JP5337618B2 - Calibration method of blood pressure removal detecting means and blood purification device - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To provide a method for easily and accurately calibrating a blood removal pressure detecting means, and a blood purifying apparatus. <P>SOLUTION: The method is provided for calibrating the blood removal pressure detecting means 9 in a blood circuit 1 including the blood removal pressure detecting means 9 having a chamber member 10 connected from the tip of an artery-side blood circuit 1a to the disposed location of a blood pump 2, and detecting blood removal pressure by detecting the force at the time of deforming the chamber member 10 and converting it into an electric signal, and a pressure transducer 13 detecting venous pressure by detecting pressure in a vein-side air trap chamber 5. The method includes connecting the tip of the artery-side blood circuit 1a to the tip of a vein-side blood circuit 1b to form a closed loop, and calibrating the blood removal pressure detecting means 9 on the basis of the pressure in the vein-side air trap chamber 5 detected by the pressure transducer 13. <P>COPYRIGHT: (C)2011,JPO&amp;INPIT

Description

  The present invention relates to a method for calibrating blood pressure removal detecting means and a blood purification apparatus in a blood circuit for circulating blood extracorporeally.

  The blood circuit used for dialysis treatment and circulating the patient's blood extracorporeally is usually mainly composed of an arterial blood circuit with an arterial puncture needle attached to one end and a venous blood circuit with a venous puncture needle attached to one end. The dialyzer as a blood purifier can be connected to each other end of the arterial blood circuit and the venous blood circuit. An iron-type blood pump is disposed in the arterial blood circuit, and blood is driven from the arterial puncture needle by driving the blood pump with the arterial puncture needle and the venous side puncture needle punctured in the patient. The blood is flowed in the arterial blood circuit and guided to the dialyzer, and the blood purified by the dialyzer is flowed in the venous blood circuit and returned to the patient's body through the venous puncture needle. Dialysis treatment is performed.

  In the blood circuit that performs extracorporeal circulation, particularly between the arterial puncture needle and the blood pump arrangement portion, there may be a negative pressure in the blood circuit due to poor blood collection from the patient (defective blood removal). For this reason, a chamber member (negative pressure detection member) called a pillow for detecting negative pressure is connected upstream of the blood pump in the arterial blood circuit. Such a chamber member is composed of a flexible hollow member that is connected to a blood circuit and can be deformed in accordance with the pressure in the blood circuit, as disclosed in, for example, Patent Document 1. The chamber member is configured to bend in the direction in which the front surface portion and the back surface portion approach each other when the blood flowing in the artery-side blood circuit becomes negative pressure, and the degree of the bend is visually observed, The negative pressure state is judged.

  By the way, although the pressure detection device can detect whether or not the pressure in the arterial blood circuit has become negative, there is a problem that it is not possible to quantitatively grasp how much the pressure is. The present applicant quantitatively detects blood pressure reduction by connecting a chamber member upstream of the blood pump in the arterial blood circuit and detecting the force at the time of deformation of the chamber member and converting it into an electrical signal. We have intensively studied possible blood pressure detection means.

JP 11-267198 A

  However, although the conventional blood pressure removal detecting means can quantitatively detect blood pressure removal, there is a problem that calibration for absorbing individual differences among chamber members is difficult. That is, the chamber member connected to the arterial blood circuit usually has individual differences. Therefore, calibration of the blood pressure reduction detecting means is required. For example, a separate sensor serving as a reference for calibration is provided. When it is newly provided in a blood circuit or the like, there is a problem that the calibration work becomes extremely troublesome and the workability deteriorates.

  The present invention has been made in view of such circumstances, and it is an object of the present invention to provide a calibration method and a blood purification apparatus for blood pressure removal detection means that can easily and accurately calibrate blood pressure removal detection means.

  The invention according to claim 1 comprises an arterial blood circuit in which a blood pump is disposed and a venous blood circuit to which an air trap chamber is connected, and from the distal end of the arterial blood circuit to the distal end of the venous blood circuit. A blood circuit capable of extracorporeally circulating the patient's blood, comprising a chamber member connected between the tip of the arterial blood circuit and a position where the blood pump is disposed, and when the chamber member is deformed Blood pressure detection means that can detect blood pressure by detecting force and converting it into an electrical signal, and connected to the upper part of the air trap chamber, can detect venous pressure by detecting the pressure in the air trap chamber A method for calibrating blood pressure reduction detecting means in a blood circuit having a venous pressure detecting means, wherein the tip of the arterial blood circuit and the tip of the venous blood circuit are connected to form a closed loop And forming, characterized by calibrating said removal pressure detecting means as a reference pressure of the venous pressure detecting means and the air trap chamber detected by the.

  According to a second aspect of the present invention, in the method for calibrating blood pressure reduction detecting means according to the first aspect, a branch line branched from the tip of the arterial blood circuit to a position where the blood pump is disposed is extended. The blood pressure reduction detecting means is arranged on the branch line.

  According to a third aspect of the present invention, in the method for calibrating blood pressure removal detecting means according to the first or second aspect, the air trap chamber is opened to the atmosphere while the air trap chamber and the chamber member are in communication with each other. And a zero point measuring step of measuring the zero point of the blood pressure removal detecting means based on the pressure in the air trap chamber detected by the venous pressure detecting means.

  According to a fourth aspect of the present invention, in the method for calibrating the blood pressure drop detecting means according to the third aspect, a pressure difference forming step for generating a pressure difference between the air trap chamber and the chamber member, and the air trap chamber, By bringing the chamber member into communication with each other to eliminate the pressure difference generated in the pressure difference forming step and to equilibrate each other's pressure. The blood pressure removal detecting means is calibrated based on the pressure in the air trap chamber detected by the venous pressure detecting means in a balanced state and the zero point measured in the zero point measuring step. .

  According to a fifth aspect of the present invention, in the method for calibrating blood pressure loss detecting means according to the fourth aspect, the blood pump is a squeezing type pump, and the pressure difference forming step is performed by driving the blood pump. It is characterized by causing a difference.

  According to a sixth aspect of the present invention, in the method for calibrating blood pressure reduction detecting means according to the fourth aspect, the blood circuit is connected to blood purification means for purifying extracorporeal blood, and the blood purification means is connected to the blood circuit. And a dual pump for supplying dialysate to the blood purification means, and the pressure difference forming step is performed by driving the drain pump or the dual pump. It is characterized by causing a difference.

  A seventh aspect of the present invention is the method of calibrating blood pressure detection means according to any one of the fourth to sixth aspects, wherein the blood circuit forming a closed loop is formed during the pressure difference forming step or the equilibration step. It is characterized by determining the presence or absence of a leak.

