JP2019042089A - Liquid discharge device and measurement tape - Google Patents

Abstract

To provide a liquid discharge device capable of suppressing a liquid from being left in a channel after sampling, and excellent in portability.SOLUTION: A liquid discharge device comprises: a main channel; a sub channel branched from the main channel; two restriction members for restricting circulation of a liquid between a range between two points on the main channel and outside of the range; and a first pressing member for pressing the main channel between the two points, in a state of restricting circulation of the liquid on the main channel. The sub channel causes the liquid from the main channel to pass in pressing by the first pressing member, and does not cause the liquid from the main channel to pass, in non-pressing time by the first pressing member.SELECTED DRAWING: Figure 5

Description

  The present invention relates to a liquid ejection device and a measuring tape.

  Conventionally, drainage is performed to discharge liquid or gas stored in a patient's body to the outside of the body after surgery or the like. With respect to this drainage, there is a device for sampling the liquid in the body in order to analyze the liquid stored in the body.

  As a device for sampling a liquid, Patent Document 1 discloses a dispensing device having a roller-type specimen suction mechanism. This dispensing apparatus moves the liquid container containing the specimen, lowers the tube nozzle, and performs suction after putting the tube tip into the specimen. At this time, the tube squeezing roller is rotated toward the suction side by a desired suction set amount. The tube is moved and restored so that the portions sandwiched between the tube squeezing rollers are sequentially released, and the inside of the tube is depressurized to suck up the serum.

  Patent Document 2 discloses a blood component preparation container for collecting a predetermined amount of blood. The blood component preparation container is slidably disposed on the inner peripheral surface of the outer cylinder, and a partition member that divides the outer cylinder into a fluid storage chamber and a gas inlet / outlet chamber slides by magnetic force to move blood. . The blood collected through the voting tube by sliding the partition member is aseptically stored in the fluid storage chamber. The serum prepared in the fluid storage chamber is led out to the component storage container through the connecting tube.

  Further, Patent Document 3 discloses a liquid collection system that separates and collects liquids to be measured in time series. This liquid collection system is provided in the middle of the flow path through which the liquid to be measured flows, and separates and extracts the liquid to be measured in time series by inserting a liquid different from the liquid to be measured as a separator.

JP 7-260640 A JP 2009-95657 A Japanese Patent No. 5564489

  The dispensing device described in Patent Document 1 has quantitativeness and continuity, but is a large device and difficult to carry. That is, it is insufficient for miniaturization and portability. The blood component preparation container described in Patent Document 2 is quantitative and portable. However, since blood is collected by sliding the partition member, the liquid remains in the secondary path such as the voting tube and the connecting tube. There was concern. The liquid collection system described in Patent Document 3 has quantitativeness and continuity, but is a large-scale device, difficult to carry, and insufficient in size and portability.

  The present invention has been made in view of the above-described circumstances, and provides a liquid ejection device and a measuring tape that are excellent in portability and can suppress liquid from remaining in a flow path after sampling.

  One aspect of the present invention is a liquid ejection device that ejects liquid, and includes a main channel, a sub-channel branched from the main channel, a range between two points in the main channel, and an outside of the range. Two restricting members that restrict the flow of the liquid between them, and a first pressing member that presses the main flow path between the two points in a state where the flow of the liquid is restricted in the main flow path. The sub-flow path allows the liquid from the main flow path to pass when pressed by the first pressing member, and does not allow the liquid from the main flow path to pass when not pressed by the first pressing member. A liquid ejection device.

  One aspect of the present invention includes a blood cell separation membrane that separates the blood cells and the non-blood cells from a drainage fluid discharged from a living body and containing blood cells and non-blood cells, and the non-blood cells separated by the blood cell separation membrane. A measurement tape having an enzyme reaction sheet that reacts with an enzyme and a spacer that has an opening and is disposed between the blood cell separation membrane and the enzyme reaction sheet.

  According to this invention, it is excellent in portability and it can suppress that a liquid remains in a flow path after sampling.

The figure which shows schematic structure of the drain drainage management system in embodiment Diagram showing the internal configuration of the drainage sensor Block diagram showing the circuit configuration of the sensor unit Diagram showing the shape of the drain bag Partially broken perspective view showing appearance of drain drainage monitor Diagram for explaining the operation of the drainage sampling mechanism Flow chart showing drain sampling operation procedure The graph which shows the measurement result of the weight for every sampling at the time of using distilled water as a 1st verification result Table showing sampling results Diagram showing schematic configuration of drainage sampling mechanism The graph which shows the measurement result of the weight for every sampling at the time of adjusting sampling amount and using distilled water as a 2nd verification result Table showing sampling results Diagram illustrating preparation of mouse tissue pulverization fluid Enlarged view showing the vicinity of the branch point of the main tube when the subtube has no opening Enlarged view showing the vicinity of the branch point of the main tube when the subtube has an opening The graph which shows the measurement result of the weight for every sampling in the case where it does not have a subtube with an opening part The average [g], standard deviation, and C. of the tissue pulverized solution shown in the graph of FIG. Table showing V value [%] Sectional view showing the structure of the measuring tape Diagram explaining how blood cells are separated and enzymatic reaction is performed using a measuring tape The figure explaining a mode that blood-cell separation and an enzyme reaction are performed using the measuring tape following FIG. 12B Table showing characteristics of various materials used for blood cell separation membrane The figure explaining the method of infiltrating a tissue grinding | pulverization liquid along the surface of a blood cell separation membrane, and isolate | separating a blood cell Graph showing the correlation between changes in absorbance due to membrane separation and changes in absorbance due to centrifugation Diagram illustrating the standard method for measuring amylase activity Diagram illustrating the osmotic filtration method for measuring amylase activity Diagram explaining the transcription method for measuring amylase activity Graph showing measurement results of amylase activity by standard method Graph showing the measurement results of amylase activity by osmotic filtration Graph showing measurement results of amylase activity by transcription method Flow chart showing measurement procedure of amylase activity Diagram showing drain drain monitor display Sectional view showing the structure of the measuring tape Diagram explaining the measurement method of bilirubin using a spectrophotometer Diagram explaining the measurement method of bilirubin using membrane measurement Graph showing the measurement results of bilirubin using the standard method Graph showing the measurement result of bilirubin when using membrane measurement Diagram showing the structure of a measuring tape that can measure both amylase and bilirubin status The perspective view which shows the structural example of a 3rd press member. AA sectional view showing an example of the state of the third pressing member and the main tube in the state α of the third pressing member. AA sectional view showing an example of the state of the third pressing member and the main tube in the state β of the third pressing member AA sectional view showing an example of the state of the 3rd press member and the main tube in state γ of the 3rd press member The figure explaining introducing biological fluid containing a medicine etc. into patient PA1 by TCI pump 10A

  Hereinafter, embodiments of a liquid ejection device and a measuring tape according to the present invention will be described with reference to the drawings. In the present embodiment, a drain drainage management system including a liquid ejection device and a measurement tape is shown. The drainage management system measures the state of the management target component contained in the drainage drainage flowing through the drainage drain tube connected to the patient's body, and performs various observations and evaluations on the drainage state.

  Drain drainage is a liquid containing blood accumulated in the body, exudate, and the like that is discharged outside the body after surgery. When digestive surgery is performed, amylase, a digestive enzyme, and bilirubin, a bile pigment, may come out of the affected area. These components damage organs and dissolve blood vessels, so that bleeding is likely to occur and can be a risk of complications. Therefore, measuring the state of the management target component contained in the drainage drainage is a big index when the medical staff examines the next medical practice. For example, it is conceivable to measure the state of amylase, bilirubin, and blood as management target components in the drainage.

(Drain drainage management system configuration)
FIG. 1 is a diagram showing a schematic configuration of a drain drainage management system 5 in the embodiment. The drain drainage management system 5 includes a non-contact drain drain sensor 10, a drain drain monitor 20, a drain tube 30, and a drain bag 40. The drainage sensor 10 is used to measure the state of management target components (for example, blood, amylase, bilirubin), which are management target components in drainage drainage flowing through the transparent drain tube 30. That is, the drain liquid sensor 10 is an example of a measuring device. As a component to be managed, amylase is a digestive enzyme secreted from the pancreas and salivary glands. Bilirubin is a yellow pigment component contained in bile. Blood is bleeding from organs and blood vessels.

  The drain drain monitor 20 is connected to the drain drain sensor 10 by wireless communication or wired communication, and records / displays the measurement result by the drain drain sensor 10. A display 21 for displaying various information is arranged on the front surface of the drainage drain monitor 20.

  The drain tube 30 distributes drainage drained from the patient's body and flows it to the drain bag 40. The drain tube 30 is formed of a material such as a translucent resin so that the user can visually observe the drainage. One end of the drain tube 30 is connected (inserted) to the patient's body, and the other end of the drain tube 30 is connected to the drain bag 40. The drain bag 40 stores the drainage drained from the drain tube 30.

  It should be noted that the drainage liquid stored in the drain bag 40 includes the waste that flows from the start of drainage to the time of measurement. Therefore, it is difficult to measure the state of the management target component in the drainage that changes with the passage of time by using the drainage in association with the time.

  For this reason, in the drainage management system 5, the state of the management target component in the drainage is measured using the drainage flowing through the drain tube 30 connected between the patient's body and the drain bag 40. It was to be. By this method, the drainage management system 5 can measure non-invasively to the patient.

  FIG. 2A is a diagram showing an internal configuration of the drain liquid discharge sensor 10. The drainage drain sensor 10 has, for example, a box-shaped housing 10z, and houses a drainage sampling mechanism 110 and a blood cell separation / enzyme reaction mechanism 150 in the housing 10z.

  In the drainage sampling mechanism 110, a main tube 130 (an example of a main flow path) is attached so as to penetrate the inside of the housing 10z. In FIG. 2A, the main tube 130 is provided in the left-right direction. Both ends of the main tube 130 may protrude from through holes 10y formed on both side surfaces of the housing 10z, and may be connected to both ends of the drain tube 30. The main tube 130 may be a part of the drain tube 30.

  A sub tube 133 (an example of a sub flow path) branched from the main tube 130 is connected to the approximate center of the main tube 130. Here, the position of the main tube 130 to which one end of the sub tube 133 is connected is also referred to as a branch point. The sub tube 133 has an elongated flow path 133 z that can communicate with the inside of the main tube 130. The branch point may be a connection position between the sub-tube 133 and the flow path 133z. The sub-tube 133 may be formed of an elastic material (rubber, resin, etc.) or may be a material that recovers elasticity. The sub tube 133 is deformed within a range where it is elastically deformed, and is not deformed within a range where it is plastically deformed. The elongated channel 133z is normally closed. Since the flow path 133z is normally closed, the drainage liquid Lq in the main tube 130 does not flow into the flow path 133z of the subtube 133, and the liquid in the flow path 133z of the subtube 133 is also transferred to the main tube 130. There is no backflow. Moreover, gas does not flow in from the opposite side (the lower side of FIG. 2S) of the sub tube 133 to the main tube 130 side.

  When viewed from the main tube 130, the sub tube 133 can be said to be a protruding portion formed to protrude in the middle of the main tube 130. It can also be said that a cut is formed as a flow path 133z in the protruding portion.

  The drainage sampling mechanism 110 includes a pair of limiting members 113 and 114 and a first pressing member 115 in addition to the main tube 130 and the subtube 133.

  The pair of limiting members 113 and 114 includes partition plates 113B and 114B, and pressurizing units 113A and 114A, each having a curved tip. The partition plates 113B and 114B driven by the pressurizing units 113A and 114A move so as to press on both sides (for example, two points) sandwiching the branch point of the main tube 130, respectively. The pair of restricting members 113 and 114 can press portions on both sides of the main tube 130 with the branch point of the sub tube 133 interposed therebetween. When the pair of restricting members 113 and 114 press the portions on both sides of the main tube 130 substantially simultaneously, the drain liquid Lq is restricted to the main tube 130, for example, it does not flow. Therefore, the drainage liquid Lq stays in the tube center portion 130c of the main tube 130 located in the vicinity of the branch point. The tube center part 130c may be a region between two points pressed by the limiting members 113 and 114, for example.

  The first pressing member 115 includes a pressing plate 115B having a flat plate along the longitudinal direction of the main tube 130, and a pressurizing unit 115A. The pressing plate 115B driven by the pressurizing unit 115A moves so as to press the main tube 130. When the first pressing member 115 presses the main tube 130, the pressure of the drainage liquid Lq staying in the tube center portion 130c of the main tube 130 that is blocked by the pair of limiting members 113 and 114 increases.

  When the pressure of the drain drainage liquid Lq in the pipe center portion 130c increases, the flow path 133z of the sub tube 133 is opened, and the drain drainage liquid Lq staying in the pipe central portion 130c flows into the flow path 133z of the sub tube 133. . The drainage fluid that has flowed into the flow path 133z of the sub-tube 133 flows out so as to be pushed out from the opposite end face of the flow path 133z. The drainage liquid Lq that has flowed out from the end face on the opposite side of the flow path 133z is dropped as a sampling liquid sq (see FIG. 12B) onto the measuring tape 200 that is disposed so as to face the subtube 133.

