Pressure measurement device and medical device

Abstract

To ensure the connection quality of a pressure measuring device, to realize highly accurate pressure measurement, and to enable highly reliable adjustment of fluid flow. [Solution] A pressure measuring device that measures pressure using a detachable circuit chamber as the measurement target, comprising a connection tube installed to allow gas to flow between it and the circuit chamber, a coupling flow path 131 of a joint 13 to which an output port 117 of the circuit chamber is connected so as to be in a connected state, a pressure sensor that measures the pressure in the pressure space S2 of the circuit chamber and the connection tube when the output port is connected to the coupling flow path and in a connected state, a pressure pump that pressurizes the inside of the connection tube, and a controller that drives the pressure pump when an O-ring 132 of the coupling flow path that makes airtight contact with the output port is separated, and the O-ring is positioned at a location where air is blown by the pressure pump when the coupling flow path is in a disconnected state when separated from the output port.

Description

Technical Field

[0001] The present invention relates to a pressure measuring device and a medical device that removably connect a pressure sensor to a space where pressure fluctuates.

Background Art

[0002] As a medical device, a pressure measuring device is installed that arranges a space where pressure fluctuates according to the fluid flowing in the fluid flow path in the middle of the fluid flow path and detects and measures the pressure in that space, thereby adjusting the fluid flow. For example, in a so-called dialysis treatment device that purifies blood, in a blood circuit that circulates blood outside the body, the blood flow is detected by a pressure sensor and adjusted (see, for example, Patent Document 1).

[0003] In this blood purification device (fluid flow device), in order to improve safety, since it is necessary to replace the blood circuit for each treatment, the pressure measuring device is manufactured with a structure that can be detachably connected to the blood circuit.

Prior Art Documents

Patent Documents

[0004]

Patent Document 1

Summary of the Invention

Problems to be Solved by the Invention

[0005] In such a pressure measuring device, since pressure fluctuations are detected to realize adjustment of fluid flow, it is necessary to measure pressure with high precision and high quality. However, if a foreign object such as a fiber is pinched at the connection point where it can be attached and detached on the space side where the pressure fluctuates and a leak occurs, inconveniences such as being unable to adjust the fluid flow with high reliability may occur.

[0006] Therefore, an object of the present invention is to achieve highly accurate pressure measurement and enable reliable adjustment of fluid flow by ensuring the connection quality of a pressure measurement device.

Means for Solving the Problems

[0007] One aspect of the invention of a pressure measurement device for solving the above problems is a pressure measurement device that measures pressure with a detachable member through which a fluid can flow being detached and attached, and the detachable member being the measurement target, comprising: a communication flow path installed so as to allow gas to flow between the communication flow path and the fluid flow path; a connection portion to which a connected portion of the detachable member is connected so that the fluid flow path and the communication flow path are in a connected state or a disconnected state; a pressure sensor that measures the pressure in the fluid flow path and the communication flow path when the connected portion is connected to the connection portion and the fluid flow path and the communication flow path are in the connected state; a pressure increasing and decreasing portion that pressurizes or depressurizes the inside of the communication flow path so as to discharge or suck gas to the outside; and a driving portion that manually or automatically drives the pressure increasing and decreasing portion at a timing when a first contact surface of the connection portion that makes airtight contact with the connected portion is separated from the connected portion. The connection portion has the first contact surface formed at a location where gas is discharged or sucked due to pressurization or depressurization of the pressure increasing and decreasing portion in the disconnected state in which the connection portion is separated from the connected portion.

[0008] One aspect of the invention of a medical device for solving the above problems has the above pressure measurement device, the detachable member comprises a blood flow path through which blood can flow as the fluid flow path, and as a part of the blood flow path, a chamber capable of storing blood and gas, and the measurement target is the internal space of the chamber.

Advantages of the Invention

[0009] Thus, according to one aspect of the present invention, a pressure measurement device can be connected to a space where pressure fluctuates with high quality, and pressure measurement can be performed with high accuracy. Therefore, it is intended to realize reliable adjustment of fluid flow and the like.

Brief Description of the Drawings

[0010]

Figure 1

Figure 2

Figure 3

Figure 4

Figure 5

Figure 6

Figure 7

Figure 8

Figure 9

Figure 10

Figure 11

Embodiments for Carrying Out the Invention

[0011] Hereinafter, embodiments of the present invention will be described in detail with reference to the drawings. FIGS. 1 to 9 are diagrams showing a hemodialysis device which is an example of a medical device equipped with a pressure measurement device according to a first embodiment of the present invention.

[0012] <First Embodiment> In FIGS. 1 and 2, the hemodialysis device M includes two sets of pressure measurement devices 1, a blood circuit 2, and a dialysis circuit 3, and drives each part of the device including the blood circuit 2 and the dialysis circuit 3 based on the measurement results of each pressure measurement device 1 in response to an input operation from an operation panel (operation unit) P to perform dialysis treatment (blood purification treatment) on a patient. The blood circuit 2 includes an arterial side blood circuit 21 and a venous side blood circuit 22, and circulates the patient's blood through the dialyzer 31 by a blood pump 23. The dialysis circuit 3 includes a dialyzer 31 that connects the arterial side blood circuit 21 and the venous side blood circuit 22 of the blood circuit 2, and a duplex pump 36 together with two systems of a dialysate introduction line 34 and a dialysate discharge line 35 connected to the dialyzer 31, and flows the dialysate in these lines 34 and 35. This hemodialysis device M is manufactured in a structure that inseparably includes the pressure measurement device 1 together with the dialysate introduction line 34, the dialysate discharge line 35, and the duplex pump 36 of the dialysis circuit 3, and is constructed so that the dialyzer 31 of the dialysis circuit 3 can be detachably attached and used disposable together with the arterial side blood circuit 21 and the venous side blood circuit 22 of the blood circuit 2.

