JP2017006415A - Blood purification device - Google Patents

Abstract

PROBLEM TO BE SOLVED: To provide a blood purification device capable of preferably and accurately performing calibration of pressure detection means, without connecting tip ends of an artery side blood circuit and a vein side blood circuit.SOLUTION: Calibration means 12 causes to perform a negative pressure state formation step in which tip ends of an artery side blood circuit 1a and a vein side blood circuit 1b are opened, and at least a liquid channel which is near a tip end 1aa side relative to an arrangement portion of a pressure detection means 11 on the artery side blood circuit 1a is closed, and a blood pump 3 is driven for making a negative pressure state, and a normal pressure state formation step in which the tip ends of the artery side blood circuit 1a and the vein side blood circuit 1b are opened, a supply line L8 is opened and the liquid channel on a tip end side relative to a connection portion of the supply line L8 on the artery side blood circuit 1a is closed and the blood pump 3 is driven for making a normal pressure state, for calibration of the pressure detection means 11.SELECTED DRAWING: Figure 1

Description

  The present invention relates to a blood purification apparatus that is attached to a predetermined site on the distal end side from a position where a blood pump is disposed in an arterial blood circuit, and that can calibrate a pressure detection means for detecting the pressure of a liquid flow path at the predetermined site. Is.

  The general blood circuit used at the time of hemodialysis treatment is mainly composed of an arterial blood circuit in which an arterial puncture needle is attached to the tip and a venous blood circuit in which a venous puncture needle is attached to the tip. A blood purifier such as a dialyzer can be connected to each proximal end of the arterial blood circuit and the venous blood circuit. The arterial blood circuit is provided with an iron-type blood pump. By driving the blood pump with both the arterial puncture needle and the venous puncture needle punctured in the patient, the arterial puncture needle The blood is collected, the blood is flowed in the arterial blood circuit and guided to the dialyzer, the blood purified by the dialyzer is flowed in the venous blood circuit, and is passed into the patient's body through the venous puncture needle. The dialysis treatment is performed by returning.

  Also, negative pressure detection means (pressure detection means) for detecting negative pressure is usually connected upstream of the blood pump in the arterial blood circuit. Conventional pressure detection means, for example, as disclosed in Patent Document 1, uses a squeezing tube that is squeezed by a squeezing part of a blood pump, and detects the radial displacement of the squeezing tube. The blood pressure removal of the arterial blood circuit (pressure between the distal end of the arterial blood circuit and the ironing tube) can be detected.

JP 2014-83092 A

  However, in the above-described conventional blood purification apparatus, when calibrating the pressure detecting means disposed in the arterial blood circuit, a closed circuit is formed by connecting the distal end of the arterial blood circuit and the distal end of the venous blood circuit. When priming with the tip of the arterial blood circuit and the tip of the venous blood circuit open, the tip of the arterial blood circuit and the tip of the venous blood circuit are connected during calibration. There is a problem that work is deteriorated because work to connect is required separately.

  That is, in the above conventional blood purification device, priming is performed by connecting the distal end of the arterial blood circuit and the distal end of the venous blood circuit to form a closed circuit. By driving the blood pump while maintaining the circuit, it is possible to calibrate without needing to connect the circuit, but to prime with the tip of the arterial blood circuit and the tip of the venous blood circuit open. When trying to apply, when the blood pump is driven, air may be inhaled from the tip of the arterial blood circuit, so it is necessary to form a closed circuit, and a connection work for that is required separately It is.

  The present invention has been made in view of such circumstances, and allows the pressure detection means to be calibrated well and accurately without connecting the distal end of the arterial blood circuit and the distal end of the venous blood circuit. It is in providing the blood purification apparatus which can be performed.

  The invention described in claim 1 has an arterial blood circuit and a venous blood circuit each having a liquid flow channel inside which a puncture needle can be connected to the tip, and the patient's blood is removed from the body through both liquid flow channels. A blood circuit capable of being circulated, and blood purification means for purifying blood circulated extracorporeally in the blood circuit, connected to the proximal ends of the arterial blood circuit and the venous blood circuit, and connected to the arterial blood circuit An ironing tube, a blood pump capable of causing blood to flow inside the ironing tube by compressing the ironing tube in the longitudinal direction while compressing the ironing tube in a radial direction, and an arrangement of the blood pump in the arterial blood circuit. An arrangement of a pressure detection means for detecting the pressure of the liquid flow path at the predetermined site, which is attached to the predetermined site on the tip side from the installation position, and the pressure detection unit in the arterial blood circuit A blood purification apparatus comprising a replenishment line connected to a distal end side from a position and having a liquid flow path inside which a predetermined replenisher can be replenished to the arterial blood circuit, and a calibration means for calibrating the pressure detection means The calibration means closes the liquid flow path on the distal end side from the site where the pressure detection means is disposed in at least the arterial blood circuit in a state where the distal ends of the arterial blood circuit and the venous blood circuit are opened. A negative pressure state forming step in which the blood pump is driven to place the pressure detecting means in a negative pressure state, and the arterial blood circuit and the venous blood circuit are opened. , While closing the replenishment line, closing the liquid flow path on the tip side from the connection site of the replenishment line in the arterial blood circuit and driving the blood pump A normal pressure state forming step in which the portion where the detecting means is disposed is in a normal pressure state, and the detected value of the pressure detecting means obtained in the negative pressure state forming step and the normal pressure state forming step. The pressure detection means is calibrated based on the detection value of the pressure detection means.

  According to a second aspect of the present invention, in the blood purification apparatus according to the first aspect, the calibration means obtains the detected value of the pressure detecting means obtained in the negative pressure state forming step and the normal pressure state forming step. A calibration curve is acquired based on the detected value of the pressure detection means, and the pressure detection means is calibrated based on the calibration curve.

  According to a third aspect of the present invention, in the blood purification apparatus according to the first or second aspect, the pressure detection means includes a displacement detection means for detecting a radial displacement of the ironing tube, and the displacement detection means. And a pressure calculating unit capable of calculating the pressure of the liquid flow path at the predetermined portion based on the detected radial displacement of the ironing tube.

  According to a fourth aspect of the present invention, in the blood purification apparatus according to the third aspect, the blood pump includes a gripping unit for gripping the ironing tube attached to the blood pump, and the displacement detection unit. Is characterized in that it is possible to detect the displacement in the radial direction of the part gripped by the gripping means.

  According to a fifth aspect of the present invention, in the blood purification apparatus according to the fourth aspect of the invention, the gripping means includes a gripping piece capable of gripping the gripping tube in a radial direction, and the gripping piece on the side of the scraping tube. The displacement detecting means detects a load applied to the fixed end side of the urging means, and based on the detected load, the radial direction of the ironed tube The displacement is detected.

  According to a sixth aspect of the present invention, in the blood purification apparatus according to the fourth aspect of the present invention, the gripping means includes a gripping piece capable of gripping the gripping tube in a radial direction, and the gripping piece on the side of the scraping tube. The displacement detecting means is disposed at a portion facing the gripping piece with the ironing tube interposed therebetween, and the side surface of the ironing tube pressed by the gripping piece. And a displacement in a radial direction of the ironing tube is detected based on the detected pressure.

  The invention according to claim 7 is the blood purification apparatus according to any one of claims 1 to 6, wherein the replenishment line is connected to a dialysate introduction line for introducing dialysate into the blood purification means. In the normal pressure state forming step, the dialysate can be replenished as a replenisher from the dialysate introduction line.

  The invention according to claim 8 is the blood purification apparatus according to any one of claims 1 to 6, wherein the replenishment line is connected to a storage bag in which a predetermined amount of physiological saline is stored, In the normal pressure state forming step, physiological saline can be replenished as a replenisher from the accommodation bag.

