Measuring device and measuring method

Abstract

A measuring device (1) includes: a storage unit (10) in which a blood sample is stored; a pump (20) that sucks the blood sample from the storage unit; a flow channel (30) that communicates with the storage unit and through which the blood sample or a flushing liquid flows when sucked by the pump; a detection unit (50) that includes an irradiation unit and a light detection unit, the irradiation unit irradiates the flow channel with light, and the light detection unit detects light emitted from the irradiation unit and having transmitted through or reflected from the flow channel; a sensor (60) that is arranged between the storage unit and the detection unit and detects a switching from a liquid to a gas in the flow channel; and a control unit (70) that controls a stop of driving of the pump.

Description

TECHNICAL FIELD

[0001] The present application relates to a red blood cell aggregation measuring device and a measuring method. BACKGROUND

[0002] Among known red blood cell aggregation (enrichment) reaction measuring methods, there is a method of stopping blood flow immediately after a predetermined shear stress is applied to the blood and measuring the optical density change (referred to as a syllectogram) that occurs at that time.

[0003] In order to accurately measure the syllectogram, it is necessary to stop blood flow immediately after a predetermined shear stress is applied to the blood. On the other hand, a tube pump described in, for example, Patent Literature 1 below can be used as a device for moving a blood sample stored in a storage unit to a detection unit as a measuring unit. The tube pump sucks the blood sample by operating in a manner that a roller presses a tube when it rotates in the circumferential direction.

[0004] BIBLIOGRAPHIC LIST

[0005] PATENT LITERATURE

[0006] Patent Literature 1: JP-A-58-83233 SUMMARY

[0007] PROBLEMS

[0008] However, due to the viscoelasticity of the entire flow passage formed by the tube pump and the resin tube connected to the tube pump, it is difficult to perform blood flow control such as precise control of the blood flow position and speed and blood flow stop. More specifically, if there is air as a compressive fluid between the blood and the tube pump when the blood is sucked by the tube pump, the pressure attenuates as it is transmitted due to the high viscoelasticity of the air, so it is difficult to perform precise control of the blood flow required for syllectogram measurement.

[0009] This problem is not limited to the case of using a tube pump, and occurs also in the case of using a suction pump.

[0010] One method of reducing pressure attenuation at the time of pressure transmission is to fill the flow passage with a flushing liquid as a non-compressive fluid. However, if the flushing liquid and the blood come into contact with each other, the concentration of the blood or its components can change, so it can not be possible to perform accurate syllectogram measurement.

[0011] The present disclosure subject matter aims to solve the above problems, and its object is to provide a measuring device and a measuring method that can accurately control blood flow and prevent contact between a flushing liquid and blood.

[0012] SOLUTION TO THE PROBLEM

[0013] A measurement device according to the disclosed subject matter that achieves the above object is a measurement device for measuring red blood cell aggregation of a blood sample. The measurement device includes a storage unit in which a blood sample is stored, a pump that draws the blood sample from the storage unit, a flow channel that communicates with the storage unit and through which the blood sample or a flushing liquid flows when drawn by the pump, a detection unit that includes an irradiation unit that irradiates the flow channel with light and a light detection unit that detects light that has been emitted from the irradiation unit and has transmitted through or reflected from the flow channel, a sensor that is arranged between the storage unit and the detection unit and detects a switch from liquid to gas in the flow channel, and a control unit that controls a stop of driving of the pump.

[0014] A measurement method according to the disclosed subject matter that achieves the above object is a measurement method of a measurement device for measuring red blood cell aggregation of a blood sample, the measurement device including a storage unit in which a blood sample is stored, a pump that draws the blood sample from the storage unit, a flow channel that communicates with the storage unit and through which the blood sample or a flushing liquid flows when drawn by the pump, a detection unit that includes an irradiation unit that irradiates the flow channel with light and a light detection unit that detects light that has been emitted from the irradiation unit and has transmitted through or reflected from the flow channel, a sensor that is arranged between the storage unit and the detection unit and detects a switch from liquid to gas in the flow channel, and a control unit that controls a stop of driving of the pump, wherein the measurement method includes stopping the pump after the flushing liquid stored in the storage unit moves to the flow channel after an air layer has entered the flow channel is detected by the sensor.