  According to an eighth aspect of the present invention, in the method for calibrating blood pressure detection means according to any one of the first to seventh aspects, the blood pressure circuit is primed by filling the blood circuit with a priming solution. It is performed at the time of a process.

  The invention according to claim 9 comprises an arterial blood circuit in which a blood pump is disposed and a venous blood circuit to which an air trap chamber is connected, and from the distal end of the arterial blood circuit to the distal end of the venous blood circuit. A blood circuit capable of extracorporeally circulating the patient's blood, comprising a chamber member connected between the tip of the arterial blood circuit and a position where the blood pump is disposed, and when the chamber member is deformed Blood pressure detection means that can detect blood pressure by detecting force and converting it into an electrical signal, and connected to the upper part of the air trap chamber, can detect venous pressure by detecting the pressure in the air trap chamber A blood purification apparatus capable of installing a blood circuit having a venous pressure detecting means, and connecting the distal end of the arterial blood circuit and the distal end of the venous blood circuit to form a closed loop State, characterized by comprising control means for calibrating said removal pressure detecting means as a reference pressure of the venous pressure detecting means and the air trap chamber detected by the.

  A tenth aspect of the present invention is the blood purification apparatus according to the ninth aspect, wherein a branch line that branches from the tip of the arterial blood circuit to a position where the blood pump is disposed is extended, and the branch line Further, the blood pressure removal detecting means is provided.

  According to an eleventh aspect of the present invention, in the blood purification apparatus according to the ninth or tenth aspect, the control means is configured to open the air trap chamber to the atmosphere while keeping the air trap chamber and the chamber member in communication with each other. In addition, a zero point measuring step of measuring the zero point of the blood pressure removal detecting means based on the pressure in the air trap chamber detected by the venous pressure detecting means is performed.

  The invention according to claim 12 is the blood purification apparatus according to claim 11, wherein the control means generates a pressure difference between the air trap chamber and the chamber member, and the air trap chamber. And the chamber member are brought into communication with each other to cause a pressure difference generated in the pressure difference forming step to be eliminated and to equilibrate each other's pressure. Calibrating the blood pressure removal detecting means based on the pressure in the air trap chamber detected by the venous pressure detection means in a state of being balanced and the zero point measured in the zero point measuring step. To do.

  A thirteenth aspect of the present invention is the blood purification apparatus according to the twelfth aspect, wherein the blood pump is a squeezing type pump, and the control means drives the blood pump in the pressure difference forming step. It is characterized by producing a pressure difference.

  The invention according to claim 14 is the blood purification apparatus according to claim 12, wherein the blood circuit is connected to blood purification means for purifying extracorporeal blood, and water is removed through the blood purification means. And a dual pump for supplying dialysate to the blood purification means, and the pressure difference forming step generates a pressure difference by driving the drain pump or the dual pump. It is characterized by that.

  According to a fifteenth aspect of the present invention, in the blood purification apparatus according to any one of the twelfth to fourteenth aspects, whether or not there is a leak in the blood circuit forming a closed loop during the pressure difference forming step or the equilibration step. The present invention is characterized by comprising a leak presence / absence judging means for judging.

  A sixteenth aspect of the present invention is the blood purification apparatus according to any one of the ninth to fifteenth aspects, wherein the control unit is configured to perform the blood pressure reduction detection unit during the priming step of filling the blood circuit with a priming solution. It is characterized in that calibration is performed.

  According to the first and ninth aspects of the present invention, the tip of the arterial blood circuit and the tip of the venous blood circuit are connected to form a closed loop, and the pressure in the air trap chamber detected by the venous pressure detecting means is adjusted. Since the blood pressure removal detection means is calibrated as a reference, a separate new sensor or the like for calibrating the blood pressure removal detection means can be eliminated, and the blood pressure removal detection means can be calibrated easily and accurately.

  According to the second and tenth aspects of the present invention, the branch line branched from the tip of the arterial blood circuit to the position where the blood pump is disposed is extended, and the blood pressure reduction detecting means is disposed on the branch line. Therefore, blood pressure can be accurately detected, and blood can be reliably and smoothly circulated outside the body.

  According to the third and eleventh aspects of the invention, while the air trap chamber and the chamber member are in communication with each other, the inside of the air trap chamber is opened to the atmosphere, and the pressure in the air trap chamber detected by the venous pressure detecting means is adjusted. Since the zero point measuring step of measuring the zero point of the blood pressure removal detecting means is included, the zero point for calibration can be measured easily and accurately.

  According to the fourth and twelfth aspects of the present invention, the pressure difference forming step for generating a pressure difference between the air trap chamber and the chamber member, and the air trap chamber and the chamber member are in communication with each other, thereby forming the pressure difference. An air trap chamber that is detected by the venous pressure detection means in a state in which the pressures are balanced in the equilibration step. Since the blood pressure removal detection means is calibrated based on the internal pressure and the zero point measured in the zero point measurement step, the blood pressure removal detection means can be calibrated more accurately.

  According to the inventions of claims 5 and 13, the blood pump is a squeezing type pump, and the pressure difference forming step generates a pressure difference by driving the blood pump. New means can be dispensed with, and the blood pressure removal detecting means can be calibrated more easily.

  According to the inventions of claims 6 and 14, the blood circuit is connected to the blood purification means for purifying the extracorporeally circulating blood, and the water removal pump for performing water removal via the blood purification means, and the While having a dual pump for supplying dialysate to the blood purification means, and the pressure difference forming step generates a pressure difference by driving the dewatering pump or the dual pump, the pressure can be increased without driving the blood pump. A difference formation process can be performed.

  According to the seventh and fifteenth inventions, at the time of the pressure difference forming step or the equilibration step, it is judged whether or not there is a leak in the blood circuit forming a closed loop. Can be performed, and workability can be further improved.

  According to the inventions of claims 8 and 16, the blood pressure detection means is calibrated during the priming process in which the blood circuit is filled with the priming liquid, so that the blood pressure reduction detection means can be calibrated during the priming operation. The workability can be further improved.

