, etc.), and the CPU 140 graphs the time transition of the flow calibration coefficient. It may be displayed on the display 14 in a format. For example, by displaying the time-series data of the flow calibration coefficient for one year (365 days) on the display 14 in a graph format, how the flow calibration coefficient fluctuates due to factors such as temperature and humidity (flow). It is possible to grasp the output stability and the stability of the measured flow before calibration).

Although the embodiment of the present invention has been described above, the present invention is not limited to this embodiment. Needless to say, it is possible to make changes within a range that does not deviate from the object and gist of the present invention.

1 ... Respiratory function test device 11 ... Main body 12 ... Rolling seal type spirometer 13 ... Keyboard 14 ... Display 123 ... Piston 131 ... Differentiating circuit 140 ... CPU
300 ... Calibration pump

Claims (13)

As a respiratory flow measuring means that measures the respiratory flow rate based on the signal corresponding to the movement of the movable body due to breathing, the DC component is cut by the differential circuit, and the signal is converted from the analog signal to the digital signal by the A / D converter. A respiratory function test device comprising a respiratory capacity measuring means for measuring a respiratory capacity based on a signal in which a signal corresponding to the movement of the movable body is converted from an analog signal to a digital signal by an A / D converter. ,
It is a calibration coefficient for the respiratory capacity measured by the respiratory capacity measuring means based on the measured capacity measured by the respiratory capacity measuring means with the operation of the reference capacity calibration pump and the reference capacity. The first calibration coefficient calculation means for calculating the first calibration coefficient, and
The target is the respiratory flow rate measured by the respiratory flow rate measuring means based on the calculated capacity calculated based on the measured flow rate measured by the respiratory flow rate measuring means according to the operation of the calibration pump and the reference capacity. A second calibration coefficient calculating means for calculating the second calibration coefficient, which is the calibration coefficient to be used, is provided.
Pulmonary function testing device. As a respiratory flow measuring means that measures the respiratory flow rate based on the signal corresponding to the movement of the movable body due to breathing, the DC component is cut by the differential circuit, and the signal is converted from the analog signal to the digital signal by the A / D converter. A respiratory function test device comprising a respiratory capacity measuring means for measuring a respiratory capacity based on a signal in which a signal corresponding to the movement of the movable body is converted from an analog signal to a digital signal by an A / D converter. ,
It is a calibration coefficient for the respiratory capacity measured by the respiratory capacity measuring means based on the measured capacity measured by the respiratory capacity measuring means with the operation of the reference capacity calibration pump and the reference capacity. The first calibration coefficient calculation means for calculating the first calibration coefficient, and
The measured flow rate measured by the breathing flow rate measuring means according to the operation of the calibration pump and the calculated flow rate calculated based on the measured capacity measured by the breathing capacity measuring means according to the operation of the calibration pump. Based on the above, a second calibration coefficient calculating means for calculating a second calibration coefficient, which is a calibration coefficient for the respiratory flow rate measured by the respiratory flow rate measuring means, is provided.
Pulmonary function testing device. Respiratory flow measuring means that measures the respiration flow rate based on the interval of the pulse signal output from the rotary encoder according to the movement of the movable body due to breathing, and the pulse signal output from the rotary encoder according to the movement of the movable body. It is a respiratory function test device provided with a respiratory capacity measuring means for measuring respiratory capacity based on the above.
It is a calibration coefficient for the respiratory capacity measured by the respiratory capacity measuring means based on the measured capacity measured by the respiratory capacity measuring means with the operation of the reference capacity calibration pump and the reference capacity. The first calibration coefficient calculation means for calculating the first calibration coefficient, and
The target is the respiratory flow rate measured by the respiratory flow rate measuring means based on the calculated capacity calculated based on the measured flow rate measured by the respiratory flow rate measuring means according to the operation of the calibration pump and the reference capacity. A second calibration coefficient calculating means for calculating the second calibration coefficient, which is the calibration coefficient to be used, is provided.
Pulmonary function testing device. Respiratory flow measuring means that measures the respiration flow rate based on the interval of the pulse signal output from the rotary encoder according to the movement of the movable body due to breathing, and the pulse signal output from the rotary encoder according to the movement of the movable body. It is a respiratory function test device provided with a respiratory capacity measuring means for measuring respiratory capacity based on the above.