[0015] Advantages of the Invention

[0016] According to the above measurement device and measurement method, it is possible to detect, by the sensor, entry of an air layer after the flushing liquid into the flow channel. Therefore, by drawing the blood sample after a small amount of air layer, it is possible to form an air layer of an amount that does not hinder blood flow control between the blood and the flushing liquid. As a result, it is possible to provide a measurement device and measurement method that can accurately control blood flow and prevent contact between the flushing liquid and the blood. BRIEF DESCRIPTION OF DRAWINGS

[0017] Figure 1 is a schematic diagram showing a measurement device according to an embodiment of the disclosed subject matter.

[0018] Figure 2This is a schematic diagram of a pipe pump illustrating a measuring device according to an embodiment.

[0019] Figure 3 This is a schematic diagram showing the detection unit of the measuring device according to an embodiment.

[0020] Figure 4 This is a graph of the example transmitted light intensity-time curve.

[0021] Figure 5 This is a schematic diagram showing the measuring device of Modified Example 1.

[0022] Figure 6 This is a schematic diagram showing the measuring device of Modified Example 2. Detailed Implementation

[0023] Embodiments of the subject matter of this disclosure will be described with reference to the accompanying drawings. In the description of the drawings, the same constituent elements will be given the same reference numerals and will not be described again. For ease of description, the scale between dimensions in the drawings may be enlarged and therefore differ from the actual scale.

[0024] Figure 1 This is a schematic diagram illustrating a measuring device 1 according to an embodiment of the subject matter of this disclosure. Figure 2 This is a schematic diagram showing the pipe pump 20 of the measuring device 1 according to an embodiment. Figure 3 This is a schematic diagram showing the detection unit 50 of the measuring device 1 according to an embodiment. Figure 4 This is a graph of the example transmitted light intensity-time curve.

[0025] Measuring device 1 is used to measure the transmitted light intensity-time curve of a blood sample (refer to...). Figure 4 (A device.) Figure 1 As shown, the measuring device 1 may include a storage unit 10, a tubular pump (corresponding to the term "pump") 20, a flow channel 30, a detection unit (detector) 50, a sensor 60, and a control unit (controller) 70.

[0026] Blood samples or flushing fluid are stored in storage unit 10. Storage unit 10 is specifically a cup-shaped object. Blood samples or flushing fluid obtained from blood collection tubes (not shown) are moved to storage unit 10 through nozzles (not shown).

[0027] Blood samples are collected from the patient beforehand and placed into blood collection tubes. For example, EDTA (ethylenediaminetetraacetic acid) can be added to the blood sample in the blood collection tube as an anticoagulant.

[0028] like Figure 1As shown, the tubular pump 20 is located downstream of the flow channel 30. The tubular pump 20 draws blood samples or flushing fluid stored in the storage unit 10. The flushing fluid is a liquid used to flush blood samples present in the flow channel 30. Figure 2 As shown, the pipe pump 20 can include three rollers 21 arranged at 120° intervals in the circumferential direction, a rotating part 22 for rotating the three rollers 21 in the circumferential direction, and a pipe 23 connected to the flow channel 30.

[0029] As the pump rotates in the circumferential direction, the three rollers 21 of the tube pump 20 press against the tube 23, thereby drawing up a blood sample.

[0030] When the tubing pump 20 draws in a blood sample, a certain shear stress is applied to the blood sample in the storage unit 10. The blood sample is drawn in when the tubing pump 20 rotates forward, and returned when the tubing pump 20 rotates in reverse. Immediately before the transmission light intensity-time curve measurement, temperature regulation is performed, and the tubing pump 20 is rotated in both forward and reverse directions by the control unit 70 to move the blood sample back and forth in the direction of travel of the flow channel 30.

[0031] like Figure 1 As shown, the flow channel 30 is continuously arranged downstream of the storage unit 10. For example, the flow channel 30 is a transparent glass tube or a resin tube. Blood samples drawn by the tubular pump 20 flow through the flow channel 30.

[0032] The detection unit 50 measures the intensity of transmitted light by detecting the time point before the flow of the blood sample through the flow channel 30 stops, using this time point as the starting point. Figure 4 The transmitted light intensity-time curve is shown. The starting point of detection by detection unit 50 is not limited to the time point before the blood sample stops flowing through flow channel 30, but can be set at a desired time point, such as after the flow stops.