[0013] Here, the dialyzer 31 forms a flow path for flowing dialysis fluid through the internal hollow fibers (not shown) by connecting the dialysis fluid introduction line 34 to the dialysis fluid inlet 31c and connecting the dialysis fluid discharge line 35 to the dialysis fluid outlet 31d, and performs dialysis treatment while passing the blood of the patient flowing through the blood circuit 2 using the blood purification membrane of the hollow fibers. The dual pump 36 is arranged so as to straddle both the dialysis fluid introduction line 34 and the dialysis fluid discharge line 35, and is driven to pump in both the introduction direction and the drainage direction so that the dialysis fluid stably passes through the dialyzer 31. The dialysis fluid introduction line 34 is connected at one end to a dialysis fluid supply device (not shown), and supplies dialysis fluid to the dialyzer 31 while adjusting the concentration through the dialysis fluid inlet 31c at the other end. The dialysis fluid discharge line 35 is connected at one end to a drainage means (not shown), and sends out the dialysis fluid that has been subjected to dialysis treatment through the dialysis fluid outlet 31d at the other end. Further, a water removal pump 37 is arranged in the dialysis fluid discharge line 35 so as to bypass the dual pump 36, and is configured to remove moisture from the blood of the patient flowing through the dialyzer 31.

[0014] The arterial side blood circuit 21 of the blood circuit 2 is connected and communicated at one end to the blood inlet 31a of the dialyzer 31 of the dialysis circuit 3, and is communicated by puncturing the arterial side puncture needle 210 at the other end into the blood vessel of the patient, and is configured to receive (so-called, draw blood) the blood to be dialyzed by the dialyzer 31. The arterial side blood circuit 21 is provided with a pressure measuring device 1 and a blood pump 23 in the middle of the circuit. The pressure measuring device 1 measures the pressure corresponding to the flow of blood in the circuit, while the blood pump 23 pumps to stably flow the blood in the circuit. The arterial side blood circuit 21 is provided with a connector 211 for connecting and connecting the arterial side puncture needle 210, and a clamp 212 for adjusting and controlling the flow of blood in the circuit by opening and closing a valve.

[0015] Here, the blood circuit 2 (21, 22) is composed of an elastically deformable tube that can accommodate flowing fluid blood within an internal fluid flow path. In contrast, the blood pump 23 is configured as a so-called tube pump (squeezing pump) that pumps the blood in the fluid flow path downstream by moving back and forth the location where the tube-shaped arterial blood circuit 21 of the blood circuit 2 is crushed, and the fluid on the upstream side is continuously drawn in by the negative pressure generated by the pumping of the fluid to the downstream side.

[0016] As shown in FIG. 3, the blood pump 23 is fabricated in a structure that rotatably houses a generally disk-shaped rotor 232 within a circular concave-shaped stator 231, and is set in a form that sandwiches the tube-shaped arterial blood circuit 21 between the circular inner wall surface 231s of the stator 231 so as to wrap around the outer peripheral side of the circular rotor 232. In this blood pump 23, a pair of rollers 233 are rotatably arranged in symmetric positions on the opposite side (opposite in the diameter direction) of the orthogonal direction of the axis of the disk-shaped rotor 232, parallel to its rotation axis. The blood pump 23 is configured to be driven to rotate passively along with the rotational drive of the rotor 232 while the pair of rollers 233 crush the arterial blood circuit 21 against the circular inner wall surface 231s of the stator 231 to tightly seal the inner surface of the tube. Thereby, the blood pump 23 can pump the blood in the tube of the arterial blood circuit 21 downstream by rotating the rotor 232, and in a state where the rotation of the rotor 232 is stopped, the rollers 233 can crush the arterial blood circuit 21 against the circular inner wall surface 231s of the stator 231 to stop the flow of the blood in the tube.

[0017] In addition, the blood pump 23 is provided with a cover 235 that covers the outer surface of the stator 231 to limit interference with the rotating rotor 232, the set arterial blood circuit 21, etc. The cover 235 has a cover detection sensor 235s (shown in FIG. 8) for detecting the opening and closing of the cover 235, and is designed to prevent accidents from occurring. In this blood pump 23, guides 234 extending in the direction orthogonal to the axis (diameter direction) of the disc-shaped rotor 232 are installed at a total of four locations, above and below, near the pair of rollers 233, and are designed to suppress the arterial blood circuit 21 in the form of a tube wound around the rotor 232 from coming off the inside of the stator 231.

[0018] The venous blood circuit 22 of the blood circuit 2 has one end connected and communicated to the blood outlet 31b of the dialyzer 31 of the dialysis circuit 3, and the other end is communicated by puncturing the venous puncture needle 220 into the patient's blood vessel, and the blood after dialysis treatment by the dialyzer 31 is returned to the patient side (so-called, blood return). This venous blood circuit 22 is provided with a pressure measuring device 1 and a venous chamber 225 in the middle of the circuit. While the pressure measuring device 1 measures the pressure corresponding to the flow of blood in the circuit, the venous chamber 225 separates the bubbles mixed into the blood on the venous blood circuit 22 side that is flowed (pumped) by the blood pump 23 and safely returns the normal blood to the patient. Note that the venous blood circuit 22 is provided with a connector 221 for connecting and connecting the venous puncture needle 220, a blood discrimination unit 222 for discriminating whether the fluid flowing in the circuit is blood, a clamp 223 for adjusting and controlling the flow of blood in the circuit by opening and closing a valve, and a bubble detection unit 224 for detecting bubbles mixed into the blood flowing in the circuit. It goes without saying that the blood discrimination unit 222 of these may be provided on the arterial blood circuit 21 side, or may be arranged on both of these blood circuits 21 and 22.

[0019] And two sets of the pressure measuring devices 1 are separately installed in the arterial blood circuit 21 and the venous blood circuit 22 of the blood circuit 2, and the pressure that varies according to the flow of the patient's blood in the blood circuit 2 is detected and measured as described later, so that the patient's blood is pumped (flowed) stably and optimally at the arterial side and the venous side.

