Pressure measuring devices and medical devices

Abstract

The purpose of this invention is to ensure the connection quality of the pressure measuring device, achieve high-precision pressure measurement, and realize highly reliable regulation of fluid flow. A pressure measuring device measures the pressure of a detachable loop chamber. The device includes a connecting pipe arranged to allow gas flow between it and the loop chamber; a connector flow path (131) of a connector (13) to which an output port (117) of the loop chamber is connected in a connected state; a pressure sensor that measures the pressure space (S2) of the loop chamber and the pressure inside the connecting pipe in the connected state where the output port is connected to the connector flow path; a booster pump that pressurizes the inside of the connecting pipe; and a controller that drives the booster pump when the sealing ring (132) of the connector flow path, which is in airtight contact with the output port, is removed. In the connector flow path, a sealing ring is provided at the location where air is ejected by the booster pump in the disconnected state where the output port is removed.

Description

TECHNICAL FIELD

[0001] The present application relates to a pressure measuring device and a medical device in which a pressure sensor is detachably connected to a pressure changing space. BACKGROUND

[0002] As a medical device, by providing a pressure measuring device in which a pressure changing space is provided in the middle of a fluid flow path in correspondence with a fluid flowing inside the fluid flow path, and the pressure inside the space is detected and measured, a process of adjusting the flow of the fluid or the like is performed. For example, in a device of so-called dialysis treatment in which blood is subjected to purification treatment, in a blood circuit in which blood is made to circulate outside the body, the flow of blood is detected and adjusted by a pressure sensor (for example, refer to Patent Literature 1).

[0003] In this blood purification device (fluid flow device), the blood circuit must be replaced every time the treatment is performed in order to improve safety, and therefore the pressure measuring device is configured to be detachably connected to the blood circuit.

[0004] PRIOR ART DOCUMENTS

[0005] PATENT LITERATURE

[0006] Patent Literature 1: JP Patent No. 2020-89588 SUMMARY

[0007] PROBLEMS TO BE SOLVED BY THE INVENTION

[0008] Since such a pressure measuring device detects pressure fluctuations and adjusts the flow rate of the fluid, it is necessary to measure the pressure with high precision and high quality. However, if a foreign object such as a fiber is caught in the detachable connection portion on the pressure changing space side and leakage occurs, an adverse situation in which the flow amount of the fluid or the like cannot be adjusted with high reliability can occur.

[0009] Therefore, an object of the present application is to achieve high-precision pressure measurement and high-reliability fluid flow adjustment by ensuring the connection quality of the pressure measuring device.

[0010] TECHNICAL SOLUTION FOR SOLVING THE PROBLEM

[0011] One aspect of the pressure measurement device of the present application that addresses the above-described problems relates to a pressure measurement device that is detachably attached to a detachable member including a fluid flow path through which a fluid flows, and that measures pressure of the detachable member as a measurement target, the pressure measurement device including: a communication flow path that is provided in a manner that gas can flow therebetween; a connection portion to which a connected portion of the detachable member is connected in a manner that the fluid flow path and the communication flow path are in a communication state or a communication release state; a pressure sensor that is connected to the connected portion and the connection portion, and that measures pressure in the fluid flow path and the communication flow path when the fluid flow path and the communication flow path are in the communication state; a pressure increasing / decreasing portion that increases or decreases pressure in the communication flow path in a manner that gas is discharged to the outside or drawn in; and a drive portion that manually or automatically drives the pressure increasing / decreasing portion at a time when a first contact surface of the connection portion that is in contact with the connected portion in a gas-tight manner is separated from the connected portion, the first contact surface being formed in the connection portion at a position at which gas is discharged or drawn in by the pressure increasing / decreasing portion in the communication release state in which the connection portion is separated from the connected portion.

[0012] One aspect of the medical device of the present application that addresses the above-described problems relates to a medical device including the pressure measurement device, the detachable member including a blood flow path through which blood flows as the fluid flow path, the detachable member including a chamber that constitutes a part of the blood flow path, and that can store blood and gas, and the measurement target being an internal space of the chamber.

[0013] Effects of the Invention

[0014] As such, according to one aspect of the present application, the pressure measurement device can be connected to a space in which pressure fluctuates with high quality, and pressure can be measured with high accuracy. Thus, the present application aims to achieve a process such as fluid flow regulation with high reliability. BRIEF DESCRIPTION OF DRAWINGS

[0015] Figure 1 FIG. 1 is a perspective view showing an appearance of a blood purification device as one example of a medical device including a pressure measurement device according to one embodiment of the present application;

[0016] Figure 2 FIG. 2 is a circuit diagram schematically showing a passage through which blood flows as a fluid;

[0017] Figure 3 FIG. 3 is a perspective view showing a main body side and a cover of a blood pump;

[0018] Figure 4 (a) is a perspective view showing a joint that constitutes a connection of a circuit chamber that forms a part of a blood circuit and a pressure measuring device, Figure 4 (b) is a perspective view showing the joint;

[0019] Figure 5 (a) is a longitudinal sectional view showing a circuit chamber that forms a part of a blood circuit, Figure 5 (b) is a longitudinal sectional view showing a joint that connects the circuit chamber and a pressure measuring device;

[0020] Figure 6 is a longitudinal sectional view showing a state in which the joint is connected to Figure 5 the circuit chamber shown in

[0021] Figure 7 (a) is a longitudinal sectional view showing a state in which the circuit chamber shown in Figure 5 is connected to a main part of the joint, Figure 7 (b) is a longitudinal sectional view showing a main part of a state in which the circuit chamber is separated from the joint;

[0022] Figure 8 is a block diagram showing a connection structure of a controller that controls the entire device;

[0023] Figure 9 is a schematic view showing a structure of a main part at the time of a connection operation of the blood circuit;

[0024] Figure 10 is a schematic view showing a structure of a main part of another circuit chamber in the blood circuit;

[0025] Figure 11 is a view showing another structure in which the joint is connected to the circuit chamber, Figure 11 (a) is a sectional view showing a state at the time of connection preparation, Figure 11 (b) is a sectional view showing a state in the middle of a connection operation. DETAILED DESCRIPTION

[0026] Embodiments of the present application will be specifically described below with reference to the accompanying drawings. Figures 1-9 is a view showing a blood purification device as one example of a medical device including a pressure measuring device of a first embodiment of the present application.