FIG. 1 is an overall schematic diagram showing a hemodialysis apparatus according to an embodiment of the present invention. Schematic showing venous pressure detection means (transducer) in the hemodialysis machine Three views (a front view, a plan view, and a side view) showing a blood pressure removal detection device applied to the hemodialysis device The top view which shows the chamber member in the blood pressure-removal detection apparatus The front view which shows the chamber member in the blood pressure-removal detection apparatus Sectional view taken along line VI-VI in FIG. Schematic diagram showing chamber member and detection means in the blood pressure removal detection apparatus The perspective view which shows the 2nd arm and fixed latching | locking part which comprise the detection means in the same blood pressure-removal detection apparatus. The schematic diagram which shows the state at the time of the priming process in the hemodialysis apparatus which concerns on embodiment. Schematic showing the state at the time of zero point measurement in the hemodialysis machine The schematic diagram which shows the state at the time of the pressure difference formation process in the hemodialysis apparatus Schematic diagram showing the state of the equilibration process in the hemodialysis machine The schematic diagram which shows the state which the priming process in the hemodialysis apparatus was complete | finished The graph which shows the fluctuation | variation of the pressure detected by the venous pressure detection means (transducer) in the same hemodialysis apparatus, and the fluctuation | variation of the actual pressure which should be detected by the blood pressure reduction detection means The schematic diagram which shows the state at the time of the pressure difference formation process in other embodiment of this invention. The schematic diagram which shows the state at the time of the pressure difference formation process in other embodiment of this invention. The schematic diagram which shows the state at the time of the pressure difference formation process in other embodiment of this invention. Schematic diagram showing the experimental configuration in this example The graph which shows the experimental result in a present Example

Hereinafter, embodiments of the present invention will be specifically described with reference to the drawings.
The blood purification apparatus applied to the present embodiment is composed of a hemodialysis apparatus for hemodialysis treatment, and is composed of a flexible tube for circulating the patient's blood extracorporeally as shown in FIG. The blood circuit 1 (the arterial blood circuit 1a and the venous blood circuit 1b) has a branch line L3 that branches from the blood circuit 1 and extends.

  More specifically, the applied hemodialysis apparatus includes a blood circuit 1 (main line) composed of an arterial blood circuit 1a and a venous blood circuit 1b, and a squeezing die disposed in the middle of the arterial blood circuit 1a. Connected to the blood pump 2, the dialyzer 3 (blood purification means) that is interposed between the arterial blood circuit 1 a and the venous blood circuit 1 b and purifies blood flowing through the blood circuit, and the arterial blood circuit 1 a. An arterial air trap chamber 4, a venous air trap chamber 5 connected to the venous blood circuit 1b, a dialyzer body 6, and a storage means 7 (supplement fluid supply source) containing a replacement fluid (such as physiological saline). A branch line L3 connecting the accommodating means 7 and the arterial blood circuit 1a, an air trap chamber 8 connected in the middle of the branch line L3, and a pressure transducer 13 (venous pressure detecting means) Leakage presence determination unit 14, and is mainly composed of a control unit 15.

  An arterial puncture needle a is connected to a tip of the arterial blood circuit 1a via a connector c, and a iron-type blood pump 2 is disposed midway, and an arterial air trap chamber 4 is connected. On the other hand, a vein side puncture needle b is connected to the distal end of the vein side blood circuit 1b via a connector d, and a vein side air trap chamber 5 is connected to the vein side blood circuit 1b. When the blood pump 2 is driven while the patient is punctured with the artery side puncture needle a and the vein side puncture needle b, the patient's blood is defoamed in the artery side air trap chamber 4 and the artery side blood circuit is removed. After reaching the dialyzer 3 through 1a, blood purification is performed by the dialyzer 3, and defoaming is performed in the venous air trap chamber 5 and then returned to the patient's body through the venous blood circuit 1b. That is, the blood of the patient is purified by the dialyzer 3 while circulating outside the body from the tip of the arterial blood circuit 1a to the tip of the venous blood circuit 1b.

  The arterial air trap chamber 4 and the venous air trap chamber 5 are respectively provided with overflow lines 4a and 5a extending from the upper part (air layer side) and having their tips released to the atmosphere. The liquid that overflows the air trap chamber 4 and the venous air trap chamber 5 (priming liquid such as physiological saline) can be discharged to the outside. The overflow lines 4a and 5a are provided with solenoid valves V4 and V5, respectively, so that the overflow lines 4a and 5a can be arbitrarily closed or opened.

  The dialyzer 3 includes a blood inlet 3a (blood inlet port), a blood outlet 3b (blood outlet port), a dialysate inlet 3c (dialysate channel inlet: dialysate inlet port) and a dialysate in its casing. A lead-out port 3d (dialysate flow path outlet: dialysate lead-out port) is formed, of which the arterial blood circuit 1a is connected to the blood introduction port 3a and the venous blood circuit 1b is connected to the blood lead-out port 3b. Has been. The dialysate inlet 3c and dialysate outlet 3d are connected to a dialysate inlet line L1 and a dialysate outlet line L2 extending from the dialyzer body 6, respectively.

  A plurality of hollow fibers (not shown) are accommodated in the dialyzer 3, and these hollow fibers constitute a blood purification membrane for purifying blood. Thus, in the dialyzer 3, a blood flow path (flow path between the blood inlet 3a and the blood outlet 3b) through which the patient's blood flows through the blood purification membrane and a dialysate flow path through which the dialysate flows. (A flow path between the dialysate inlet 3c and the dialysate outlet 3d) is formed. The hollow fiber constituting the blood purification membrane is formed with a large number of minute holes (pores) penetrating the outer peripheral surface and the inner peripheral surface to form a hollow fiber membrane, and blood is passed through the membrane. It is configured so that wastes and the like therein can permeate into the dialysate.

  On the other hand, as shown in FIG. 1, the dialysis machine body 6 bypasses the dual pump 11 formed across the dialysate introduction line L1 and the dialysate discharge line L2, and the dual pump 11 in the dialysate discharge line L2. It is mainly composed of a connected bypass line L4 and a water removal pump 12 connected to the bypass line L4. One end of the dialysate introduction line L1 is connected to the dialyzer 3 (dialyte introduction port 3c), and the other end is connected to a dialysate supply device (not shown) for preparing a dialysate having a predetermined concentration. The dialysate introduction line L1 and the dialysate discharge line L2 are provided with solenoid valves V6 and V7, respectively, and these flow paths can be arbitrarily opened or closed.

  One end of the dialysate discharge line L2 is connected to the dialyzer 3 (dialysate outlet port 3d), and the other end is connected to a drain means (not shown). The dialysate supplied from the dialysate supply device After reaching the dialyzer 3 through the dialysate introduction line L1, it is sent to the drainage means through the dialysate discharge line L2 and the bypass line L4. The dewatering pump 12 is for driving to remove water from the blood of the patient flowing in the dialyzer 3 (in the blood flow path).

  The storage means 7 (so-called “physiological saline bag”) is made of a flexible transparent container and can store a predetermined volume of a replacement fluid such as physiological saline (priming solution). It is attached to the tip of a pole (not shown) protruding from the apparatus body 6. The branch line L3 is connected to a portion (connecting portion H) between the arterial puncture needle a and the arterial air trap chamber 4 in the arterial blood circuit 1a, and the physiological saline solution (priming solution) in the storage means 7 is supplied. It can be supplied into the blood circuit 1. In addition, the connection part H uses connection parts, such as a general purpose T-shaped tube and a Y-shaped tube.