  The invention according to claim 9 is the blood purification apparatus according to any one of claims 1 to 8, wherein the calibration means is configured to open the tips of the arterial blood circuit and the venous blood circuit. After the priming step of filling the blood circuit with the priming solution, the negative pressure state forming step and the normal pressure state forming step are sequentially performed, and the calibration of the pressure detecting means is terminated after the normal pressure state forming step. Features.

  According to the first aspect of the present invention, the calibration means is a state in which the tips of the arterial blood circuit and the venous blood circuit are opened, and at least the liquid on the tip side from the site where the pressure detecting means is provided in the arterial blood circuit. A negative pressure state forming step in which the flow pump is closed and the blood pump is driven to place the pressure detecting means at a negative pressure state, and the arterial blood circuit and the venous blood circuit are opened at their tips. In addition, while the replenishment line is in an open state, the liquid flow path on the tip side from the connection site of the replenishment line in the arterial blood circuit is closed and the blood pump is driven, so that the site where the pressure detection means is disposed is in a normal pressure state. The normal pressure state forming step is performed, and the pressure detection based on the detected value of the pressure detecting means obtained in the negative pressure state forming step and the detected value of the pressure detecting means obtained in the normal pressure state forming step. means Since the calibration, without connecting the front end of the tip and the venous blood circuit of the arterial blood circuit, it can be performed well good and accuracy calibration of the pressure detecting means.

  According to the invention of claim 2, the calibration means is calibrated based on the detection value of the pressure detection means obtained in the negative pressure state formation step and the detection value of the pressure detection means obtained in the normal pressure state formation step. Since the line is acquired and the pressure detection means is calibrated based on the calibration curve, the pressure detection means can be calibrated easily and accurately.

  According to the third aspect of the present invention, the pressure detecting means has a displacement detecting means for detecting the radial displacement of the ironing tube and a predetermined displacement based on the radial displacement of the ironing tube detected by the displacement detecting means. Pressure calculating means capable of calculating the pressure of the liquid flow path at the site, it is not necessary to connect a separate means for detecting the pressure to the liquid flow path, and the stagnation of the flowing liquid is suppressed. In addition, the manufacturing cost and capacity of the liquid channel can be reduced.

  According to the invention of claim 4, the blood pump includes a gripping means for gripping the ironing tube attached to the blood pump, and the displacement detection means has a diameter of a part gripped by the gripping means. Since the displacement in the direction can be detected, the ironing tube is attached to the pressure detecting means by attaching the ironing tube to the blood pump and gripping it with the gripping means. The work burden can be reduced.

  According to the invention of claim 5, the gripping means has a gripping piece that can press and grip the ironing tube in the radial direction, and a biasing means that biases the gripping piece toward the ironing tube, The displacement detecting means detects the load applied to the fixed end side of the biasing means, and detects the radial displacement of the ironing tube based on the detected load. Therefore, the biasing means in the blood pump A function of generating a gripping force for the ironing tube and a function of detecting the pressure of the liquid channel can be provided.

  According to the invention of claim 6, the gripping means includes a gripping piece that can press and grip the ironing tube in the radial direction, and a biasing means that biases the gripping piece toward the ironing tube. The displacement detecting means is disposed at a portion facing the gripping piece with the ironing tube interposed therebetween, detects the pressure applied to the side surface of the ironing tube pressed by the gripping piece, and detects the detected pressure. Since the displacement in the radial direction of the ironing tube is detected based on the above, the displacement detection means in the blood pump can have both a function of receiving a pressing force against the ironing tube and a function of detecting the pressure of the fluid flow path.

  According to the invention of claim 7, the replenishment line is connected to the dialysate introduction line for introducing the dialysate into the blood purification means, and replenishes the dialysate from the dialysate introduction line during the normal pressure state forming step. Since it can be replenished as a solution, it can have both a function of replenishing a priming solution or a dialysate as a replenisher during priming or replenishment and a function of replenishing a dialysate as a replenisher during calibration.

  According to the invention of claim 8, the replenishment line is connected to a storage bag in which a predetermined amount of physiological saline is stored, and at the time of the normal pressure state forming process, the physiological saline is used as a replacement liquid from the storage bag. Since it can be replenished, it can have a function of replenishing a priming solution or a physiological saline solution as a replenishing solution at the time of priming or replenishment and a function of replenishing a physiological saline solution as a replenishing solution at the time of calibration.

  According to the ninth aspect of the present invention, the calibration means includes the negative pressure state forming step and the normal step after the priming step of filling the blood circuit in a state where the tips of the arterial blood circuit and the venous blood circuit are opened. Since the pressure state forming step is sequentially performed and the calibration of the pressure detecting means is terminated after the normal pressure state forming step, the post-calibration step can be performed smoothly.

The schematic diagram which shows the blood purification apparatus which concerns on the 1st Embodiment of this invention. The perspective view which shows the blood pump applied to the blood purification apparatus Top view showing the blood pump Cross-sectional schematic diagram showing pressure detection means disposed in the blood pump The schematic diagram which shows the state (negative pressure state formation process) at the time of calibration of the pressure detection means in the blood purification apparatus Schematic diagram showing the state (normal pressure state forming process) at the time of calibration of the pressure detection means in the blood purification apparatus Flow chart showing calibration of displacement detecting means in the blood purification apparatus A graph showing a calibration curve for calibration of the displacement detection means The schematic diagram which shows the blood purification apparatus (at the time of a negative pressure state formation process) which concerns on the 2nd Embodiment of this invention. Schematic showing the blood purification device (during normal pressure state formation process) The perspective view which shows the blood pump which concerns on other embodiment of this invention. Cross-sectional schematic diagram showing pressure detection means disposed in the blood pump

Hereinafter, embodiments of the present invention will be specifically described with reference to the drawings.
The blood purification apparatus according to the first embodiment is for circulating a patient's blood extracorporeally to perform blood purification treatment (for example, hemodialysis treatment). As shown in FIG. An arterial blood circuit 1a that can be connected to a needle (not shown) and has a liquid channel inside, and a venous blood circuit 1b that can be connected to a venous puncture needle (not shown) and has a liquid channel inside. And is connected to the proximal ends of the arterial blood circuit 1a and the venous blood circuit 1b, respectively, through which the blood of the patient can be circulated extracorporeally through both of the liquid channels. Dialyzer 2 (blood purification means) for purifying blood flowing through the blood, blood pump 3 disposed in the arterial blood circuit 1a, arterial air trap chamber 4 connected to the arterial blood circuit 1a, and venous blood Connected to circuit 1b Venous air trap chamber 5, dialysate introduction line L1 for introducing dialysate into dialyzer 2, dialysate discharge line L2 for discharging drainage from dialyzer 2, control means 10, pressure detection means 11, replenishment The line L8 and the calibration means 12 are included.

  The arterial blood circuit 1a has a connector (not shown) connected to its distal end 1aa, and an arterial puncture needle can be connected via the connector, and the iron blood pump 3 and the artery A side air trap chamber 4 is provided. Clamping means (for example, electromagnetic valves V8 and V9) that can close the flow path are disposed at the distal end of the arterial blood circuit 1a and the distal end of the venous blood circuit 1b. On the other hand, a connector (not shown) is connected to the distal end 1ba of the venous blood circuit 1b, and a venous puncture needle can be connected via the connector. It is connected.

  Further, the arterial air trap chamber 4 and the venous air trap chamber 5 are respectively attached with pressure sensors (P1, P2) capable of detecting the pressure of the upper part (air layer) of each chamber, and the arterial air trap. The pressure sensor P1 of the chamber 4 can detect the pressure (fluid pressure) of each part of the venous blood circuit 1b by the pressure sensor P2 of the arterial blood circuit 1a and the venous air trap chamber 5. .