  The pressurizing units 113A, 114A, 115A, and 116A (described later) move the partition plates 113B and 114B, the pressing plate 115B, and the front end portion 116B in the forward and backward directions, respectively, according to the drive signal from the sensor unit 180. For example, when the pressurizing unit is configured by a motor gear mechanism, the partition plates 113B and 114B, the pressing plate 115B, and the tip portion 116B move straight by driving the motor. The pressurizing unit is not limited to the motor gear mechanism, and may be configured by an electromagnetic slide mechanism, a piezoelectric element, a hydraulic slide mechanism, or the like.

  The blood cell separation / enzyme reaction mechanism 150 separates blood cells contained in the drainage effluent Lq, reacts the enzyme with a reagent, and optically measures the absorbance of the enzyme. The blood cell separation / enzyme reaction mechanism 150 may optically measure the absorbance of components to be managed (for example, blood cells and bilirubin) other than the enzyme. The blood cell separation / enzyme reaction mechanism 150 includes a second pressing member 116, a tape take-up and feeding mechanism 170, and a sensor unit 180.

  The second pressing member 116 includes, for example, a tip portion 116B having a round tip and a pressure unit 116A. The tip 116B driven by the pressurizing unit 116A moves forward and backward so as to press the measuring tape 200. When the measurement tape 200 is pressed, the reaction between the enzyme and the reagent contained in the sampling solution sq dropped onto the measurement tape 200 may be performed. Details of the operation of reacting the enzyme with the reagent using the measuring tape 200 will be described later.

  The tape take-up feed mechanism 170 includes a measurement tape 200 to which the sampling liquid sq is dropped, a feed reel 171 around which an unused measurement tape 200 is wound, and a take-up reel around which the measurement tape 200 after reaction is taken up. 172. Further, the tape take-up feed mechanism 170 includes a motor 175 that drives the take-up reel 172 and rollers 177 and 176 that guide the movement of the measuring tape 200. The take-up reel 172 is rotated by driving the motor 175 and takes up the measuring tape 200 after the reaction. The feed reel 171 rotates with the movement of the measuring tape 200.

  Here, the take-up reel 172 is rotated so as to take up the measuring tape. However, each of the take-up reel 172 and the feed reel 171 is driven by a motor, and the measuring tape 200 is taken up and fed simultaneously. In other words, the movement of the measuring tape 200 can be further stabilized. Alternatively, only the feed reel 171 may be driven by a motor, and the take-up reel 172 may be rotated.

  The sensor unit 180 is disposed so as to face the drainage sampling mechanism 110 with the measurement tape 200 interposed therebetween. The sensor unit 180 optically measures the absorbance of the enzyme contained in the sampling solution sq2 (see FIG. 12B) that has penetrated into the measuring tape 200 delivered by the tape take-up feed mechanism 170. In this measurement, the sensor unit 180 projects light having a predetermined wavelength (for example, a wavelength of 410 nm) as a measurement light toward the measuring tape 200 into which the sampling liquid sq2 containing a large amount of enzyme has permeated. The sensor unit 180 may receive light scattered without being absorbed by the enzyme in the sampling liquid sq2, and measure the absorbance of the enzyme contained in the sampling liquid sq2 based on the amount of scattered light received.

  FIG. 2B is a block diagram showing a circuit configuration of the sensor unit 180. The sensor unit 180 has a housing 180z in which a circuit board 188 is laid. The sensor unit 180 includes a CPU (Central Processing Unit) 181, an LED (Light Emitting Diode) 182, a photo sensor (PD) 183, a wireless chip 184, and a battery 185. A CPU 181, a photosensor 183, and an LED 182 are mounted on the circuit board 188.

  The CPU 181 controls the operation of each unit in the sensor unit 180. The CPU 181 may perform various arithmetic processes such as calculating the absorbance based on the amount of light received from the photosensor 183. The CPU 181 includes functions as a pressure unit driving unit 186 and a motor driving unit 187. The pressurizing unit driving unit 186 outputs driving signals to the pressurizing units 113A, 114A, 115A, and 116A, respectively. The motor drive unit 187 outputs a drive signal to the motor 175 that rotates the take-up reel 172. The CPU 181 has a timekeeping function, and may measure a sampling time or a measurement time.

  The CPU 181 generates measurement data (an example of first information) such as absorbance. The measurement data is data related to the management target component (for example, blood, amylase, bilirubin). The measurement data may be managed in association with the time when the measurement data is measured. The measurement data may include, for example, information on the absorbance of the management target component and the amount of change in absorbance. The measurement data may include information on the discharge amount of the management target component per unit time. The measurement data may include information on the total emission amount of the management target component. The discharge amount of the management target component may be the discharge amount of the management target component flowing through the main tube 130 or the discharge amount (sampling amount) of the management target component sampled via the sub-tube 133. Good.

  The LED 182 emits light having a predetermined wavelength (for example, a wavelength of 410 nm) as a peak value as measurement light. The photosensor 183 receives light scattered without being absorbed by the management target component such as amylase, and outputs a signal corresponding to the amount of received light.

  The wireless chip 184 performs wireless communication with the drain drain monitor 20 and transmits various data measured by the sensor unit 180 to the drain drain monitor 20. For the wireless communication, communication such as short-range wireless communication (Bluetooth (registered trademark), ZigBee (registered trademark), etc.) or wireless LAN (Local Area Network) can be used. The battery 185 supplies power to each part of the sensor unit 180. The battery 185 may be a secondary battery such as a rechargeable lithium ion battery or a primary battery such as an alkaline battery.

  FIG. 3 is a view showing the shape of the drain bag 40. The drain bag 40 is a bag for storing drainage liquid. The drain bag 40 is provided with an inflow tube 41 through which drain drainage flows. The tip of the inflow tube 41 is connected to one end of the drain tube 30. Note that the inflow tube 41 may be a part of the drain tube 30. The drainage drained from the drain tube 30 flows into the drain bag 40 and is stored therein. Further, since the inside of the drain bag 40 is maintained at a negative pressure, even if the tip of the inflow tube 41 is connected to one end of the drain tube 30, the drainage drained in the drain bag 40 does not flow back to the drain tube 30. . In addition, maintaining the negative pressure also prevents infection of patients who drain drainage fluid.

  Here, the main tube 130 is connected to the drain tube 30, and the sub tube 133 branches from the main tube 130. A flow path 133z is formed in the sub-tube 133 in order to sample and extract the drainage liquid Lq. However, the sub-tube 133 basically closes the flow path 133z when the drain liquid Lq does not pass through. Therefore, the subtube 133 can suppress the entry of air or the like from the flow path 133z to the main tube 130 side (drain tube 30 side). Therefore, even if the drain drain sensor 10 includes the main tube 130 and the sub tube 133, it is possible to suppress the entry of air or the like from the sub tube 133 and maintain the negative pressure of the drain bag 40. Therefore, it is possible to suppress the drain drainage stored in the drain bag 40 from flowing back into the drain tube 30. In addition, even after one week with the drain drain sensor 10, the drain tube 30, and the drain bag 40 connected, it was confirmed that almost no gas such as air was mixed in the drain bag 40. .

  FIG. 4 is a partially broken perspective view showing the appearance of the drainage drain monitor 20. The drainage drain monitor 20 has a box-shaped housing 20z. A display 21 is disposed on the front surface of the housing 20z. The display 21 is notified of a graph 22 representing the measurement result over time, various explanatory texts 23 such as the name of the patient, a meter 24 representing the current value of the measurement result, and the patient status (normal / abnormal). A state marker 25 and the like are displayed.

  The drain drain monitor 20 includes a CPU 26 that performs various controls of the drain drain monitor 20, a memory 27 that records measurement data of the drain drain sensor 10, and wireless communication with the wireless chip 184 of the drain drain sensor 10. A wireless chip 28 for performing the above is provided.

  The drain drain monitor 20 includes an internal clock (not shown), and the measurement data measured by the drain drain sensor 10 (specifically, the sensor unit 180) and the time when the measurement data was measured. Are recorded in the memory 27 in association with each other. The measurement data may include information on the discharge amount of the management target component per unit time. The information regarding the discharge amount of the management target component per unit time of the drainage liquid Lq includes, for example, information on the absorbance of the management target component (for example, amylase, bilirubin, blood) and the amount of change in absorbance per unit time. Good. The graph 22 is displayed based on time series data (an example of the second information) recorded in the memory 27 so as to represent a change with time of the measurement result. The measurement data may be information related to the total discharge amount of the management target component.

  The CPU 26 may register (hold) some or all of the time-series data recorded in the memory 27 and at least one of the display results of the graph 22 in the electronic medical record for each patient. The electronic medical record may be stored in the memory 27, or may be stored in a server (not shown) separate from the drain drain monitor 20. When the electronic medical record is stored in the server, the drain drainage monitor 20 can be configured to be able to register with the electronic medical record and view the electronic medical record by communicating with the server through the wireless chip 28.

(Operation of drain sampling mechanism)
Details of the operation of the drain sampling mechanism 110 will be described. FIG. 5 is a diagram for explaining the operation of the drainage sampling mechanism 110. In a no-pressure state (state A) in which the main tube 130 is not pressed, a liquid (for example, drainage liquid or distilled water) flows in the main tube 130.

  First, the restricting members 113 and 114 press the main tube 130 substantially simultaneously to restrict the flow of the liquid (state B). The pipes on both sides of the main tube 130 sandwiching the branch point, that is, the pipe center part 130c are closed by the partition plates 113B and 114B (see state B in FIG. 5). This restricts the flow of liquid inside and outside the tube central portion 130c. The liquid may flow slightly without being completely blocked. A certain amount of liquid between the limiting members 113 and 114 stays in the tube central portion 130c. In the state B, the flow path 133z of the sub tube 133 is closed, and the flow path 133z does not allow liquid to pass through.

  The first pressing member 115 presses the tube central portion 130c of the main tube 130 in a state where the restricting members 113 and 114 press the main tube 130 substantially simultaneously and the liquid stays in the tube central portion 130c of the main tube 130 ( State C). When the tube center portion 130c is pressed, the pressure of the liquid staying in the tube center portion 130c of the main tube 130 increases. Due to the increase in the pressure of the liquid, the flow path 133z of the sub tube 133 connected to the main tube 130 at the branch point is expanded. The liquid staying in the tube central portion 130 c of the main tube 130 flows into the flow path 133 z of the subtube 133 and flows out from the end face on the opposite side of the subtube 133. When almost all of the liquid flows out, the tube central portion 130c of the main tube 130 is depressed. As a result, a certain amount of liquid staying between the limiting members 113 and 114 can be sent out via the sub-tube 133. Therefore, in the state C, the flow path 133z of the sub tube 133 is opened, and the flow path 133z allows liquid to pass through.

  In a state where the first pressing member 115 presses the tube central portion 130c of the main tube 130, the restricting members 113 and 114 stop the pressing and exclude the two sides (two locations) sandwiching the branch point of the main tube 130. Pressure (state D). Further, when the first pressing member 115 releases the pressing of the tube center portion 130c, the main tube 130 returns to the state A and enters a no-pressure state. In addition, by being in the state A following the state D, it is possible to suppress the backflow of liquid from the sub tube 133 to the main tube 13 due to a decrease in the pressure in the tube center portion 130c.

  Further, when the state B is further changed to the state B after the state A, a new fixed amount of liquid flowing through the main tube 130 stays and can be secured.

  By repeating the states A to D, the drainage sampling operation can be continuously performed and a certain amount of liquid can be extracted. The drain sampling operation by the drain sampling mechanism 110 is not limited to the drain drain Lq, but can be applied to various liquids as the liquid sampling operation by the liquid sampling mechanism.

  FIG. 6 is a flowchart showing a drain sampling operation procedure by the drain drain sensor 10. The CPU 181 waits until the sampling time comes (S1). The sampling time is set to an appropriate time, for example, once an hour. When the sampling time comes, the CPU 181 outputs a drive signal to the pressure units 113A and 114A, and starts pressing by the limiting members 113 and 114 (S2). When the portions on both sides of the main tube 130 sandwiching the branch point are pressed by the restricting members 113 and 114, the tube central portion 130c of the main tube 130 is blocked by the partition plates 113B and 114B. The liquid stays in the tube central portion 130 c of the main tube 130.

  In a state where the pressing by the limiting members 113 and 114 is maintained, the CPU 181 outputs a driving signal to the pressing unit 115A and starts pressing by the first pressing member 115 (S3). When the tube center portion 130c of the main tube 130 is pressed, the pressure of the liquid staying in the tube center portion 130c increases. Due to the increase in the pressure of the liquid, the flow path 133z of the sub-tube 133 is expanded. The liquid staying in the tube central portion 130c of the main tube 130 passes through the flow path 133z of the sub tube 133 and flows out from the end face on the opposite side of the flow path 133z. When almost all of the liquid flows out, the tube central portion 130c of the main tube 130 is in a recessed state.

  The CPU 181 outputs a drive signal to the pressure unit 115A, stops the drive signal to the pressure units 113A and 114A while maintaining the pressing operation by the first pressing member 115, and removes the pressure by the restriction members 113 and 114. Is started (S4). Even if the depressurization by the limiting members 113 and 114 is performed, the state where the tube central portion 130c of the main tube 130 is recessed is maintained.