  In addition, an air trap chamber 8 is connected in the middle of the branch line L3, and is configured so that the supply (dropping) of a physiological saline solution (priming solution) can be visually observed, and an electromagnetic valve V3 is provided. Yes. The electromagnetic valve V3 is located between the blood pressure removal detection means 9 and the storage means 7 (replacement fluid supply source) in the branch line L3 (more specifically, between the blood pressure removal detection means 9 and the air trap chamber 8). The predetermined part to be clamped can be clamped, and the flow path of the predetermined part can be closed at an arbitrary timing. A similar electromagnetic valve is disposed at the distal end of the arterial blood circuit 1a (near the connector c) and the distal end of the venous blood circuit 1b (near the connector d). It can be closed at the timing.

  The blood pressure removal detection means 9 has a chamber member 10 that is connected to the branch line L3 and can store a liquid (a replacement fluid such as physiological saline) flowing through the branch line L3. By detecting this, it is possible to detect the fluid pressure (that is, blood pressure removal) in the blood circuit 1 (the flow path from the distal end to the blood pump 2 in the arterial blood circuit 1a). More specifically, as shown in FIG. 3, the blood pressure removal detection means 9 includes a chamber member 10, a first arm 18, and a second arm 19. The chamber member 10 is formed with a pair of ports P1 and P2, and a branch line L3 is connected to the ports P1 and P2.

  The chamber member 10 is connected to the branch line L3 via the ports P1 and P2, and is made of a flexible hollow member that can be deformed with a pressure change in the branch line L3. It is formed in a substantially circular shape in plan view. As shown in FIGS. 4 to 6, the chamber member 10 is formed with a communication space S communicating with the branch line L <b> 3 therein, and a liquid (such as a physiological saline solution) that flows through the branch line L <b> 3. Supplementary fluid).

  Further, the chamber member 10 according to the present embodiment is formed of a soft resin 10a (soft vinyl chloride or the like) and a hard resin portion made of a hard resin (hard vinyl chloride or the like) harder than the soft resin 10a. 10b. That is, the entire shape is made of the soft resin 10a, the communication space S and the ports P1 and P2 are formed, and the hard resin portion 10b is formed to protrude from the front and back surfaces. The soft resin 10a and the hard resin portion 10b need only be relatively soft and hard. The hard resin portion 10b is harder than the soft resin 10a. The hard resin 10b has higher rigidity and flexibility. It means that it is scarce.

  The hard resin portion 10b is formed, for example, on the front and back surfaces of the soft resin 10a by insert molding with respect to the soft resin 10a, and protrudes upward and downward in FIG. A locking portion 10ba that can be locked with the arm 19 or the fixed locking portion 20 (see FIGS. 3 and 8) is integrally formed. The locking portion 10ba is composed of a narrow diameter portion at the protruding portion of the hard resin portion 10b, and is formed in the notch portion 19a and the fixed locking portion 20 formed in the second arm 19, as shown in FIG. The shape and dimensions are such that they can be inserted into the notch 20a and locked. The fixed locking portion 20 is fixed to the frame F, and the chamber member 10 is held between the locking portion 20 and the second arm 19.

  The second arm 19 is connected to the first arm 18 via a connecting member 21, and the first arm 18 is connected to the protrusion Fa of the frame F in a cantilever manner. That is, the base end of the first arm 18 is connected to the protrusion Fa by a support member 22 such as a screw, and the tip is connected to the second arm 19 via the connection member 21, so that the deformation of the chamber member 10 is performed. The pressure can be received by the displacement accompanying the.

  The first arm 18 is formed with a strain gauge as a force sensor. When a force accompanying deformation of the chamber member 10 is received via the second arm 19, a voltage (electric signal) corresponding to the magnitude of the pressure is received. ) Can be generated. In other words, the force sensor can detect a force when the chamber member 10 is deformed due to a change in hydraulic pressure, and can convert the detected force into an electric signal. The voltage generated at this time is approximately proportional to the force applied to the second arm 19 (that is, the amount of displacement of the hard resin portion 10b). Thereby, the force due to the deformation of the chamber member 10 can be detected, and the pressure in the branch line L3 can be detected by detecting the force due to the displacement of the surface of the chamber member 10.

  Specifically, the strain gauge uses the principle that the resistance value changes when the metal resistor expands and contracts, and the notch portion 20a formed in the notch portion 19a of the second arm 19 and the fixed locking portion 20 is used. On the other hand, the chamber member 10 is set as shown in FIG. 7 by inserting a pair of locking portions 10ba into contact with each other and locking them, and blood circuit 1 (arterial blood) As the pressure in the circuit 1a) changes, the fluid pressure in the branch line L3 changes and the chamber member 10 deforms (deforms such that it expands due to an increase in pressure in the arterial blood circuit 1a and contracts due to a decrease in pressure). Accordingly, the hard resin portion 10b is displaced, and the first arm 18 and the second arm 19 are distorted in the α direction (when the chamber member 10 expands) or the β direction (when the chamber member 10 contracts) in FIG. Distortion If the change in resistance value due to the strain is detected by a gauge (force sensor), the displacement amount of the hard resin portion 10b can be detected, and therefore the pressure in the blood circuit 1 (in the arterial blood circuit 1a) is detected. It can be done.

  According to the blood pressure removal detection means 9 of the present embodiment, the pressure (in the arterial blood circuit 1a) in the branch line L3 (ie, in the arterial blood circuit 1a) is detected by the second arm 19 contacting the hard resin portion 10b and detecting the force. In other words, the blood pressure can be detected accurately, so that the pressure in the blood circuit can be accurately detected while suppressing the change in the pressure receiving area of the second arm 19 with respect to the hard resin portion 10b. That is, when the chamber member is composed of only a soft resin rich in flexibility and an attempt is made to detect the displacement of the front and back surfaces, the contact area (pressure receiving area) with the second arm 19 as the chamber member is deformed. ) Changes and an error occurs in the detection of the displacement amount, but according to the present embodiment, the second arm 19 is in contact with the hard resin portion 10b that is relatively difficult to bend. Therefore, the problem can be suppressed.

  The chamber member 10 has a communication space S communicating with the blood circuit therein, and the communication space S is filled with a liquid (a supplement such as a physiological saline) flowing through the branch line L3. The pressure in the blood circuit 1 can be detected with higher accuracy than that in which an air layer is formed. That is, when an air layer is formed in the upper part like an air trap chamber connected to the blood circuit and the pressure detection device is configured, the volume of the air layer fluctuates. While the relationship with the pressure is not constant and the pressure in the blood circuit cannot be detected with high accuracy, according to the present embodiment, the communication space S is filled with a liquid (a supplement such as a physiological saline). Therefore, the problem can be suppressed.