  Then, the blood pump 3 is driven in a state where the patient is punctured with the arterial puncture needle connected to the distal end 1aa of the arterial blood circuit 1a and the venous puncture needle connected to the distal end 1ba of the venous blood circuit 1b (see FIG. 5 and 6), the patient's blood reaches the dialyzer 2 through the arterial blood circuit 1a while being defoamed (removal of bubbles) in the arterial air trap chamber 4. After the blood purification is performed by the dialyzer 2, the blood is returned to the patient's body through the venous blood circuit 1b while defoaming (removing bubbles) in the venous air trap chamber 5. Thereby, the blood of the patient can be purified by the dialyzer 2 while circulating outside the body from the tip 1aa of the arterial blood circuit 1a of the blood circuit 1 to the tip 1ba of the venous blood circuit 1b.

  A covered tube C is connected in the middle of the arterial blood circuit 1a, and the covered tube C can be attached to the blood pump 3. The ironing tube C is compressed in the longitudinal direction while being compressed in a radial direction by a roller 15 (ironing part) of a blood pump 3 (ironing pump), which will be described in detail later. It is made of a flexible tube that is softer and larger in diameter than the other flexible tubes that make up the arterial blood circuit 1a.

  The dialyzer 2 has a blood inlet 2a (blood inlet port), a blood outlet 2b (blood outlet port), a dialysate inlet 2c (dialysate channel inlet: dialysate inlet port) and a dialysate in its casing. A lead-out port 2d (dialysate flow channel outlet: dialysate lead-out port) is formed, of which the arterial blood circuit 1a is connected to the blood introduction port 2a, and the venous blood circuit 1b is connected to the blood lead-out port 2b. Has been. The dialysate inlet 2c and the dialysate outlet 2d are connected to the dialysate inlet line L1 and the dialysate outlet line L2, respectively.

  A plurality of hollow fiber membranes (not shown) are accommodated in the dialyzer 2, and the hollow fibers constitute a blood purification membrane for purifying blood. In the dialyzer 2, a blood flow path (flow path between the blood inlet 2 a and the blood outlet 2 b) through which the patient's blood flows through a blood purification membrane and a dialysate flow path (dialysate) through which the dialysate flows. A flow path between the inlet 2c and the dialysate outlet 2d) is formed. Usually, blood flows inside the hollow fiber and dialysate flows outside. The hollow fiber membrane constituting the blood purification membrane is formed with a number of minute holes (pores) penetrating the outer peripheral surface and the inner peripheral surface to form a hollow fiber membrane. Impurities and the like in the blood can pass through the dialysate.

  Furthermore, the blood in the blood flowing through the artery-side blood circuit 1a or the vein-side blood circuit 1b during blood purification treatment (at the tip of the artery-side blood circuit 1a and the tip of the vein-side blood circuit 1b according to the present embodiment) Bubble detectors (D1, D2) capable of detecting bubbles) are connected. Such bubble detectors (D1, D2) are mounted in a predetermined unit together with, for example, a blood discriminator and clamp means (V8, V9) not shown.

  The bubble detectors (D1, D2) are composed of sensors capable of detecting bubbles (air) flowing through a flexible tube constituting the arterial blood circuit 1a or the venous blood circuit 1b. For example, ultrasonic vibrations composed of piezoelectric elements. An element and an ultrasonic receiving element made of a piezoelectric element are provided. Then, ultrasonic waves can be irradiated from the ultrasonic vibration element toward the flexible tube constituting the arterial blood circuit 1a or the venous blood circuit 1b, and the vibration can be received by the ultrasonic reception element. ing.

  The ultrasonic receiving element is configured to change the voltage according to the received vibration, and is configured to detect that the bubble has flowed when the detected voltage exceeds a predetermined threshold. Yes. In other words, since the attenuation rate of ultrasonic waves is higher than that of blood or replacement liquid, detecting the ultrasonic waves that have passed through the liquid results in the detection of bubbles (gas ) Is detected to flow.

  On the other hand, the dialysate introduction line L1 and the dialysate discharge line L2 allow the dialysate 2 to be discharged together with the dialysate while discharging dialysate prepared at a predetermined concentration to the dialyzer 2 and discharge the wastes and the like. A dual pump 6 is connected. That is, the dual pump 6 is disposed across the dialysate introduction line L1 and the dialysate discharge line L2. By driving the dual pump 6, the dialysate is introduced into the dialysate 2 via the dialysate introduction line L1. The effluent can be discharged through the introduction and dialysate discharge line L2.

  The dialysate introduction line L1 is connected to solenoid valves V1, V3 and filtration filters F1, F2. The dialysate introduced into the dialyzer 2 can be filtered by the filtration filters F1, F2, and the solenoid valve V1. , V3 can be blocked or opened at any timing. The dialysate introduction line L1 is connected to the dialysate discharge line L2 via bypass lines L4 and L5, and electromagnetic valves V4 and V5 are connected to the bypass lines L4 and L5, respectively. However, symbol H in the figure indicates a heating means (heater) for heating the dialysate supplied to the dialyzer 2 or the blood circuit 1.

  Further, bypass lines L3 and L6 that bypass the duplex pump 6 are connected to the dialysate discharge line L2, and an electromagnetic valve V6 is connected to the bypass line L6, and a water removal pump 7 is connected to the bypass line L3. Is connected. Thus, the water removal pump 7 is driven in the course of extracorporeal circulation of the patient's blood in the blood circuit 1, so that water can be removed from the blood flowing through the dialyzer 2.

  Further, a pressure pump 8 for adjusting the fluid pressure of the dialysate discharge line L2 in the duplex pump 6 is connected to the upstream side (left side in FIG. 1) of the duplex pump 6 in the dialysate discharge line L2. An open line L <b> 7 extends between the pressurizing pump 8 and the duplex pump 6 through a degassing chamber 9. Solenoid valves V2 and V7 are respectively connected to the dialysate discharge line L2 and the open line L7 branched from the dialysate discharge line L2, and the dialysate flow path can be shut off or opened at an arbitrary timing.

  The replenishment line L8 has one end connected to a sampling port P (sample port) formed at a predetermined portion of the dialysate introduction line L1 (between the electromagnetic valve V1 and the filtration filter F2 in this embodiment) The other end is connected to the arterial blood circuit 1a (the tip 1aa side from the position where the pressure detecting means 11 is disposed), and the dialysate (predetermined replenisher) in the dialysate introduction line L1 is replenished to the arterial blood circuit 1a. A liquid flow path is provided inside. That is, the replenishment line L8 is connected to the distal end 1aa side from the position where the pressure detecting means 11 is provided in the arterial blood circuit 1a, and is configured to replenish dialysate (predetermined replenisher) to the arterial blood circuit 1a. It has been done. In addition, an electromagnetic valve V10 is connected to the replenishment line L8. By opening the electromagnetic valve V10, the dialysate (replenisher) in the dialysate introduction line L1 is supplied to the blood circuit 1 (arterial blood). The circuit 1a) can be supplied (supplemented).

