Blood purification device and method for controlling feed pump

Abstract

A blood purification device is provided with: a blood circuit (21); a dialysate circuit (41) having a dialysate supply flow path (52), a dialysate discharge flow path (53), and a bypass flow path (54); a pressure pump (73) disposed in the dialysate circuit (41); and a main control unit (22) for controlling the driving of the pressure pump (73), the main control unit (22) switching from a bypass liquid delivery mode in which liquid is delivered from the dialysate supply flow path (52) to the dialysate discharge flow path (53) via the bypass flow path (54) to a main liquid delivery mode in which liquid is delivered from the dialysate supply flow path (52) to the dialysate discharge flow path (53) via the dialyzer (10), and the main control unit (22) controlling the driving of the pressure pump (73) when switching from a bypass liquid delivery mode in which liquid is delivered from the dialysate supply flow path (52) to the dialysate discharge flow path (53) via the bypass flow path (54) to the main liquid delivery mode. When a pressure difference occurs between the blood circuit (21) and the dialysate circuit (41), the pump speed of the pressure pump (73) is adjusted so as to reduce the pressure difference.

Description

Technical Field

[0001] The invention relates to a blood purification device and a control method for a liquid feeding pump. Background Art

[0002] As a blood purification device, a device having a bypass flow path (bypass line) is included (refer to patent document 1), and the bypass flow path bypasses the blood purifier and connects the supply side pipeline and the discharge side pipeline. The blood purification device (dialysis device) has: a blood purifier; a supply side pipeline for circulating the dialysate supplied to the blood purifier; a discharge side pipeline for circulating the supplied dialysate; a pump mechanism for flowing the dialysate from the supply side pipeline to the discharge side pipeline; a bypass flow path that bypasses the dialyzer and connects the supply side pipeline and the discharge side pipeline; and a flow path switching mechanism, which switches the liquid delivery method between a first liquid delivery method (hereinafter referred to as the main liquid delivery method) for conveying the dialysate from the supply side pipeline to the discharge side pipeline via the dialyzer and a second liquid delivery method (hereinafter referred to as the bypass liquid delivery method) for conveying the dialysate from the dialysate line to the discharge side pipeline via the bypass flow path. In the blood purification device, in any time period other than during dialysis treatment, the bypass liquid delivery mode is switched to allow the dialysate to flow without passing through the dialyzer. During dialysis treatment, the main liquid delivery mode is switched to perform dialysis treatment. With such a structure, it is possible to avoid the dialysate from being retained in the supply side pipeline and the discharge side pipeline during the time period other than during dialysis treatment, and the dialysis treatment can be restarted immediately.

[0003] Prior art literature

[0004] Patent Literature

[0005] Patent Document 1: Japanese Patent Application Publication No. 2010-29376 Summary of the invention

[0006] Problem that the invention aims to solve

[0007] However, in the existing blood purification device, when the liquid delivery mode is switched from the bypass liquid delivery mode to the main liquid delivery mode, a sudden pressure change (so-called water hammer) occurs due to the pressure difference between the dialysate circuit and the blood circuit. Since this sudden pressure change affects the flow control of the dialysate circuit, there is a concern that an error will be generated in the amount of water removed from the patient's blood.

[0008] Therefore, an object of the present invention is to provide a blood purification device and a driving control method of a liquid delivery pump, which can reduce the adverse effects caused by pressure fluctuations when the liquid delivery mode is switched from a bypass liquid delivery mode to a main liquid delivery mode.

[0009] Technical solutions to solve problems

[0010] A blood purification device according to one embodiment of the present invention comprises:

[0011] a blood circuit that circulates the patient's blood through a blood purifier that purifies the patient's blood;

[0012] A dialysate circuit, the dialysate circuit comprising: a dialysate supply flow path, the dialysate supply flow path supplies dialysate to the above-mentioned blood purifier; a dialysate discharge flow path, the dialysate discharge flow path discharges dialysate from the above-mentioned blood purifier; and a bypass flow path, the bypass flow path connects the above-mentioned dialysate supply flow path and the above-mentioned dialysate discharge flow path, and transports liquid according to any one of a first liquid transporting method of transporting liquid from the above-mentioned dialysate supply flow path to the above-mentioned dialysate discharge flow path via the above-mentioned blood purifier, and a second liquid transporting method of transporting liquid from the above-mentioned dialysate supply flow path to the above-mentioned dialysate discharge flow path without passing through the above-mentioned blood purifier and via the above-mentioned bypass flow path;