  Further, since the hard resin portion 10b is integrally formed with a locking portion 10ba that can be locked with the second arm 19, the second arm 19 and the first arm 18 can be reliably engaged with the force caused by the deformation of the chamber member 10. The pressure in the branch line L3 (that is, in the blood circuit 1) can be detected with higher accuracy. Further, since the locking portion 10ba is locked and set to the fixed locking portion 20 and the second arm 19, the first arm 18 is surely protected against deformation due to contraction as well as deformation due to expansion of the chamber member 10. And the 2nd arm 19 can be made to follow.

  On the other hand, in the present embodiment, as shown in FIG. 1, a monitor tube 5b is extended from the air layer side of the venous air trap chamber 5 (that is, the upper side of the venous air trap chamber 5). A pressure transducer 13 as a venous pressure detecting means is connected to the tip of the monitor tube 5b. The pressure transducer 13 is composed of a venous pressure sensor that is disposed in the dialyzer main body 6 and communicates with the air layer side of the venous air trap chamber 5. During the dialysis treatment, the blood transducer 1 (venous blood circuit 1 b). The blood pressure (venous pressure) of the patient flowing through the device can be detected in real time. The pressure transducer 13 is disposed in the dialyzer main body 6 and does not require calibration for a long time, while the chamber member 10 connected to the blood circuit 1 that is assumed to be disposable (disposable). The blood pressure removal detection means 9 possessed needs to be calibrated for each treatment.

  In addition, as shown in FIG. 2, a protective filter 16 (transducer protector called a TP filter) is disposed in the middle of the monitor tube 5b (on the side connected to the dialyzer body 5). 13 is configured to communicate with the air layer side of the venous air trap chamber 5 through the protective filter 16 and the pressure port 17. The protective filter 16 has a configuration in which a minute space communicating with the vein-side air trap chamber 5 side and a minute space communicating with the pressure transducer 13 side are separated by a filter member (not shown). Thus, the passage of liquid can be restricted while allowing the passage of air.

  In the dialyzer main body 6, a leak presence / absence determining means 14 electrically connected to the pressure transducer 13 is disposed. The leak presence / absence determining means 14 is used to determine whether or not there is a leak (leakage) in the blood circuit 1 forming a closed loop when the blood pressure detecting means 9 described later is calibrated (during the pressure difference forming process or during the equilibration process). In the present embodiment, the leak is judged in the priming process.

  The control means 15 is detected by the pressure transducer 13 (venous pressure detection means) in a state where the distal end of the arterial blood circuit 1a and the distal end of the venous blood circuit 1b are connected to form a closed loop (see FIG. 9 and the like). The blood pressure removal detecting means 9 is calibrated on the basis of the pressure in the venous air trap chamber 5, and is disposed in the dialyzer body 6 in this embodiment. That is, the control means 15 is for instructing various operations (calibration operations of the electromagnetic valves V1 to V7, driving of the blood pump 2 or driving of the water removal pump 12, etc.) for calibrating the blood pressure removal detecting means 9. It is.

Next, a priming method (priming step before treatment) in the blood circuit according to the present embodiment will be described.
First, as shown in FIG. 9, the connector c at the distal end of the arterial blood circuit 1a and the connector d at the distal end of the venous blood circuit 1b are connected. The solenoid valves V4, V6, and V7 are closed (the flow path is closed: the same applies hereinafter) and the other electromagnetic valves (V1-V3, V5) are opened (the flow path is opened: the same applies hereinafter). At the same time, the blood pump 2 is driven in the normal rotation direction (the direction of the arrow in the figure).

  At this time, if the driving speed of the blood pump 2 does not exceed the supply speed of the priming solution (a replacement fluid such as a physiological saline solution stored in the storage means 7), the blood pump 2 passes through the arterial blood circuit 1a. The priming liquid is discharged from the overflow line 5a installed in the venous air trap chamber 5 while filling the arterial air trap chamber 4 and the dialyzer 3, and simultaneously, the arterial blood circuit is passed through the venous blood circuit 1b. The priming fluid can be discharged from the overflow line 5a installed in the venous air trap chamber 5 while filling the priming fluid at the connection portion between the connector c at the distal end 1a and the connector d at the distal end of the venous blood circuit 1b.

  Thus, the priming step is performed by filling the blood circuit 1 with the priming solution while discharging the priming solution (a supplement solution such as a physiological saline solution stored in the storage unit 7) from the overflow line 5a. In the priming step, the electromagnetic valve V5 may be closed, while the electromagnetic valve V4 may be opened, and the priming liquid may be discharged from the overflow line 4a. Furthermore, both the electromagnetic valves V4 and V5 may be discharged. As an open state, the priming liquid may be discharged from both overflow lines 4a and 5a.

  After the priming liquid is filled in the blood circuit 1 as described above, the solenoid valve V3 is closed according to an instruction from the control means 15 as shown in FIG. 10 (the other solenoid valves are shown in FIG. 9). The blood pump 2 is stopped (zero point measuring step). As a result, the vein-side air trap chamber 5 and the chamber member 10 constituting the blood pressure-lowering detection means 9 are in communication with each other, the inside of the vein-side air trap chamber 5 is opened to the atmosphere, and the pressure transducer 13 (venous pressure detection means) The zero point of the blood pressure removal detecting means 9 can be measured based on the pressure in the venous air trap chamber 5 detected in (1).

  Then, as shown in FIG. 11, the solenoid valve V4 is opened while the solenoid valves V2 and V5 are closed according to the instruction of the control means 15 (the other solenoid valves V1, V3, V6, and V7 are shown in FIG. The state is maintained), and the blood pump 2 is driven to the forward rotation side (pressure difference forming step). As a result, a negative pressure is applied to the flow path on the chamber member 10 side (the flow path from the electromagnetic valve V2 through the electromagnetic valve V1 to the blood pump 2 and the electromagnetic valve V3) that constitutes the blood pressure reduction detection means 9 in the blood circuit 1. On the other hand, a flow path on the venous air trap chamber 5 side (flow path from the blood pump 2 to the electromagnetic valve V2 through the arterial air trap chamber 4 and the venous air trap chamber 5) The atmospheric pressure can be maintained, and as shown in FIG. 14, a pressure difference (a pressure difference formed by the pressure α and the pressure β) is generated between the venous air trap chamber 5 and the chamber member 10. Can do.