  The control means 10 is composed of a microcomputer electrically connected to various actuators and sensors included in the blood purification device. For example, the dialysate pipes such as the dialysate introduction line L1 and the dialysate discharge line L2 are dialyzed. The fluid replacement step of filling with, the priming step of replacing the blood flow path in the blood circuit 1 and the dialyzer 2 with a priming solution (such as physiological saline or dialysate), and dialysis of the dialysate flow channel in the dialyzer 2 A gas purge step for filling with a liquid, a blood removal step for extracting the patient's blood into the blood circuit 1, a dialysis step (blood purification treatment step) for purifying the patient's blood with the dialyzer 2 while circulating the patient's blood extracorporeally, and a blood circuit A blood return process for returning the blood in 1 to the patient, a liquid discharge process for discharging the liquid in the blood circuit 1 and / or the liquid in the dialyzer 2 to the dialysate discharge line L2, dialysis Washing and disinfecting process for cleaning and disinfecting the inside of the location of the pipe, each step in the order of preset step of waiting until the next liquid replacement step is carried out there is a controllable to be performed.

  By the way, as shown in FIGS. 2 to 4, the blood pump 3 according to this embodiment includes a stator 13, a rotor 14 that can be driven to rotate within the stator 13, and a roller 15 (squeezing portion) formed on the rotor 14. ), A pair of upper and lower guide pins 16, an upstream gripping means 17, a downstream gripping means 18, and a load sensor 11a (displacement detection means) and a calculation means 11b (see FIG. 4) constituting the pressure detection means. It is mainly composed. In the figure, the cover that covers the upper portion of the stator 13 in the blood pump 3 is omitted.

  Since the stator 13 is provided with the mounting recess 13a to which the ironing tube C is attached, the stator 13 is configured so that the ironing tube C is attached along the inner peripheral wall surface that forms the mounting recess 13a. A rotor 14 that can be rotationally driven by a motor is disposed substantially at the center of the mounting recess 13a. A pair of rollers 15 and guide pins 16 are disposed on the side surface of the rotor 14 (the surface facing the inner peripheral wall surface of the mounting recess 13a).

  The roller 15 is rotatable about a rotation axis M formed on the outer edge side of the rotor 14, and rotates the rotor 14 while radially compressing the ironing tube C attached to the attachment recess 13a. Accordingly, by squeezing in the longitudinal direction (blood flow direction), fluid such as blood can flow in the arterial blood circuit 1a. That is, when the ironing tube C is mounted in the mounting recess 13a and the rotor 14 is driven to rotate, the ironing tube C is compressed between the roller 15 and the inner peripheral wall surface of the mounting recess 13a. With the rotation drive, the rotation direction (longitudinal direction) can be squeezed. By this ironing action, blood in the arterial blood circuit 1a flows in the direction of rotation of the rotor 14, so that it can be circulated extracorporeally in the blood circuit 1.

  As shown in FIG. 2, the guide pin 16 is composed of a pair of upper and lower pin-like members that are formed to protrude from the upper end side and the lower end side of the rotor 14 toward the inner peripheral wall surface of the mounting recess 13a. The ironing tube C is held between the pair of guide pins 16. That is, when the rotor 14 is driven, the ironing tube C is held in a normal position by the pair of upper and lower guide pins 16 and the ironing tube C is prevented from being detached from the mounting recess 13a by the upper guide pin 16. -ing

  The upstream side gripping means 17 is for gripping the upstream side (the part to which the distal end 1aa side of the arterial blood circuit 1a is connected) of the ironing tube C attached to the mounting recess 13a of the stator 13 in the blood pump 3. 2-4, a grip piece 19 that can press and grip the ironing tube C in the radial direction, and a torsion spring 20 (biasing force) that biases the gripping piece 19 toward the ironing tube C side. Means).

  As shown in FIG. 4, the gripping piece 19 is composed of components that can swing around the swinging axis La, and is relatively urged in the gripping direction by the torsion spring 20. It can be fixed by pressing and firmly clamping the upstream portion. As shown in the figure, the torsion spring 20 is attached to the swing shaft La to urge the grip piece 19 and also to a fixed portion of the stator 13 (in this embodiment, a load sensor 11a attached to the stator 13). ) And a pressing end 20b that presses the grip piece 19. Instead of the torsion spring 20, other urging means for urging the grip piece 19 may be used.

  The downstream side gripping means 18 is the downstream side of the ironing tube C attached to the mounting recess 13a of the stator 13 in the blood pump 3 (the part to which the proximal side (dialyzer 2 side) of the arterial blood circuit 1a is connected). A gripping piece 21 that can press and grip the ironing tube C in the radial direction, and a torsion spring 22 that urges the gripping piece 21 toward the ironing tube C side.

  Like the grip piece 19 of the upstream grip means 17, the grip piece 21 is composed of components that can swing around the swing shaft Lb, and is relatively urged in the grip direction by the torsion spring 22. It can be fixed by pressing and firmly clamping the downstream side portion of the ironing tube C. The torsion spring 22 is attached to the rocking shaft Lb and urges the grip piece 21 as well as the torsion spring 20 of the upstream side grip means 17, and presses the grip end 21 and the fixed end located at the fixed portion of the stator 13. A pressing end.

  The load sensor 11a as the displacement detecting means can detect the radial displacement of the portion gripped by the upstream gripping means 17 in the ironing tube C. In the present embodiment, the torsion spring 20 (biasing means) ) Is applied to the fixed end 20a side, and the radial displacement of the ironing tube C is detected based on the detected load. The load sensor 11a can generate an electrical signal corresponding to the applied load.

  That is, since an arterial puncture needle is attached to the distal end 1aa of the arterial blood circuit 1a at the time of treatment, blood is collected from the patient and flows through the arterial blood circuit 1a (FIGS. 5 and 6). ), A negative pressure is generated between the distal end 1aa of the artery-side blood circuit 1a and the blood pump 3. When such a negative pressure is generated, the hydraulic pressure in the ironing tube C decreases, and the portion of the ironing tube C gripped by the upstream gripping means 17 is displaced in the radial direction (the diameter becomes small). The load detected by the sensor 11a will decrease. By detecting such a decrease in load, it is possible to detect that negative pressure is generated in the arterial blood circuit 1a.

  The load sensor 11a (displacement detection means) according to the present embodiment is electrically connected to the pressure calculation means 11b by extending wiring and the like. The pressure calculating means 11b is composed of, for example, a microcomputer or the like disposed in the dialysis machine body, and based on the radial displacement of the ironing tube C detected by the load sensor 11a (displacement detecting means), the artery side The pressure of the blood circuit 1a (liquid flow path) can be calculated. That is, the load sensor 11a and the pressure calculating means 11b constitute the pressure detecting means of the present invention. When the radial displacement of the ironing tube C is detected by the load sensor 11a, a predetermined value corresponding to the displacement is obtained. Is transmitted to the pressure calculation means 11b, and the pressure calculation means 11b causes the arterial blood circuit 1a (in this embodiment, from the distal end 1aa of the arterial blood circuit 1a to the site where the load sensor 11a is disposed). ) (Pressure reduction during blood purification treatment) is calculated.

  Here, in this embodiment, the calibration means 12 for calibrating the pressure detection means 11 (the load sensor 11a (displacement detection means) and the pressure calculation means 11b) is provided. As shown in FIG. 5, the calibration means 12 is in a state where the tips (1aa, 1ba) of the arterial blood circuit 1a and the venous blood circuit 1b are opened, and the pressure in the replenishment line L8 and the arterial blood circuit 1a. The liquid flow path on the tip 1aa side from the arrangement part of the detection means 11 (in this embodiment, the arrangement part of the blood pump 3) is closed by the clamp means V10 and the clamp means V8 to drive the blood pump 3. As shown in FIG. 6, the arterial blood circuit 1a and the venous blood circuit 1b are opened at the tips (1aa, 1ba). The flow path on the distal end side 1aa from the location where the pressure detecting means 11 is provided (the location where the blood pump 3 is provided) in the arterial blood circuit 1a while the replenishment line L8 is opened. A normal pressure state forming step of bringing the pressure detecting means 11 into a normal pressure state (a state in which the negative pressure is released) by driving the blood pump 3 by closing with the pump means V8, The pressure detection means 11 is calibrated based on the detection value of the pressure detection means 11 obtained in the negative pressure state formation step and the detection value of the pressure detection means 11 obtained in the normal pressure state formation step. Yes.