[0033] like Figure 3 As shown, the detection unit 50 may include an irradiation unit (light emitter) 51 for irradiating light onto the flow channel 30, a light detection unit (light detector) 52 for detecting light emitted from the irradiation unit 51 and transmitted through the flow channel 30, an optical pool 53 through which the blood sample flows, a holding unit 54 for holding the optical pool 53, and a temperature adjustment unit (not shown) for adjusting the temperature of the optical pool 53. In this embodiment, the flow channel in the optical pool 53 is part of the flow channel 30. The flow channel 30 and the optical pool 53 may be provided separately. The optical pool 53 may be a transparent glass tube, and other parts of the flow channel 30 may be resin tubes.

[0034] Two irradiation units 51 and two light detection units 52 are provided. The irradiation unit 51 is, for example, a near-infrared light generator. The light detection unit 52 detects the intensity of a light beam transmitted through a blood sample. The light detection unit 52 is, for example, a photodiode. The temperature adjustment unit is a heater, and is provided on, for example, the outer peripheral surface of the holding unit 54. The temperature adjustment unit enables the temperature of the blood sample in the optical cell 53 to be kept constant, and thereby enables the transmitted light intensity-time curve to be measured in an appropriate manner.

[0035] Since two irradiation units 51 and two light detection units 52 are provided, the transmitted light intensity-time curve of a blood sample can be measured at two positions. Therefore, by comparing the two measured transmitted light intensity-time curves, for example, if one transmitted light intensity-time curve is different from a predetermined curve, it can be judged that it has not been measured correctly due to the inclusion of a bubble or contamination, and the other transmitted light intensity-time curve is adopted.

[0036] As shown in FIG. 6, the horizontal axis and the vertical axis of the transmitted light intensity-time curve respectively represent time and transmitted light intensity. In the example transmitted light intensity-time curve shown in FIG. 6, the output voltage of the photodiode used as the light detection unit 52 is used as a representation of the transmitted light intensity. Figure 4 Figure 4

[0037] In the transmitted light intensity-time curve, the transmitted light intensity takes a minimum value V min at a time (t = to) a short time after the flow of the blood sample through the flow channel 30 has stopped (t = 0). The transmitted light intensity takes the minimum value V min because the irradiation light is scattered and absorbed by the free and dispersed individual red blood cells in the flow channel 30. On the other hand, at the instant (t = 0) when the flow has stopped, the red blood cells are deformed and oriented in the flow direction due to the shear stress generated in the flow, and thus the transmitted light intensity is slightly higher than V min .

[0038] After the minimum value V min is taken at the time to, the transmitted light intensity increases. This is because the red blood cells begin to aggregate at the time of flow stoppage, and the irradiation light passes between the aggregated (i.e., increased in size) red blood cells. The red blood cells aggregate because blood proteins such as fibrinogen, which are positively charged and increase in number due to inflammation, hinder the repulsion between the negatively charged red blood cells.

[0039] A parameter related to the aggregation of red blood cells (hereinafter referred to as an "aggregation parameter") is calculated on the basis of the transmitted light intensity-time curve. The aggregation parameter can be any one of a plurality of parameters related to the aggregation of red blood cells.

[0040] In order to calculate the aggregation parameter, a time t is set as a predetermined time after the time to. The time t is, for example, 1 minute. The aggregation parameter is calculated by the following equation (1).​​A In the transmitted light intensity-time curve, a predetermined time can be set as the desired time required for the rate of increase in transmitted light intensity to decrease to a certain extent, thus saturating the transmitted light intensity. When calculating the focusing parameters, time t is used... A The transmitted light intensity at point V is set to the maximum value. max The aggregation parameter can be a parameter AI calculated based on the transmitted light intensity-time curve in the following manner. The parameter AI is calculated as the ratio of the area of ​​region B, which is the portion of rectangular region S located below the transmitted light intensity-time curve, to region S, where the rectangular region S is at time intervals t. A -t0 is used as one side and the maximum value V max and minimum value V min The difference AMP is used as the other side. That is, parameter AI is calculated as the ratio of the area of ​​region B to the sum of the areas of region A and region B (i.e., B / (A+B)). Region A is the region located above the transmitted light intensity-time curve of region S, and is different from AI. The aggregation parameter can be the area of ​​region B, the area of ​​region A, AMP, or time t. 1 / 2 Time t 1 / 2 It is the minimum value V of the transmitted light intensity from time t0. min Increase the time for AMP / 2.