[0027] <First Embodiment>

[0028] In Figure 1 and Figure 2In this embodiment, the blood purification device M is configured from a medical device including two sets of pressure measuring devices 1, a blood circuit 2, and a dialysis circuit 3, and performs dialysis treatment (blood purification treatment) of a patient based on the measurement results of the respective pressure measuring devices 1 by driving the respective portions of the device including the blood circuit 2 and the dialysis circuit 3 in response to an input operation from an operation panel (operation section) P. The blood circuit 2 includes an arterial side blood circuit 21 and a venous side blood circuit 22, and circulates the blood of the patient through the dialyzer 31 by means of a blood pump 23. The dialysis circuit 3 includes the dialyzer 31 that connects the arterial side blood circuit 21 and the venous side blood circuit 22 of the blood circuit 2, two systems of a dialysate introduction line 34 and a dialysate discharge line 35 connected to the dialyzer 31, and a double pump 36 that makes the dialysate inside these lines 34, 35 flow. The blood purification device M is manufactured from the dialysate introduction line 34, the dialysate discharge line 35, and the double pump 36 of the dialysis circuit 3, and the arterial side blood circuit 21 and the venous side blood circuit 22 of the blood circuit 2, and is configured in a manner that the dialyzer 31 of the dialysis circuit 3 is detachably attached and used once.

[0029] Here, the dialyzer 31 connects the dialysate introduction line 34 to the dialysate introduction port 31c and connects the dialysate discharge line 35 to the dialysate discharge port 31d, thereby forming a flow path in which the dialysate flows inside the hollow fibers (not shown in the drawing) and performs dialysis treatment using the hollow fiber blood purification membrane via the blood of the patient flowing in the blood circuit 2. The double pump 36 is disposed across the dialysate introduction line 34 and the dialysate discharge line 35, and the dialysate is driven in a manner that it is pressure-fed in both the introduction direction and the discharge direction in a stable manner through the dialyzer 31. In addition, one end of the dialysate introduction line 34 is connected to a dialysate supply device (not shown in the drawing), and the dialysate is supplied to the dialysate 31 through the dialysate introduction port 31c of the other end while adjusting the concentration of the dialysate, and one end of the dialysate discharge line 35 is connected to a dialysate discharge mechanism (not shown in the drawing), and the dialysate after dialysis is discharged via the dialysate discharge port 31d of the other end. Furthermore, a water pump 37 is disposed in the dialysate discharge line 35 in a manner that it bypasses the double pump 36, and removes water from the blood of the patient flowing through the dialyzer 31.

[0030] One end of the arterial side blood circuit 21 of the blood circuit 2 is connected to the blood inlet 31a of the dialyzer 31 of the dialysis circuit 3, and the other end is connected by an arterial puncture needle 210 that punctures the patient's blood vessel, thereby establishing a connection and allowing the dialyzer 31 to receive blood for dialysis (so-called de-hemolysis) in a processable manner. The arterial side blood circuit 21 has a pressure measuring device 1 and a blood pump 23 installed midway through the circuit. The pressure measuring device 1 measures the pressure corresponding to the blood flow in the circuit, while the blood pump 23 pumps blood in a manner that ensures a stable flow of blood in the circuit. Additionally, the arterial side blood circuit 21 includes a connector 211 for connecting the arterial puncture needle 210 and a clamp 212 for regulating and controlling the blood flow in the circuit by opening and closing valves.

[0031] Here, the blood circuit 2 (21, 22) consists of an elastically deformable tube that can flowably contain blood within an internal fluid flow path. In contrast, the blood pump 23 is a so-called tubular pump (squeeze pump) that compresses the arterial side of the tubular blood circuit 21 of the blood circuit 2 by moving it in both directions to squeeze the blood within the fluid flow path and deliver it downstream. Through the negative pressure generated by the pressure of the fluid being delivered downstream, fluid from the upstream side is continuously introduced.

[0032] Blood pump 23 Figure 3 As shown, the blood pump 23 is manufactured with the following structure, in which a generally disc-shaped rotor 232 is rotatably received inside a circular concave stator 231. The blood pump 23 is configured such that a tubular arterial blood circuit 21 is sandwiched between the rotor 232 and the circular inner wall surface 231s of the stator 231, wound around the outer circumference of the rotor 232. In the blood pump 23, a pair of rollers 233 are rotatably arranged parallel to the axis of rotation of the disc-shaped rotor 232 at symmetrical positions on opposite sides (opposite diameter directions) of the axis of rotation. In the blood pump 23, the pair of rollers 233 press the arterial blood circuit 21 against the circular inner wall surface 231s of the stator 231, flattening the inner surface of the tube in a liquid-sealed manner, and simultaneously rotating in conjunction with the rotational drive of the rotor 232. Thus, the blood pump 23 can rotate the rotor 232 to push the blood in the arterial side blood circuit 21 to the downstream side. When the rotor stops rotating, the roller 233 on the circular inner wall surface 231s of the stator 231 flattens the arterial side blood circuit 21 in a liquid-sealing manner, stopping the flow of blood in the tube.

[0033] Additionally, the blood pump 23 includes a cover 235 that covers the outside of the rotor 231 and limits interference to the rotating rotor 232, the pre-set arterial blood circuit 21, etc. The blood pump 23 also includes a cover detection sensor 235s (e.g., a cover detection sensor 235s) for detecting the opening and closing of the cover 235.Figure 8 (As shown), to prevent accidents from occurring in the future. In this blood pump 23, guide members 234 extending in a direction orthogonal to the axis (diameter direction) of the disc-shaped rotor 232 are arranged at four locations above and below a pair of rollers 233 to prevent the tubular arterial side blood circuit 21 wound around the rotor 232 from falling out of the stator 231.

[0034] One end of the venous side blood circuit 22 of blood circuit 2 is connected to the blood outlet 31b of the dialyzer 31 of dialysis circuit 3, thereby achieving communication. The other end is connected by a venous puncture needle 220 puncturing the patient's blood vessel. Through the dialyzer 31, the dialyzed blood is returned to the patient side (so-called backflow). The venous side blood circuit 22 has a pressure measuring device 1 and a venous chamber 225 set in the middle of the circuit. While the pressure measuring device 1 measures the pressure corresponding to the blood flow in the circuit, the venous chamber 225 removes air bubbles mixed in with the blood flowing (pumped) through the blood pump 23 on the venous side blood circuit 22, safely returning normal blood to the patient. Additionally, the venous blood circuit 22 includes: a connector 221 for connecting to the venous puncture needle 220; a blood discrimination unit 222 for determining whether the fluid flowing in the circuit is blood; a clamp 223 for regulating and controlling the flow of blood in the circuit by opening and closing a valve; and a bubble detector 224 for detecting air bubbles mixed in with the blood flowing in the circuit. Of course, the blood discrimination unit 222 can also be located on the arterial blood circuit 21 side, or it can be configured in both of these blood circuits 21 and 22.