[0013] a liquid delivery pump, which is disposed in the dialysate circuit and delivers liquid in the dialysate circuit;

[0014] a flow path switching mechanism, which is disposed in the dialysate circuit and switches the liquid delivery mode between the first liquid delivery mode and the second liquid delivery mode; and a drive control unit, which controls the liquid delivery pump and the flow path switching mechanism;

[0015] The drive control unit adjusts the drive of the liquid feeding pump so as to reduce the pressure difference when a pressure difference occurs between the blood circuit and the dialysate circuit when the flow path switching mechanism switches the liquid feeding mode from the second liquid feeding mode to the first liquid feeding mode.

[0016] In addition, a blood purification device according to one embodiment of the present invention has:

[0017] a blood circuit that circulates the patient's blood through a blood purifier that purifies the patient's blood;

[0018] A dialysate circuit, the dialysate circuit comprising: a dialysate supply flow path, the dialysate supply flow path supplies dialysate to the above-mentioned blood purifier; a dialysate discharge flow path, the dialysate discharge flow path discharges dialysate from the above-mentioned blood purifier; and a bypass flow path, the bypass flow path connects the above-mentioned dialysate supply flow path and the above-mentioned dialysate discharge flow path, and transports liquid according to any one of a first liquid transporting method of transporting liquid from the above-mentioned dialysate supply flow path to the above-mentioned dialysate discharge flow path via the above-mentioned blood purifier, and a second liquid transporting method of transporting liquid from the above-mentioned dialysate supply flow path to the above-mentioned dialysate discharge flow path without passing through the above-mentioned blood purifier and via the above-mentioned bypass flow path;

[0019] a liquid delivery pump, which is disposed in the dialysate circuit and delivers liquid in the dialysate circuit;

[0020] a flow path switching mechanism, which is disposed in the dialysate circuit and switches the liquid delivery mode between the first liquid delivery mode and the second liquid delivery mode; and

[0021] a drive control unit that controls the liquid feeding pump and the flow path switching mechanism to perform a liquid feeding mode switching operation of switching the liquid feeding mode from the second liquid feeding mode to the first liquid feeding mode;

[0022] The drive control unit has:

[0023] a receiving part, the receiving part receiving the pressure of the blood circuit and the pressure of the dialysate circuit;

[0024] an adjustment amount prediction unit that uses a prediction model that performs machine learning using the pressure of the blood circuit, the pressure of the dialysate circuit, and the error in the amount of water removed in the past switching operation of the liquid feeding mode as training data, and predicts a drive adjustment amount of the liquid feeding pump that suppresses the error in the amount of water removed based on the pressure of the blood circuit and the pressure of the dialysate circuit;

[0025] a drive adjustment unit that adjusts the driving of the liquid feeding pump according to the drive adjustment amount predicted by the adjustment amount prediction unit when the liquid feeding method is switched from the second liquid feeding method to the first liquid feeding method.

[0026] In addition, a method for controlling a liquid delivery pump according to an embodiment of the present invention includes a drive control step of controlling the drive of the liquid delivery pump of a blood purification device, wherein the blood purification device includes:

[0027] a blood circuit that circulates the patient's blood through a blood purifier that purifies the patient's blood;

[0028] a dialysate circuit, the dialysate circuit comprising a dialysate supply flow path, the dialysate supply flow path supplying dialysate to the above-mentioned blood purifier; a dialysate discharge flow path, the dialysate discharge flow path discharging dialysate from the above-mentioned blood purifier; and a bypass flow path, the bypass flow path connecting the above-mentioned dialysate supply flow path and the above-mentioned dialysate discharge flow path, and transporting liquid according to any one of a first liquid transporting method of transporting liquid from the above-mentioned dialysate supply flow path to the above-mentioned dialysate discharge flow path via the above-mentioned blood purifier, and a second liquid transporting method of transporting liquid from the above-mentioned dialysate supply flow path to the above-mentioned dialysate discharge flow path without passing through the above-mentioned blood purifier and via the above-mentioned bypass flow path;

[0029] a liquid delivery pump, which is disposed in the dialysate circuit and delivers liquid in the dialysate circuit; and

[0030] a flow path switching mechanism, which is disposed in the dialysate circuit and switches a liquid delivery mode between the first liquid delivery mode and the second liquid delivery mode;

[0031] In the drive control step, when the flow path switching mechanism switches the liquid delivery mode from the second liquid delivery mode to the first liquid delivery mode, the command value of the liquid delivery pump is adjusted so as to reduce the pressure difference when a pressure difference occurs between the blood circuit and the dialysate circuit.