  The CPU 181 stops the drive signal to the pressurizing unit 115A and starts the pressure removal by the first pressing member 115 (S5). When the pressure releasing operation by the first pressing member 115 is performed, the pressure returns to the non-pressure state, and the liquid flows through the tube center portion 130 c of the main tube 130. The direction in which the liquid flows is the direction from the patient side toward the drain bag 40.

  According to such a drain sampling operation procedure, the drain drainage management system 5 can control the states A to D and easily transition the states A to D. Thereby, the drainage management system 5 can sample the drainage quantitatively and continuously.

(Verification of drain sampling operation)
Next, a first verification result of the drainage sampling operation by the drainage sampling mechanism 110 is shown. In the first verification operation, first, using the distilled water instead of the drain waste liquid Lq, the drain sampling operation was repeatedly performed to examine the change in the sampling amount. FIG. 7A is a graph showing the measurement result of the weight for each sampling when distilled water is used as the first verification result. The vertical axis of the graph indicates the sampling amount (g), and the horizontal axis indicates the number of samplings. In the case of distilled water, 1 g corresponds to 1 ml (milliliter). A graph shows the case where sampling of distilled water was performed 16 times. The sampling amount is in the range of 0.3 g to 0.6 g. FIG. 7B is a table showing sampling results. In this table, average value: 0.46 g, standard deviation: 0.07, C.I. V (coefficient of variation): 15.8% is indicated.

  From the first verification result, it can be understood that when distilled water is used, the drainage sampling mechanism 110 can stabilize the sampling amount to a constant amount (having quantitativeness) and can continuously sample.

  Subsequently, a second verification result of the drainage sampling operation in the drainage sampling mechanism 110 is shown. In the second verification operation, as in the first verification operation, distilled water was used, the sampling amount was set in three ways, the drain sampling operation was repeated, and the change in the sampling amount was examined.

  FIG. 8A is a diagram showing a schematic configuration of the drainage sampling mechanism 110. The amount of sampling was adjusted by changing the internal volume of the tube central portion 130c of the main tube 130. That is, by changing the distance (distance) L between the restricting members 113 and 114, the internal volume of drain drainage or the like in the tube central portion 130c of the main tube 130 is changed. The interval L may be set in the range of 10 mm to 50 mm. Further, the length of the pressing plate 115B of the first pressing member 115 may be adjusted to be equal to the length of the interval L so that the tube central portion 130c can be pressed uniformly.

  FIG. 8B is a graph showing the measurement results of the weight for each sampling when the sampling amount is adjusted and distilled water is used as the second verification result. The vertical axis of the graph indicates the sampling amount (g), and the horizontal axis indicates the number of samplings. A graph g11 shows a change in the sampling amount when the interval L is 50 mm. A graph g12 shows a change in the sampling amount when the interval L is 24 mm. A graph g13 shows a change in the sampling amount when the interval L is 20 mm.

  FIG. 8C is a table showing sampling results. In this table, when the interval L is 50 mm, the average value: 0.48 g, the standard deviation: 0.02, C.I. V: 5.2% is indicated. When the distance L is 24 mm, the average value: 0.22 g, the standard deviation: 0.033, C.I. V: 15.2% is indicated. When the distance L is 20 mm, the average value: 0.55 g, the standard deviation: 0.0065, C.I. V: 12.0% is indicated.

  According to the second verification result, when distilled water is used, the drainage sampling mechanism 110 can stabilize the sampling amount to a constant amount (having quantitativeness) and can continuously sample at any sampling amount. I understand that. Further, it can be understood that the sampling operation can be stably performed even with a sampling amount of 100 μl (0.1 g in the case of distilled water) or less.

(Consideration on pressure in drain sampling operation)
Next, the force applied to the flow path 133z of the subtube 133 when performing the drain sampling operation will be considered. When sampling the liquid flowing through the main tube 130, it is necessary to satisfy Expression (1) as a sampling condition.
P2 <P <P1 (1)

  P1 is a pressing force by which the partition plates 113B and 114B of the limiting members 113 and 114 press the main tube 130, respectively. P is an internal pressure of the liquid that is partitioned by the limiting members 113 and 114 and stays in the tube central portion 130 c of the main tube 130. P2 is an opening force P21 that opens the flow path 133z of the sub-tube 133, or a resistance force P22 when a liquid flows through the flow path 133z.

  Therefore, P1> P indicates that the limiting force by the limiting members 113 and 114 is a force that can maintain the liquid flow limitation in the main tube 130 even when pressed by the first pressing member 115. P> P2 indicates a force with which the pressing force by the first pressing member 115 can pass the liquid through the sub-tube 133.

  In order to perform the drainage sampling operation stably, it is conceivable to make the pressing force P1 higher than the internal pressure P and to make the opening force P21 and the resistance force P22 low. Here, the opening force P21 may be decreased without increasing the pressing force P1 more than necessary. In this case, it is possible to suppress a large pressing force P1 from being repeatedly applied to the main tube 130, and it is possible to suppress deterioration of the main tube 130.

When the flow path 133z is closed, that is, when P2> P, P2 is the opening force P21. The opening force P21 may be represented by Expression (2). c: length of crack, Gc: energy release rate, E: Young's modulus.

  Referring to equation (2), it can be understood that the opening force P21 decreases as the crack length increases. Therefore, if an opening 133b (see FIG. 10B) is provided as a crack at a position where the sub tube 133 is connected to the main tube 130, the liquid easily flows into the flow path 133z of the sub tube 133, that is, necessary for sampling. The pressing force by the first pressing member 115 can be small. The opening 133b may be an opening having a larger cross-sectional area than the flow path 133z even in a normal state (when the first pressing member 115 is not pressed). In addition, the longer the length of the opening 133b in the direction along the flow path 133z, the easier the liquid flows into the flow path 133z of the subtube 133, and the pressing force by the first pressing member 115 necessary for sampling is smaller. I'll do it.

Moreover, when the liquid is flowing through the flow path 113z, that is, when P2 <P, P2 is the resistance force P22. The resistance force P22 may be expressed by Expression (3). ε: strain, L: flow path length, λ: friction coefficient, ρ: density, v: flow velocity.

  Next, the drainage sampling operation is verified using the biological tissue grinding liquid. Here, a case where a mouse is used as a living body is shown.

(Collecting tissue grinding fluid)
FIG. 9 is a view for explaining preparation of a mouse tissue pulverizing solution. The mouse tissue pulverization solution was prepared by the following procedure. The intestinal tissue sp1 is taken out from the mouse ms1 and immersed in the physiological saline ws1 contained in the container 310. Thereafter, the container 310 in which the intestinal tissue sp1 is immersed in the physiological saline ws1 is set in the homogenizer 300. The homogenizer 300 pulverizes the intestinal tissue sp1 immersed in the physiological saline ws1 contained in the container 310, and disperses the pulverized intestinal tissue sp1 in the physiological saline. Various types of homogenizers can be used, such as an ultrasonic type that pulverizes the tissue by ultrasonic cavitation, an agitation type that pulverizes the tissue by stirring, and a high-pressure type that pulverizes the tissue by applying pressure to the tissue. The tissue fragment mz is dispersed in the physiological saline ws1 by the homogenizer 300, whereby the mouse tissue pulverized liquid Lq1 is obtained. In addition, there is a possibility that various tissues are mixed in the drainage liquid Lq discharged from the living body, and it is assumed that the mouse tissue pulverization liquid Lq1 approximates the drainage liquid Lq.

(Subtube opening shape)
Next, the opening 133b that can be provided near the branch point of the subtube 133 will be considered.

  FIG. 10A is an enlarged view showing the vicinity of a branch point of the main tube 130 when the sub tube 133 does not have the opening 133b. The tube center portion 130c of the main tube 130 may be filled with a tissue pulverization liquid Lq1 containing a large amount of tissue pieces mz. When a pressing force is applied by the first pressing member 115, the internal pressure P of the tube central portion 130c increases, and when the opening force P21 expressed by the formula (2) is exceeded, the flow path 133z of the sub tube 133 is opened.

  In FIG. 10A, since the opening 133b does not exist, the length c of the crack is almost zero. When the opening 133b does not exist, the inlet of the flow path 133z is narrow (the cross-sectional area on the main tube 130 side is small), so the opening force P21 when the tissue piece mz adheres to the vicinity of the inlet of the flow path 133z is likely to change. .

  FIG. 10B is an enlarged view showing the vicinity of the branch point of the main tube 130 when the sub-tube 133 has the opening 133b. The shape of the opening 133b is, for example, a triangular cross section, but may be another shape (for example, a semicircular cross section or a polygon other than a triangle). When the opening 133b is provided, the opening area (opening area and cross-sectional area of the opening 133b) at the connection position where the main tube 130 and the sub-tube 133 are connected is equal to the cross-sectional area of the flow path 133z in the sub-tube 133 (flow-path break). It may be larger than (area). That is, the cross section of the opening 133b is wider than the cross section of the flow path 133z other than the opening 133b. For example, in FIG. 10B, in the flow path 133z, the cross-sectional area of the cross section s1 of the opening 133b may be larger than the cross-sectional area of the cross section s2 of the flow path 133z. Further, the length L11 in the direction along the flow path 133z of the opening 133b, which corresponds to the crack length c, may be 1 mm, for example. In this case, since the length c of the crack is sufficiently longer than the length of the tissue piece mz (about 100 μm), the opening force P21 for opening the flow path 133z is stabilized. Therefore, a stable drain sampling operation can be performed. Note that not only the crack length c but also the crack width may be related to the opening force P21. In addition, the cross-sectional area of the above-described flow path 133z assumes a case where the flow path 133z is open. The flow path 133 is normally closed, and the cross-sectional area of the flow path 133z in this case is 0.

  Further, the opening area of the opening 133b may be determined by the size of the particles contained in the drainage liquid Lq flowing through the main tube 130. For example, when the particle of the management target component is small, it is rarely clogged in the vicinity of the inlet of the sub-tube 133. Therefore, it is difficult to clog the vicinity of the inlet of the flow path 133z and the quantitativeness of sampling does not deteriorate so much. The area may be relatively small, or the opening 133b may not be provided. On the other hand, when the particle of the management target component is large, the opening area of the opening 133b may be made relatively large considering that the particles are easily clogged in the vicinity of the inlet of the flow path 133z.

  As described above, the drainage sensor 10 includes the opening 133b, thereby suppressing the clogging of the tissue piece in the vicinity of the branch point between the main tube 130 and the subtube 133. Therefore, the drain drainage sensor 10 can collect the drain drainage as the sampling liquid that has passed through the sub-tube 133 in a stable amount. That is, the drainage sensor 10 can improve the quantitativeness of the sampling amount. The tissue piece may cause clogging in the vicinity of the branch point of the sub-tube 133, but can pass through the flow path 133z if it enters the flow path 133z at one end.

  In addition, the drainage sensor 10 includes the opening 133b, so that it is difficult for the tissue piece mz to adhere to the vicinity of the inlet of the flow path 133z and the state where the inlet of the flow path 133z is blocked. The increase in the opening force P21 can be suppressed. For this reason, since the force of the internal pressure P of the pipe center portion 130c can be reduced, the main tube 130 is hardly damaged, and the drainage can be stably sampled.

  FIG. 11A is a graph showing the measurement results of the weight for each sampling when the subtube 133 has the opening 133b and when it does not have the opening 133b. As shown in the graph g22, when the sub-tube 133 does not have the opening 133b, the sampling amount of the tissue pulverization liquid varies greatly in the range of 0.1 g to 0.5 g. On the other hand, as shown in the graph g21, when the sub-tube 133 has the tapered opening 133b, the sampling amount of the tissue pulverization liquid is within a narrow range of 0.4 g to 0.5 g.

  FIG. 11B shows the average weight [g], standard deviation, and C.D. of the tissue pulverized solution shown by the graphs g21 and g22 in FIG. V. It is a table which shows [%]. When the subtube 133 does not have the opening 133b, the average weight is 0.32 [g], the standard deviation is 0.11, and the C.I. V. 35.8 [%]. When the subtube 133 has the opening 133b, the average weight 0.48 [g], the standard deviation 0.02, C.I. V. 5.2 [%].

  As a result, when sampling the tissue pulverized liquid, it is desirable to provide the opening 133b and connect the outlet of the opening 133b to the inlet of the flow path 133z. As a result, clogging of the tissue pulverization liquid near the inlet of the flow path 133z is suppressed, and the tissue pulverization liquid is easily introduced into the flow path 133z. Note that the shape of the opening is not limited to the shape of the opening 133b, and is preferably a shape in which the tissue piece mz easily flows.

(Measurement of sampling solution)
Next, a method for measuring the amount of enzyme contained in drainage drainage (sampling fluid) sampled by the drainage sampling mechanism 110 will be described.

  As described above, the blood cell separation / enzyme reaction mechanism 150 separates blood cells contained in the drainage, reacts the enzyme with the reagent, and optically measures the amount of the enzyme.