[0020] The pressure measuring device 1 is configured to measure the pressure within a circuit chamber (detachable member) 11 that is detachably installed so as to be positioned in the flow path of each of the arterial-side blood circuit 21 and the venous-side blood circuit 22 of the blood circuit 2. As shown in FIGS. 4 to 6, a joint 13 is detachably attached to the circuit chamber 11 to connect a pressure sensor 15. In FIG. 2, the circuit chamber 11 and the joint 13 are shown in a schematic diagram in a separated and connected state, but as will be described later, they are manufactured with a detachable structure that integrates with each other with a filter 116 interposed therebetween. This joint 13 enables the detection (measurement) of the pressure that fluctuates due to the flow of blood in the blood circuit 2 by allowing the connection tube 14C to be connected to a cylindrical protrusion 131p (to be described later), so that the space pressure within the circuit chamber 11 reaches the pressure sensor 15.

[0021] As shown in FIGS. 4(a) and 5(a), the circuit chamber 11 is provided with connection ports 112 and 113 that communicate with a space S formed within a housing 111. The connection ports 112 and 113 are connected so that the space S is interposed therebetween for each blood circuit 2 (21, 22), thereby constituting a part of a continuous fluid flow path via a dialyzer 31.

[0022] This circuit chamber 11 is manufactured by installing a diaphragm 115 within the housing 111 to divide the space S into a communication space S1 and a pressure space S2. Among them, the communication space S1 functions as a fluid flow path (blood flow path through which blood flows) that communicates between the connection ports 112 and 113, and the pressure space S2 functions such that its volume fluctuates as the diaphragm 115 deforms in response to the flow of blood within the communication space S1.

[0023] Further, the circuit chamber 11 is provided with an output port 117 that communicates with the pressure space S2 via a filter 116. This circuit chamber 11 is inserted into a cylindrical receiving joint 139 of a joint 13 described later and connected and fixed to a cylindrical insertion joint 119 formed around the output port 117, and the output port (connected portion) 117 is connected to a joint flow path (connection portion) 131 of the joint 13 to form an integrated structure. Note that the filter 116 of the circuit chamber 11 prevents blood in the communication space S1 from flowing into the pressure space S2 due to damage to the diaphragm 115 or the like and flowing out from the output port 117 into the joint 13 on the pressure sensor 15 side.

[0024] As shown in FIGS. 4 to 6, the joint 13 houses an O-ring 132 made of an elastic material in a large-diameter portion 131d formed at one end side of the joint flow path (connection portion) 131, and sandwiches the O-ring 132 (the first contact surface thereof) in a close state between the outer surface of the output port (connected portion) 117 of the circuit chamber 11 to be inserted, and is manufactured to be airtightly connected (see FIG. 7(a)). Further, the joint 13 is provided with a cap 134 made of an elastic material formed in a flat ring shape on the end surface of the large-diameter portion 131d at one end side of the joint flow path 131. The cap 134 is formed with a short flange 143 having an inner peripheral side inclined surface 143s formed on the peripheral edge of the ring shape and located on the inner peripheral side of the large-diameter portion 131d of the joint flow path 131.

[0025] As shown in FIG. 7(b), when the insertion joint 119 of the circuit chamber 11 is pulled out from the joint flow path 131, the joint 13 is manufactured such that the O-ring 132 that moves in the direction of arrow F1 while being deformed between them abuts against the inner peripheral side inclined surface 143s of the cap 134 and presses the flange 143 against the inner surface of the large-diameter portion 131d in the direction of arrow F2 to suppress detachment. Further, the cap 134 can function as a retaining member for preventing the O-ring 132 from coming off from the large-diameter portion 131d when the insertion joint 119 of the circuit chamber 11 is pulled out from the joint flow path 131.

[0026] Here, the joint 13 has a cylindrical receiving joint 139 that inserts and fits the insertion joint 119 of the circuit chamber 11 fixed outside the large-diameter portion 131d on one end side of the joint flow path 131. A cylindrical protrusion 131p for connecting a connection tube 14C communicating with the pressure sensor 15 is formed on the other end side of this joint flow path 131. This joint 13 is integrated with the circuit chamber 11, and its output port 117 of the circuit chamber 11 is connected to the joint flow path 131 and communicated and connected to the pressure sensor 15 via the connection tube (communication flow path) 14C.

[0027] Further, an engaging protrusion 118 is formed on the outer surface of the cylindrical insertion joint 119 in the circuit chamber 11, and an L-shaped crank groove 138 continuous from the opening-side end edge of the cylindrical receiving joint 139 is formed in the joint 13. When inserting the insertion joint 119 into the receiving joint 139, the circuit chamber 11 and the joint 13 can be locked so that they cannot be pulled out simply by moving in the cylindrical axial direction by inserting the engaging protrusion 118 into the crank groove 138 and relatively rotating at the fitting position.

[0028] In addition to the connection tubes 14C1 and 14C2 being communicatively connected to the joint flow paths 131 of the joints 13 integrated with the circuit chambers 11 for each blood circuit 2 (21, 22) of the pressure measuring device 1 of this embodiment, a pair of branch tubes 14D1 and 14D2 and a common tube 14G are also communicatively connected. Specifically, one end sides of the pair of branch tubes 14D1 and 14D2 are communicatively connected and branched to the pair of connection tubes 14C1 and 14C2 communicatively connected to the joint flow path 131 of the joint 13, and the other end sides of the branch tubes 14D1 and 14D2 are gathered and communicatively connected to one end side of the common tube 14G and merged.

[0029] The branch tube 14D1 branches from the connection tube 14C1 in which the pressure sensor 15 is communicably connected to the joint 13 integrated with the circuit chamber 11 on the arterial blood circuit 21 side, and a solenoid valve (opening / closing part) 161 for opening and closing the communication flow path is installed midway to the common tube 14G. Similarly, the branch tube 14D2 branches from the connection tube 14C in which the pressure sensor 15 is installed on the venous blood circuit 22 side, and a solenoid valve 162 for opening and closing the communication flow path is installed midway to the common tube 14G.