  Then, as shown in FIG. 12, according to an instruction from the control means 15, the electromagnetic valve V2 is opened while the electromagnetic valve V4 is closed, and the blood pump 2 is stopped (equilibration step). As a result, the venous air trap chamber 5 and the chamber member 10 can be brought into communication with each other, and as shown in FIG. 14, the pressure difference generated in the pressure difference forming step is eliminated to balance each other's pressure ( The pressure α: the actual pressure of the blood pressure removal detecting means 9 and the pressure β: the venous pressure can be balanced to a pressure γ (−200 mmHg)).

  However, the pressure in the venous air trap chamber 5 detected by the transducer 13 (venous pressure detecting means) in a state where the pressures are balanced in the balancing step and the zero point measured in the zero point measuring step. On the basis of this, the blood pressure removal detection means 9 can be calibrated (by two points, one point in the equilibration step (the pressure γ that has reached equilibrium) and one point in the zero point measurement step). Such calibration is preferably performed automatically by the control means 15, but is performed manually based on the pressure detected in the equilibration step and the zero point measured in the zero point measurement step. May be.

  Further, in the present embodiment, at the time of the pressure difference forming step or the equilibration step as described above, the presence / absence of leakage of the blood circuit 1 forming the closed loop can be determined by the leakage presence / absence determination means 14. Yes. That is, at the time of the pressure difference forming step or the equilibration step, a negative pressure portion is formed, but if the liquid circuit and the dialyzer 3 in the blood circuit 1 and the dialyzer 3 are insufficiently liquid-tight and leaky, Air is sucked in from that part and gradually returns to normal pressure. Thus, the presence / absence of a leak can be determined by detecting this by the leak presence / absence determination means 14.

  After the calibration of the blood pressure removal detecting means 9 is completed as described above, as shown in FIG. 13, the electromagnetic valve V3 is opened, the inside of the blood circuit 1 is set to normal pressure (atmospheric pressure), and the electromagnetic valve V3 is closed again. By doing so, a series of priming steps including the calibration work of the blood pressure removal detecting means 9 is completed. According to this embodiment, since the blood pressure detection means 9 is calibrated during the priming process in which the blood circuit 1 is filled with the priming solution, the blood pressure removal detection means 9 can be calibrated during the priming operation. Workability can be further improved.

  After the priming process is finished, as shown in FIG. 1, the arterial puncture needle a and the venous puncture needle b in the state of puncturing the patient are connected to the connectors c and d, and the blood pump 2 is driven to the normal rotation side. As a result, blood purification treatment (dialysis treatment) is performed by the dialyzer 3 while circulating the patient's blood extracorporeally in the blood circuit 1. At this time, the arterial blood circuit 1a and the branch line L3 are connected via the connecting portion H (however, the electromagnetic valve V3 is closed). By detecting this fluid pressure, the fluid pressure (that is, blood pressure removal) in the blood circuit 1 (the upstream side of the blood pump 2 in the arterial blood circuit 1a) can be detected.

  According to the above embodiment, the distal end of the arterial blood circuit 1a and the distal end of the venous blood circuit 1b are connected to form a closed loop, and the venous air trap detected by the pressure transducer 13 (venous pressure detecting means). Since the blood pressure removal detection means 9 is calibrated on the basis of the pressure in the chamber 5, a separate new sensor or the like for calibration of the blood pressure removal detection means 9 can be dispensed with, and the blood pressure removal detection means 9 can be easily and It can be calibrated accurately.

  Further, a branch line L3 branched from the tip of the arterial blood circuit 1a to the position where the blood pump 2 is disposed (connecting portion H) is extended, and a blood pressure-lowering detection means 9 is arranged on the branch line L3. Therefore, blood pressure can be detected with high accuracy, and a step is formed at a site where blood flows compared to the case where the chamber member 10 is connected to dispose the blood pressure detecting means 9 in the arterial blood circuit 1a. And the like can be avoided, and blood can be reliably and smoothly circulated outside the body.

  In addition, the vein-side air trap chamber 5 and the chamber member 10 are in communication with each other, and the vein-side air trap chamber 5 is opened to the atmosphere, and the vein-side air trap detected by the pressure transducer 13 (venous pressure detecting means). Since the zero point measuring step of measuring the zero point of the blood pressure removal detecting means 9 based on the pressure in the chamber 5 is provided, the zero point for calibration can be measured easily and accurately.

  Furthermore, a pressure difference forming step for generating a pressure difference between the venous air trap chamber 5 and the chamber member 10 and a pressure difference forming step by bringing the venous air trap chamber 5 and the chamber member 10 into communication with each other. The pressure transducer 13 (venous pressure detection means) detects the pressure difference in a state where the pressures are balanced in the balancing step. Since the blood pressure removal detection means 9 is calibrated based on the pressure in the venous air trap chamber 5 and the zero point measured in the zero point measurement step, the blood pressure removal detection means 9 can be calibrated more accurately.

  In the present embodiment, the blood pump 2 is composed of a squeezing type pump, and the pressure difference forming step generates a pressure difference by driving the blood pump 2. Thus, the blood pressure removal detecting means 9 can be calibrated more easily. In addition, since it is determined whether or not there is a leak in the blood circuit 1 forming the closed loop during the pressure difference forming step or the equilibration step, it is possible to perform a leak test of the blood circuit 1 simultaneously with the calibration of the blood pressure removal detecting means 9. The workability can be further improved.

Next, experiments showing the technical superiority of the present invention will be described based on examples.
First, as shown in FIG. 18, a water recirculation system circuit (circuit that circulates 37 ° C. water accommodated in the container A) in which the chamber member 10 is connected to a flow channel resembling a blood circuit is prepared, In the middle of this, the ironing type blood pump 2 similar to the above embodiment was disposed. In addition, a sensor (reference manometer T) for measuring the reference fluid pressure is connected between the tip of the flow path and the blood pump 2 to measure the fluid pressure at the part and detect blood pressure drop. The means 9 is the same as that in the above embodiment. In addition, the code | symbol B in the figure has shown the pressure throttle valve.

  However, this experiment is an experiment for confirming the pressure responsiveness for every hour by plotting the relationship between the indicated pressure of the reference manometer T and the output voltage of the force sensor in the blood pressure removal detecting means 9 every hour. Yes, the correlation between the output voltage of the blood pressure reduction detecting means 9 and the indicated pressure of the reference manometer T when 0 hour, 1 hour, 2 hours, 3 hours, 4 hours and 5 hours have elapsed is examined.