[0035] In addition, two sets of pressure measuring devices 1 are respectively installed in the arterial side blood circuit 21 and the venous side blood circuit 22 of the blood circuit 2. As described later, they detect and measure the pressure inside the blood circuit 2 that changes in response to the flow of the patient's blood, so that the patient's blood is delivered (flowing) at the optimal pressure on the arterial and venous sides.

[0036] Pressure measuring device 1 is configured as follows: Figures 4-6 As shown, a connector 13 is detachably installed in the loop chamber 11 to connect a pressure sensor 15. This is done to measure the pressure within the loop chamber (detachable component) 11, which is detachably positioned midway between the arterial side blood loop 21 and the venous side blood loop 22 of the blood loop 2. Furthermore, in Figure 2The diagram illustrates the situation in which the loop chamber 11 and connector 13 are in a disconnected and connected state. However, as described later, they are constructed in a way that allows for the integration and removal of the filter 116 as a single unit. In connector 13, by connecting the connecting tube 14C to the cylindrical protrusion 131p (described later), the spatial pressure within the loop chamber 11 reaches the pressure sensor 15, enabling the detection (measurement) of pressure fluctuations in blood flow.

[0037] like Figure 4 (a) and Figure 5 As shown in (a), the circuit chamber 11 includes connection ports 112, 113 communicating with the space S formed in the housing 111, such that the space S is located midway in each of the blood circuits 2 (21 and 22), thereby forming part of a continuous fluid flow path via the dialyzer 31.

[0038] The circuit chamber 11 is configured such that a diaphragm 115 is provided inside the outer shell 111, dividing the space S into a connecting space S1 and a pressure space S2. The connecting space S1 serves as a fluid flow path (blood flow path) between the connecting ports 112 and 113. The pressure space S2 functions such that its volume changes as the diaphragm 115 deforms in response to the flow of blood in the connecting space S1.

[0039] Additionally, the loop chamber 11 has an output port 117 that communicates with the pressure space S2 via a filter 116. The loop chamber 11 is manufactured in such a way that it forms an integrated structure by inserting a cylindrical insertion connector 119 formed around the output port 117 into a cylindrical socket connector 139 of the connector 13 (described later), and the output port (connected portion) 117 is connected to the connector flow path (connection portion) 131 of the connector 13. Furthermore, the filter 116 of the loop chamber 11 prevents, in the future, situations such as diaphragm 115 rupture, from causing blood in the communication space S1 to flow into the pressure space S2 and out from the output port 117 into the interior of the connector 13 on the pressure sensor 15 side.

[0040] like Figures 4-6As shown, the connector 13 is manufactured in the following manner: a sealing ring 132 made of elastic material is received inside the large-diameter portion 131d formed at one end of the connector flow path (connection portion) 131; the sealing ring 132 (first contact surface) is airtightly sandwiched between the sealing ring 132 and the outside of the output port (connected portion) 117 of the inserted circuit chamber 11; and the sealing ring 132 is airtightly connected (see [reference]). Figure 7 (a) Furthermore, in the connector 13, a cap 134 made of elastic material and formed in an annular shape is provided on the end face of the large diameter portion 131d at one end of the connector flow path 131. In the cap 134, a short flange is formed on the periphery of the annular shape, and has an inner peripheral slope 143s located on the inner peripheral side of the large diameter portion 131d of the connector flow path 131.

[0041] Connector 13 is manufactured in a manner that suppresses the following conditions, such as Figure 7 As shown in (b), when the insertion connector 119 of the circuit chamber 11 is pulled out from the connector flow path 131, the sealing ring 132, which deforms and moves in the direction of arrow F1, collides with the inner peripheral inclined surface 143s of the cap 134, pressing the flange 143 against the inner surface of the large diameter portion 131d in the direction of arrow F2, causing it to fall off. Furthermore, when the insertion connector 119 of the circuit chamber 11 is pulled out from the connector flow path 131, the cap 134 can act as a stop for the sealing ring 132 from the large diameter portion 131d.

[0042] Here, in connector 13, a cylindrical socket connector 139, which fits into the insertion connector 119 of the insertion loop chamber 11, is fixed to the outside of the large-diameter portion 131d at one end of connector flow path 131, and a cylindrical protrusion 131p of the connecting tube 14C, which communicates with the pressure sensor 15, is formed at the other end of connector flow path 131. This connector 13 is implemented in such a way that it is integrated with the loop chamber 11, whose output port 117 is connected to connector flow path 131 and communicates with pressure sensor 15 via connecting tube (communicating flow path) 14C.

[0043] Furthermore, in the circuit chamber 11, a locking protrusion 118 is formed on the outside of the cylindrical insertion connector 119, and an L-shaped crank groove 138 is formed in the connector 13, which is continuous with the open side end of the cylindrical socket connector 139. When the insertion connector 119 is inserted into the socket connector 139, the circuit chamber 11 and the connector 13 can be locked in a non-removable manner by simply moving the cylindrical part axially, by causing the locking protrusion 118 to rotate relative to the insertion crank groove 138 in a simultaneously engaged position.

[0044] Therefore, in the pressure measuring device 1 of this embodiment, connecting pipes 14C1 and 14C2 are respectively connected to the connector flow path 131 of the connector 13 integrally formed in the respective circuit chamber 11 of the blood circuit 2 (21, 22), and a pair of branch pipes 14D1 and 14D2 are connected to the common pipe 14G. Specifically, on the pair of connecting pipes 14C1 and 14C2 connected to the connector flow path 131 of the connector 13, one end of a pair of branch pipes 14D1 and 14D2 is respectively connected and branches off. The other end of the branch pipes 14D1 and 14D2 converge and connect to one end of the common pipe 14G, and the flow is merged.