[0030] One end of the common tube 14G is provided with a pressure pump (pressure increasing / decreasing part) 17 for introducing pressurized air to the joint 13 side via the connection tubes 14C1 and 14C2 on the opposite side (the other end side) of the branch tubes 14D1 and 14D2, and a pressure sensor 18 is installed in the middle of the flow path thereof so as to be functional. The pressure pump 17 is provided with a filter 17f for preventing dust and the like from being mixed into the introduced air. Here, the pressure pump 17 has a function of being able to increase and decrease the pressure on the joint 13 side by driving in both forward and reverse rotations, but it is not limited thereto, and it may be a dedicated machine having only one function of forward rotation (pressurization) or reverse rotation (decompression). For example, when driving in decompression, the fluid (air) flowing by the suction operation can be sprayed to a desired location in the same manner as the pressurized air described later.

[0031] Here, the pressure pump 17 is composed of a tube pump having the same function as the blood pump 23. As the rotor-side roller 17r rotates while sandwiching and crushing the common tube 14G between it and the stator 17s, pressurized air is sent to the joint 13 side of the blood circuit 2 (21, 22) via the branch tubes 14D1, 14D2 and the connection tubes 14C1, 14C2. In contrast to the blood pump 23 where the rotor-side roller 233 is arranged at two equal intervals in the diameter direction, the rotor-side roller 17r of the pressure pump 17 is arranged at four equal intervals to crush the common tube 14G against the stator 17s side so as to be airtight. For this reason, the pressure pump 17 pumps the air in the common tube 14G to the branch tubes 14D1, 14D2 side by rotating the rotor-side roller 17r, and can close the common tube 14G so that it cannot flow without providing a valve when the rotation of the roller 17r stops.

[0032] Incidentally, the blood purification device M executes dialysis treatment for purifying the patient's blood by causing the controller 50 shown in FIG. 8 to comprehensively control each part of the device including the blood pump 23 and the dual pump 36 so that the patient's blood passes through the dialyzer 31 in parallel via the arterial-side blood circuit 21 and the venous-side blood circuit 22, and the dialysate passes through the dialyzer 31 via the dialysate introduction line 34 and the dialysate discharge line 35.

[0033] The controller 50 is configured to include various memories such as a RAM and a ROM together with a CPU, and implements various control processes including dialysis processing by executing based on detection information, stored parameters, etc. that acquire a control program stored in advance according to an input operation from the operation panel P.

[0034] Specifically, as shown in FIG. 8, the controller 50 is connected to the clamp 212, 223 installed in the blood circuit 2, the blood discrimination unit 222, the air bubble detection unit 224, the blood pump 23, the compound pump 36 installed in the dialysis circuit 3, and the water removal pump 37, so that each part of the device can exchange control signals and the like with the operation panel P and the human sensor 51. Based on the input operation from the operation panel P on the premise of the presence of a user such as a nurse operating the operation panel P, the controller 50 controls the driving of each part of these devices to perform a dialysis treatment for purifying the patient's blood by passing the patient's blood and the dialysate through the dialyzer 31 at a constant flow rate and pressure, thereby treating the patient. Here, the operation panel P includes various input operation areas for inputting and setting, for example, driving conditions of the blood purification device M, and a display area for outputting and notifying driving time and the like. Along with messages prompting various operations, a preparation button Pb for starting and stopping the preparation operation to be performed before starting the dialysis treatment described later is arranged so that a user such as a nurse can operate it.

[0035] In addition, the controller 50 is also connected to the pressure sensors 15, 18, the solenoid valves 161, 162, and the pressurizing pump 17 so that various signals and the like can be exchanged. When performing dialysis treatment, the controller 50 closes the solenoid valves 161, 162 and detects the pressure in the pressure space (measurement target) S2 in the circuit chamber 11 communicated through the connection tubes 14C1, 14C2 by the pressure sensor 15 respectively, and obtains the pressure fluctuation in the communication space S1 in the circuit chamber 11. Thereby, the controller 50 can grasp the flow quality of the patient's blood in each of the arterial side blood circuit 21 and the venous side blood circuit 22 of the blood circuit 2, and can perform the dialysis treatment safely and appropriately by, for example, displaying and outputting various messages on the operation panel P.

[0036] At this time, while the controller 50 continues the dialysis treatment of detecting the pressure in the pressure space S2 of the circuit chamber 11 with the pressure sensor 15 and acquiring the pressure fluctuation in the communication space S1, it also functions as a drive unit that opens the solenoid valves 161 and 162 and drives the pressure pump 17. This controller 50 pressurizes (pumps in outside air) the inside of the pressure space S2 of the circuit chamber 11 through the branch tubes 14D1 and 14D2 and the common tube 14G by the pressure pump 17 to change the fluid volume (pressure) in the communication space S1, thereby adjusting and controlling the blood flow rate and speed of the patient. At the same time, the controller 50 detects the pressure in the common tube 14G with the pressure sensor 18, and obtains the pressurization effect on the inside of the pressure space S2 of the circuit chamber 11 detected by the pressure sensor 15, that is, the pressurization effect in the communication space S1 of the circuit chamber 11, and adjusts and controls the drive of the pressure pump 17 to be optimal. In this embodiment, the case where one pressure pump 17 is installed to adjust and control the blood flow rate and speed of the patient in the communication space S1 of the circuit chamber 11 is described as an example, but it is not limited to this. Needless to say, it may be installed in each of the arterial blood circuit 21 and the venous blood circuit 22 of the blood circuit 2 and be separately adjustable and controllable.