  That is, in the negative pressure state forming step, as shown in FIG. 5, the distal ends (1aa, 1ba) of the arterial blood circuit 1a and the venous blood circuit 1b are opened, and the solenoid valve of the replenishment line L8 is used. Since the liquid flow path is closed by closing the clamp means V8 at the tip of the V10 and the arterial blood circuit 1a, when the blood pump 3 is driven, the clamp means V8 in the arterial blood circuit 1a that is upstream thereof And the area where the blood pump 3 is disposed is a negative pressure. And the detected value (α in FIG. 8) by the pressure detecting means 11 at that time is stored. Note that the liquid flow path is closed as long as the liquid flow path on the distal end 1aa side of the arterial blood circuit 1a can be closed at least from the position where the pressure detecting means 11 is provided in the arterial blood circuit 1a. It is not limited to. For example, an electromagnetic valve can be provided between the position where the pressure detecting means 11 is disposed in the artery-side blood circuit 1a and the connection site of the replenishment line L8, and the liquid flow path can be closed by this electromagnetic valve.

  In the normal pressure state forming step, as shown in FIG. 6, the tips (1aa, 1ba) of the arterial blood circuit 1a and the venous blood circuit 1b are opened, and the solenoid valve of the replenishment line L8 is used. Since the distal end clamping means V8 in the arterial blood circuit 1a is closed and the flow path is closed while the V10 is in the open state, when the blood pump 3 is driven, air flows from the distal end 1aa of the arterial blood circuit 1a. The dialysate as the replenisher is replenished and flows from the replenishment line L8 while preventing inhalation. As a result, the negative pressure in the negative pressure state forming step is released and becomes a normal pressure state (a state in which no negative pressure is applied). Therefore, the detection value (β in FIG. 8) at that time is stored. deep.

  Therefore, the calibration unit 12 according to the present embodiment includes the detection value α of the pressure detection unit 11 obtained in the negative pressure state formation step, and the detection value β of the pressure detection unit 11 obtained in the normal pressure state formation step. A calibration curve is acquired based on the calibration curve, and the pressure detection means 11 is calibrated based on the calibration curve. Specifically, Va represents the output voltage at the detected value α of the pressure detecting means 11 obtained in the negative pressure state forming step, and Vb represents the output voltage at the detected value β of the pressure detecting means 11 obtained in the normal pressure state forming step. Then, as shown in FIG. 8, a graph with the vertical axis representing the pressure (mmHg) and the horizontal axis representing the output voltage (V) can be obtained. When the voltage is x, y = ax−b) is obtained.

  Therefore, the pressure detection means 11 (load sensor 11a and pressure calculation means 11b) is calibrated based on the obtained calibration curve, and after calibration at the time of dialysis treatment (at the time of blood purification treatment). The blood pressure removal means 11 detects the blood pressure removal. That is, the post-calibration pressure detection means 11 reduces the blood pressure removal, which is the pressure of the liquid flow path from the tip of the arterial blood circuit 1a to the covered tube C, during the extracorporeal circulation of blood during blood purification treatment. It can be calculated.

  In this embodiment, the calibration of the pressure detection means 11 by the calibration means as described above is performed for each blood purification treatment (every dialysis treatment). For example, after priming, the blood purification treatment (dialysis treatment) is performed. Before starting, the pressure detecting means 11 is calibrated in the calibration process (see the flowchart in FIG. 7). As a result, an error based on individual differences such as the load sensor 11a (displacement detecting means) constituting the iron tube C or the pressure detecting means 11 can be suppressed every time the blood purifying treatment is performed. Can be monitored with higher accuracy.

  Furthermore, the calibration means 12 according to the present embodiment, after the priming step of filling the blood circuit 1 in a state where the tips (1aa, 1ba) of the arterial blood circuit 1a and the venous blood circuit 1b are opened, The negative pressure state forming step and the normal pressure state forming step are sequentially performed, and the calibration of the pressure detecting means 11 is ended after the normal pressure state forming step. That is, in the next step of the calibration step, the negative pressure at the distal end portion of the artery-side blood circuit 1a (the flow path between the site where the blood pump 3 is disposed and the distal end 1aa) is released to be in a normal pressure state. It is composed.

Next, control in the blood purification apparatus according to the present embodiment will be described based on the flowchart of FIG.
Before the start of dialysis treatment (blood purification treatment), the liquid replacement step S1 is first performed to fill the inside of the dialyzer body with dialysate, and self-diagnosis such as pipe leak diagnosis and operation test of each actuator. carry out. Then, it progresses to priming process S2, and fills the blood circuit 1 with the dialysate as a priming liquid by supplying the dialysate to the arterial blood circuit 1a via the replenishment line L8. In the present embodiment, the priming solution (dialysis solution) is filled in the blood circuit 1 in a state where the tips (1aa, 1ba) of the arterial blood circuit 1a and the venous blood circuit 1b are opened. In the priming step S2, priming (gas purge) on the dialysate flow path side of the dialyzer 2 is also performed.

  When this priming step S2 is completed, the process proceeds to a calibration step. In this calibration step, as described above, the tips (1aa, 1ab) of the arterial blood circuit 1a and the venous blood circuit 1b are opened, and at least the arrangement of the pressure detection means 11 in the arterial blood circuit 1a is arranged. A negative pressure state is created by closing the liquid flow path on the tip 11aa side from the installation site (the location where the blood pump 3 is provided) and driving the blood pump 3 so that the location where the pressure detecting means 11 is provided is a negative pressure state. Step S3 and the connection site of the replenishment line L8 in the arterial blood circuit 1a with the tips (1aa, 1ba) of the arterial blood circuit 1a and the venous blood circuit 1b opened and the replenishment line L8 opened. The normal pressure state forming step S for closing the liquid flow path on the tip 1aa side and driving the blood pump 3 to place the arrangement site of the pressure detecting means 11 in the normal pressure state. And the pressure detection based on the detection value α of the pressure detection means 11 obtained in the negative pressure state formation step S3 and the detection value β of the pressure detection means 11 obtained in the normal pressure state formation step S4. The means 11 is calibrated.

  Thereafter, the process proceeds to S5, where it is determined whether or not the negative pressure state forming step S3 and the normal pressure state forming step S4 have been performed a predetermined number of times. If not, the negative pressure state forming step S3 and the normal pressure state in the calibration step are performed. When the pressure state forming step S4 is performed again and it is performed a predetermined number of times, it is determined whether or not a desired negative pressure state is formed in S6, and if it is determined that the negative pressure state is not formed, Returning to S3, the negative pressure state forming step S3 and the normal pressure state forming step S4 are performed a predetermined number of times. In this case, whether or not a desired negative pressure state has been formed is determined by the detection value (Va) of the detection means 11 obtained in the negative pressure state formation step S3 and the detection means obtained in the normal pressure state formation step S4. 11 when the voltage difference of the detected value (Vb) exceeds the threshold value. When it is determined in S6 that the desired negative pressure state has been formed, the process proceeds to the treatment step S7. In this treatment step S6, the patient is punctured with an arterial puncture needle and a venous puncture needle, and an arterial puncture needle and a venous puncture needle are respectively inserted into the distal end 1aa of the arterial blood circuit 1a and the distal end 1ba of the venous blood circuit 1b. The blood pump 3 is driven to rotate the roller 15 (squeezing part) to start blood removal, and the patient's blood is circulated extracorporeally via the arterial blood circuit 1a and the venous blood circuit 1b. . Thereby, the blood in the extracorporeal circulation process is purified by the dialyzer 2, and dialysis treatment (blood purification treatment) is performed. Thus, during blood purification treatment, the pressure detection means 11 calibrated in the calibration process is used to detect the pressure (hydraulic pressure) between the tip 1aa of the arterial blood circuit 1a and the blood pump 3, thereby removing the blood. Blood status can be monitored.