[0045] Branch pipe 14D1 branches off from connecting pipe 14C1. Within connecting pipe 14C1, at a connector 13 integrated with the circuit chamber 11 on the arterial side of the blood circuit 21, a pressure sensor 15 is functionally connected. A solenoid valve (on / off section) 161 for opening and closing the connecting flow path is provided midway to the common pipe 14G. Similarly, branch pipe 14D2 branches off from connecting pipe 14C of the pressure sensor 15 on the venous side of the blood circuit 22. A solenoid valve 162 for opening and closing the connecting flow path is provided midway to the common pipe 14G.

[0046] On the opposite side (the other end side) of the branch pipes 14D1 and 14D2 on one end of the common pipe 14G, a booster pump (boosting / reducing unit) 17 for introducing pressurized air is provided via connecting pipes 14C1 and 14C2 on the connector 13 side. Additionally, a pressure sensor 18 is installed along this flow path in a functional manner. A filter 17f is installed in the booster pump 17 to prevent dust or other contaminants from entering the introduced air. Here, the booster pump 17 has the function of boosting and depressurizing the connector 13 side by driving in both forward and reverse directions, but it is not limited to this; it could also be a dedicated machine with only one function of forward (boosting) or reverse (reducing). For example, during depressurization drive, similar to the booster air described later, the fluid (air) flowing by suction action could be sprayed towards the desired location.

[0047] Here, the booster pump 17 is a tubular pump with the same function as the blood pump 23. A common pipe 14G is sandwiched between it and the stator 17s. While flattening the common pipe 14G, the rotor-side rollers 17r rotate, thereby delivering pressurized air to the connector 13 side of the blood circuit 2 (21, 22) via branch pipes 14D1, 14D2 and connecting pipes 14C1, 14C2. The booster pump 17 has four equally spaced rotor-side rollers 17r positioned relative to the radially spaced two locations of the rotor-side rollers 233 of the blood pump 23, flattening the common pipe 14G against the stator 17s side in an airtight manner. Thus, the booster pump 17 rotates the rotor-side rollers 17r, compressing the air in the common pipe 14G to the branch pipes 14D1, 14D2. Furthermore, the common pipe 14G can be shut off in a non-flowing manner without a valve when the rollers 17r have stopped rotating.

[0048] However, the blood purification device M allows the patient's blood to pass through the arterial blood circuit 21 and the venous blood circuit 22, while the dialysate passes through the dialysate inlet line 34 and the dialysate outlet line 35 in parallel through the dialyzer 31. Figure 8 The controller 50 shown integrates the control of various parts of the device, including the blood pump 23, the dual pump 36, etc., thereby implementing dialysis treatment to process the patient's blood.

[0049] The controller 50 consists of a CPU and various memories such as RAM and ROM. It performs various control processes, including dialysis processing, by executing a pre-stored control program corresponding to the input operation from the operation panel P based on the obtained detection information, stored parameters, etc.

[0050] Specifically, such as Figure 8As shown, the controller 50 connects the following components: clamps 212 and 223 installed in the blood circuit 2, a blood discriminator 222 and a bubble detector 224, and a blood pump 23; and the various parts of the device, including a dual pump 36 and a dewatering pump 37 installed in the dialysis circuit 3, are connected to the operation panel P and the human body sensor 51 in a manner that allows exchangeable control signals. The controller 50, based on input operations from the operation panel P and assuming the presence of a user such as a nurse operating the operation panel P, controls the drive of each part of these devices, thereby allowing the patient's blood and dialysate to pass through the dialyzer 31 at specific flow rates and pressures for dialysis treatment of the purified blood. Here, the operation panel P has an operation area for inputting and setting various input operations of the blood purification device M, such as drive conditions, and a display area for outputting and notifying drive times, etc., and a preparation button Pb is provided in a manner operable by a user such as a nurse. This preparation button Pb, along with messages prompting various operations, performs preparatory actions before starting and stopping the dialysis treatment described later.

[0051] Additionally, the controller 50 is connected to pressure sensors 15 and 18, solenoid valves 161 and 162, and pressure pump 17 in exchange for various signals. During dialysis, the controller 50 closes solenoid valves 161 and 162, and the pressure sensors 15 detect the pressure in the pressure space (measurement object) S2 of the circuit chamber 11 connected via connecting pipes 14C1 and 14C2, respectively, to obtain the pressure fluctuation within the connected space S1 of the circuit chamber 11. Thus, the controller 50 can monitor the flow quality of the patient's blood in the arterial side blood circuit 21 and the venous side blood circuit 22 of the blood circuit 2. For example, the operation panel P can display and output various messages, ensuring safe and appropriate dialysis treatment.

[0052] At this time, the controller 50 can also be used as a drive unit, which, while continuing dialysis, opens solenoid valves 161 and 162 to drive the booster pump 17. During this dialysis process, the pressure in the pressure space S2 of the loop chamber 11 is detected by the pressure sensor 15 to obtain the pressure fluctuation in the communication space S1. The controller 50 pressurizes (push in outside air) the pressure space S2 of the loop chamber 11 via the booster pump 17, through branch pipes 14D1 and 14D2 and the common pipe 14G, thereby changing the fluid volume (pressure) in the communication space S1 and regulating the flow rate and speed of the patient's blood. In addition, the controller 50 performs regulation and control in the following manner: simultaneously, the pressure in the common pipe 14G is detected by the pressure sensor 18 to obtain the pressurization in the pressure space S2 of the loop chamber 11 detected by the pressure sensor 15. In other words, the pressurization effect in the communication space S1 of the loop chamber 11 is optimized by adjusting the drive of the booster pump 17. In addition, in this embodiment, the following case is used as an example to illustrate that a booster pump 17 is provided to regulate the flow rate and speed of the patient's blood in the communication space S1 of the control circuit chamber 11. However, it is not limited to this. Obviously, it can also be installed in the arterial side blood circuit 21 and the venous side blood circuit 22 of the blood circuit 2, and can be regulated and controlled separately.