[0037] Furthermore, when preparing for the dialysis treatment of the blood flowing through the blood circuit 2 (21, 22), before connecting the circuit chamber 11 to the joint 13, when a preparation button Pb or the like is pressed according to a message prompting the preparation operation of the operation panel P, the controller 50 performs a circuit connection preparation operation described below to blow off foreign matter adhering to the O-ring 132 of the joint flow path 131 of the joint 13. Specifically, in response to the pressing of the preparation button Pb, the controller 50 opens the solenoid valves 161 and 162 and drives the pressure pump 17 to pressurize the pressure space S2 in the circuit chamber 11 communicating through the various tubes 14C1, 14C2, 14D1, 14D2, 14G to a desired pressure (pressurize and send outside air), as schematically illustrated in FIG. 9, for example. After that, when the preparation button Pb or the like on the operation panel P is pressed again, the controller 50 closes the solenoid valves 161 and 162 and stops driving the pressure pump 17 to standby. Thereby, the controller 50 can perform a circuit connection preparation operation to eject air from the joint flow path 131 of the joint 13 before connecting the circuit chamber 11.

[0038] Here, the controller 50 drives the pressure pump 17 so that the pressure sensor 18 detects and measures the pressure in the common tube 14G pressurized to such an extent as to blow off foreign matter adhering to the O-ring 132 of the joint flow path 131 of the joint 13. In this way, since the pressure sensor 18 is different from the pressure sensor 15 that detects and measures the pressure in the pressure space S2 that varies due to the flow of the blood flowing in the communication space S1 of the circuit chamber 11, the controller 50 appropriately adjusts the measurement ranges of the pressure sensors 15 and 18 to measure the pressure.

[0039] Therefore, when performing the preparation work for connecting the circuit chamber 11 to the joint 13 in order to perform the dialysis treatment of the patient's blood flowing through the blood circuit 2, the pressure measuring device 1 only needs to press the preparation button Pb on the operation panel P, and the pressure pump 17 is driven to eject air from the joint flow path 131 of the joint 13 while being inserted into the insertion joint 119 of the receiving joint 139 to be airtightly connected.

[0040] Therefore, the blood purification device M can blow off foreign matter adhering by blowing the pressurized air of the pressure pump 17 against the O-ring 132 in the large-diameter portion 131d of the joint flow path 131 of the joint 13.

[0041] As a result, the blood purification device M can prevent in advance that foreign matter is sandwiched between the O-ring 132 of the joint flow path 131 of the joint 13 and the outer surface of the output port 117 of the circuit chamber 11, causing a leak in the pressure space S2 and making it impossible to measure the pressure fluctuation corresponding to the flow of blood flowing into the communication space S1 of the circuit chamber 11.

[0042] <Effect of the First Embodiment> Thus, in the blood purification device M of the present embodiment, the joint 13 of the pressure measuring device 1 is communicatively connected to the circuit chamber 11, and the pressure fluctuation in the pressure space S2 of the circuit chamber 11 can be detected and measured with high precision by the pressure sensor 15.

[0043] Therefore, the blood purification device M can adjust the flow of blood in the blood circuit 2 with high precision, and can stably flow the patient's blood with high reliability for dialysis treatment and purification.

[0044] <Another Aspect of the First Embodiment> Here, in the present embodiment, a type (so-called pressure pod) in which the circuit chamber 11 is liquid-tightly partitioned by the diaphragm 115 of the diaphragm between the communication space S1 communicating with the blood circuit 2 and the pressure space S2 communicating with the joint flow path 131 of the joint 13 will be described as an example, but the present invention is not limited thereto. For example, as shown as another aspect in FIG. 10, a so-called air trap type circuit chamber 1011 provided with one internal space S in which the diaphragm 115 is omitted can also be applied to the blood circuit 2 installed in each of the arterial side blood circuit 21 and the venous side blood circuit 22.

[0045] Specifically, the circuit chamber 1011 is fabricated to form a part of the blood circuit 2 in such a manner that flowing blood is caused to flow into the internal space S from the gas phase side at the upper part and flow out from the liquid phase side at the lower part of the internal space S. The output port 117 and the plug joint 119 are located on the upper side of the internal space S of the circuit chamber 1011 and are inserted into the successor joint 139 of the joint 13 to be communicatively connected to the joint flow path 131.

[0046] In this other embodiment, during dialysis treatment, the pressure inside the internal space S of the circuit chamber 1011 without the diaphragm 115 can be detected by the pressure sensor 15 to obtain pressure fluctuations in the blood circuit 2 (21, 22), and the flow quality of the patient's blood can be grasped to safely and appropriately perform dialysis treatment.

[0047] At this time, in this other embodiment, while continuing dialysis treatment, the gas phase pressure inside the internal space S of the circuit chamber 1011 is detected by the pressure sensor 15, and the pressure pump 17 is driven according to the pressure fluctuations to pressurize the inside of the internal space S (pump in outside air), change the liquid level at the boundary between the gas phase and the liquid phase, and adjust and control the flow rate and speed of the patient's blood.

[0048] <Second Embodiment> Next, a blood purification device, which is an example of a medical device equipped with a pressure measurement device according to the second embodiment of the present invention, will be described. Here, since this embodiment is configured substantially the same as the above-described embodiment, the drawings are reused, the same reference numerals are given to the same configurations, and the characteristic parts will be described (the same applies to other embodiments described below).

[0049] As shown in FIGS. 1 to 9, the controller 50 of the blood purification device M performs the circuit connection preparation operation in the above-described embodiment when the cover 235 of the blood pump 23 is opened and closed and the set of the arterial side blood circuit 21 is detected from the detection signal of the cover detection sensor 235s, instead of pressing the preparation button Pb of the operation panel P in the above-described embodiment.

[0050] Specifically, when the cover 235 of the blood pump 23 is opened and closed and the arterial blood circuit 21 is set up, the controller 50 starts driving the pressure pump 17 while opening the solenoid valves 161 and 162 at the timing when the arterial blood circuit 21 is set up. After that, the controller 50 measures the elapsed time from the start time, and when it confirms that the preset driving time, for example, the working time sufficient to sufficiently perform the operation of connecting the circuit chamber 11 to the joint 13 has elapsed, it closes the solenoid valves 161 and 162 and stops driving the pressure pump 17.