[0041] like Figure 1 As shown, sensor 60 is arranged between storage unit 10 and detection unit 50. Sensor 60 is used to detect the presence of an air layer or liquid in the portion of flow channel 30 that is continuous with storage unit 10. That is, sensor 60 detects the switching from liquid to gas within flow channel 30. There are no limitations on the type of sensor 60 except that it should detect an air layer or liquid; for example, impedance sensors or optical sensors can be used as sensor 60.

[0042] When using an impedance sensor as sensor 60, sensor 60 connects the end of the flow channel 30 on the storage unit 10 side to the portion of the flow channel 30 connected to the detection unit 50. Sensor 60 detects the current flowing through it. If no current flows due to the inflow of an air layer, sensor 60 determines that an air layer has been inflowed.

[0043] When using an optical sensor as sensor 60, sensor 60 detects the inflow of air by utilizing the change in refractive index that occurs when switching from a rinsing fluid or blood sample to an air layer.

[0044] The control unit 70 controls, for example, the driving of various components. The control unit 70, acting as a CPU or similar device, controls these constituent elements and performs various calculations according to a program.

[0045] Next, a measurement method using the above-described measuring device 1 will be described.

[0046] First, the control unit 70 supplies the rinse solution to the storage unit 10.

[0047] Subsequently, the control unit 70 fills the flow channel 30 with the rinse solution by driving the tube pump 20 in the forward direction. When the air layer flows into the flow channel 30 after all the rinse solution stored in the storage unit 10 flows into the flow channel 30, the control unit 70 detects the inflow of the air layer by the sensor 60.

[0048] If the sensor 60 does not detect the rinse solution or the air layer while the tube pump 20 continues to suck the rinse solution, the control unit 70 determines that the flow channel 30 is clogged or the rinse solution is cut off.

[0049] When the sensor 60 detects the inflow of the air layer, the control unit 70 stops the tube pump 20.

[0050] Subsequently, the control unit 70 acquires the blood sample from the blood collection tube through the nozzle and supplies the blood sample to the storage unit 10.

[0051] Subsequently, the control unit 70 supplies the blood sample to the detection unit 50 by driving the tube pump 20 in the forward direction. As a result, the air layer is formed between the rinse solution filling the channel between the tube pump 20 and the sensor 60 and the blood sample. For example, if the air layer is not formed between the rinse solution and the blood sample and they are in direct contact with each other, the blood sample can be mixed with the rinse solution and then drawn, and thus diluted, so that an accurate transmittance intensity-time curve measurement cannot be performed. On the other hand, if a large amount of air layer is formed between the storage unit 10 and the tube pump 20, the air layer can generate high viscoelasticity, thereby reducing the blood drawing and stirring speed, so that an accurate transmittance intensity-time curve measurement cannot be performed. From these viewpoints, it is preferable to include an air layer of about 2 to 10 μl.

[0052] In contrast, according to the measurement method of the embodiment, since a small amount of air layer is formed between the rinse solution and the blood sample, the blood sample is not mixed with the rinse solution and the stirring speed of the blood is not reduced, so that an accurate transmittance intensity-time curve measurement can be performed.

[0053] Subsequently, the control unit 70 moves the blood sample back and forth by rotating the tube pump 20 in the forward and reverse directions, to prevent the blood sample from starting to aggregate.

[0054] Subsequently, the control unit 70 stops the driving of the tube pump 20 at the time of measurement of the transmittance intensity-time curve. The blood flow of the blood sample can be quickly stopped by using the tube pump 20.

[0055] Subsequently, the transmitted light intensity-time curve of the blood sample is measured by the detection unit 50. Since the detection unit 50 has two irradiation units 51 and two light detection units 52, it is possible to measure the transmitted light intensity-time curve at two positions. Therefore, if it is found by comparing the two measured transmitted light intensity-time curves that, for example, one transmitted light intensity-time curve is different from the predetermined graph, it is possible to judge that the one transmitted light intensity-time curve has not been measured correctly due to inclusion of a bubble or contamination, and to adopt the other transmitted light intensity-time curve. Or, if one transmitted light intensity-time curve is different from the predetermined graph, an instruction to perform the measurement again can be issued to the user.