[0053] Furthermore, when preparing for dialysis treatment of blood flowing in blood circuits 2 (21, 22), before connecting circuit chamber 11 to connector 13, controller 50 presses the preparation button Pb according to the preparation operation message on the operation panel P. If so, the circuit connection preparation action described later is performed, in which foreign matter adhering to the sealing ring 132 of connector flow path 131 of connector 13 is ejected. Specifically, controller 50 responds to the pressing of preparation button Pb, for example, as... Figure 9 As schematically shown, solenoid valves 161 and 162 are opened, and booster pump 17 is driven to pressurize the pressure space S2 of the loop chamber 11, which is connected via various pipes 14C1, 14C2, 14D1, 14D2, and 14G, to the desired pressure (compressing outside air). Afterward, when the prepare button P on the operation panel Pb is pressed again, controller 50 closes solenoid valves 161 and 162 and stops the drive of booster pump 17, allowing it to wait. Thus, controller 50 can continue the loop connection preparation operation, injecting air from the connector flow path 131 of connector 13 before connecting the loop chamber 11.

[0054] Here, the controller 50 drives the booster pump 17 in such a manner that the pressure sensor 18 detects and measures the pressure in the common tube 14G, which is pressurized to the extent that foreign matter adhering to the sealing ring 132 of the connector flow path 131 of the connector 13 is ejected. In this way, the pressure sensor 18 differs from the pressure sensor 15, which detects and measures the pressure in the pressure space S2, where the pressure fluctuates due to the blood flow in the communicating space S1 of the loop chamber 11. Therefore, the controller 50 appropriately adjusts the measurement range of the pressure sensors 15 and 18 to perform pressure measurement.

[0055] Therefore, in order to perform dialysis treatment of the patient's blood flowing in the blood circuit 2, when the pressure measuring device 1 is preparing to connect the circuit chamber 11 to the connector 13, it can simply press the button Pb on the preparation operation panel P to drive the booster pump 17 to spray air from the connector flow path 131 of the connector 13, and insert the socket connector 139 into the insertion connector 119 to make an airtight connection.

[0056] Therefore, the blood purification device M can spray the pressurized air from the booster pump 17 onto the sealing ring 132 of the large diameter portion 131d of the connector flow path 131 of the connector 13, thus spraying away the attached foreign matter.

[0057] As a result, the blood purification device M can prevent the following situation in the future: a foreign object is trapped between the sealing ring 132 in the connector flow path 131 of the connector 13 and the outside of the output port 117 of the loop chamber 11, causing leakage in the pressure space S2, and making it impossible to measure the pressure change corresponding to the flow of blood in the communication space S1 of the loop chamber 11.

[0058] <Effects of the First Implementation Plan>

[0059] In this way, in the blood purification device M of this embodiment, the connector 13 of the pressure measuring device 1 can be connected to the circuit chamber 11, and the pressure sensor 15 can detect and measure the pressure change of the pressure space S2 of the circuit chamber 11 with high precision.

[0060] Therefore, the blood purification device M can precisely adjust the blood flow in the blood circuit 2, enabling the patient's blood to flow stably and reliably for dialysis and purification.

[0061] <Other Forms of the First Implementation Plan>

[0062] Here, in this embodiment, the following type (so-called pressure chamber) is used as an example for illustration, but it is not limited thereto. In this type, the circuit chamber 11 is divided into a communication space S1 communicating with the blood circuit 2 and a pressure space S2 communicating with the connector flow path 131 of the connector 13 by means of a diaphragm 115 of the separating membrane in a liquid-sealed manner. For example, as Figure 10 As shown in another manner, the so-called air-enclosed circuit chamber 1011, which omits the diaphragm 115 and includes an internal space S, can also be applied to the blood circuit 2 in the corresponding circuits of the arterial side blood circuit 21 and the venous side blood circuit 22.

[0063] Specifically, the loop chamber 1011 is constructed in such a manner that flowing blood enters from the gas phase side of the upper part of the internal space S and exits from the liquid phase side of the lower part of the internal space S, forming part of the blood loop 2. In the loop chamber 1011, the output port 117 and the insertion connector 119 are located on the upper side of the internal space S and are inserted into the socket connector 139 of the connector 13, communicating with the connector flow path 131.

[0064] In other ways, during dialysis, the pressure in the internal space S of the circuit chamber 1011 without the diaphragm 115 can be detected by the pressure sensor 15 to obtain the pressure fluctuations in the blood circuit 2 (21, 22), so as to grasp the quality of the patient's blood flow and perform dialysis safely and appropriately.

[0065] In this other configuration, while dialysis continues, the pressure sensor 15 detects the gas phase pressure in the internal space S of the circuit chamber 1011. Corresponding to the pressure change, the booster pump 17 is driven, thereby pressurizing (pressurizing external gas) the internal space S, changing the liquid level at the gas and liquid phase boundary, and regulating and controlling the flow rate and volume of the patient's blood.

[0066] <Second Implementation Plan>

[0067] The following describes a blood purification apparatus as an example of a medical device that includes a pressure measuring device according to the second embodiment of the present invention. Here, since this embodiment is configured in a substantially the same way as the embodiments described above, the same reference numerals are used to describe the same structures (the same applies to other embodiments described later).

[0068] like Figures 1-9As shown, the controller 50 of the blood purification device M performs the circuit connection preparation operation as described above when the preparation button Pb of the operation panel P of the above embodiment is pressed instead of the button Pb of the control panel P of the above embodiment. When the cover 235 of the blood pump 23 is opened and closed and the setting of the arterial blood circuit 21 is detected according to the detection signal of the cover detection sensor 235s, the circuit connection preparation operation of the above embodiment is performed.

[0069] Specifically, when the cover 235 of the blood pump 23 opens and closes, and the arterial blood circuit 21 is set, the controller 50 opens the solenoid valves 161 and 162 and starts driving the booster pump 17. Afterward, the controller 50 measures the elapsed time from the start time, and when a preset driving time has elapsed—for example, the time required to sufficiently connect the circuit chamber 11 to the connector 13—the controller 50 closes the solenoid valves 161 and 162 and stops driving the booster pump 17.

[0070] Therefore, the pressure measuring device 1 can reliably perform the following preparation operation with high quality and high reliability, in which the circuit chamber 11 of the blood circuit 2 is airtightly connected to the connector 13 in a slack manner, and the following situation can be prevented: after the preparation operation, the booster pump 17 is automatically stopped, and the common pipe 14G and the like are consumed by the winding operation of the roller 17r.

[0071] <Effects of the Second Implementation Plan>

[0072] In this way, in the blood purification device M of this embodiment, the load of the booster pump 17 of the pressure measuring device 1 during the preparation of the circuit connection can be reduced, the consumption of various components around the booster pump 17 including the common pipe 14G can be reduced, and the drive can be stably performed.