(Measurement tape structure)
FIG. 12A is a cross-sectional view showing the structure of the measuring tape 200. The measuring tape 200 has a four-layer sheet structure. The four-layer sheet is composed of a PET (polyethylene terephthalate) sheet 201 disposed on the lowermost layer, a reagent 202 laminated thereon, a spacer 203 laminated thereon, and a blood cell separation membrane disposed on the uppermost layer. It is comprised with the glass film 204 as an example. The PET sheet 201 and the reagent 202 form an enzyme reaction sheet 205. The blood cell separation membrane can be separated from blood cells and non-blood cells (for example, amylase) based on the size of the management target components (for example, blood cells, amylase, bilirubin) contained in the drainage drain, the adsorption of the management target components, and the like.

  The glass film 204 is formed by bundling glass fibers into a sheet shape and is formed like a nonwoven fabric. The glass film 204 may be formed into a sheet by overlapping and folding a large number of glass fibers.

  The glass film 204 adsorbs the management target component. The adsorptive power of the glass film 204 may be different for each component to be managed (for example, blood cell, amylase, bilirubin). Further, the adsorption force of the glass film 204 may vary depending on the surface area of the glass film 204. The size of the surface area of the glass film 204 may be determined according to the density of the glass film 204. The glass film 204 may be charged and adsorbed. Specifically, glass fiber may be positively charged, blood cells (for example, phospholipids of blood cells) may be negatively charged in the sampling solution, and both may be electrically attracted. On the other hand, the adsorption force between the glass fiber and the enzyme in the sampling solution may be weaker than the adsorption force between the glass fiber and blood cells. In this case, the enzyme may be adsorbed to the glass fiber after moving slightly on the glass fiber.

  The enzyme reaction sheet 205 includes a reagent 202 that reacts with an enzyme. For example, when the enzyme is amylase, the reagent 202 reacts with amylase and changes the color of amylase to yellow. The amylase that has reacted with this reagent absorbs part of the measurement light. The reagent 202 may be, for example, a reagent for measuring amylase activity used in a commercially available dry clinical chemistry test apparatus.

  The spacer 203 has holes 203z (an example of openings) for allowing the sampling solution sq2 containing the enzyme to pass through the lower layer among the sampling solution sq collected by the upper glass film 204 at regular intervals.

  The PET sheet 201 is a resin having translucency and transmits measurement light (for example, light having a peak value of 410 nm wavelength).

  Amylase reacted with the reagent 202 easily absorbs light having a wavelength of 410 nm. On the other hand, the absorption wavelength of blood cells is 420 nm. Therefore, when measuring light having a peak value of 410 nm is projected onto the amylase that has reacted with the reagent 202 and the absorbance of amylase is measured from the scattered light based on the measuring light, the absorbance of the blood cell partially overlaps with 420 nm, and accurate measurement is possible. It becomes difficult. Therefore, the blood cell separation / enzyme reaction mechanism 150 separates blood cells and non-blood cells (for example, amylase and bilirubin), and measures the absorbance and the like.

  FIG. 12B and FIG. 12C are diagrams illustrating a state in which blood cell separation / enzyme reaction is performed using the measuring tape 200. When the sampling solution sq flowing out from the flow path 133z of the sub tube 133 is dropped onto the glass film 204, blood cells are adsorbed on the glass film 204. Therefore, the sampling liquid sq1 (blood cell component) containing a lot of blood cells remains in the vicinity of the dropping position of the glass film 204.

  On the other hand, when the sampling solution sq2 (enzyme component) containing a large amount of an enzyme (for example, amylase) is dropped on the glass film 204, it is not immediately adsorbed at the dropping position of the glass film 204, but spreads from the dropping position. For example, it moves to the left in FIG. 12B. After the sampling solution sq2 containing a large amount of amylase is dropped on the glass film 204, it moves through the glass film 204 for about 1 second and permeates, and is adsorbed on the glass film 204. Therefore, the sampling liquid sq1 containing a lot of blood cells stays near the dropping position of the glass film 204, and the sampling liquid sq2 containing a lot of amylase stays at a position away from the dropping position of the glass film 204. That is, on the surface of the glass film 204, a blood cell adsorption region ar1 (an example of a first adsorption region) in which the sampling solution sq1 in which many blood cells are present stays, and a sampling solution sq2 in which many non-blood cells such as enzymes are present. Separated into a blood cell adsorption region ar2 (an example of a second adsorption region).

  Holes 203z are formed on the surface of the spacer 203 at regular intervals. The hole 203z is positioned to face the glass film 204 in which the sampling liquid sq2 containing a large amount of amylase is retained. The hole 203z is formed in such a size that the tip 116B of the second pressing member 116 can press the glass film 204 in order to send the sampling solution sq2 moved in the plane of the glass film 204 to the enzyme reaction sheet 205.

  In FIG. 12C, the tip 116B of the second pressing member 116 presses the glass film 204 into which the sampling liquid sq2 has penetrated. The sampling solution sq2 that has permeated the glass film 204 flows out to the enzyme reaction sheet 205 through the hole 203z of the spacer 203. In the enzyme reaction sheet 205, the amylase contained in the sampling solution sq2 reacts with the reagent 202 and turns yellow (see the dot display shown in the hole 203z and the reagent 202 in FIG. 12C).

  The sensor unit 180 measures the absorbance of amylase contained in the sampling liquid sq2 that has penetrated into the measuring tape 200 delivered by the tape take-up feed mechanism 170. When measuring the absorbance of amylase, the LED 182 of the sensor unit 180 projects measurement light having a peak value of 410 nm, which is an absorption wavelength, onto the measurement tape 200 into which the sampling solution sq2 has penetrated. The photo sensor 183 of the sensor unit 180 receives the scattered light that is projected from the LED 182 and is not absorbed by the amylase in the sampling liquid sq2. The CPU 181 of the sensor unit 180 measures the absorbance of amylase contained in the sampling liquid sq2 based on the amount of scattered light received by the photosensor 183.

(Examination of blood cell separation membrane)
In this embodiment, the glass membrane 204 is mainly used as the blood cell separation membrane, but it is compared with the case where other membrane materials are used. FIG. 13 is a table showing characteristics of various materials used for the blood cell separation membrane. This table shows the comparison results when a monolith film, a cellulose film, and a glass film are used. In the examination of this blood cell separation membrane, a sample obtained by adding amylase to chicken blood was used as a measurement target.

  The monolith membrane has a small pore size of 1 μm, and the extraction exceeding 5 μl necessary for measurement cannot be performed, and the amount of amylase extracted is small. Cellulose membranes have a large pore size of 5-10 μm, and blood cells having a size of 10-15 μm cannot be separated. In addition, when a cellulose membrane is used, blood cells deformed and subdivided may pass through the cellulose membrane, and necessary separation may not be possible. On the other hand, in the glass film 204, blood cells can be separated by utilizing the difference in the adsorption power of the components to be managed, and an amount exceeding 5 μl necessary for measurement can be secured.

  FIG. 14 is a diagram for explaining a method of separating blood cells and non-blood cells contained in the sampling liquid sq along the surface of the blood cell separation membrane. The blood cell ba has a higher affinity for the glass film 204 than the non-blood cell, and is easily adsorbed to the glass film 204. Therefore, the blood cell ba remains in the vicinity of the dropping position in the glass film 204. Amylase rz, which is an example of a non-blood cell contained in the sampling solution sq, has a lower affinity for the glass membrane 204 than the blood cell ba, and is less likely to be adsorbed by the glass membrane 204 compared to the blood cell. Therefore, the amylase rz moves along the glass film 204 due to, for example, capillary action, and permeates. The amylase rz remains adsorbed in a region away from the region where the blood cells ba remain. Thus, separation of blood cells using a blood cell separation membrane is also referred to as membrane separation.

FIG. 15 is a graph showing the correlation between the change in absorbance due to membrane separation and the change in absorbance due to centrifugation. As a measurement object, a sample obtained by adding amylase to stored chicken blood was used to examine the change in absorbance for 1 minute in the measurement of amylase activity. Amylase activity represents the ability of amylase to react with reagent 202 and is expressed in units of U / L. The vertical axis of the graph indicates the amount of change ΔA in absorbance due to membrane separation. The horizontal axis of the graph indicates the amount of change ΔA in absorbance due to centrifugation. The graph g31 is expressed by Expression (4), where y is the amount of change in absorbance ΔA due to membrane separation, and x is the amount of change ΔA in absorbance due to centrifugation. The correlation coefficient is 0.999.
y = 1.03x (4)

  Therefore, it can be said that the change in absorbance due to membrane separation can be obtained with the same accuracy as the change in absorbance due to centrifugation. In other words, it can be said that the same accuracy as blood cell separation by centrifugation and blood cell separation by membrane separation are possible. Therefore, even if a large device such as a centrifuge is not used, an equivalent measurement result such as absorbance can be obtained using a blood cell separation membrane such as the glass membrane 204.

(Measurement of amylase activity)
FIG. 16A, FIG. 16B, and FIG. 16C are diagrams illustrating various methods for measuring amylase activity. In order to measure amylase activity, a liquid containing amylase is added to the enzyme reaction sheet 205. As this addition method, a standard method, an osmotic filtration method, and a transfer method were examined.

  FIG. 16A shows the standard method. In the standard method, the liquid sqx1 containing amylase separated by centrifugation is dropped onto the enzyme reaction sheet 205 with a micropipette MP.

  FIG. 16B shows the osmotic filtration method. In the osmotic filtration method, the enzyme reaction sheet 205 is brought into contact with the back surface of the glass membrane 204 in advance, and the sampling solution sqx2 is dropped onto the surface of the glass membrane 204. In this case, the blood cell component contained in the sampling solution sqx2 remains in the vicinity of the dropping position of the glass film 204. On the other hand, the amylase component contained in the sampling solution sqx2 moves through the glass film 204 and penetrates to the enzyme reaction sheet 205. The sampling solution sqx2 may be, for example, a product obtained by adding amylase to chicken blood.

  FIG. 16C shows the transfer method. In the transfer method, the sampling solution sqx2 is dropped on the surface of the glass film 204 without bringing the enzyme reaction sheet 205 into contact with the glass film 204 in advance. In this case, the components of blood cells contained in the sampling liquid sqx2 remain in the blood cell adsorption region ar1 in the vicinity of the dropping position of the glass film 204. On the other hand, the amylase component contained in the sampling solution sqx2 moves through the glass film 204 and remains in the non-blood cell adsorption region ar2. After the amylase component is transferred, the enzyme reaction sheet 205 is brought into contact with the glass film 204 to transfer the amylase from the glass film 204 to the enzyme reaction sheet 205.

  FIGS. 17A, 17A, and 17C are graphs showing measurement results of amylase activity in the various measurement methods shown in FIGS. 16A, 16B, and 16C. The vertical axis of each graph indicates the amount of change in absorbance (ΔA) in various measurement methods. The horizontal axis shows amylase activity.

  In the standard method, as shown in FIG. 17A, it was confirmed that the change in absorbance (ΔA) and amylase activity were highly correlated (closely linear). In the osmotic filtration method, as shown in FIG. 17B, it was confirmed that the correlation between the change in absorbance (ΔA) and the amylase activity was low. In the transcription method, as shown in FIG. 17C, as in the standard method, it was confirmed that the amount of change in absorbance (ΔA) and amylase activity were highly correlated (closely linear). In the transcription method, the correlation coefficient is 0.988 in the range of amylase activity: 75-2400 U / L. V. Is 5.72%.

  The standard method requires a centrifuge to perform centrifugation. Therefore, if the drainage sensor 10 includes a centrifuge, the drainage sensor 10 is expensive and large, and portability is reduced.

  In the osmotic filtration method, the reagent 202 in the enzyme reaction sheet 205 easily flows out because the glass membrane 204 and the enzyme reaction sheet 205 are in contact with each other in advance. In this case, the reaction between the reagent 202 and amylase may be insufficient. In FIG. 17B, the low correlation between the amount of change in absorbance (ΔA) and the amylase activity can be attributed to insufficient reaction between the reagent 202 and amylase.

  In the transfer method, the contact time between the glass membrane 204 and the enzyme reaction sheet 205 is shorter than that in the osmotic filtration method, so that the reagent 202 in the enzyme reaction sheet 205 is difficult to flow out. Therefore, in FIG. 17C, it can be considered that the correlation between the change in absorbance (ΔA) and the amylase activity is high. In addition, since FIGS. 17A and 17C have approximate graph shapes, the transfer method can obtain measurement results with the same measurement accuracy as the standard method. In FIG. 12C, the enzyme reaction sheet 205 can be brought into contact with the region containing amylase in the glass film 204 after the amylase has moved (after separation). That is, in FIG. 12C, the transfer method is adopted.

  FIG. 18 is a flowchart showing a procedure for measuring amylase activity by the drainage management system 5. This measurement is set to an appropriate time, for example, once every hour, similarly to the drain sampling operation.