The results are shown in the graph of FIG. The approximate expression when 0 hour has passed between the output voltage of the blood pressure removal detecting means 9 and the command pressure of the reference manometer is y = 0.010x + 2.10, correlation coefficient (R ² ) = 0.98, 1 hour has passed. In this case, the approximate expression is y = 0.010x + 2.10, the correlation coefficient (R ² ) = 0.98, and the approximate expression after ² hours is y = 0.010x + 2.10, the correlation coefficient (R ² ) = 0.96 The approximate expression when 3 hours elapses is y = 0.010x + 2.10, the correlation coefficient (R ² ) = 0.96, and the approximate expression when 4 hours elapses is y = 0. 0011x + 2.10, correlation coefficient (R ² ) = 0.96 The approximate expression when 5 hours have elapsed is y = 0.010x + 2.11, correlation coefficient (R ² ) = 0.96. cage, the correlation coefficients for all examples ^{(R 2)} is 0.96 or more and It was a good result. Thus, it can be seen that the calibration of the blood pressure removal detecting means 9 is effective over a long period of time, and if calibration is performed during the priming process, it is not necessary to recalibrate in subsequent blood purification treatment (hemodialysis treatment). It proved good.

  Although the present embodiment has been described above, the present invention is not limited to this. For example, in the pressure difference forming step, the solenoid valves V1 and V3 are opened by an instruction from the control means 15 as shown in FIG. While the electromagnetic valves V2, V4, V5, V6, and V7 are closed, the blood pump 2 can be driven to the normal rotation side.

  Also in the pressure difference forming step, the flow on the chamber member 10 side constituting the blood pressure removal detecting means 9 in the blood circuit 1 (flow between the electromagnetic valve V2 and the blood pump 2 and the electromagnetic valve V3 through the electromagnetic valve V1). The flow path between the blood pump 2 and the arterial air trap chamber 4 and the venous air trap chamber 5 to the electromagnetic valve V2 while maintaining the atmospheric pressure at atmospheric pressure. ) Can be a positive pressure (positive pressure), and a pressure difference can be generated between the venous air trap chamber 5 and the chamber member 10 as in FIG.

  In each of the above embodiments, the pressure difference forming step is performed by driving the blood pump 2, but instead, as shown in FIG. 16, the control means 15 performs the pressure difference forming step. The pressure difference may be generated by driving the water removal pump 12. That is, according to an instruction from the control means 15, the electromagnetic valves V2 to V5 are closed while the electromagnetic valves V1, V6 and V7 are opened, and the water removal pump 12 is driven (the blood pump 2 is stopped).

  Thereby, the priming liquid (the filling liquid in the blood circuit 1 and the dialyzer 3) can be moved by positive filtration from the blood flow path side in the dialyzer 3 to the dialysate flow path side (water removal). While the flow path on the air trap chamber 5 side (the flow path from the blood pump 2 to the electromagnetic valve V2 through the artery side air trap chamber 4 and the vein side air trap chamber 5) is set to a negative pressure (negative pressure), The flow path on the chamber member 10 side (the flow path from the electromagnetic valve V2 through the electromagnetic valve V1 to the blood pump 2 and the electromagnetic valve V3) constituting the blood pressure removal detecting means 9 can be maintained at atmospheric pressure. As in the case of FIG. 11, a pressure difference can be generated between the venous air trap chamber 5 and the chamber member 10.

  Furthermore, in the above embodiment, the pressure difference forming step is performed by driving the blood pump 2 or the water removal pump 12, but instead of this, as shown in FIG. It is good also as what produces a pressure difference by driving the compound pump 11 in a difference formation process. That is, according to the instruction of the control means 15, the electromagnetic valves V2 to V5 and V7 are closed while the electromagnetic valves V1 and V6 are opened, and the dual pump 11 is driven (the blood pump 2 and the dewatering pump 12 are stopped). To make it happen.

  Thus, the priming solution can be back-filtered from the dialysate flow channel in the dialyzer 3 to the blood flow channel to pump the dialysate to the blood circuit 1 side, and the flow channel on the vein side air trap chamber 5 side in the blood circuit 1 While the blood pressure between the blood pump 2 and the artery-side air trap chamber 4 and the vein-side air trap chamber 5 and the electromagnetic valve V2 is set to a positive pressure (positive pressure), a blood pressure-reducing device 9 is configured. The flow path on the chamber member 10 side (the flow path from the electromagnetic valve V2 through the electromagnetic valve V1 to the blood pump 2 and the electromagnetic valve V3) can be maintained at atmospheric pressure. A pressure difference can be generated between the side air trap chamber 5 and the chamber member 10.

  According to the embodiment as described above, the blood circuit 1 is connected to the dialyzer 3 (blood purification means) for purifying extracorporeally circulating blood, and water is removed through the dialyzer 3 (blood purification means). A water removal pump 12 and a dual pump 11 for supplying dialysate to the dialyzer 3 (blood purification means) are provided, and the pressure difference forming step is performed by driving the water removal pump 12 or the dual pump 11. Since the pressure difference is generated, the pressure difference forming step can be performed without driving the blood pump 2.

  On the other hand, in each of the above embodiments, the branch line L3 branched from the tip of the arterial blood circuit 1a to the position where the blood pump 2 is disposed is extended, and the blood pressure drop detecting means 9 is connected to the branch line L3. However, instead of this, the chamber member 10 is connected between the distal end of the arterial blood circuit 1a and the position where the blood pump 2 is disposed, and the blood pressure-reducing means 9 is disposed at that portion. You may make it do. That is, the chamber member 10 is a branch line L3 that branches from the tip of the arterial blood circuit 1b to the position where the blood pump 2 is disposed (even the arterial blood circuit 1a is branched from the arterial blood circuit 1a. It is sufficient if it is connected to the

  The branch line L3 is not limited to an extension end connected to a replacement fluid supply source for storing a replacement fluid such as a physiological saline solution, but includes a replacement fluid line for introducing a dialysate into the blood circuit 1 to replace the fluid. A drug solution injection line for injecting a drug into the blood circuit 1 may be used. In this embodiment, the present invention is applied to a dialysis apparatus used at the time of dialysis treatment, but is used in other apparatuses that can purify the patient's blood while circulating it outside the body (for example, blood filtration dialysis, blood filtration, AFBF). The present invention may be applied to blood purification devices, plasma adsorption devices, and the like.

  Furthermore, in this embodiment, the blood pressure removal means 9 is calibrated at the time of the priming process and the blood circuit 1 is filled with the priming liquid. However, the blood circuit 1 is filled with the priming liquid. The calibration is possible even in a state where the blood circuit 1 is filled with air (not limited to the priming step). However, in that case, when negative pressure or positive pressure is generated in the pressure difference forming process, volume change of gas (air) occurs, and when the blood pump 2 (water removal pump 12 or dual pump 11 is driven by that amount, Since it is necessary to drive the water removal pump 12 or the dual pump 11) for a long time, the blood pressure detection means 9 is calibrated after filling the blood circuit 1 with a liquid such as a priming liquid as in the above embodiment. Is preferred.