[0056] After the transmitted light intensity-time curve measurement, the control unit 70 supplies the flushing liquid to the storage unit 10 again. The control unit 70 flushes the flow passage 30 by causing the tube pump 20 to suck the supplied flushing liquid. Since the sensor 60 is provided, when the step of flushing the flow passage 30 by supplying the flushing liquid to the storage unit 10 is repeatedly performed, it is possible to detect that all of the flushing liquid in the storage unit 10 has been sucked and an air layer has flowed in. Therefore, it is possible to supply new flushing liquid to the storage unit 10 after the flushing liquid has been completely removed from the storage unit 10. This makes it possible to correctly prevent the event of partial flushing liquid overflowing the storage unit 10.

[0057] As described above, the measurement device 1 according to the embodiment is a measurement device for measuring the erythrocyte aggregation of a blood sample. The measurement device 1 can include a storage unit 10 that stores a blood sample, a tube pump 20 that sucks the blood sample from the storage unit 10, a flow passage 30 that communicates with the storage unit 10 and through which the blood sample or a flushing liquid flows when sucked by the tube pump 20, a detection unit 50 that can include an irradiation unit 51 that irradiates the flow passage 30 with light and a light detection unit 52 that detects light emitted from the irradiation unit 51 and that has transmitted through the flow passage 30, a sensor 60 that is arranged between the storage unit 10 and the detection unit 50 and that detects a switch from a liquid to a gas in the flow passage 30, and a control unit 70 that controls the stop of the drive of the tube pump 20. The measurement device 1 thus configured can detect by the sensor 60 that an air layer has entered the flow passage after the flushing liquid. Therefore, by sucking the blood after a small amount of air layer, it is possible to form an air layer of an amount that does not hinder the blood flow control between the blood and the flushing liquid. From the above, it is possible to make the blood move accurately and to prevent contact between the flushing liquid and the blood.

[0058] After the flushing liquid stored in the storage unit 10 so far is moved to the flow channel 30, the control unit 70 stops the tube pump 20 after detecting that the air layer has entered the flow channel 30 by the sensor 60. In the measurement device 1 thus configured, the air layer can be reliably formed between the blood and the flushing liquid.

[0059] If the sensor 60 does not detect the flushing liquid or the air layer while the tube pump 20 is sucking the flushing liquid, the control unit judges that the flow channel 30 is clogged or the flushing liquid is cut off. The measurement device 1 thus configured can reliably detect the clogging of the flow channel 30 or the absence of the flushing liquid.

[0060] Two irradiation units 51 and two light detection units 52 are provided, and the control unit 70 compares the transmission light intensity-time curve waveforms acquired by the two respective light detection units 52. According to the measurement device 1 thus configured, if it is found by comparing the two measured transmission light intensity-time curves that, for example, one transmission light intensity-time curve is different from a predetermined curve, it can be judged that the one transmission light intensity-time curve has not been measured correctly due to the inclusion of a bubble or contamination, and information is presented to prompt the user to take another measurement or adopt another transmission light intensity-time curve.

[0061] In addition, as described above, the measurement method according to the embodiment is a measurement method of the measurement device 1 for measuring a transmission light intensity-time curve, which can include: a storage unit 10 that stores a blood sample; a tube pump 20 that sucks the blood sample from the storage unit 10; a flow channel 30 that communicates with the storage unit 10 and through which the blood sample flows when sucked by the tube pump 20; a detection unit 50 that can include an irradiation unit 51 that irradiates the flow channel 30 with light and a light detection unit 52 that detects light emitted from the irradiation unit 51 and that has transmitted through the flow channel 30; a sensor 60 that is arranged between the storage unit 10 and the detection unit 50 and that detects a switch from a liquid to a gas in the flow channel 30; and a control unit 70 that controls the stop of the drive of the tube pump 20. After the flushing liquid stored in the storage unit 10 so far is moved to the flow channel 30, the measurement method stops the tube pump 20 after detecting that the air layer has entered the flow channel 30 by the sensor 60. According to the measurement method, the sensor 60 can detect that the air layer has entered after the flushing liquid. Thereby, by sucking the blood after the air layer, the air layer can be formed between the blood and the flushing liquid. As is apparent from the above, the blood can be moved accurately and contact between the flushing liquid and the blood can be prevented.