  Further, when the treatment step S7 is completed, a blood return step (step of returning the blood in the blood circuit 1 to the body of the patient) is performed in S8, and then a drainage step S9 for draining the dialyzer 2 is performed. A series of controls will end. Through the above series of steps, after calibrating the pressure detecting means 11 in dialysis treatment (blood purification treatment), the blood pressure can be detected in real time during the dialysis treatment by the pressure detecting means 11, The blood removal status can be monitored.

  According to the above embodiment, the calibration means 12 is in a state where the tips (1aa, 1ba) of the arterial blood circuit 1a and the venous blood circuit 1b are opened, and at least the pressure detection means 11 in the arterial blood circuit 1a. A negative pressure state forming step of closing the liquid flow path on the tip 1aa side from the arrangement site and driving the blood pump 3 to make the arrangement site of the pressure detecting means 11 a negative pressure state, and the arterial blood circuit 1a In the state where the distal end (1aa, 1ba) of the venous blood circuit 1b is opened and the supplementary line L8 is opened, the liquid flow path on the distal end 1aa side from the connection site of the supplemental line L8 in the arterial blood circuit 1a is opened. Obtained by the negative pressure state forming step by causing the blood pump 3 to be closed and performing the normal pressure state forming step of setting the portion where the pressure detecting means 11 is disposed to the normal pressure state. Since the pressure detection means 11 is calibrated based on the detection value (Va) of the force detection means 11 and the detection value (Vb) of the pressure detection means 11 obtained in the normal pressure state forming step, the arterial blood circuit 1a is calibrated. The pressure detection means 11 can be calibrated with good accuracy without connecting the distal end 1aa of the blood vessel 1 and the distal end 1ba of the venous blood circuit 1b.

  Further, the calibration unit 12 according to the present embodiment is based on the detection value of the pressure detection unit 11 obtained in the negative pressure state formation step and the detection value of the pressure detection unit 11 obtained in the normal pressure state formation step. Since the calibration curve is acquired and the pressure detection means 11 is calibrated based on the calibration curve, the pressure detection means 11 can be calibrated easily and accurately.

  Further, the pressure detection means 11 according to the present embodiment is based on a displacement detection means 11a for detecting the radial displacement of the ironing tube C and the radial displacement of the ironing tube C detected by the displacement detection means 11a. And a pressure calculating means 11b that can calculate the pressure of the liquid flow path at a predetermined site, so that it is not necessary to connect a separate means for detecting the pressure to the liquid flow path, It is possible to suppress stagnation and to reduce the manufacturing cost and capacity of the liquid flow path (blood circuit 1).

  Furthermore, the blood pump 3 according to the present embodiment includes gripping means (upstream gripping means 17 and downstream gripping means 18) for gripping the ironing tube C attached to the blood pump 3. Since the displacement detection means 11a can detect the displacement in the radial direction of the part gripped by the gripping means (the upstream gripping means 17 in the present embodiment), the displacement detection means 11a By attaching and gripping by the gripping means (upstream gripping means 17), the ironing tube C is attached to the pressure detection means 11, and the work burden on the medical staff can be reduced.

  In particular, the upstream side gripping means 17 (gripping means) according to the present embodiment includes a gripping piece 19 that can press and grip the ironing tube C in the radial direction, and urges the gripping piece 19 toward the ironing tube C side. The displacement detecting means 11a detects a load applied to the fixed end side of the torsion spring 20, and based on the detected load, the displacement detecting means 11a has a torsion spring 20 (biasing means). Since the displacement in the radial direction is detected, the torsion spring 20 (biasing means) in the blood pump 3 generates a gripping force against the covered tube C and the liquid on the distal end 1aa side from the blood pump 3 in the arterial blood circuit 1a. It can have the function of detecting the pressure of the flow path.

  The replenishment line L8 according to this embodiment is connected to a dialysate introduction line L1 for introducing dialysate into the dialyzer 2 (blood purification means), and the dialysate introduction line L1 during the normal pressure state forming step. Therefore, the dialysate can be replenished as a replenisher, so that the function of replenishing the dialysate as the priming liquid or the replenisher during priming or replenishment and the function of replenishing the dialysate as the replenisher during calibration can be provided.

  Furthermore, the calibration means 12 according to the present embodiment, after the priming step of filling the blood circuit 1 in a state where the tips (1aa, 1ba) of the arterial blood circuit 1a and the venous blood circuit 1b are opened, The negative pressure state forming step and the normal pressure state forming step are sequentially performed, and the calibration of the pressure detecting means 11 is terminated after the normal pressure state forming step. Therefore, the post-calibration step (the treatment step in this embodiment) is performed. It can be performed smoothly.

Next, a blood purification apparatus according to a second embodiment of the present invention will be described.
As in the first embodiment, the blood purification apparatus according to this embodiment is for circulating a patient's blood extracorporeally to perform blood purification treatment (for example, hemodialysis treatment), as shown in FIGS. In addition, an arterial blood circuit 1a to which an arterial puncture needle (not shown) can be connected to the tip 1aa, and a venous blood circuit 1b to which a venous puncture needle (not shown) can be connected to the tip 1ba, A blood circuit 1 capable of circulating blood extracorporeally, a dialyzer 2 (blood purification means) connected to the proximal ends of the arterial blood circuit 1a and the venous blood circuit 1b, respectively, for purifying blood flowing through the blood circuit 1, and an artery A blood pump 3 disposed in the side blood circuit 1a, an artery side air trap chamber 4 connected to the artery side blood circuit 1a, a vein side air trap chamber 5 connected to the vein side blood circuit 1b, and a dialyzer 2 A dialysate introduction line L1 for introducing dialysate, a dialysate discharge line L2 for discharging drainage from the dialyzer 2, a control means 10, a pressure detection means 11, a replenishment line L9, and a calibration means 12. Configured. In addition, the same code | symbol is attached | subjected to the component similar to 1st Embodiment, and those description shall be abbreviate | omitted.

  The replenishment line L9 is connected to the distal end 1aa side from the position where the pressure detecting means 11 is provided in the arterial blood circuit 1a, and is composed of a flow path capable of replenishing the arterial blood circuit 1a with a predetermined amount. It is connected to a storage bag B in which a physiological saline solution is stored, and is configured to be replenished from the storage bag B as a replenishment solution during the normal pressure state forming step. In the figure, symbol g indicates an air trap chamber connected to the replenishment line L9, and symbol V11 indicates clamp means (for example, an electromagnetic valve) that can open and close the flow path of the replenishment line L9. .