[0051] Thereby, the pressure measuring device 1 can surely perform the preparatory work for airtightly connecting the circuit chamber 11 of the blood circuit 2 to the joint 13 with a margin in a high-quality and highly reliable manner, and after the preparatory work, the pressure pump 17 is automatically stopped to prevent the common tube 14G and the like from being consumed by the squeezing operation of the roller 17r.

[0052] <Effect of the Second Embodiment> As described above, in the blood purification device M of the present embodiment, the pressure pump 17 of the pressure measuring device 1 can reduce the load associated with the circuit connection preparation operation, reduce the consumption of various components around the pressure pump 17 including the common tube 14G, and enable stable driving.

[0053] <Third Embodiment> Next, a blood purification device which is an example of a medical device provided with the pressure measuring device according to the third embodiment of the present invention will be described.

[0054] As shown in FIGS. 1 to 9, the controller 50 of the blood purification device M performs the circuit connection preparation operation in the above-described embodiment when the human sensor 51 operates the operation panel P or detects a user who sets the arterial blood circuit 21 to the blood pump 23, instead of pressing the preparation button Pb of the operation panel P in the above-described embodiment.

[0055] Specifically, when the human presence sensor 51 detects a user in front of the blood purification device M, the controller 50 starts driving the pressure pump 17 while opening the solenoid valves 161 and 162, as in the above-described embodiment. When it is confirmed that the elapsed time measured from the start time exceeds, for example, the working time sufficient to fully perform the work of connecting the circuit chamber 11 to the joint 13, the solenoid valves 161 and 162 are closed and the driving of the pressure pump 17 is stopped.

[0056] <Effects of the Third Embodiment> Thus, also in the blood purification device M of the present embodiment, as in the above-described embodiment, the pressure pump 17 of the pressure measurement device 1 can reduce the load associated with the circuit connection preparation operation, and can reduce the consumption of various components around the pressure pump 17 including the common tube 14G and drive it stably.

[0057] <Fourth Embodiment> Next, a blood purification device, which is an example of a medical device provided with the pressure measurement device according to the fourth embodiment of the present invention, will be described.

[0058] As shown in FIGS. 1 to 9, when the controller 50 of the blood purification device M performs the circuit connection preparation operation in the above-described embodiment, the pressure pump 17 is driven with the solenoid valves 161 and 162 closed in a shut-off state, and after confirming that the pressurizing pressure (measured value) in the common tube 14G detected by the pressure sensor 18 has reached a preset opening pressure (i.e., the pressure has been accumulated), the solenoid valves 161 and 162 are opened and switched to a communication state. After that, when the controller 50 confirms that the pressurizing pressure in the pressure space S2 of the circuit chamber 11 detected by the pressure sensor 15 has reached a preset end pressure, the solenoid valves 161 and 162 are closed and the driving of the pressure pump 17 is stopped.

[0059] As a result, in addition to the operations according to the above-described embodiment, the pressure measurement device 1 can effectively blow off foreign matter adhering to the O-ring 132 by driving the pressure pump 17 to eject the compressed air stored in the common tube 14G from the joint flow path 131 of the joint 13, and can also surely determine the completion of connection and automatically stop the pressure pump 17 to suppress the consumption of the common tube 14G and the like due to the squeezing operation of the roller 17r.

[0060] <Effects of the Fourth Embodiment> Thus, in the blood purification device M of the present embodiment, in addition to the effects according to the above-described embodiment, the operation of communicatively connecting the output port 117 of the circuit chamber 11 in the blood circuit 2 to the joint flow path 131 of the joint 13 can be performed with high quality and high reliability, and the consumption of various components around the pressure pump 17 including the common tube 14G can be reduced to enable stable driving.

[0061] <Fifth Embodiment> Next, a blood purification device, which is an example of a medical device provided with the pressure measurement device according to the fifth embodiment of the present invention, will be described.

[0062] As shown in FIGS. 1 to 9, when the controller 50 of the blood purification device M performs the circuit connection preparation operation in the above-described embodiment, the controller 50 repeatedly performs the forward rotation (pressurization) drive and the reverse rotation (decompression) drive of the pressure pump 17 at regular intervals while opening the solenoid valves 161 and 162. After that, at the timing when the controller 50 confirms the elapse of the set working time (driving time) from the start time, the controller 50 closes the solenoid valves 161 and 162 and stops the drive of the pressure pump 17.

[0063] As a result, in addition to the operations according to the above-described embodiment, the pressure measurement device 1 can intermittently blow compressed air onto the O-ring 132 of the joint flow path 131 of the joint 13 by repeatedly performing the forward rotation drive and the reverse rotation drive of the pressure pump 17, and can also intermittently suck the vicinity of the O-ring 132, and can effectively peel off foreign matter adhering to the O-ring 132.

[0064] <Effects of the Fifth Embodiment> As described above, in the blood purification device M of the present embodiment, in addition to the effects of the above-described embodiment, the operation of communicatively connecting the output port 117 of the circuit chamber 11 in the blood circuit 2 to the joint flow path 131 of the joint 13 can be performed with high quality and high reliability.

[0065] <Sixth Embodiment> Next, with reference to FIG. 11, a blood purification device, which is an example of a medical device equipped with a pressure measuring device according to the sixth embodiment of the present invention, will be described.

[0066] As shown in FIGS. 1 to 9, the blood purification device M is configured such that the joint 13 is communicatively connected to the circuit chamber 11 installed in the blood circuit 2 to enable the pressure measuring device 1 to function. In the present embodiment, as shown in FIG. 11(a), the joint flow path 1131 of the joint 13 is inserted into the output port 1117 that communicates with the pressure space S2 of the circuit chamber 11, and is formed in a communication structure.

[0067] Specifically, the joint flow path 1131 of the joint 13 is formed in a frustum of a cone shape, and the output port 1117 of the circuit chamber 11 is formed in a joint shape having an inner surface for fitting the frustum of the cone of the joint flow path 1131, instead of the receiving joint 139 of the above-described embodiment. The joint flow path 1131 and the output port 1117 are formed such that an O-ring 1132 is sandwiched between the outer surface and the inner surface of the frustum of the cone that fit together, and are hermetically connected and joined.