It is a calibration coefficient for the respiratory capacity measured by the respiratory capacity measuring means based on the measured capacity measured by the respiratory capacity measuring means with the operation of the reference capacity calibration pump and the reference capacity. The first calibration coefficient calculation means for calculating the first calibration coefficient, and
The measured flow rate measured by the breathing flow rate measuring means according to the operation of the calibration pump and the calculated flow rate calculated based on the measured capacity measured by the breathing capacity measuring means according to the operation of the calibration pump. Based on the above, a second calibration coefficient calculating means for calculating a second calibration coefficient, which is a calibration coefficient for the respiratory flow rate measured by the respiratory flow rate measuring means, is provided.
Pulmonary function testing device. A respiratory function test device selected from claims 1 to 4.
The first calibration coefficient calculating means calculates, as the first calibration coefficient, a first calibration coefficient for exhalation and a first calibration coefficient for inspiration, respectively.
The second calibration coefficient calculating means calculates, as the second calibration coefficient, a second calibration coefficient for exhalation and a second calibration coefficient for inspiration, respectively.
Pulmonary function testing device. A respiratory function test device selected from claims 1 to 5.
A first breathing path in which a storage case containing an absorbent that absorbs carbon dioxide gas contained in the subject's exhaled breath is installed.
Including a second breathing path in which the storage case is not installed,
The calibration pump can be connected to the second breathing path.
Pulmonary function testing device. The respiratory function test device according to claim 6.
A connection notification means for notifying the connection of the calibration pump to the second breathing path is provided.
Pulmonary function testing device. A respiratory function testing device according to any one of claims 1 to 7.
By manually moving the operation unit in the first direction, the calibration pump can supply a volume of air corresponding to the moving distance of the operation unit to the respiratory function test device, and the operation unit can be supplied with air. By manually moving the air in the second direction, it is possible to discharge a volume of air corresponding to the moving distance of the operation unit from the respiratory function test device.
In both the case of calculating the first calibration coefficient and the case of calculating the second calibration coefficient, the first speed for moving the operation unit in the first direction and the operation unit in the second direction. The moving notification means for notifying the second speed to be moved to is provided.
Pulmonary function testing device. The respiratory function test apparatus according to claim 8.
In both the case of calculating the first calibration coefficient and the case of calculating the second calibration coefficient, the movement notification means makes the first speed different and moves the operation unit a plurality of times in the first direction. The notification for moving the operation unit in the second direction is performed a plurality of times by differentiating the second speed.
Pulmonary function testing device. The respiratory function test device according to claim 9.
The movement notification means performs notification so that the first speed is common between the case of calculating the first calibration coefficient and the case of calculating the second calibration coefficient, and the second Pulmonary function test device that provides notification so that the speed is common. The respiratory function testing device according to claim 9 or 10.
In both the case of calculating the first calibration coefficient and the case of calculating the second calibration coefficient, a flow volume curve showing the relationship between the measured flow rate and the measured capacity based on the operation of the calibration pump is displayed. Equipped with display means,
Pulmonary function testing device. The respiratory function test device according to claim 11.
The display means
The flow volume curve is displayed on the graph consisting of the capacity axis and the flow rate axis.
In both the case of calculating the first calibration coefficient and the case of calculating the second calibration coefficient, when the operation unit is moved in the first direction, the first velocity is described from the origin position. When a flow volume curve that is on the positive direction side of the capacitance axis and is directed to the positive direction side of the flow rate axis is displayed and the operation unit is moved in the second direction, the capacitance is measured from the origin position for each second velocity. A respiratory function test device that displays a flow volume curve that is on the positive side of the axis and toward the negative side of the flow rate axis. A respiratory function testing device selected from claims 1 to 12.
A storage means for storing the first calibration coefficient and the second calibration coefficient, and
A time transition display means for displaying the time transition of the first calibration coefficient and the time transition of the second calibration coefficient is provided.
Pulmonary function testing device.

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