  As shown in FIG. 9, the calibration means 12 is in a state where the tips (1aa, 1ba) of the arterial blood circuit 1a and the venous blood circuit 1b are opened, and pressure detection in the replenishment line L9 and the arterial blood circuit 1a. The pressure detecting means is configured by driving the blood pump 3 by closing the liquid flow path on the distal end 1aa side with respect to the arrangement part of the means 11 (in this embodiment, the arrangement part of the blood pump 3) by the clamp means V8. A negative pressure state forming step in which the arrangement site of 11 is in a negative pressure state, and as shown in FIG. 10, a state where the tips (1aa, 1ba) of the arterial blood circuit 1a and the venous blood circuit 1b are opened, and The blood pump 3 is driven by closing the liquid flow path on the distal end side 1aa from the connecting portion of the replenishment line L9 in the artery side blood circuit 1a with the clamping means V8 while the replenishment line L9 is opened. The normal pressure state forming step of setting the portion where the pressure detecting unit 11 is disposed to the normal pressure state (a state where the negative pressure is released) is performed, and the detection of the pressure detecting unit 11 obtained in the negative pressure state forming step is performed. The pressure detection means 11 is calibrated based on the value and the detection value of the pressure detection means 11 obtained in the normal pressure state forming step.

  That is, in the negative pressure state forming step, as shown in FIG. 9, the tips (1aa, 1ba) of the arterial blood circuit 1a and the venous blood circuit 1b are opened, and the replenishment line L9 is clamped. Since the liquid flow path is closed by closing the clamp means V8 at the distal end of the V11 and the arterial blood circuit 1a, and the blood pump 3 is driven, the clamp means V8 in the arterial blood circuit 1a on the upstream side is driven. And the area where the blood pump 3 is disposed is a negative pressure. Then, the detection value by the pressure detection means 11 at that time (α in FIG. 8 as in the first embodiment) is stored. Note that the liquid flow path is closed as long as the liquid flow path on the distal end 1aa side of the arterial blood circuit 1a can be closed at least from the position where the pressure detecting means 11 is provided in the arterial blood circuit 1a. It is not limited to. For example, an electromagnetic valve may be provided between the position where the pressure detection means 11 is disposed in the arterial blood circuit 1a and the connection site of the replenishment line L9, and the liquid flow path may be closed by this electromagnetic valve.

  Further, in the normal pressure state forming step, as shown in FIG. 10, the tips (1aa, 1ba) of the arterial blood circuit 1a and the venous blood circuit 1b are opened, and the replenishment line L9 is clamped. Since the flow path is closed by closing the clamp means 8 at the tip of the arterial blood circuit 1a while the V11 is in the open state, when the blood pump 3 is driven, air flows from the tip 1aa of the arterial blood circuit 1a. The physiological saline solution as a replenisher is replenished and flows from the replenishment line L9 while preventing inhalation. As a result, the negative pressure in the negative pressure state forming step is released and becomes a normal pressure state (a state in which no negative pressure is applied), so that the detected value by the pressure detection means 11 at that time (as in the first embodiment) 8) is stored.

  Therefore, the calibration unit 12 according to the present embodiment includes the detection value α of the pressure detection unit 11 obtained in the negative pressure state formation step, and the detection value β of the pressure detection unit 11 obtained in the normal pressure state formation step. A calibration curve is acquired based on the calibration curve, and the pressure detection means 11 is calibrated based on the calibration curve. Specifically, Va represents the output voltage at the detected value α of the pressure detecting means 11 obtained in the negative pressure state forming step, and Vb represents the output voltage at the detected value β of the pressure detecting means 11 obtained in the normal pressure state forming step. Then, as shown in FIG. 8, a graph with the vertical axis representing the pressure (mmHg) and the horizontal axis representing the output voltage (V) can be obtained. When the voltage is x, y = ax−b) is obtained.

  Therefore, the pressure detection means 11 (load sensor 11a and pressure calculation means 11b) is calibrated based on the obtained calibration curve, and after calibration at the time of dialysis treatment (at the time of blood purification treatment). The blood pressure removal means 11 detects the blood pressure removal. That is, the post-calibration pressure detection means 11 reduces the blood pressure removal, which is the pressure of the liquid flow path from the tip of the arterial blood circuit 1a to the covered tube C, during the extracorporeal circulation of blood during blood purification treatment. It can be calculated.

  According to the above embodiment, as in the first embodiment, the calibration means 12 is in a state where the tips (1aa, 1ba) of the arterial blood circuit 1a and the venous blood circuit 1b are opened, and the replenishment line L9 and In the arterial blood circuit 1a, the liquid flow path on the distal end 1aa side is closed from the position where the pressure detecting means 11 is disposed, and the blood pump 3 is driven so that the position where the pressure detecting means 11 is disposed is in a negative pressure state. The pressure state forming step, the state in which the tips (1aa, 1ba) of the arterial blood circuit 1a and the venous blood circuit 1b are opened, and the replenishment line L9 in the arterial blood circuit 1a while the replenishment line L9 is opened. A normal pressure state forming step is performed in which the liquid flow path on the tip 1aa side from the connection site is closed and the blood pump 3 is driven to place the pressure detecting means 11 at a normal pressure state. Based on the detection value (Va) of the pressure detection means 11 obtained in the negative pressure state formation step and the detection value (Vb) of the pressure detection means 11 obtained in the normal pressure state formation step, the pressure detection means 11 Since the calibration is performed, the pressure detecting means 11 can be calibrated with good and high accuracy without connecting the distal end 1aa of the arterial blood circuit 1a and the distal end 1ba of the venous blood circuit 1b.

  In particular, the replenishment line L9 according to the present embodiment is connected to a storage bag B in which a predetermined amount of physiological saline is stored, and the normal saline is supplied from the storage bag B during the normal pressure state forming step. Therefore, it is possible to have both a function of replenishing a priming solution or a physiological saline solution as a replenishing solution at the time of priming or replenishment and a function of replenishing a physiological saline solution as a replenishing solution at the time of calibration.

  Although the present embodiment has been described above, the present invention is not limited thereto. For example, as illustrated in FIGS. 11 and 12, the stator 13, the rotor 14 that can be rotationally driven in the stator 13, It has a roller 15 (ironing portion) formed on the rotor 14, a pair of upper and lower guide pins 16, an upstream gripping means 17 ', a downstream gripping means 18, and a pressure transducer 11a' as a displacement detection means. It may be a blood pump 3 ′. In addition, the same code | symbol is attached | subjected to the component similar to previous embodiment in blood pump 3 ', and those description is abbreviate | omitted.

  The upstream side gripping means 17 ′ is for gripping the upstream side (the part to which the distal end side of the arterial blood circuit 1a is connected) of the ironing tube C attached to the mounting recess 13a of the stator 13 in the blood pump 3 ′. As shown in FIG. 12, a gripping piece 19 that can press and grip the ironing tube C in the radial direction, and a torsion spring 20 that biases the gripping piece 19 toward the ironing tube C (biasing means). ).

  The pressure transducer 11a ′ as the displacement detecting means can detect the radial displacement of the portion gripped by the upstream gripping means 17 ′ in the ironing tube C. In this embodiment, the ironing tube C is The pressure applied to the side surface of the ironing tube C disposed between the gripping piece 19 and pressed by the gripping piece 19 is detected, and the ironing tube C is detected based on the detected pressure. The displacement in the radial direction is detected.

  That is, when blood is collected from a patient and flowed in the arterial blood circuit 1a, if negative pressure is generated between the distal end 1aa of the arterial blood circuit 1a and the blood pump 3 ′, Since the hydraulic pressure decreases and the portion gripped by the upstream gripping means 17 ′ in the ironing tube C tends to be displaced in the radial direction (diameter tends to decrease), the contact area with the pressure transducer 11 a ′ is small. Thus, the pressure detected by the pressure transducer 11a ′ is reduced. By detecting such a decrease in pressure, it is possible to detect that negative pressure is generated in the arterial blood circuit 1a.