  The CPU 181 of the sensor unit 180 outputs a command signal via the motor driving unit 187, and drives the motor 175 so as to send the measuring tape 200 in the winding direction (S11). When the motor 175 rotates, the take-up reel 172 rotates and winds and feeds the measuring tape 200 so that the dropping position is just below the subtube 133 (opposite position) in order to perform the drain sampling operation. The reel 151 sends out the measuring tape 200.

  The CPU 181 performs a drainage sampling operation and drops the sampling solution sq on the measuring tape 200 (S12). This drainage sampling operation may be performed according to the procedure shown in the flowchart of FIG.

  The CPU 181 waits for a predetermined time in order to separate blood cells and move the sampling solution sq (S13). During the waiting for the predetermined time, out of the sampling liquid sq dropped on the glass film 204 of the measuring tape 200, the sampling liquid sq1 containing a lot of blood cells stays in the vicinity of the dropping position (blood cell adsorption area ar1) and contains amylase. Sampling liquid sq2 moves to a location (non-blood cell adsorption region ar2) away from the dropping position (see FIG. 12B).

  The CPU 181 outputs a command signal to the motor driving unit 187, and drives the motor 175 so as to move the measuring tape 200 by a predetermined amount in the winding direction (S14). When the motor 175 rotates, the take-up reel 172 rotates, moves the measuring tape 200 from the dropping position by a predetermined amount in the take-up direction (right direction in FIG. 12C), is taken up by the take-up reel 172, and sent. It is sent out to the reel 171. This predetermined amount corresponds to the distance from the dropping position of the sampling liquid sq to the position where the sampling liquid sq2 penetrates, that is, the distance between the outlet of the sub-tube 133 and the hole 203z of the spacer 203.

  The CPU 181 presses the second pressing member 116 by the pressing unit driving unit 186 in a state where the glass film 204 into which the sampling liquid sq2 has penetrated is positioned above the hole 203z (opposite position) of the spacer 203 (S15). . In this pressing, the tip end portion 116B of the second pressing member 116 presses the glass film 204 into which the sampling liquid sq2 has permeated, for example, from directly above. The sampling solution sq2 that has permeated the glass film 204 passes through the hole 203z and oozes out to the enzyme reaction sheet 205.

  Note that the sampling solution sq2 does not ooze out of the glass film 204, and 204 is elastically deformed through the hole 203z, so that the permeation portion (adsorption portion) of the sampling solution sq2 in the glass membrane 204 and the enzyme reaction sheet 205 come into contact with each other. It may be made to do. In this case, the glass film 204 may be configured to be elastically deformable.

  The CPU 181 waits for the reaction time of the amylase and the reagent (S16). During this reaction time, the reagent 202 contained in the enzyme reaction sheet 205 reacts with the amylase contained in the sampling solution sq2, and the reacted amylase turns yellow.

  The CPU 181 performs optical reading on the reaction site between the amylase and the reagent 202 (S17). In this optical reading, the CPU 181 turns on the LED 182 and projects measurement light toward the reaction site. At the reaction site, a part of the projected measurement light is absorbed by amylase and the remaining part is scattered. The CPU 181 receives the light scattered by the photosensor 183 and calculates the amount of change in absorbance (ΔA) based on the amount of received light.

  For example, the CPU 181 calculates the amylase activity from the amount of change in absorbance (ΔA) based on the graph shown in FIG. 17C (S18). The CPU 181 communicates with the drain drainage monitor 20 through the wireless chip 184 to measure measurement data related to amylase (for example, the amount of change in amylase absorbance (ΔA), the value of amylase activity, and the value of amylase concentration). (S19). When the CPU 26 of the drainage drain monitor 20 receives measurement data and measurement time information related to amylase from the drain drainage sensor 10 via the wireless chip 28, various data (measurement data, measurement time, other information) are displayed via the display 21. Data).

According to the measurement procedure of such a component to be managed (for example, amylase), the drain drainage management system 5 allows the CPU 181 to control each part of the blood cell separation / enzyme reaction mechanism 150,
It is possible to automatically measure the state of the sampling liquid sq from which the drainage liquid has been sampled and derive measurement data. In addition, the drainage management system 5 can display information on the drainage monitor 20, and can visualize information related to managed components such as measurement data. Therefore, the user can easily grasp the recovery tendency of the patient.

  FIG. 19 is a diagram showing a display on the drainage drain monitor 20. For example, a graph 22 showing the measurement result of the amount of change in absorbance (ΔA) representing the amylase activity may be displayed on the display 21 disposed in front of the drainage monitor 20. The display 21 also includes various explanatory texts 23 such as the name of the patient, a meter 24 indicating the amount of change in absorbance (ΔA), and a status marker 25 for notifying the patient's status (normal / abnormal). May be displayed.

  In the graph 22, a broken line L1 indicates the upper limit of the normal range, and a broken line L2 indicates the lower limit of the normal range. If the condition of the patient after the operation is normal, the amount of change in absorbance due to amylase in the drainage fluid flowing in the drain tube 30 connected to the patient's body gradually decreases with the passage of time after the operation. In this example, the temporal transition of each measurement result is maintained within the normal range. At this time, “normal” characters are displayed as the status marker 25. On the other hand, when the temporal transition of each measurement result is out of the normal range, the characters “abnormal” may be displayed as the status marker 25.

(Measurement of bilirubin)
In the above, amylase which is a digestive enzyme has been mainly described as a management target component in the drainage liquid Lq. As an example of organ secretion, bilirubin contained in bile and urine can be one of the components to be managed. Since bilirubin itself has a yellow pigment, it is possible to optically detect the concentration of bilirubin without contact. Therefore, when measuring the concentration of bilirubin, an enzyme reaction sheet for reacting with a reagent and coloring is unnecessary.

  FIG. 20 is a cross-sectional view showing the structure of the measuring tape 200A. The measuring tape 200A has a two-layer structure of a glass film 204A and a PET sheet 201A.

  21A and 21B are diagrams illustrating a method for measuring bilirubin. In FIG. 21A, bilirubin is measured using a spectrophotometer BK (standard method). In FIG. 21B, bilirubin is measured using a blood cell separation membrane (membrane measurement).

  As with amylase, bilirubin can also be membrane-separated as described in FIG. That is, bilirubin, which is an example of a non-blood cell contained in the sampling solution sq, has a lower affinity for the glass film 204 than the blood cell, and is less likely to be adsorbed by the glass film 204 than the blood cell. Therefore, bilirubin moves and permeates along the glass film 204 by, for example, capillary action. Bilirubin remains adsorbed and stays in a region away from the region where the blood cells ba remain.

  As shown in FIG. 21B, in the membrane measurement, a sampling solution region (non-blood cell adsorption region ar3) containing a large amount of bilirubin is obtained by adsorbing the sampling solution sq to the glass film 204 using the difference in adsorption force between blood cells and bilirubin. ) Is formed. Specifically, when the sampling solution sq is dropped onto the glass film 204, blood cells are preferentially adsorbed on the glass film 204. That is, the adsorption force of blood cells to the glass film 204 is larger than the adsorption force of bilirubin to the glass film 204. In the glass film 204, blood cells are adsorbed in the blood cell adsorption region ar1, and bilirubin is adsorbed in the non-blood cell adsorption region ar3. The absorbance of bilirubin can be measured by measuring the non-blood cell adsorption region ar3 on which bilirubin is adsorbed using light having a wavelength of 410 nm as a peak value as measurement light.

  FIG. 22A is a graph showing the measurement result of bilirubin when the standard method is used. The vertical axis of the graph represents absorbance (Abs). The horizontal axis represents the amount of bilirubin (mg / ml). In the measurement of bilirubin by the spectrophotometer BK, the absorbance (Abs) and the bilirubin amount (mg / ml) have a high correlation in the range where the bilirubin amount is 0-32 (mg / ml).

  FIG. 22B is a graph showing the measurement result of bilirubin when membrane measurement is used. The vertical axis of the graph represents absorbance (Abs). The horizontal axis represents the amount of bilirubin (mg / ml). Also in the measurement of bilirubin using the glass membrane 204, the absorbance (Abs) and the amount of bilirubin (mg / ml) have a high correlation (a relationship close to linear). Here, in the range of bilirubin amount: 0-32 (mg / ml), the correlation coefficient is 0.987. V. Is 1.06%.

  Therefore, it can be said that the absorbance by the film measurement can be obtained with the same accuracy as the measurement accuracy of the absorbance by the spectrophotometer BK. The drainage sensor 10 measures bilirubin using a blood cell separation membrane such as a glass membrane 204, so that it does not require a large-sized device like the spectrophotometer BK, and is excellent in portability and cost reduction. .

  Measurement data such as the absorbance of bilirubin may be sent to the drainage monitor 20 and displayed on the display 21.

(Modification example of measuring tape)
In FIG. 12A, as the measuring tape 200, a tape having a four-layer structure used for measuring amylase is illustrated. Moreover, in FIG. 20, the tape which has a 2 layer structure used for the measurement of bilirubin was illustrated. The structure of the measuring tape is not limited to the structure of these tapes.

  FIG. 23 is a diagram showing the structure of a measuring tape 200B capable of measuring both amylase and bilirubin states. The measuring tape 200B is manufactured so as to repeat the above-described four-layer structure and two-layer structure in the length direction of the measuring tape 200B. When measuring the state of amylase, the drainage sensor 10 uses a region AS1 having a four-layer structure in the measuring tape 200B. On the other hand, when measuring bilirubin, the drainage sensor 10 uses the region AS2 having a two-layer structure in the measuring tape 200B.

  In this way, the drain drainage sensor 10 uses the measuring tape 200B having the region AS2 having the two-layer structure and the region ASS1 having the four-layer structure, so that the types of substances that the drain drainage sensor 10 can simultaneously measure are selected. Can be increased. Moreover, since the drain drainage sensor 10 can be shared in the measurement of a plurality of different management target components, the cost is reduced and the space can be saved as compared with the case where two drain drainage sensors are provided. Further, since only one measuring tape 200 is required for measuring a plurality of different management target components, costs are reduced and space saving is possible as compared with the case where two measuring tapes 200 are used.

  As mentioned above, although embodiment was described referring drawings, it cannot be overemphasized that this invention is not limited to this example. It will be apparent to those skilled in the art that various changes and modifications can be made within the scope of the claims, and these are naturally within the technical scope of the present invention. Understood.

  In the above-described embodiment, the drain drain sensor 10 is provided with the two limiting members 113 and 114. The limiting members 113 and 114 are not limited to two. As long as a certain amount of drainage liquid Lq is blocked and can stay in the tube central portion 130c, the number of limiting members may be one or three or more. In addition, a member (for example, a valve) other than the restricting member may be provided as long as a certain amount of drainage drainage is blocked in the tube central portion 130c and can be retained. For example, the drainage and passage of the drainage may be switched by electrically opening and closing the valve.

  In the above-described embodiment, the drain drainage sensor 10 is exemplified as the two limiting members 113 and 114 and the first pressing member 115 provided separately, but the limiting members 113 and 114 and the first pressing member 115 are not provided. At least a part may be provided integrally. For example, instead of the two limiting members 113 and 114 and the first pressing member 115, one third pressing member 140 may be provided.

  FIG. 24 is a perspective view showing a structural example of the third pressing member 140. The third pressing member 140 includes two first pressing parts 141, a second pressing part 142, and a rotating shaft 143.

  The first pressing portion 141 is located at both ends of the third pressing member 140 along the direction in which the drain drainage Lq flows in the main tube 130. In the 1st press part 141, the rotating shaft 143 passes along the direction where the main tube 130 is extended. The first pressing portion 141 rotates around the rotation shaft 143 as a rotation center. The first pressing portion 141 has a substantially fan-shaped cross section in a direction perpendicular to the direction in which the drainage liquid Lq flows. For example, the first pressing portion 141 has a substantially semicircular shape having a sector central angle of approximately 180 degrees. The distance between the rotation center of the first pressing part 141 and the outer periphery of the first pressing part 141 is not constant. Therefore, the first pressing unit 141 restricts the flow of the drain drainage liquid Lq flowing through the main tube 130 or releases the restriction on the flow of the drainage liquid Lq by the rotation of the rotating shaft 143. Accordingly, the first pressing portion 141 acts in the same manner as the limiting members 113 and 114.

  The second pressing portion 142 is located between the two first pressing portions 141 in the third pressing member 140. As for the 2nd press part 142, the rotating shaft 143 passes along the direction where the main tube 130 is extended. The second pressing portion 142 rotates about the rotation shaft 143 as a rotation center. The second pressing portion 142 has a substantially sector-shaped cross section in a direction perpendicular to the direction in which the drainage liquid Lq flows, for example, a sector-shaped central angle is approximately 60 degrees. The distance between the rotation center of the second pressing part 142 and the outer periphery of the second pressing part 142 is not constant. Therefore, the second pressing portion 142 presses the drain drainage Lq whose flow is restricted by the first pressing portion 141 in the main tube 130 by the rotation of the rotating shaft 143, and passes the sub-tube 133, or drain drainage. The sub-tube 133 is not allowed to pass without pressing Lq. Therefore, the second pressing portion 142 acts in the same manner as the first pressing member 115.

  The rotation shaft 143 may rotate according to a drive signal from the CPU 181 of the sensor unit 180. The first pressing portion 141 and the second pressing portion 142 are rotated by the rotation of the rotating shaft 143.