[0062] <Modification Example 1>

[0063] Next, referring to Figure 5The configuration of the measuring device 2 of the modification example 1 will be described. Figure 5 is a schematic diagram showing the measuring device of the modification example 1. The measuring device 2 according to the modification example 1 differs from the measuring device 1 of the above-described embodiment in that the valve 40 is provided. The constituent elements having the same constituent elements as the measuring device 1 according to the above-described embodiment will be given the same symbols as the latter and the description will be omitted.

[0064] As shown in Figure 5 , the measuring device 2 of the modification example 1 can include the storage unit 10, the tube pump 20, the flow passage 30, the valve 40, the detection unit 50, the sensor 60, and the control unit (controller) 70. Since the storage unit 10, the tube pump 20, the flow passage 30, the detection unit (detector) 50, the sensor 60, and the control unit 70 are configured in the same manner as the measuring device 1 according to the above-described embodiment, and thus, the description will not be given again.

[0065] As shown in Figure 5 , the valve 40 is arranged between the detection unit 50 and the tube pump 20. By opening the valve 40, it is possible to make the blood sample or the rinse solution for rinsing the blood sample remaining in the flow passage 30 flow through the flow passage 30 by opening the flow passage 30. On the other hand, by closing the valve 40, it is possible to stop the blood sample or the rinse solution from flowing through the flow passage 30 by shutting off the flow passage 30. The valve 40 is opened and closed by the control unit 70.

[0066] Next, the measurement method of the measuring device 2 according to the above-described modification example 1 will be described.

[0067] First, the control unit 70 supplies the rinse solution to the storage unit 10.

[0068] Subsequently, the control unit 70 fills the flow passage 30 with the rinse solution by driving the tube pump 20 in the forward direction in a state where the valve 40 is open. The sensor 60 detects the inflow of the air layer that occurs after all the rinse solution stored in the storage unit 10 so far flows into the flow passage 30.

[0069] When the sensor 60 detects the inflow of the air layer, the control unit 70 closes the valve 40. The control unit 70 stops the tube pump 20 immediately after the valve 40 is closed.

[0070] Subsequently, the control unit 70 acquires the blood sample from the blood collection tube through the nozzle and supplies it to the storage unit 10.

[0071] Subsequently, the control unit 70 opens the valve 40 and supplies the blood sample to the detection unit 50 by driving the tube pump 20 in the forward direction. As a result, the air layer is formed between the rinse solution and the blood sample that fill the passage between the tube pump 20 and the sensor 60.

[0072] Subsequently, the control unit 70 moves the blood sample back and forth with respect to the flow channel 30 by rotating the tube pump 20 in the forward and reverse directions, so that the blood sample does not start to aggregate.

[0073] Subsequently, the control unit 70 closes the valve 40 at the time of the transmission light intensity-time curve measurement and immediately thereafter stops the drive of the tube pump 20. At this time, compared with the measurement device 1 of the above-described embodiment, it is possible to stop the blood flow of the blood sample more quickly.

[0074] Since the subsequent steps are the same as in the measurement device 1 of the above-described embodiment, the description thereof is omitted.

[0075] <Modification Example 2>

[0076] Next, the structure of the measurement device 3 of Modification Example 2 will be described with reference to Figure 6 the drawing. Figure 6 is a schematic diagram showing the measurement device of Modification Example 2. The measurement device 3 of Modification Example 2 differs from the measurement device 2 of Modification Example 1 in that an initialization flow channel 80 or the like is provided. Constituent elements having the same constituent elements as the above-described measurement device 1 according to the embodiment or the above-described measurement device 2 according to Modification Example 1 will be given the same symbols as the latter and the description thereof will be omitted.

[0077] As shown in Figure 6 , the measurement device 3 of Modification Example 2 can include a storage unit 10, a tube pump 20, a flow channel 30, a valve 40, a detection unit (detector) 50, a sensor 60, a control unit (controller) 70, an initialization flow channel 80, a switching valve 90, and a detection sensor 100. Since the storage unit 10, the tube pump 20, the flow channel 30, the valve 40, the detection unit 50, the sensor 60, and the control unit 70 are configured in the same manner as the measurement device 2 according to the above-described Modification Example 1, and therefore, the description thereof will not be given again.