[0068] As a result, when the pressure measuring device 1 performs the circuit connection preparation operation of connecting the circuit chamber 11 to the joint 13 in order to perform the dialysis treatment of the patient's blood flowing through the blood circuit 2, as shown in FIG. 11(b), foreign matters adhering by blowing the pressurized air of the pressurizing pump 17 can be blown off to the output port 1117 side or the O-ring 1132 side of the joint flow path 1131. At this time, the pressurized air pumped by the pressurizing pump 17 can be blown into the output port 1117 and then blown back while being ejected from the joint flow path 1131 side of the joint 13 immediately before connecting to the output port 1117 of the circuit chamber 11, and the foreign matters adhering to the O-ring 1132 can be strongly blown off through the narrow gap between the joint flow path 1131.

[0069] As a result, the blood purification device M can more effectively prevent in advance the situation where foreign matters are caught between the O-ring 132 of the joint flow path 1131 of the joint 13 and the output port 1117 of the circuit chamber 11, causing a leak in the pressure space S2 and making it impossible to measure the pressure fluctuations corresponding to the flow of blood flowing into the communication space S1 of the circuit chamber 11.

[0070] <Effect of the Sixth Embodiment> Thus, also in the blood purification device M of the present embodiment, the same operational effects as those of the above-described embodiment can be obtained, and by ejecting pressurized air from the narrow gap between the output port 1117 of the circuit chamber 11 and the joint flow path 1131 of the joint 13, together with the O-ring 1132 (the first contact surface), the foreign matters adhering to the conical inner surface (the second contact surface) of the output port 1117 with which the O-ring 1132 is in close contact can be strongly blown off.

[0071] Therefore, the joint 13 of the pressure measuring device 1 can be connected to the circuit chamber 11 with high quality without sandwiching foreign matters, and the pressure fluctuations in the pressure space S2 of the circuit chamber 11 can be detected and measured with high precision by the pressure sensor 15.

[0072] As a result, the blood purification device M can highly accurately adjust the flow of blood in the blood circuit 2, and can stably flow the patient's blood with high reliability for dialysis treatment and purification.

[0073] Here, in the present embodiment, a case will be described in which foreign matter that adheres by spraying the pressure air of the pressure pump 17 near the O-ring 1132 is pinched due to the shapes of the output port 1117 and the joint flow path 1131 immediately before the connection of the circuit chamber 11 and the joint 13, but the present invention is not limited thereto. For example, a proximity sensor or the like may be installed in the output port 117 of the circuit chamber 11 and the joint flow path 131 of the joint 13, and the pressure air of the pressure pump 17 may be sprayed at the timing of approaching an effective separation interval.

[0074] <Summary of the Embodiment> Next, the invention specific matters constituting the present invention will be listed by referring to the reference numerals and the like in the above-described embodiment. It should be noted that each of the following reference numerals and the like is merely an explanation by referring to the description of the embodiment for the components in the claims, and it goes without saying that the components are not limited to specific members or the like.

[0075] "1" A detachable member (circuit chamber 11) having a fluid flow path (blood circuit 2) through which a fluid can flow is a measurement target, a communication flow path (connection tube 14C) installed so that a gas can flow between the fluid flow path of the detachable member, and A connection portion (joint flow path 131) to which the connected portion (output port 117) of the detachable member is detached so that the fluid flow path and the communication flow path are in a communicating state or a communication-disconnected state, and A pressure measuring device (1) including a pressure sensor (15, 18) that measures the pressures in the fluid flow path and the communication flow path when the fluid flow path and the communication flow path are in a communicating state, A pressure increasing / decreasing unit (pressure pump 17) that pressurizes or depressurizes the inside of the communication flow path via branch tubes 14D1, 14D2 or a common tube 14G so as to discharge or suck a gas to the outside, A drive unit (controller 50) that manually or automatically drives the pressure increasing / decreasing unit at a timing when a first contact surface (O-ring 132) of the connection part that is brought into airtight contact with the connected part of the detachable member is separated from the connected part. The connection part is a pressure measuring device in which a first contact surface is formed at a location where gas is released or gas is sucked by pressurization or depressurization of the pressure increasing / decreasing unit in a communication elimination state where the connection part is separated from the connected part.

[0076] "2" The pressure measuring device according to "1", wherein the connection part is made of an elastic material (O-ring 132) capable of airtightly adhering the first contact surface to the connected part.

[0077] "3" The communication flow path includes an opening / closing part (solenoid valves 161, 162) that switches between a communication state and a cutoff state between the pressure increasing / decreasing unit and the measurement target. The pressure measuring device according to "1" or "2", wherein the opening / closing part pressurizes or depressurizes the inside of the communication flow path in the cutoff state and then switches to the communication state to blow gas onto the first contact surface of the connection part.

[0078] "4" The pressure measuring device according to any one of "1" to "3", wherein the pressure increasing / decreasing unit has a function of reversely driving to depressurize the inside of the communication flow path in addition to the forward driving to pressurize the inside of the communication flow path.

[0079] "5" Having the pressure measuring device according to any one of "1" to "4" above. The detachable member includes a blood flow path (blood circuit 2) through which blood can flow as the fluid flow path. As a part of the blood flow path, a chamber (circuit chamber 11) capable of storing blood and gas is provided. A medical device (blood purification device M), wherein the measurement target is the internal space (pressure space S2) of the chamber.

[0080] "6" The medical device according to "5", having an operation part (operation panel P) for operating the drive of the pressure increasing / decreasing unit.

[0081] "7. The medical device according to "5" or "6", wherein the drive unit automatically starts driving the pressure increasing / decreasing unit when detecting an operating user (detection signal of the human presence sensor 51) or an operation by the user (detection signal of the cover detection sensor 235s of the cover 235 of the blood pump 23).

[0082] "8. The medical device according to any one of "5" to "7", wherein the drive unit automatically stops driving the pressure increasing / decreasing unit at the timing when the measured value of the pressure sensor reaches a predetermined pressure set in advance.