  The first pressing portion 141 and the second pressing portion 142 have a substantially fan-shaped cross section, but the sector central angle (for example, 180 degrees) in the cross section of the first pressing portion 141 is the cross section of the second pressing portion 142. It is made larger than the central angle (for example, 60 degrees) of the sector. That is, when the sectional fan shape of the first pressing portion 141 and the sectional sector shape of the second pressing portion 142 are projected onto a projection plane parallel to these cross sections, the sectional sector shape of the second pressing portion 142 having a small central angle becomes the central angle. The first pressing portion 141 having a large cross section is included in the sector fan shape (see, for example, FIGS. 25A to 25C).

  25A, 25B, and 25C are AA cross-sectional views showing an example of the state of the third pressing member 140 and the main tube 130 in each rotational state of the third pressing member 140. FIG. FIG. 25A corresponds to the state of FIG. 24 and shows a no-load state (state α). In the state α, both the first pressing part 141 and the second pressing part 142 are not pressing the main tube 130. Therefore, the state α corresponds to the state A in FIG.

  FIG. 25B shows a state β rotated by a predetermined angle from the state α. In the state β, the main tube 130 is pressed at two points by the two first pressing portions 141, but not pressed by the second pressing portion 142. That is, the main tube 130 is pressed by the two first pressing portions 141, and the drainage liquid Lq flowing through the main tube 130 stays between the two first pressing portions 141. On the other hand, the accumulated drainage liquid Lq is not yet pressed by the second pressing portion 142 and therefore does not flow into the sub-tube 133. Therefore, the state β corresponds to the state B in FIG.

  FIG. 25C shows a state γ rotated by a predetermined angle from the state α. In the state γ, the main tube 130 is pressed by the first pressing portion 141 and is pressed by the second pressing portion 142. That is, the drain liquid Lq flowing through the main tube 130 is pressed by the two first pressing portions 141 and stays between the two first pressing portions 141 (at the tube center portion 130c). Furthermore, the drainage liquid Lq staying in the pipe center part 130c is pressed by the second pressing part 142, flows into the subtube 133, passes through, and is extracted as the sampling liquid Sq. Therefore, the state γ corresponds to the state C in FIG.

  As described above, the drain liquid sensor 10 uses a mechanism such as a camshaft, for example, by rotating the third pressing member 140, so that a certain amount of sampling liquid can be obtained from the drain liquid Lq flowing through the main tube 130. Sq can be extracted. Therefore, it is possible to realize the restriction of the flow of the liquid in the main tube 130 and the extraction of the liquid from the sub tube 133 with one member, and the configuration related to the liquid sampling can be simplified. In addition, since the third pressing member 140 only needs to drive the rotating shaft 143, the number of driving points can be reduced, compared with, for example, driving three of the limiting members 113 and 114 and the first pressing member 115. The possibility of mechanism failure can be reduced. Therefore, the drain liquid sensor 10 can improve the long-term reliability of the liquid sampling by using the third pressing member 140.

  In the above-described embodiment, the drainage discharged from the living body via the drain tube 30 is exemplified as a sampling or measurement target. However, a liquid other than the drainage drain may be a sampling or measurement target. For example, a biological fluid that is discharged from a living body or introduced into a living body through a body fluid guiding tube may be an object of sampling or measurement.

  The body fluid guide tube may include, for example, a drain (drain tube), a catheter (catheter tube), and a dosing tube (tube used for dosing). A biological fluid flows through the body fluid guide tube.

  The drain may include drains for cranial nerve, otolaryngology, respiratory, circulatory, mammary gland / endocrine, upper gastrointestinal tract, biliary hepatopancreas, urological, gynecological, orthopedic and the like. Cranial nerve drains may include ventricular drains, cisternal drains, epidural drains, subcutaneous drains, hematoma cavity drains, lumbar drains, drains used after endoscopic surgery, and the like. Otolaryngological drains may include drains used after head and neck surgery, and the like. Respiratory drains may include thoracic drains, mediastinal drains, and the like. Cardiovascular drains may include pericardial drains, drains used after head and neck surgery, and the like. The mammary gland / endocrine drain may include a drain used after breast cancer surgery, a mastitis drain, a drain used after thyroid surgery, and the like. The upper gastrointestinal drain may include chest / mediastinal drain, cervical drain, abdominal drain, upper abdominal peritonitis drain, intraabdominal abscess drain, drain used after gastric surgery, and the like. Biliary hepatopancreatic drain is used after percutaneous transhepatic gallbladder drain, percutaneous transhepatic biliary drain, hepatic abscess drain, endoscopic biliary drain, drain for acute pancreatitis, retroperitoneal abscess drain for lower gastrointestinal tract, rectal cancer surgery Drainage, perianal abscess drainage, and the like. Urological drains may include drains used after general surgery, drains used after endoscopic surgery, drains used for percutaneous and transurethral approaches, and the like. Gynecological drains may include drains used after laparotomy, drains used after endoscopic surgery, and the like. Orthopedic drains may include joint cavity drains, and the like. Other drains may include an incision drainage drain and the like.

  Catheters may include angiographic catheters, balloon catheters, heart catheters, cerebral vascular catheters, catheters used for cancer catheter treatment, vascular indwelling catheters, urethral catheters, and the like.

  The dosing tube may include a tube used in a dosing device (dosing system), and the like. The dosing device may include a dosing pump (TCI (Target Controlled Infusion) pump) that directly controls the drug concentration in the blood, and the like. The TCI pump controls the operation of the pump, adjusts the administration rate of the drug, and controls the blood concentration of the drug to become the target blood concentration.

  FIG. 26 is a diagram for explaining the introduction of a biological fluid containing a medicine or an infusion (hereinafter also referred to as a medicine) into the patient PA1 by the TCI pump 10A. A biological fluid containing a drug or the like is introduced from the TCI pump 10A to the patient PA1 through the dosing tube 30A. Further, the biological fluid is sent from the patient PA1 to the TCI pump 10A via the dosing tube 30A. That is, the TCI pump 10A adjusts the dose and rate of the drug to the patient PA1, circulates the biological fluid with the patient PA1, and controls the concentration of the drug in the patient PA1. With such a TCI pump 10A, for example, a medication system that directly controls the drug concentration in the blood of the patient PA1 can be realized.

  The TCI pump 10A may have the same configuration as that of the drain drainage sensor 10 except for the configuration related to the administration of the drug administered to the patient PA1, for example, the same as the configuration shown in FIG. Good. The TCI pump 10A may sample the biological fluid going from the TCI pump 10A to the patient PA1 and measure the management target component. Further, the TCI pump 10A may sample the biological fluid heading from the patient PA1 to the TCI pump 10A and measure the management target component.

  In the above embodiment, the glass membrane 204 is exemplified as the blood cell separation membrane, but other members may be used. For example, a positively charged membrane that can be charged and adsorbed with blood cells may be used, or a member having an adsorption mechanism other than charged adsorption may be used.

  In the said embodiment, it illustrated that the data of each management object component in sampling liquid sq were acquired in time series. In addition to these time series data, time series data of the total discharge amount of the drain liquid Lq and the sampling liquid sq may be acquired. The time series data of the total discharge amount of the drain liquid Lq may be acquired based on an output value of a sensor (for example, a strain sensor) that measures the weight of the drain bag, for example. The time-series data of the total discharge amount of the sampling liquid sq may be acquired, for example, by measuring the extraction amount of the sampling liquid sq each time by the drainage sampling mechanism 110 and integrating each batch. Further, the time series data may include data on the discharge amount per unit time of the drain liquid Lq and the sampling liquid sq.

  In the above embodiment, the CPU 181 of the drainage sensor 10 may calculate the concentration of amylase based on the amount of change in absorbance of amylase. The amylase concentration data is an example of measurement data. For example, correspondence information between the amount of change in amylase absorbance and amylase concentration may be stored in a memory or the like, and the amylase concentration may be derived based on this correspondence information. The CPU 181 of the drainage sensor 10 may calculate the concentration of bilirubin based on the absorbance of bilirubin. The bilirubin concentration data is an example of measurement data. For example, correspondence information between the absorbance of bilirubin and the concentration of bilirubin may be held in a memory or the like, and the concentration of bilirubin may be derived based on this correspondence information.

  In the above embodiment, the drain drain sensor 10 and the drain drain monitor 20 are configured as separate devices, but the drain drain sensor 10 and the drain drain monitor 20 are configured as devices having the same casing. Also good.

  In the above embodiment, the drain tube 30 is connected to the main tube 130, but the main tube 130 may be a part of the drain tube 30.

  In the above embodiment, the blood cell separation / enzyme reaction mechanism 150 of the drain drainage sensor 10 may measure the blood concentration contained in the sampling liquid sq as a management target component. The blood concentration in the sampling liquid sq can be measured, for example, as follows. For example, the blood concentration in the sampling solution sq can be derived by irradiating the blood cell adsorption region ar1 (sampling solution sq1 containing a lot of blood cells) with measurement light and receiving scattered light. For example, light having a wavelength of 660 nm or 850 nm as a peak value may be used as measurement light for measuring the blood concentration. As described above, the biological fluid (for example, the management target component) may include biological blood cells (for example, venous blood of the patient). The drainage sensor 10 can evaluate the patient's condition based on the blood condition by measuring the patient's venous blood.

  In the said embodiment, although the example which concerns on the sampling of a liquid was disclosed, embodiment is not limited to this. For example, it is obvious that the present invention can be applied to applications such as dispensing and dropping of liquid, in which liquid is ejected by a certain volume.

  In this manner, the drainage management system 5 performs collection, separation, dispensing, analysis, and the like of the drainage Lq discharged from the patient's living body, and provides an index for examining subsequent treatment for the patient. Can be provided to the user. Further, the drainage liquid Lq can be collected, separated, dispensed, analyzed, and the like by the drainage liquid sensor 10 which is one device.

  Further, it is assumed that the patient wears the drain tube 30 on the patient's body for about one week, for example. The frequency of sampling the drainage liquid Lq may be, for example, about once per hour or about 170 times per week.

  As described above, the drain drainage management system 5 includes the drainage sampling mechanism 110 (an example of an acquisition unit) that acquires at least a part of drainage drained from the living body through the drain tube 30, and the acquired drainage drainage. A blood cell separation / enzyme reaction mechanism 150 (an example of a generation unit) that measures a management target component (for example, blood, amylase, bilirubin) in the liquid and generates measurement data (an example of first information related to the management target component); A memory 27 (an example of a recording unit) that records data in which measurement data is associated with the time at which the measurement data was detected, and time-series data that represents changes in the measurement data over time based on this data ( And a display 21 (an example of a display unit) that displays an example of the second information. The acquired drainage liquid may be, for example, the sampling liquid sq. Acquiring at least a part of the drainage discharged from the living body through the drain tube 30 may include “sorting” in which the drainage is acquired from the middle of the drain tube 30. The drain tube 30 is an example of a body fluid induction tube. Drain drainage is an example of biological fluid. Note that the acquisition unit may acquire at least part of the biological fluid introduced into the living body through the body fluid guide tube.

  Thereby, the drainage management system 5 can extract the management object component which affects drainage to the exterior from a drain tube. Further, the drainage management system 5 can measure the extracted management target component, and can derive measurement data based on the measurement result. In addition, the drain drainage management system 5 displays time-series data representing changes over time in the measurement data on the display 21 so that the user (doctor / nurse, other medical personnel) can check the state of drain drainage. When evaluating, it can replace with visual evaluation (or in addition to visual evaluation), and can evaluate based on time series data. Therefore, the user can evaluate the recovery tendency of the patient more objectively than the evaluation based only on visual observation.

  In addition, similarly to the drain drainage, with respect to the biological fluid other than the drain drainage, the management target component that affects the biological fluid can be extracted to the outside from the drain tube. Further, the extracted management target component can be measured, and measurement data based on the measurement result can be derived. In addition, by displaying time-series data representing changes in the measurement data over time on the display 21, when the user evaluates the state of the biological fluid, instead of visual evaluation (or visual evaluation). In addition, it can be evaluated based on time series data. Therefore, the user can more objectively evaluate the recovery tendency of the patient based on the biological fluid than the evaluation based only on visual observation.

  In this manner, the drainage management system 5 can objectively evaluate the state of the management target component contained in the biological fluid that is discharged from the living body or introduced into the living body.

  The managed component may include an enzyme, bilirubin, or blood cell component.

  Thereby, the drainage management system 5 can manage, for example, components of enzymes, bilirubin, or blood cells that are discharged or introduced into the patient, and can easily grasp the patient's condition.

  The first information may include information on the amount of enzyme, the amount of bilirubin, or the amount of blood cells.

  As a result, the drainage management system 5 can measure, for example, the amount of enzyme discharged from the patient or introduced into the patient, the amount of bilirubin, or the amount of blood cells, thereby making it easier to grasp the patient's condition.

  The managed component may include blood cells and non-blood cells. The blood cell separation / enzyme reaction mechanism 150 includes a glass membrane 204 (an example of a blood cell separation membrane) that separates blood cells and non-blood cells (for example, amylase and bilirubin) from drainage, and a state of non-blood cells separated by the glass membrane 204 Sensor unit 180 (an example of a measurement unit).