[0078] As described in the above-described embodiment, when the three rollers 21 of the tube pump 20 are rotated in the circumferential direction to thereby press the tube 23, the blood sample is sucked by the detection unit 50. As a result, depending on the portion pressed by the rollers 21, a temporary decrease in the flow rate can occur, resulting in a problem that the blood suction cannot be controlled to the correct position or the shear stress cannot be controlled to a predetermined value for the free movement of red blood cells, which is important for the transmission light intensity-time curve measurement. Therefore, when the blood sample is stirred by moving the blood sample back and forth by rotating the tube pump 20 in the forward and reverse directions, it is necessary to set (initialize) the flow rate reduction press position of the rollers 21 at a predetermined initial position. Furthermore, in order to suck the blood into the detection unit 50 to a predetermined position and initialize the tube pump 20, it is necessary to drive the tube pump 20 independently of the blood suction. Therefore, it is necessary to cut off the flow channel at a position between the storage unit 10 and the tube pump 20 and switch to a different flow channel.

[0079] The configuration of the measuring apparatus 3 according to the modification 2 will be described below. The initialization flow passage 80 branches at a position between the valve 40 and the tube pump 20. The initialization flow passage 80 is open to a large chamber or the atmosphere.

[0080] The on-off valve 90 is arranged in the initialization flow passage 80. The opening of the initialization flow passage 80 by closing the valve 40 and opening the on-off valve 90 enables the blood sample or the flush liquid to flow into the initialization flow passage 80. On the other hand, the closing of the initialization flow passage 80 by opening the valve 40 and closing the on-off valve 90 enables the flow of the blood sample or the flush liquid through the initialization flow passage 80 to be stopped. The opening / closing of the on-off valve 90 is controlled by the control unit 70.

[0081] The detection sensor 100 detects whether the roller 21 of the tube pump 20 is positioned at a predetermined position. The type of the detection sensor 100 is not particularly limited as long as it is a sensor capable of detecting whether the roller 21 is positioned at a predetermined position. For example, the detection sensor 100 can be an encoder, a flow sensor, a magnetic force sensor, or a distance sensor.

[0082] In the case where the detection sensor 100 is an encoder, it outputs a pulse signal to the control unit 70 every time the tube pump 20 rotates by 120°. Thus, the position of the roller 21 can be checked.

[0083] In the case where the detection sensor 100 is a flow sensor, the position of the roller 21 can be confirmed from the flow rate of the flush liquid flowing in the vicinity of the tube pump 20.

[0084] Next, the measurement method of the measuring apparatus 3 according to the modification 2 will be described. The measurement method of the measuring apparatus 3 according to the modification 2 is the same as the step of forming an air layer between the flush liquid and the blood sample in the measurement method of the measuring apparatus 2 according to the modification 1.

[0085] After the air layer is formed between the flush liquid and the blood sample, the control unit 70 closes the valve 40 and opens the on-off valve 90. Subsequently, based on the information obtained by the detection sensor 100, the control unit 70 initializes the position of the roller 21 by driving the tube pump 20. By initializing the position of the roller 21 in this way, the blood sample can be moved forward and backward correctly by rotating the tube pump 20 in the forward and reverse directions.

[0086] Subsequently, the control unit 70 opens the valve 40 and closes the on-off valve 90. Subsequently, the control unit 70 starts the blood suction to the detection unit 70 and the forward and backward movement of the blood. The following steps are the same as in the measurement method of the measuring apparatus 2 according to the modification 1.

[0087] The present disclosed subject matter is not limited to the above-described embodiments and modifications, and various modifications can be made within the scope of the claims.

[0088] For example, it is possible to adopt a configuration in which the valve 40 used in the above-described modification example is provided as a three-way valve connected to the detection unit 50, the tube pump 20, and the initialization flow passage 80. This configuration can simplify the measurement device.

[0089] Although two irradiation units 51 and two light detection units 52 are provided in the above-described embodiment, three irradiation units 51 and three light detection units 52 can be provided. As a further alternative, one irradiation unit 51 and one light detection unit 52 can be provided.

[0090] Although the measurement device 1 according to the above-described embodiment is provided with the sensor 60, the measurement device does not necessarily always have to be provided with the sensor 60.

[0091] In the above-described embodiment, each light detection unit 52 detects the intensity of transmitted light transmitted from the blood sample. Alternatively, each light detection unit can detect the intensity of reflected light reflected from the blood sample.

[0092] Although a tube pump is used as an example pump in the above-described embodiment, another type of pump can be used.

[0093] Although the nozzle is provided separately from the storage unit 10 in the above-described embodiment, the nozzle can be integrated with the storage unit.