[0083] "9. The medical device according to any one of "5" to "7", wherein the pressure increasing / decreasing unit discharges or sucks gas toward both the first contact surface of the connection part and the second contact surface of the connected part immediately before the connection part approaches the connected part on the chamber side for connection.

[0084] In the cases of the above "1", "2" and "5", before connecting the fluid flow path with fluctuating pressure and the communication flow path, pressure air or suction air can be blown onto the first contact surface contacting the connected part to effectively blow off foreign matters, and a high-quality and highly reliable communication connection can be achieved.

[0085] In the cases of the above "3" and "4", before connecting the fluid flow path with fluctuating pressure and the communication flow path, pressure air or suction air can be effectively blown onto the first contact surface contacting the connected part to more surely blow off foreign matters, and a high-quality and highly reliable communication connection can be achieved.

[0086] In the case of the above "6", the operation unit can be operated to drive and stop the pressure increasing / decreasing unit, and it is possible to prevent unnecessary consumption of parts.

[0087] In the cases of the above "7" and "8", the pressure increasing / decreasing unit can be automatically driven to stop, and it is possible to more surely prevent parts from being consumed.

[0088] In the case of the above "9", compressed air or suction air can be blown into the narrow gap between the connection part and the connected part on the chamber side, so that foreign matters can be more surely blown away, and high-quality and highly reliable communication connection can be achieved.

[0089] Here, the medical device described above will be described by taking a blood purification device (dialysis device) that allows blood fluid (liquid) to flow as an example, but it is not limited thereto. Needless to say, it can also be applied to, for example, a cardiopulmonary bypass device that supplies and discharges fluids such as breathing air (gas).

[0090] In addition, in the above-described embodiment, the circuit connection preparation operation when connecting the joint 13 to the circuit chamber 11 is mainly described. In addition to this operation, or instead of this operation, an operation of ejecting (suction may also be possible) air from the joint flow path 131 of the joint 13 may be performed regularly or irregularly. In this case, even when the circuit chamber 11 is connected and the blood circuit 2 is not attached, it is possible to prevent foreign matters from adhering and accumulating at the connection portion of the joint 13 to be connected to the circuit chamber 11, and the device state can be maintained and preserved in a sound manner.

[0091] The scope of the present invention is not limited to the illustrated and described exemplary embodiments, but also includes all embodiments that bring about equivalent effects to those intended by the present invention. Further, the scope of the present invention is not limited to the combinations of the features of the inventions defined by each claim, but may be defined by any desired combination of specific features among all the disclosed features.

Explanation of Reference Numerals

[0092] 1... Pressure measuring device 2... Blood circuit 3... Dialysis circuit 11, 1011... Circuit chamber 13... Joint 14C, 14C1, 14C2... Connection tube 14D1, 14D2... branch tubes 14G... common tube 15, 18... pressure sensors 17... pressure pump 17r, 233... rollers 17s, 231... stators 21... arterial blood circuit 22... venous blood circuit 23... blood pump 31... dialyzer 50... controller 51... human presence sensor 115... diaphragm 116... filter 117, 1117... output ports 119... plug-in joint 131, 1131... joint flow paths 132, 1132... O-rings 134... cap 139... receiving joint 143... flange 143s... inner peripheral slope 161, 162... solenoid valves 210... arterial puncture needle 220... venous puncture needle 235... cover 235s... cover detection sensor M... blood purification device P... operation panel Pb... preparation button S... internal space S1... communication space S2... pressure space

Claims

1. A medical device comprising a detachable member having a fluid flow path through which a fluid can flow, the detachable member being detachable, and a pressure measuring device for measuring pressure with the detachable member as a measurement target, wherein the pressure measuring device includes: a communication flow path installed so as to allow gas to flow between the communication flow path and the fluid flow path; a connection part to which a connected part of the detachable member is connected so that the fluid flow path and the communication flow path are in a communicating state or a non-communicating state; a pressure sensor for measuring the pressure in the fluid flow path and the communication flow path when the connected part is connected to the connection part and the fluid flow path and the communication flow path are in the communicating state; a pressure increasing / decreasing part for pressurizing or depressurizing the inside of the communication flow path so as to discharge or suck gas to the outside; a driving part for manually or automatically driving the pressure increasing / decreasing part at a timing when a first contact surface of the connection part that makes airtight contact with the connected part is separated from the connected part, and the connection part has the first contact surface formed at a location where gas is discharged or sucked by pressurization or depressurization of the pressure increasing / decreasing part in the non-communicating state in which the connection part is separated from the connected part, wherein the pressure increasing / decreasing part is configured to intake external gas through a filter. A medical device.

2. The medical device according to claim 1, wherein the driving part automatically starts driving the pressure increasing / decreasing part at a timing when completion of setting of the fluid flow path is detected.

3. The medical device according to claim 1 or claim 2, wherein the driving part automatically stops driving the pressure increasing / decreasing part at a timing when it is confirmed that a set time has elapsed since the start of driving of the pressure increasing / decreasing part.

4. The medical device according to claim 1 or claim 2, wherein the driving part automatically stops driving the pressure increasing / decreasing part at a timing when a measured value of the pressure sensor reaches a predetermined pressure set in advance.

5. The pressure increasing / decreasing part has a function of reversely driving to depressurize the inside of the communication flow path in addition to the forward driving for pressurizing the inside of the communication flow path, and the driving part repeatedly performs forward driving and reverse driving of the pressure increasing / decreasing part at regular intervals to repeatedly discharge and suck gas to the first contact surface, and then automatically starts driving to pressurize or depressurize the inside of the communication flow path by the pressure increasing / decreasing part. The medical device according to any one of claims 1 to 4.

6. The fluid flow path includes an arterial blood flow path and a venous blood flow path through which blood flows. The pressure measurement device is separately installed in each of the arterial side blood flow path and the venous side blood flow path, and is the medical device according to any one of claims 1 to 4.

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