  Thereby, the drainage management system 5 can suppress the measurement of a mixture of blood cell components having characteristics different from those of the non-blood cells when the state of the non-blood cells is measured by using the glass film 204. Therefore, the drainage management system 5 can improve the measurement accuracy of the non-blood cell component. Therefore, the drainage management system 5 can objectively evaluate the state of the non-blood cells contained in the drainage while improving the measurement accuracy of the components of the non-blood cells. Further, since the drainage management system 5 can separate blood cells and non-blood cells by membrane separation, it is not necessary to use a centrifuge, and the apparatus for separating blood cells and non-blood cells can be reduced in size and cost. Is possible.

  Further, the glass film 204 may have a greater adsorption force with blood cells than with non-blood cells. The sensor unit 180 may measure the absorbance of the non-blood cells that are separated from the blood cells and adsorbed on the glass film 204.

  As a result, the drainage management system 5 can easily separate blood cells and non-blood cells using the difference in adsorption force with the glass film 204. Further, the drainage management system 5 can derive (for example, calculate) the concentration of non-blood cells whose correspondence with the absorbance is uniquely determined based on the absorbance by measuring the absorbance of the non-blood cells.

  Further, the glass film 204 moves non-blood cells along the glass film 204, and a blood cell adsorption region ar1 (an example of a first adsorption region) on which blood cells are adsorbed, and a non-blood cell adsorption region ar2, ar3 (an example of a first blood adsorption region) An example of the second adsorption region) may be formed.

  Accordingly, the drainage management system 5 can separate the positions of the region where the blood cell component stays and the region where the non-blood cell component stays in the glass film 204. Therefore, the drainage management system 5 can detect the respective states of blood cells and non-blood cells separately by, for example, irradiating each region with measurement light.

  In addition, the drainage management system 5 may include an enzyme reaction sheet 205. Non-blood cells may contain enzymes. The enzyme reaction sheet 205 may react with the enzyme separated by the glass membrane 204. The sensor unit 180 may measure the absorbance of the enzyme reacted by the enzyme reaction sheet 205.

  Accordingly, the drainage management system 5 can color the enzyme using the enzyme reaction sheet 205 even when the colorless enzyme is a component to be managed. Therefore, when the measurement light is irradiated to the colored enzyme, the enzyme in the enzyme reaction sheet 205 can scatter the measurement light, and the photosensor 183 can receive the scattered light. Therefore, the drainage management system 5 can measure the absorbance of the enzyme even when a colorless enzyme is a component to be managed, and can also derive the concentration of the enzyme based on the absorbance.

  In addition, the enzyme reaction sheet 205 may be configured to come into contact with the non-blood cell adsorption region ar <b> 2 in the glass film 204 after at least part of the drainage is acquired by the drainage sampling mechanism 110.

  Thereby, after a non-blood cell moves in the glass film 204 and reaches the non-blood cell adsorption region ar2, the enzyme and the enzyme reaction sheet 205 can come into contact with each other. In addition, the drainage management system 5 makes the contact time between the glass film 204 and the enzyme reaction sheet 205 by contacting the glass film 204 and the enzyme reaction sheet 205 after the enzyme reaches the non-blood cell adsorption region ar2. Can be shortened. Therefore, the reagent 202 in the enzyme reaction sheet 205 is difficult to flow out to the glass film 204. Therefore, the reaction between the enzyme and the enzyme reaction sheet 205 is sufficient, and the absorbance of the enzyme can be measured with high accuracy.

  Moreover, the management target component may include amylase.

  Thereby, the drainage management system 5 can measure the information (amylase absorbance, amylase absorbance change, amylase activity, amylase concentration, etc.) related to the digestive enzyme amylase and generate measurement data.

  Moreover, the management object component may include bilirubin.

  As a result, the drainage management system 5 can measure information (bilirubin absorbance, bilirubin concentration, etc.) related to bilirubin, which is a bile pigment, and generate measurement data.

  The glass membrane 204 may be formed as a sheet by bundling glass fibers and used as an example of a blood cell separation membrane.

  As a result, the drainage management system 5 can use the glass membrane 204 as the blood cell separation membrane to suppress the insufficient acquisition of non-blood cells because the pores of the monolith membrane are small compared to the monolith membrane. The amount of non-blood cells necessary and sufficient for use can be secured. In addition, since the drainage management system 5 uses the glass membrane 204 as the blood cell separation membrane, since there are no pores like the cellulose membrane, it can suppress the passage of both blood cells and non-blood cells, and the glass fiber capillary phenomenon. Thus, blood cells and non-blood cells can be suitably separated. In addition, the drainage management system 5 can easily handle the glass film 204 in the same manner as the nonwoven fabric by using the glass film 204 that is formed by bundling glass fibers into a sheet shape.

  The measurement data may include information regarding the amount of drainage discharged per unit time.

  Thereby, the drainage management system 5 can evaluate the drainage amount per unit time of drainage, and can evaluate a patient's recovery tendency appropriately. Furthermore, the drainage management system 5 can perform a more appropriate evaluation by examining the correlation between the drainage drainage amount and other information depending on the contents of the surgery performed by the patient.

  The measurement data may include information regarding the total drainage drainage.

  Thereby, the drainage management system 5 can evaluate the total drainage of the drainage (for example, the total drainage from the start of use of the drain tube 30 to the current time) and appropriately evaluate the recovery tendency of the patient. Furthermore, the drainage management system 5 can perform further appropriate evaluation by examining the correlation between the total drainage drainage amount and other information depending on the contents of the surgery performed by the patient.

  The drainage management system 5 may include a memory 27 (an example of a registration unit) that registers part or all of data and at least one of time-series data in the electronic medical record.

  Thereby, a plurality of users can share information on a patient's recovery tendency via an electronic medical record. In other words, the drain drainage state of the patient can be evaluated by a plurality of persons. As a result, objective and appropriate evaluation can be performed as compared with the case where the user evaluates alone. The drain drainage management system 5 accumulates measurement data related to drain drainage and time-series data related to measurement data in order to enable the evaluation of the drain drainage state by a plurality of persons, and supports the evaluation by the user. it can.

  The drainage sampling mechanism 110 includes a main tube 130 (an example of a main flow path), a sub tube 133 (an example of a sub flow path) branched from the main tube 130, a range between two points in the sub tube 133, and a range of this range. Two restricting members 113 and 114 that restrict the flow of drainage between the outside and the outside, and the main tube 130 presses the main tube 130 between two points in a state where the flow of drainage is restricted in the main tube 130. 1 pressing member 115 may be provided. The sub-tube 133 does not need to allow drain drain from the main tube 130 to pass when pressed by the first pressing member 115, and does not allow drain drain from the main tube 130 to pass when not pressed by the first pressing member 115. .

  Thereby, the drainage management system 5 can sample the drainage with a simple configuration, and can have the drainage sampling mechanism 110 that is excellent in portability and easy to carry. Therefore, it is not necessary for the patient to remain at a fixed position during sampling, and the degree of freedom of the user during sampling is improved. Further, the drain drainage management system 5 can stabilize the amount of drain drainage existing between the two points by keeping the distance between the two points in the main tube 130 unchanged during the measurement. The amount of drain drainage is one sampling amount. In addition, the drain drainage management system 5 allows the drainage drainage to pass through when pressed by the first pressing member 115, and does not allow the drainage drainage to pass through when pressed by the first pressing member 115, so that the drainage drainage management system 5 does not pass through once. The drainage of the sampling amount can be discharged. Therefore, liquid remaining in the sub-tube 133 can be suppressed. Therefore, the drain drainage management system 5 can suppress the drain drainage from being mixed with the previous time in each sampling, and can derive measurement data with high measurement accuracy according to the sampling timing.

  In the above embodiment, the drain drain sensor 10 (an example of a liquid discharge device) that samples drain drain (an example of liquid) includes a main tube 130 (an example of a main flow path) and a sub branched from the main tube 130. A tube 133 (an example of a sub-channel), two restricting members 113 and 114 for restricting the flow of drainage liquid between a range between two points in the sub-tube 133 and the outside of the range, and the main tube 130 The first pressing member 115 that presses the main tube 130 between two points in a state where the flow of the drainage liquid is restricted. The sub tube 133 does not have to pass the liquid from the main tube 130 when pressed by the first pressing member 115, and does not allow the liquid from the main tube 130 to pass when not pressed by the first pressing member 115. Sampling may be an example of ejection.

  Thereby, the drainage sensor 10 can sample the drainage with a simple configuration, is excellent in portability, and is easy to carry. Therefore, it is not necessary for the patient to remain at a fixed position during sampling, and the degree of freedom of the user during sampling is improved. In addition, the drain drain sensor 10 can stabilize the amount of drain drain existing between two points by keeping the distance between the two points in the main tube 130 unchanged at the time of measurement. The amount of drain drainage is one sampling amount. In addition, the drain drainage management system 5 allows the drainage drainage to pass through when pressed by the first pressing member 115, and does not allow the drainage drainage to pass through when pressed by the first pressing member 115, so that the drainage drainage management system 5 does not pass once. The drainage of the sampling amount can be discharged. Therefore, liquid remaining in the sub-tube 133 can be suppressed. Therefore, the drain drainage sensor 10 can suppress the drain drainage from being mixed with the previous time in each sampling, and can derive measurement data with high measurement accuracy according to the sampling timing.

  Thus, the drain liquid sensor 10 is excellent in portability and can suppress the liquid remaining in the sub-tube 133 after sampling.

  The limiting force by the limiting members 113 and 114 may be a force that can maintain the liquid flow limitation in the main tube 130 even when pressed by the first pressing member 115. The pressing force by the first pressing member 115 may be a force that allows the sub tube 133 to pass the liquid.

  As a result, the drainage sensor 10 can sample the drainage in a state where the flow of the drainage is restricted by the restriction members 113 and 114, and the drainage of the drainage to the outside of the two points in the main tube 130 and the two points The inflow of the drainage from the outside can be suppressed. Therefore, the drainage sensor 10 can keep a single sampling amount constant, and can improve quantitativeness. In addition, the drain liquid sensor 10 can allow the sub tube 133 to pass the liquid by the pressing of the first pressing member 115, and can extract one sampling amount through the sub tube 133.

  The opening area of the connection position in the subtube 133 where the main tube 130 and the subtube 133 are connected may be larger than the cross-sectional area (flow-path cross-sectional area) of the flow path 133z in the subtube 133.

  Thereby, the drain drainage sensor 10 can suppress the drainage drainage that can include various tissue pieces as well as the tissue pulverization fluid from being clogged in the vicinity of the inlet of the sub-tube 133. Therefore, the drain drainage sensor 10 It makes it easy for the drainage liquid to enter from the inlet of the tube 133, can guide the drainage liquid into the flow path 133z having a smaller area than the opening area of the connection position, and sends out the drainage liquid through the flow path 133z. Easy to do. Therefore, the drainage sensor 10 can stabilize the sampling amount at one time and improve the quantitativeness even when sampling the drainage fluid containing many tissue pieces or containing a relatively large tissue piece, for example.

  The drain liquid sensor 10 may be configured such that the pressure by the first pressing member 115 is released after the restriction by the restriction members 113 and 114 is released.

  Thereby, the drain liquid sensor 10 can guide the drain liquid discharged in the next sampling between two points in the main tube 130 by releasing the restriction by the restriction members 113 and 114. The drain drainage sensor 10 is ready to allow a new drain drainage to flow into the sub-tube 133 side in the next sampling by releasing the pressing by the first pressing member 115. Further, when the pressing by the first pressing member 115 is released, the restriction by the limiting members 113 and 114 has already been released, and therefore, between two points on the main tube 130 according to the release of the pressing by the first pressing member 115. It can suppress that a pressure falls in. Therefore, it is possible to suppress the drain drainage that has been pressed and moved to the sub-tube 133 from flowing back to the main tube 130 again. For this reason, the drain drain sensor 10 has an amount of drain drain sent by one sampling operation (one pressing operation by the first pressing member 115) with the release of the pressing by the first pressing member 115. It can suppress changing. Therefore, the drainage sensor 10 can suppress a decrease in the quantitativeness of the sampling amount.

  The drainage sampling mechanism 110 may be configured such that the restriction by the restriction members 113 and 114 and release of the restriction and the pressing and release of the pressure by the first pressing member 115 are repeatedly performed.

  Thereby, the drain liquid sensor 10 can continuously sample the drain liquid. The drain drain sensor 10 automatically performs sampling periodically and regularly by performing restriction and release of the restriction by the restriction members 113 and 114 and release and release of the pressure by the first pressing member 115 once an hour. The liquid can be obtained.

  The restricting members 113 and 114 may press two points on the main tube 130 and restrict the flow of the drain liquid between the range between the two points and the outside of the range.

  As a result, the drainage sensor 10 can restrict the flow of drainage by a simple operation of pressing two points of the main tube 130.

  Further, the interval between the two points in the main tube 130 may be adjustable.