[0073] <Third Implementation Plan>

[0074] The following describes a blood purification device as an example of a medical device that includes a pressure measuring device according to a third embodiment of the present invention.

[0075] like Figures 1-9 As shown, the controller 50 of the blood purification device M in the above embodiment replaces the press of the preparation button Pb on the operation panel P of the above embodiment, and performs the circuit connection preparation action of the above embodiment when the human body sensor 51 detects that the user is operating the operation panel P or setting the arterial side blood circuit 21 in the blood pump 23.

[0076] Specifically, when the human body sensor 51 detects a user in front of the blood purification device M, the controller 50, in the same manner as in the above embodiment, opens the solenoid valves 161 and 162 and starts driving the booster pump 17. When it is confirmed that the time elapsed since the start time exceeds, for example, the working time for sufficiently connecting the loop chamber 11 to the connector 13, the controller 50 closes the solenoid valves 161 and 162 and stops driving the booster pump 17.

[0077] <Effects of the Third Implementation Plan>

[0078] In the blood purification device M of this embodiment, similarly to the above embodiment, the pressure pump 17 of the pressure measuring device 1 can also reduce the load of the accompanying circuit connection preparation operation, reduce the consumption of the components around the booster pump 17 including the common pipe 14G, and drive stably.

[0079] <Fourth Implementation Plan>

[0080] Next, a blood purification device will be described as an example of a medical device that includes a pressure measuring device according to the fourth embodiment of the present invention.

[0081] like Figures 1-9 As shown, when the controller 50 of the blood purification device M performs the loop connection preparation operation as described in the above embodiment, it opens solenoid valves 161 and 162 to switch to the connected state after confirming the following condition: when the solenoid valves 161 and 162 are closed in the disconnected state, the booster pump 17 is driven, and the booster pressure (measured value) in the common pipe 14G detected by the pressure sensor 18 reaches the predetermined opening pressure (accumulation pressure). Afterward, when the controller 50 confirms that the booster pressure in the pressure space S2 of the loop chamber 11 detected by the pressure sensor 15 has reached the predetermined final pressure, it closes solenoid valves 161 and 162 and stops driving the booster pump 17.

[0082] Therefore, in addition to the effects of the above-described implementation scheme, the pressure measuring device 1 can also drive the booster pump 17 to spray compressed air stored in the common pipe 14G from the connector flow path 131 of the connector 13, effectively spraying away foreign objects attached to the sealing ring 132. In addition, it can accurately determine that the connection is complete and automatically stop the booster pump 17 to suppress the consumption of the common pipe 14G due to the narrowing action of the roller 17r.

[0083] <Effects of the Fourth Implementation Plan>

[0084] In this way, in the blood purification device M of this embodiment, in addition to the functions of the above-described embodiment, the operation of connecting the output port 117 of the circuit chamber 11 in the blood circuit 2 to the connector flow path 131 connected to the connector 13 can be performed with high quality and high reliability. This can reduce the consumption of various components around the booster pump 17, including the common pipe 14G, and ensure stable driving.

[0085] <Fifth Implementation Plan>

[0086] Next, a blood purification device will be described as an example of a medical device that includes a pressure measuring device according to the fifth embodiment of the present invention.

[0087] like Figures 1-9 As shown, when the controller 50 of the blood purification device M performs the circuit connection preparation operation as described above, it opens solenoid valves 161 and 162 and repeatedly drives the booster pump 17 in forward (boosting) and reverse (depressurizing) directions at certain intervals. Afterwards, when the controller 50 confirms that the set operating time (drive time) has elapsed since the start time, it closes solenoid valves 161 and 162 and stops the booster pump 17.

[0088] Therefore, in addition to the functions of the above-described implementation scheme, the pressure measuring device 1 also intermittently sprays compressed air into the sealing ring 132 of the connector flow path 131 of the connector 13 by repeatedly driving the booster pump 17 in both forward and reverse directions, and can intermittently suck air into the vicinity of the sealing ring 132, which can effectively remove foreign matter attached to the sealing ring 132.

[0089] <Effects of the Fifth Implementation Plan>

[0090] In this way, in the blood purification device M of this embodiment, in addition to the effects of the above-described embodiment, the operation of connecting the output port 117 of the circuit chamber 11 in the blood circuit 2 to the connector flow path 131 connected to the connector 13 can be performed with high quality and high reliability.

[0091] <Sixth Implementation Plan>

[0092] Next, combined Figure 11 A blood purification device will be described as an example of a medical device that includes a pressure measuring device according to the sixth embodiment of the present invention.

[0093] like Figures 1-9 As shown, the blood purification device M has a connector 13 connected to the circuit chamber 11 installed in the blood circuit 2, which enables the function of the pressure measuring device 1. In this embodiment, as... Figure 11As shown in (a), it is made of a connecting structure of connector flow path 1131 of connector 13 inserted inside the output port 1117 which is connected to the pressure space S2 of the loop chamber 11.

[0094] Specifically, the connector flow path 1131 of connector 13 is truncated cone-shaped, and the output port 1117 of the loop chamber 11 is formed by a connector shape having an inner surface of the truncated cone embedded in the connector flow path 1131, replacing the socket connector 139 of the above embodiment. The connector flow path 1131 and the output port 1117 are formed in a way that a sealing ring 1132 is sandwiched between the mutually fitting outer and inner truncated cones, and are connected and joined in an airtight manner.

[0095] Therefore, in order to perform dialysis treatment of the patient's blood flowing in the blood circuit 2, the pressure measuring device 1, during the circuit connection preparation operation of connecting the circuit chamber 11 to the connector 13, such as... Figure 11 As shown in (b), the pressurized air from the booster pump 17 can be injected toward the output port 1117 side and the sealing ring 1132 side of the connector flow path 1131 to spray away the attached foreign matter. At this time, the pressurized air compressed by the booster pump 17 can be injected from the connector flow path 1131 side of the connector 13, and then injected into the interior of the output port 1117 before it is immediately connected to the output port 1117 of the circuit chamber 11, and then injected back, so that it can pass through the narrow gap between it and the connector flow path 1131 and forcefully spray away the foreign matter attached to the sealing ring 1132.