[0094] This application claims priority from Japanese Patent Application No. 2020-014053 filed on January 30, 2020, the entire contents of which are incorporated herein by reference.

Claims

1. A measuring apparatus for measuring erythrocyte aggregation of a blood sample, comprising: a storage unit in which a blood sample and a washing liquid are selectively stored; a pump which draws the blood sample from the storage unit; a flow channel which communicates with the storage unit and through which the blood sample and the washing liquid flow when drawn by the pump; a detection unit which includes an irradiation unit that irradiates the flow channel with light and a light detection unit that detects light that has been emitted from the irradiation unit and has transmitted through or reflected from the flow channel; a sensor which is arranged between the storage unit and the detection unit and detects a switch from liquid to gas in the flow channel; and a control unit which controls a stop of driving of the pump in response to detection by the sensor. The control unit stops the pump after an air layer has entered the flow channel is detected by the sensor after the washing liquid stored in the storage unit moves to the flow channel.

2. The measuring device of claim 1, wherein, When the sensor does not detect the washing liquid or an air layer while the pump continues to draw the washing liquid, the control unit determines that the flow channel is clogged or that the washing liquid is cut off.

3. The measuring device of claim 2, wherein, 4. The measuring apparatus according to any one of claims 1 to 3, wherein: the pump is a tube pump; and the measuring apparatus further includes a valve which stops delivery of the blood sample by shutting off or switching the flow channel in a state in which the blood sample has a flow rate in the flow channel. The control unit stops the pump after switching the valve to shut off the flow channel.

5. The measuring device of claim 4, wherein, 6. The measuring apparatus according to any one of claims 1 to 3, wherein: a plurality of the irradiation units and a plurality of the light detection units are provided, and the control unit compares transmitted light intensity-time curve waveforms obtained by the plurality of the light detection units. The sensor is at least one of an impedance sensor and an optical sensor.

7. The measuring device according to any one of claims 1 to 3, wherein, 8. The measuring apparatus according to any one of claims 4, wherein: the pump is a tube pump; and the measuring apparatus further includes: an initialization flow channel which is provided to branch at a position between the valve and the tube pump; an on-off valve which is arranged in the initialization flow channel and switches opening and shutting of the initialization flow channel; and a detection sensor which detects whether a roller of the tube pump is positioned at a predetermined position. The detection sensor is at least one of an encoder and a flow sensor.

9. The measuring device of claim 8, wherein, The valve is a three-way valve which is connected to the detection unit, the tube pump, and the initialization flow channel.

10. The measuring device of claim 8, wherein, 11. The measuring apparatus according to any one of claims 1 to 3, further comprising a temperature adjustment unit which adjusts a temperature of the blood sample in the flow channel to a predetermined temperature. The control unit acquires the blood sample from a blood collection tube through a nozzle and supplies the blood sample to the storage unit in response to the stop of driving of the pump.

12. The measuring device of claim 1, wherein, ​ 13. A measurement method of a measurement apparatus for measuring erythrocyte aggregation of a blood sample, the measurement apparatus comprising: a storage unit in which a blood sample and a flushing liquid are selectively stored; a pump that draws the blood sample from the storage unit; a flow channel that communicates with the storage unit and through which the blood sample and the flushing liquid flow when drawn by the pump; a detection unit that includes an irradiation unit that irradiates the flow channel with light and a light detection unit that detects light that has been emitted from the irradiation unit and has transmitted through or reflected from the flow channel; a sensor that is arranged between the storage unit and the detection unit and detects a switch from a liquid to a gas in the flow channel; and a control unit that controls a stop of driving of the pump, wherein: the measurement method includes stopping the pump after a switch from the liquid to the gas in the flow channel is detected by the sensor after the flushing liquid stored in the storage unit moves to the flow channel. the sensor detects a switch from the flushing liquid to the gas in the flow channel, and 14. The measuring method according to claim 13, wherein, the measurement method includes stopping the pump after a switch from the flushing liquid to the gas in the flow channel is detected by the sensor after the flushing liquid stored in the storage unit moves to the flow channel. the control unit acquires the blood sample from a blood collection tube through a nozzle and supplies the blood sample to the storage unit in response to the stop of driving of the pump.

15. The measuring method according to claim 13, wherein, an impedance sensor is used as the sensor.

16. The measuring method according to claim 13, wherein, ​

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