[0032] In addition, a control method of a liquid feeding pump according to an embodiment of the present invention includes a liquid feeding mode switching step of a blood purification device for performing a liquid feeding mode switching action of switching a liquid feeding mode from a second liquid feeding mode to a first liquid feeding mode, wherein the blood purification device includes:

[0033] a blood circuit that circulates the patient's blood through a blood purifier that purifies the patient's blood;

[0034] a dialysate circuit, the dialysate circuit comprising a dialysate supply flow path, the dialysate supply flow path supplying dialysate to the above-mentioned blood purifier; a dialysate discharge flow path, the dialysate discharge flow path discharging dialysate from the above-mentioned blood purifier; and a bypass flow path, the bypass flow path connecting the above-mentioned dialysate supply flow path and the above-mentioned dialysate discharge flow path, and transporting liquid according to any one of a first liquid transporting method of transporting liquid from the above-mentioned dialysate supply flow path to the above-mentioned dialysate discharge flow path via the above-mentioned blood purifier, and a second liquid transporting method of transporting liquid from the above-mentioned dialysate supply flow path to the above-mentioned dialysate discharge flow path without passing through the above-mentioned blood purifier and via the above-mentioned bypass flow path;

[0035] a liquid delivery pump, which is disposed in the dialysate circuit and delivers liquid in the dialysate circuit; and

[0036] a flow path switching mechanism, which is disposed in the dialysate circuit and switches a liquid delivery mode between the first liquid delivery mode and the second liquid delivery mode;

[0037] In the liquid delivery method switching process, perform:

[0038] a receiving step, in which the pressure of the blood circuit and the pressure of the dialysate circuit are received;

[0039] an adjustment amount prediction step of predicting a driving adjustment amount of the liquid feeding pump that suppresses the error in the water removal amount based on the pressure of the blood circuit and the pressure of the dialysate circuit, using a prediction model that performs machine learning using the pressure of the blood circuit and the pressure of the dialysate circuit in the past liquid feeding mode switching operation as training data;

[0040] and a drive adjustment step of adjusting a command value of the liquid feeding pump according to the drive adjustment amount predicted by the adjustment amount prediction step when the liquid feeding method is switched from the second liquid feeding method to the first liquid feeding method.

[0041] Effects of the Invention

[0042] According to one embodiment of the present invention, it is possible to reduce adverse effects caused by pressure fluctuations when the liquid supply method is switched from the bypass liquid supply method to the main liquid supply method. BRIEF DESCRIPTION OF THE DRAWINGS

[0043] [ Figure 1 ] is a schematic structural diagram showing the structure of a blood purification device according to one embodiment of the present invention.

[0044] [ Figure 2A ] is a graph showing the error in pressure and water removal amount in the blood circuit and the dialysate circuit when the water removal error reduction action is not performed when the water delivery mode is switched from the bypass liquid delivery mode to the main liquid delivery mode.

[0045] [ Figure 2B ] is a graph showing the pressure of the blood circuit and the dialysate circuit and the pump speed of the pressure pump when the water removal error reduction action is performed when the liquid delivery mode is switched from the bypass liquid delivery mode to the main liquid delivery mode.

[0046] [ Figure 2C ] is a graph showing the error in pressure and water removal amount in the blood circuit and the dialysate circuit when the water removal error reduction action is performed when the liquid delivery mode is switched from the bypass liquid delivery mode to the main liquid delivery mode.

[0047] [ Figure 3 ] is a flow chart showing the water removal error reduction action.

[0048] [ Figure 4 ] is a flow chart showing a modified example of the water removal error reduction action.

[0049] [ Figure 5 ] is a schematic structural diagram showing the structure of the blood purification device of the second embodiment.

[0050] [ Fig. 6A ] is a graph showing the error in pressure and water removal amount in the blood circuit and the dialysate circuit when the water delivery mode is switched from the bypass liquid delivery mode to the main liquid delivery mode without performing water removal error reduction control.