[0096] As a result, the blood purification device M can more effectively prevent the following situation in the future: a foreign object gets stuck between the sealing ring 132 of the connector flow path 1131 of the connector 13 and the output port 1117 of the loop chamber 11, causing leakage in the pressure space S2 and making it impossible to measure the pressure fluctuations corresponding to the blood flow in the communication space S1 of the loop chamber 11.

[0097] <Effects of the Sixth Implementation Plan>

[0098] In this way, the same effect as in the above-described embodiment can be achieved in the blood purification device M of this embodiment. Pressurized air is ejected from the narrow gap head 13 between the output port 1117 of the circuit chamber 11 and the connector flow path 1131 of the connector 13, and together with the sealing ring 1132 (first contact surface), it powerfully ejects away foreign matter still attached to the inner surface (second contact surface) of the truncated cone of the output port 1117 that is tightly connected to the sealing ring 1132.

[0099] Therefore, the connector 13 of the pressure measuring device 1 can be connected to the loop chamber 11 with high quality without any foreign objects being trapped, and the pressure fluctuations in the pressure space S2 of the loop chamber 11 can be detected and measured with high precision through the pressure sensor 15.

[0100] As a result, the blood purification device M can precisely regulate the blood flow within the blood circuit 2, ensuring stable blood flow for dialysis and purification with high reliability.

[0101] In this embodiment, the case where foreign matter is trapped near the sealing ring 1132, where the pressurized air from the booster pump 17 is injected by the shape of the output port 1117 and the connector flow path 1131 before the loop chamber 11 is immediately connected to the connector 13, is described. However, this is not a limitation. For example, a proximity sensor or similar device could be installed in the output port 117 of the loop chamber 11 and the connector flow path 131 of the connector 13, so that the booster air from the booster pump 17 is injected when the contact reaches an effective separation interval.

[0102] <Summary of the Implementation Plan>

[0103] Next, specific aspects constituting the present invention will be described by reference to the reference numerals and other designations used in the embodiments described above. The following reference numerals and other designations are merely for illustrating the constituent elements in the claims by referring to the description of the embodiments; obviously, these constituent elements are not limited to specific components, etc.

[0104] [1] A pressure measuring device (1) uses a loading / unloading component (circuit chamber 11) of a fluid flow path (blood circuit 2) as the measuring object. The pressure measuring device includes: a connecting flow path (connecting pipe 14C) provided in such a way that gas can flow between it and the fluid flow path of the loading / unloading component; a connecting part (connector flow path 131) on which the connected part (output port 117) of the loading / unloading component is loaded / unloaded according to whether the fluid flow path and the connecting flow path are in a connected state or a disconnected state; and pressure sensors (15, 18) that measure the pressure inside the fluid flow path and the connecting flow path when the fluid flow path and the connecting flow path are in a connected state. The pressure measuring device includes: a pressure boosting unit (pressure booster pump 17), which boosts or depressurizes the interior of the aforementioned connected flow path via branch pipes 14D1, 14D2 and common pipe 14G in a manner that discharges or draws gas to the outside; and a drive unit (controller 50), which manually or automatically drives the pressure boosting unit at the following time: the first contact surface (sealing ring 132) of the connection part that is in airtight contact with the connected part of the aforementioned loading and unloading component is separated from the connected part. The first contact part forms a first contact surface at the following location: the location where gas is discharged or drawn in by the pressure boosting or depressurization of the pressure boosting unit in the disconnected state from the connected part.

[0105] [2] The pressure measuring device described in [1] above, wherein the connecting part is made of an elastic material (sealing ring 132) that is airtightly connected to the connected part through the first contact surface.

[0106] [3] The pressure measuring device described in [1] or [2] above, wherein the connecting flow path includes: an opening and closing part (solenoid valve 161, 162), which switches the pressure increasing and decreasing part and the measuring object to a connected state or an isolated state. After the opening and closing part pressurizes or depressurizes the interior of the connecting flow path in the isolated state, it switches to the connected state and sprays gas onto the first contact surface of the connecting part.

[0107] [4] The pressure measuring device according to any one of [1] to [3] above, wherein the pressure increasing and decreasing unit has the function of not only performing forward drive to increase the internal pressure of the connected flow path, but also performing reverse drive to decrease the internal pressure of the connected flow path.

[0108] [5] A medical device (blood purification device M) includes a pressure measuring device as described in any one of [1] to [4] above, wherein the loading and unloading component includes a blood flow path (blood circuit 2) that allows blood to flow as a fluid flow path, and a chamber (circuit chamber 11) that can store blood and gas is included as part of the blood circuit, and the object of measurement is the internal space of the chamber (pressure space S2).

[0109] [6] The medical device described in [5] above includes an operating unit that operates the drive of the pressure-increasing unit (operating panel P).

[0110] [7] In relation to the medical device described in [5] or [6] above, the drive unit automatically starts driving the pressure-increasing unit when it confirms the detection of the user operating (detection signal of the human body sensor 51) or the detection of the user's operation (detection signal of the cover detection sensor 235s of the cover 235 of the blood pump 23).

[0111] [8] The medical device relating to any one of [5] to [7] above, wherein the drive unit automatically stops driving the pressure increase / depression unit when the measured value of the pressure sensor reaches a preset predetermined pressure.

[0112] [9] The medical device relating to any one of [5] to [7] above, wherein the pressure-reducing unit releases or draws gas in a manner toward both the first contact surface of the connecting part and the second contact surface of the connected part before the connecting part is immediately connected to the connected part of the chamber.

[0113] In the cases described above [1], [2] and [5], before connecting the fluid flow path with pressure variation and the connecting flow path, pressurized air or suction air can be sprayed onto the first contact surface that contacts the part to be connected, effectively ejecting foreign objects and enabling high-quality and high-reliability connection.

[0114] In the cases described above [3] and [4], before connecting the fluid flow path with pressure variation and the connecting flow path, pressurized air or suction air can be effectively sprayed onto the first contact surface that contacts the part to be connected, so as to more reliably eject foreign objects and make a high-quality and highly reliable connection.

[0115] In the above [6] case, the operating unit can be operated to drive or stop the pressure increase / decrease unit, thus preventing unnecessary component consumption.

[0116] In the cases described above [7] and [8], the pressure-reducing unit can be automatically driven to stop, which can more reliably prevent component wear.

[0117] In the above[9] case, pressurized air or suction air can be injected into the narrow gap between the connecting part and the connected part on the chamber side, so that foreign objects can be ejected more reliably, and the connection can be made with high quality and high reliability.