  Thereby, the sampling amount can be easily varied. For this reason, the drain drainage sensor 10 determines the management target component (for example, amylase) to be measured even when the sampling amount required for the measurement of the management target component is different for each management target component (for example, blood, amylase, bilirubin). The interval between the two points may be adjusted so that a desired sampling amount can be obtained. Further, the interval between the two points may be determined in advance or may be dynamically changed. For example, the position where the limiting members 113 and 114 press the main tube 130 by a motor or the like may be moved along the direction in which the main tube 130 extends. For example, in the drainage sensor 10, the CPU 181 obtains a sampling amount necessary for measuring the management target component from a memory or the like by inputting information on the management target component via an operation unit (not shown), and performs sampling. The interval between the two points may be adjusted according to the amount.

  Further, the drainage sensor 10 may include a blood cell separation / enzyme reaction mechanism 150 (an example of an analysis unit) that analyzes the drain liquid that has passed through the sub-tube 133.

  Thereby, the drain drainage sensor 10 can carry out from drain drain sampling to analysis consistently. Therefore, the drainage sensor 10 is carried by the patient and can also analyze the drainage. Therefore, the drainage sensor 10 can automatically grasp the patient's condition while improving the patient's degree of freedom. Further, the drain drain sensor 10 can shorten the time required for the analysis from the drain drain sampling to the analysis as compared with the case where the drain drain sampling and the analysis are performed by separate apparatuses.

  Further, the main tube 130 may be connected to the drain tube 30 through which the drainage discharged from the living body flows. Drain drainage may be used as an example of a liquid.

  Thereby, the drain liquid sensor 10 can easily sample the drain liquid discharged from the living body. Moreover, liquids other than the drainage may be sampled. In this case, the drainage sensor 10 can analyze the state of the sampled liquid.

  Further, the drainage liquid may contain blood cells and non-blood cells. The blood cell separation / enzyme reaction mechanism 150 includes a glass membrane 204 (an example of a blood cell separation membrane) that separates blood cells and non-blood cells from drainage fluid, and may measure the state of the non-blood cells separated by the glass membrane 204. .

  As a result, the drainage sensor 10 can suppress measurement of a mixture of blood cell components having different characteristics when measuring the state of a non-blood cell by using the glass film 204. Therefore, the drainage sensor 10 can improve the measurement accuracy of the non-blood cell component. Therefore, the drainage sensor 10 can objectively evaluate the state of the non-blood cells contained in the drainage while improving the measurement accuracy of the non-blood cell components. Further, since the drainage sensor 10 can separate blood cells and non-blood cells by membrane separation, it is not necessary to use a centrifuge, and the drainage sensor 10 that separates blood cells and non-blood cells can be reduced in size and cost. Is possible.

  Further, the blood cell separation / enzyme reaction mechanism 150 may include an enzyme reaction sheet 205 that reacts with an enzyme contained in a non-blood cell separated by the glass membrane 204, and may measure the absorbance of the enzyme reacted by the enzyme reaction sheet 205.

  Accordingly, the drainage sensor 10 can color the enzyme using the enzyme reaction sheet 205 even when the colorless enzyme is a component to be managed. Therefore, when the measurement light is irradiated to the colored enzyme, the enzyme in the enzyme reaction sheet 205 can scatter the measurement light, and the photosensor 183 can receive the scattered light. Therefore, the drainage sensor 10 can measure the absorbance of the enzyme even when a colorless enzyme is a component to be managed, and can also derive the concentration of the enzyme based on the absorbance.

  The blood cell separation / enzyme reaction mechanism 150 includes a glass film 204, an enzyme reaction sheet 205, a spacer 203 having a hole 203z (an example of an opening) and disposed between the glass film 204 and the enzyme reaction sheet 205. , A take-up reel 172 for taking up the measurement tape 200 or a feed reel 171 (an example of a take-up member) for sending out the measurement tape 200, and a take-up reel for each measurement of enzyme absorbance. And a motor 175 for driving 172 (an example of a drive unit). The take-up reel 172 or the feed reel 171 may take up or send out the measuring tape 200 by driving the motor 175.

  Accordingly, the drainage sensor 10 can separate the glass film 204 and the enzyme reaction sheet 205 via the spacer 203. Therefore, the drainage sensor 10 can suppress the reagent 202 of the enzyme reaction sheet 205 from diffusing on the glass film 204 due to the long contact time between the enzyme reaction sheet 205 and the glass film 204. Further, since the measurement tape 200 is held in the feed reel 171 or the take-up reel 172, the measurement tape 200 is sent out when necessary, so that the measurement tape 200 can be used in enzyme measurement. Further, by feeding the measuring tape 200 by the driving force of the motor 175, it is possible to adjust the desired position on the measuring tape 200 to face the outlet of the sub tube 133. Therefore, the glass film 204 in the measuring tape 200 can receive the sampling liquid sq from the sub-tube 133 at a desired position. Further, by continuously driving the motor 175, the sampling solution sq containing the enzyme can be obtained continuously, and the absorbance of the enzyme can be measured.

  The blood cell separation / enzyme reaction mechanism 150 may include a second pressing member 116. The second pressing member 116 presses the measuring tape 200 at a position where the second pressing member 116 faces the hole 203z of the spacer 203 in the measuring tape 200 and is separated by the glass film 204 in the measuring tape 200. The enzyme and the enzyme reaction sheet 205 may be brought into contact with each other.

  In the drainage sensor 10, the acquired drainage is separated by the glass film 204, and the enzyme as a non-blood cell moves to a position facing the hole 203z in the glass film 204. At the position where the enzyme has moved, the glass film 204 is pressed by the second pressing member 116, whereby the region of the glass film 204 containing the enzyme and the enzyme reaction sheet 205 come into contact via the spacer 203. Therefore, the enzyme contacts the enzyme reaction sheet 205 after the movement of the enzyme, and the enzyme adsorbed in the non-blood cell adsorption region ar2 can be transferred to the enzyme reaction sheet 205 as in the transfer method. Therefore, it can be suppressed that the reagent 202 contained in the enzyme reaction sheet 205 moves outside without reacting with the enzyme and coloring of the enzyme becomes insufficient. Therefore, the drainage sensor 10 can suppress a decrease in measurement accuracy of the absorbance of the enzyme, and can suppress a decrease in measurement accuracy of the enzyme state.

  In the above-described embodiment, the measurement tape 200 includes a glass membrane 204 (an example of a blood cell separation membrane) that separates blood cells and non-blood cells from a drainage drained from a living body and containing blood cells and non-blood cells, and glass An enzyme reaction sheet 205 that reacts with enzymes contained in non-blood cells separated by the membrane 204, a spacer 203 having a hole 203z (an example of an opening) and disposed between the glass membrane 204 and the enzyme reaction sheet 205; May be included.

  Thereby, the measuring tape 200 can separate the glass film 204 and the enzyme reaction sheet 205 through the spacer 203. The measuring tape 200 can prevent the reagent 202 of the enzyme reaction sheet 205 from diffusing on the glass film 204 due to the long contact time between the enzyme reaction sheet 205 and the glass film 204. In addition, the measuring tape 200 has the hole 203z in a part of the spacer 203, so that the glass film 204 and the enzyme reaction sheet 205 are brought into contact with each other through the hole 203z using an external force such as pressing. When necessary, the enzyme on the glass film 204 and the reagent 202 contained in the enzyme reaction sheet 205 can be reacted. Therefore, the measuring tape 200 can assist various analyzes (for example, measurement of absorbance) using an enzyme that has reacted with the reagent 202.

  INDUSTRIAL APPLICABILITY The present invention is useful for a liquid ejecting apparatus, a measuring tape, and the like that are excellent in portability and can suppress liquid from remaining in a flow path after sampling.

DESCRIPTION OF SYMBOLS 5 Drain drainage management system 10 Drain drainage sensor 10A TCI pump 10z Case 10y Through-hole 20 Drain drainage monitor 20z Case 21 Display 22 Graph 23 Description 24 Meter 25 Status marker 26 CPU
27 Memory 28 Wireless chip 30 Drain tube 30A Dosing tube 40 Drain bag 41 Inflow tube 110 Drainage sampling mechanism 113, 114 Restriction member 113A, 114A, 115A, 116A Pressurization unit 113B, 114B Partition plate 115 First pressing member 115B Pressing plate 116 Second pressing member 116B Tip portion 130 Main tube 130c Tube central portion 133 Sub tube 133b Opening portion 133z Flow path 140 Third pressing member 141 First pressing portion 142 Second pressing portion 143 Rotating shaft 150 Blood cell separation / enzyme reaction mechanism 171 Feed reel 172 Take-up reel 175 Motor 176, 177 Roller 180 Sensor unit 180z Housing 181 CPU
182 LED
183 Photosensor 184 Wireless chip 185 Battery 186 Pressure unit drive unit 187 Motor drive unit 188 Circuit board 200, 200A, 200B Measuring tape 201, 201A, 201B PET sheet 202, 202B Reagent 203, 203B Spacer 204, 204A, 204B Glass Membrane 205, 205B Enzyme reaction sheet 300 Homogenizer 310 Container ar1 Blood cell adsorption area ar2 Non-blood cell adsorption area AS1 Area having four-layer structure AS2 Area having two-layer structure ba Blood cell g1, g11, g12, g21, g22, g31 Graph L1, L2 Broken line Lq Drain drainage Lq1 Mouse tissue pulverized solution ms1 Mouse mz Tissue piece P1 Pressing force P Internal pressure P2 Opening force or resistance PA1 Patient rz amylase sp1 Intestinal tissue sq, s 1, sq2 sampling liquid ws1 saline

Claims (14)

A liquid discharge device for discharging a liquid,
A main flow path;
A sub-channel branched from the main channel;
Two restricting members that restrict the flow of the liquid between the range between the two points in the main flow path and the outside of the range;
A first pressing member that presses the main channel between the two points in a state where the flow of the liquid is limited in the main channel;
With
The sub-channel allows the liquid from the main channel to pass when pressed by the first pressing member, and does not allow the liquid from the main channel to pass when not pressed by the first pressing member.
Liquid ejection device. The liquid ejection device according to claim 1,
The limiting force by the limiting member is a force capable of maintaining the flow restriction of the liquid in the main channel even when pressed by the first pressing member,
The pressing force by the first pressing member is a force that allows the sub-passage to pass through the liquid.
Liquid ejection device. The liquid ejection device according to claim 1 or 2,
The opening area of the connection position where the main channel and the sub channel in the sub channel connect is larger than the channel cross-sectional area in the sub channel,
Liquid ejection device. The liquid ejection device according to claim 1,
After the restriction by the restriction member is released, the pressure by the first pressing member is configured to be released.
Liquid ejection device. The liquid ejection device according to claim 1,
The restriction by the restriction member and the release of the restriction and the pressure by the first pressing member and the release of the pressure are configured to be repeatedly performed.
Liquid ejection device. The liquid ejection device according to any one of claims 1 to 5,
The restricting member presses the two points in the main flow path and restricts the flow of the liquid between a range between the two points and an outside of the range;
Liquid ejection device. The liquid ejection device according to any one of claims 1 to 6,
The interval between the two points in the main channel is adjustable.
Liquid ejection device. The liquid ejection apparatus according to claim 1, further comprising:
An analysis unit for analyzing the liquid that has passed through the sub-flow path;
Liquid ejection device. The liquid ejection device according to claim 8, wherein
The liquid is drained from the living body,
The main flow path is connected to a drain tube through which the drainage flows.
Liquid ejection device. The liquid ejection device according to claim 9, wherein
The drainage includes blood cells and non-blood cells,
The analysis unit includes a blood cell separation membrane that separates the blood cells and the non-blood cells from the drainage, and measures the state of the non-blood cells separated by the blood cell separation membrane,
Liquid ejection device. The liquid ejection device according to claim 10,
The analysis unit includes an enzyme reaction sheet that reacts with an enzyme contained in the non-blood cells separated by the blood cell separation membrane, and measures the absorbance of the enzyme reacted by the enzyme reaction sheet.
Liquid ejection device. The liquid ejection apparatus according to claim 11,
The analysis unit
A measuring tape having the blood cell separation membrane, the enzyme reaction sheet, and a spacer having an opening and disposed between the blood cell separation membrane and the enzyme reaction sheet;
A winding member for winding the measuring tape;
A drive unit for driving the winding member for each measurement of the absorbance of the enzyme;
With
The winding member winds or sends out the measurement tape by driving the driving unit,
Liquid ejection device. The liquid ejection device according to claim 12, wherein
The analysis unit
A second pressing member,
The second pressing member presses the measuring tape at a position where the opening of the spacer and the second pressing member face each other in the measuring tape, and is separated by the blood cell separation membrane in the measuring tape. Contacting the enzyme and the enzyme reaction sheet,
Liquid ejection device. A blood cell separation membrane that separates the blood cells and the non-blood cells from a drainage fluid discharged from the living body and containing blood cells and non-blood cells;
An enzyme reaction sheet that reacts with an enzyme contained in the non-blood cells separated by the blood cell separation membrane;
A spacer having an opening and disposed between the blood cell separation membrane and the enzyme reaction sheet;
Measuring tape having

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