  A blood pressure removal device that connects the distal end of the arterial blood circuit and the distal end of the venous blood circuit to form a closed loop and calibrates the blood pressure removal detection means based on the pressure in the air trap chamber detected by the venous pressure detection means As long as the detection means calibration method and the blood purification apparatus are applicable, the present invention can be applied to one having a different overall shape or one to which another function is added.

DESCRIPTION OF SYMBOLS 1 Blood circuit 1a Arterial side blood circuit 1b Vein side blood circuit 2 Blood pump 3 Dialyzer (blood purification means)
4 Arterial-side air trap chamber 5 Vein-side air trap chamber 6 Dialysis machine body 7 Accommodating means (supplement fluid supply source)
8 Air trap chamber 9 Fluid pressure detection means 10 Chamber member 11 Duplex pump 12 Dewatering pump 13 Pressure transducer (Venous pressure detection means)
14 Leak presence / absence judging means 15 Control means 16 Protective filter 17 Pressure port 18 First arm 19 Second arm 20 Fixed locking portion 21 Connecting member 22 Support member L3 Branch lines V1 to V7 Solenoid valve

Claims (16)

Consisting of an arterial blood circuit in which a blood pump is arranged and a venous blood circuit to which an air trap chamber is connected, the patient's blood can be circulated extracorporeally from the distal end of the arterial blood circuit to the distal end of the venous blood circuit A blood circuit,
It has a chamber member connected between the tip of the arterial blood circuit and the position where the blood pump is arranged, and detects blood pressure by detecting the force at the time of deformation of the chamber member and converting it into an electric signal. Blood pressure detection means capable of detection;
A venous pressure detecting means connected to the upper portion of the air trap chamber and capable of detecting the venous pressure by detecting the pressure in the air trap chamber;
A method of calibrating blood pressure detection means in a blood circuit having
The distal end of the arterial blood circuit and the distal end of the venous blood circuit are connected to form a closed loop, and the blood pressure removal detecting means is based on the pressure in the air trap chamber detected by the venous pressure detecting means. A method for calibrating blood pressure detection means characterized by calibrating the blood pressure.   2. A branch line that branches from the tip of the artery-side blood circuit to a position where the blood pump is disposed is extended, and the blood pressure-reducing means is disposed on the branch line. The method for calibrating blood pressure removal detecting means according to 1.   While the air trap chamber and the chamber member are in communication with each other, the air trap chamber is opened to the atmosphere, and the blood pressure removal detecting means is based on the pressure in the air trap chamber detected by the venous pressure detecting means. 3. A method for calibrating blood pressure reduction detecting means according to claim 1, further comprising a zero point measuring step for measuring the zero point of the blood pressure. A pressure difference forming step for generating a pressure difference between the air trap chamber and the chamber member;
An equilibration step in which the air trap chamber and the chamber member are brought into communication with each other to cancel the pressure difference generated in the pressure difference forming step and to balance each other's pressure;
Based on the pressure in the air trap chamber detected by the venous pressure detection means and the zero point measured in the zero point measuring step in a state where the pressures are balanced in the equilibration step. 4. The method of calibrating blood pressure removal detecting means according to claim 3, wherein the blood pressure removal detecting means is calibrated.   5. The method according to claim 4, wherein the blood pump is a squeezing type pump, and the pressure difference forming step generates a pressure difference by driving the blood pump.   A blood purification means for purifying blood circulating outside the body is connected to the blood circuit, and a water removal pump for performing water removal through the blood purification means and for supplying dialysate to the blood purification means 5. The method of calibrating blood pressure removal detecting means according to claim 4, wherein the pressure difference forming step generates a pressure difference by driving the water removal pump or the dual pump.   The calibration of the blood pressure removal detecting means according to any one of claims 4 to 6, wherein whether or not there is a leak in the blood circuit forming a closed loop is determined during the pressure difference forming step or the equilibration step. Method.   The method of calibrating the blood pressure removal detecting means according to any one of claims 1 to 7, wherein the blood pressure removal detection means is calibrated during a priming step of filling the blood circuit with a priming solution. Consisting of an arterial blood circuit in which a blood pump is arranged and a venous blood circuit to which an air trap chamber is connected, the patient's blood can be circulated extracorporeally from the distal end of the arterial blood circuit to the distal end of the venous blood circuit A blood circuit,
It has a chamber member connected between the tip of the arterial blood circuit and the position where the blood pump is arranged, and detects blood pressure by detecting the force at the time of deformation of the chamber member and converting it into an electric signal. Blood pressure detection means capable of detection;
A venous pressure detecting means connected to the upper portion of the air trap chamber and capable of detecting the venous pressure by detecting the pressure in the air trap chamber;
A blood purification apparatus capable of installing a blood circuit having
In the state where the distal end of the arterial blood circuit and the distal end of the venous blood circuit are connected to form a closed loop, the blood pressure is detected based on the pressure in the air trap chamber detected by the venous pressure detecting means. A blood purification apparatus comprising control means for calibrating the means.   2. A branch line that branches from the tip of the artery-side blood circuit to a position where the blood pump is disposed is extended, and the blood pressure-reducing means is disposed on the branch line. 9. The blood purification apparatus according to 9.   The control means opens the air trap chamber to the atmosphere while communicating the air trap chamber and the chamber member, and based on the pressure in the air trap chamber detected by the venous pressure detection means. The blood purification apparatus according to claim 9 or 10, wherein a zero point measuring step of measuring a zero point of the blood pressure removal detecting means is performed. The control means includes
A pressure difference forming step for generating a pressure difference between the air trap chamber and the chamber member;
An equilibration step in which the air trap chamber and the chamber member are brought into communication with each other to cancel the pressure difference generated in the pressure difference forming step and to balance each other's pressure;
Based on the pressure in the air trap chamber detected by the venous pressure detection means and the zero point measured in the zero point measurement step in a state where the pressures are balanced in the equilibration step. The blood purification apparatus according to claim 11, wherein the blood pressure removal detecting means is calibrated.   13. The blood purification apparatus according to claim 12, wherein the blood pump comprises a squeezing type pump, and the control means generates a pressure difference by driving the blood pump in the pressure difference forming step. .   A blood purification means for purifying blood circulating outside the body is connected to the blood circuit, and a water removal pump for performing water removal through the blood purification means and for supplying dialysate to the blood purification means The blood purification apparatus according to claim 12, wherein the pressure difference forming step generates a pressure difference by driving the water removal pump or the dual pump.   15. The leak presence / absence judging means for judging whether or not there is a leak in the blood circuit that forms a closed loop during the pressure difference forming step or the equilibration step is provided. Blood purification device.   The blood purification apparatus according to any one of claims 9 to 15, wherein the control unit causes calibration of the blood pressure removal detection unit during a priming step of filling the blood circuit with a priming solution.

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