[0118] Here, the medical device described above, a blood purification device (dialysis device) for making blood fluid (liquid) flow, is illustrated as an example, but it is not limited thereto. Obviously, the present invention can also be applied to, for example, artificial heart-lung devices that supply and exhaust fluids such as breathed air (gas).

[0119] Furthermore, in the above embodiment, the description mainly focuses on the circuit connection preparation operation when connecting the connector 13 to the circuit chamber 11. However, in addition to this operation, the following operation can be performed periodically or irregularly beforehand: the operation of spraying (or sucking) air from the connector flow path 131 of the connector 13. In this case, even when the circuit chamber 11 is connected but the blood circuit 2 is not installed, it is still possible to prevent foreign objects from adhering and accumulating at the connection point of the connector 13 connected to the circuit chamber 11 in the future, thus effectively maintaining and protecting the condition of the device.

[0120] The scope of this invention is not limited to the illustrated and described embodiments, but also includes all embodiments with equivalent effects. Furthermore, the scope of this invention is not limited to the combination of inventive features defined by each claim, but may be defined by all desired combinations of specific features from all disclosed features.

[0121] Explanation of the labels:

[0122] The designation 1 indicates a pressure measuring device;

[0123] Label 2 indicates the blood circuit;

[0124] The number 3 indicates the dialysis circuit;

[0125] The numbers 11 and 1011 indicate the circuit chamber;

[0126] The number 13 indicates a connector;

[0127] The designations 14C, 14C1, and 14C2 indicate connecting pipes;

[0128] The designations 14D1 and 14D2 indicate branch pipes;

[0129] The designation 14G indicates a shared pipe;

[0130] The numbers 15 and 18 indicate pressure sensors;

[0131] The designation 17 indicates a booster pump;

[0132] The designations 17r and 233 indicate rollers;

[0133] The designations 17s and 231 indicate the stator;

[0134] Label 21 indicates the arterial side blood circuit;

[0135] Label 22 indicates the venous blood circuit;

[0136] The number 23 indicates a blood pump;

[0137] The designation 31 indicates a dialyzer;

[0138] The number 50 indicates a controller;

[0139] The designation 51 indicates a human body sensor;

[0140] The designation 115 indicates a diaphragm;

[0141] The designation 116 indicates a filter;

[0142] Labels 117 and 1117 indicate output ports;

[0143] The designation 119 indicates an insertion connector;

[0144] The designations 131 and 1131 indicate the flow path of the connector;

[0145] The designations 132 and 1132 indicate sealing rings;

[0146] The number 134 indicates a cap;

[0147] The designation 139 indicates a socket connector;

[0148] The designation 143 indicates a flange;

[0149] The designation 143s indicates the inner circumferential slope;

[0150] The designations 161 and 162 indicate solenoid valves;

[0151] The designation 210 indicates an arterial puncture needle;

[0152] The designation 220 indicates a venous puncture needle;

[0153] The designation 235 indicates a cover;

[0154] The designation 235s indicates a cover detection sensor;

[0155] The symbol M represents a blood purification device;

[0156] The symbol P represents the operation panel;

[0157] The symbol Pb represents the ready button;

[0158] The symbol S represents interior space;

[0159] Symbol S1 represents the communication space;

[0160] The symbol S2 represents the pressure space.

Claims

1. A pressure measuring device which is detachably provided with a detachable member including a fluid flow path through which a fluid flows, and which measures a pressure of the detachable member as a measurement object, the pressure measuring device comprising: a communication flow path which is provided in a manner that a gas can flow therebetween; a connection portion to which a connected portion of the detachable member is connected in a manner that the fluid flow path and the communication flow path are in a communication state or a communication release state; a pressure sensor which is connected to the connected portion and the connection portion, and which measures a pressure in the fluid flow path and the communication flow path when the fluid flow path and the communication flow path are in the communication state; a pressure increasing / decreasing portion which increases or decreases a pressure in an inside of the communication flow path in a manner that a gas is discharged or sucked to / from the outside; and a driving portion which manually or automatically drives the pressure increasing / decreasing portion at a timing that a first contact surface of the connection portion which is in contact with the connected portion in a gas-tight manner is separated from the connected portion; in the connection portion, the first contact surface is formed at a position at which the gas is discharged or sucked by the pressure increasing / decreasing portion in the communication release state in which the connection portion is separated from the connected portion, before the fluid flow path and the communication flow path in which the pressure is changed are connected, the first contact surface which is in contact with the connected portion can be sprayed with pressure air or suction air, and foreign matters can be effectively sprayed away.

2. The pressure measurement device of claim 1, wherein, the connection portion is made of an elastic material which allows the first contact surface to be in close contact with the connected portion in a gas-tight manner.

3. The pressure measurement device of claim 1, wherein, the communication flow path includes an opening / closing portion which switches between a communication state and an isolation state between the pressure increasing / decreasing portion and the measurement object; after the inside of the communication flow path is increased or decreased in pressure in the isolation state, the opening / closing portion is switched to the communication state, and the first contact surface of the connection portion is sprayed with the gas.

4. The pressure measurement device of claim 1, wherein, the pressure increasing / decreasing portion has a function of not only performing a forward rotation drive to increase the pressure in the inside of the communication flow path but also performing a reverse rotation drive to decrease the pressure in the inside of the communication flow path.

5. A medical device including the pressure measuring device according to any one of claims 1 to 4; the fluid flow path is a blood flow path through which blood flows; the detachable member includes a chamber which constitutes a part of the blood flow path and which can store blood and a gas; the measurement object is an inside space of the chamber.

6. The medical device of claim 5, wherein, the medical device includes an operation portion which operates the drive of the pressure increasing / decreasing portion.

7. The medical device of claim 5, wherein, the driving portion automatically starts the drive of the pressure increasing / decreasing portion at a timing at which it is confirmed that a user who operates is detected or an operation by the user is detected.

8. The medical device of claim 5, wherein, the driving portion automatically stops the drive of the pressure increasing / decreasing portion at a timing at which a measured value of the pressure sensor reaches a predetermined prescribed pressure.

9. The medical device of claim 5, wherein, the pressure increasing / decreasing portion discharges or sucks the gas between both of the first contact surface of the connection portion and a second contact surface of the connected portion immediately before the connection portion approaches the connected portion.

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