  As in the first embodiment, the pressure transducer 11a '(displacement detection unit) according to the present embodiment is electrically connected to the pressure calculation unit 11b by extending wiring and the like. The pressure calculation means 11b is composed of, for example, a microcomputer or the like disposed in the dialyzer body, and based on the radial displacement of the ironing tube C detected by the pressure transducer 11a ′ (displacement detection means), the artery The pressure of the side blood circuit 1a (liquid flow path) can be calculated. That is, the pressure transducer 11a '(displacement detector) and the pressure calculator 11b constitute the pressure detector of the present invention.

  As in the previous embodiment, the negative pressure state forming step and the normal pressure state forming step are performed by the calibration unit 12 to calibrate the pressure transducer 11a ′ (displacement detection unit) and the pressure calculation unit 11b as pressure detection units. Configured to get. In this way, the gripping means (upstream gripping means 17 ′) includes a gripping piece 19 that can press and grip the ironing tube C in the radial direction, and a twist that biases the gripping piece 19 toward the ironing tube C side. The displacement detecting means includes a spring 20 (biasing means), and the displacement detecting means is disposed at a position facing the gripping piece 19 with the covering tube C interposed therebetween, and the pressing tube C pressed by the gripping piece 19 is provided. Since the pressure applied to the side surface is detected and the radial displacement of the ironing tube C is detected based on the detected pressure, the displacement detecting means in the blood pump 3 'receives a pressing force against the ironing tube C. The function and the function of detecting the pressure of the fluid flow path on the distal end 1aa side from the blood pump 3 ′ in the arterial blood circuit 1a can be combined.

  In the present embodiment, all of the pressure detection means are disposed in the blood pump, but are attached to a predetermined site on the distal end 1aa side from the position where the blood pump is disposed in the arterial blood circuit 1a. Any other form may be used as long as the pressure of the liquid flow path can be detected. The replenishment line is connected to the distal end 1aa side from the position where the pressure detecting means 11 is disposed in the arterial blood circuit 1a, and can be used to replenish a predetermined replenisher to the arterial blood circuit 1a. May be different from the replenishment line L8 for replenishing as a replenisher and the replenishment line L9 for replenishing physiological saline as a replenisher.

  The calibration means is in a state in which the tips of the arterial blood circuit and the venous blood circuit are open, and at least the liquid flow channel on the tip side from the position where the pressure detection means is disposed in the arterial blood circuit is closed. The negative pressure state forming step of setting the portion where the pressure detecting means is disposed to the negative pressure state by driving, the state where the tips of the arterial blood circuit and the venous blood circuit are opened, and the replenishment line are opened The normal pressure state forming step of closing the liquid flow path on the tip side from the connection site of the replenishment line in the arterial blood circuit and driving the blood pump to bring the pressure detection means to the normal pressure state. A blood purification device that calibrates the pressure detection means based on the detection value of the pressure detection means obtained in the negative pressure state formation step and the detection value of the pressure detection means obtained in the normal pressure state formation step If, it is possible external shape is applied to such different or what other functions are added.

1 Blood circuit (liquid flow path)
1a Arterial blood circuit 1b Venous blood circuit 2 Dialyzer (blood purifier)
3, 3 ′ Blood pump 4 Arterial air trap chamber 5 Venous air trap chamber 6 Duplex pump 7 Dewatering pump 8 Pressurizing pump 9 Degassing chamber 10 Control means 11 Pressure detecting means 12 Calibration means 13 Stator 14 Rotor 15 Roller ( Ironing section)
16 Guide pins 17, 17 'Upstream side gripping means 18 Downstream side gripping means 19 Holding piece 20 Torsion spring (biasing means)
21 gripping piece 22 torsion spring

Claims (9)

A blood circuit that has an arterial blood circuit and a venous blood circuit each having a liquid flow path therein and a puncture needle connectable to the tip, and can circulate the patient's blood extracorporeally via both liquid flow paths;
Blood purification means connected to the proximal ends of the arterial blood circuit and the venous blood circuit, respectively, for purifying blood circulating extracorporeally in the blood circuit;
An ironing tube connected to the arterial blood circuit;
A blood pump capable of flowing blood into the ironing tube by squeezing the ironing tube in the longitudinal direction while compressing the ironing tube in a radial direction;
A pressure detection means for detecting the pressure of the liquid flow path at the predetermined site, which is attached to a predetermined site on the distal end side from the position of the blood pump in the arterial blood circuit;
A replenishment line that is connected to the distal side from the position of the pressure detection means in the arterial blood circuit, and has a liquid flow path inside that can replenish a predetermined replenisher into the arterial blood circuit;
Calibration means for calibrating the pressure detection means;
In the blood purification apparatus comprising
The calibration means includes
The blood pump is operated by closing the liquid flow path on the distal end side from the position where the pressure detecting means is disposed in the arterial blood circuit in a state where the distal ends of the arterial blood circuit and the venous blood circuit are opened. A negative pressure state forming step of setting the pressure detection means to a negative pressure state by driving;
The state where the tips of the arterial blood circuit and the venous side blood circuit are opened, and the liquid flow path on the tip side from the connection site of the replenishment line in the arterial blood circuit is closed while the replenishment line is opened. A normal pressure state forming step of driving the blood pump to place the pressure detection means at a normal pressure state;
And calibrating the pressure detecting means based on the detected value of the pressure detecting means obtained in the negative pressure state forming step and the detected value of the pressure detecting means obtained in the normal pressure state forming step. The blood purification apparatus characterized by performing.   The calibration means obtains a calibration curve based on the detection value of the pressure detection means obtained in the negative pressure state formation step and the detection value of the pressure detection means obtained in the normal pressure state formation step. 2. The blood purification apparatus according to claim 1, wherein the pressure detection means is calibrated based on the calibration curve. The pressure detecting means includes
A displacement detecting means for detecting a radial displacement of the ironing tube;
Pressure calculating means capable of calculating the pressure of the liquid flow path in the predetermined portion based on the radial displacement of the ironing tube detected by the displacement detecting means;
The blood purification apparatus according to claim 1 or 2, further comprising:   The blood pump has a gripping means for gripping the ironing tube attached to the blood pump, and the displacement detection means can detect a radial displacement of a part gripped by the gripping means. The blood purification apparatus according to claim 3, wherein   The gripping means includes a gripping piece that can press and grip the ironing tube in a radial direction, and a biasing means that biases the gripping piece toward the ironing tube, and the displacement detection means includes: 5. The blood purification apparatus according to claim 4, wherein a load applied to the fixed end side of the urging means is detected, and a radial displacement of the ironing tube is detected based on the detected load. .   The gripping means includes a gripping piece that can press and grip the ironing tube in a radial direction, and a biasing means that biases the gripping piece toward the ironing tube, and the displacement detection means includes: The pressure applied to the side surface of the ironing tube, which is disposed at a position facing the gripping piece across the ironing tube and is pressed by the gripping piece, is detected based on the detected pressure. The blood purification apparatus according to claim 4, wherein a displacement in a radial direction of the ironing tube is detected.   The replenishment line is connected to a dialysate introduction line for introducing dialysate into the blood purification means, and can be replenished as a replenisher from the dialysate introduction line during the normal pressure state forming step. The blood purification apparatus according to any one of claims 1 to 6.   The replenishment line is connected to a storage bag in which a predetermined amount of physiological saline is stored, and is capable of replenishing the physiological saline as a supplement from the storage bag during the normal pressure state forming step. The blood purification apparatus according to any one of claims 1 to 6.   The calibration means includes the negative pressure state forming step and the normal pressure state forming step after the priming step of filling the blood circuit with the tips of the arterial blood circuit and the venous blood circuit open. The blood purification apparatus according to any one of claims 1 to 8, wherein the blood purification apparatus is sequentially performed and the calibration of the pressure detection means is terminated after the normal pressure state forming step.

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