[0051] [ Figure 6B ] is a graph showing the pressure of the blood circuit and the dialysate circuit and the pump speed of the pressure pump when the liquid delivery method is switched from the bypass liquid delivery method of the second embodiment to the main liquid delivery method.

[0052] [ Figure 6C ] is a graph showing the error in pressure and water removal amount of the blood circuit and the dialysate circuit when the liquid delivery method is switched from the bypass liquid delivery method of the second embodiment to the main liquid delivery method.

[0053] [ Figure 7 ] is an explanatory diagram showing the prediction model of the second embodiment.

[0054] [ Figure 8 ] is a flow chart showing the liquid delivery mode switching action of the second embodiment. DETAILED DESCRIPTION

[0055] A blood purification device according to an embodiment of the present invention is described below with reference to the accompanying drawings. The blood purification device is a medical device that uses a dialyzer to purify the patient's blood for dialysis treatment, and is a so-called hemodialysis device. In particular, the blood purification device adopts a pump control that can reduce the water removal error when switching from the bypass liquid delivery mode to the main liquid delivery mode.

[0056] (Structure of blood purification device)

[0057] like Figure 1 As shown, the blood purification device 1 has: a dialyzer 10 for purifying the blood of the patient C; an extracorporeal circulation unit 11 for circulating the blood of the patient C through the dialyzer 10; and a dialysate supply and discharge unit 12 connected to the dialyzer 10, supplying dialysate to the dialyzer 10, and discharging the dialysate from the dialyzer 10. The extracorporeal circulation unit 11 and the dialysate supply and discharge unit 12 are constructed in a separate manner, and the dialyzer 10 is detachably mounted on the extracorporeal circulation unit 11 via a fixing clamp 13.

[0058] The dialyzer 10 has a blood purification membrane (hollow fiber type hemodialysis membrane, or hemodialysis filtration membrane, flat membrane type hemodialysis membrane, or hemofiltration membrane) inside. In addition, the dialyzer 10 has a blood inlet 10a for introducing blood and a blood outlet 10b for extracting the introduced blood, and has a dialysate inlet 10c for introducing dialysate and a dialysate outlet 10d for discharging the introduced dialysate. In the dialyzer 10, blood is contacted with the dialysate by the blood purification membrane, thereby purifying the blood. In addition, in the dialyzer 10, by controlling the liquid supply flow rate to the dialyzer 10 and the liquid discharge flow rate from the dialyzer 10, the blood of the patient C can be dehydrated. The dialyzer 10 is an example of a blood purifier.

[0059] The extracorporeal circulation unit 11 includes a blood circuit 21 that circulates the blood of the patient C through the dialyzer 10 and a main control unit 22. The main control unit 22 will be described later.

[0060] The blood circuit 21 includes an arterial blood flow path 31 connected to the blood inlet port 10a of the dialyzer 10 to introduce blood collected from the blood vessel of the patient C into the dialyzer 10, and a venous blood flow path 32 connected to the blood outlet port 10b of the dialyzer 10 to return the blood discharged from the dialyzer 10 to the blood vessel of the patient C. A blood pump 34 for circulating blood is provided on the arterial blood flow path 31. In addition, a blood pressure detection unit 35 for detecting the pressure of the venous blood flow path 32 is provided on the venous blood flow path 32. The blood pressure detection unit 35 is an example of a pressure detection mechanism for detecting the pressure of the blood circuit 21, and detects the pressure of the blood circuit 21 by detecting the pressure of the venous blood flow path 32.

[0061] In the blood circuit 21, by driving the blood pump 34, the blood from the patient C is introduced into the dialyzer 10 via the arterial blood flow path 31, and after being purified by the dialyzer 10, the blood is returned to the patient C via the venous blood flow path 32. Thus, the blood of the patient C is purified.

[0062] (Structure of the dialysate supply and discharge unit)

[0063] The dialysate supply and discharge unit 12 includes a dialysate circuit 41 that supplies dialysate to the dialyzer 10 and discharges dialysate from the dialyzer 10 , and a sub-controller 42 .

[0064] The dialysate circuit 41 includes: a dialysate preparation unit 51 for refining dialysate; a dialysate supply flow path 52 connected to the dialysate inlet 10c of the dialyzer 10 and supplying the dialysate refined by the dialysate preparation unit 51 to the dialyzer 10; a dialysate discharge flow path 53 connected to the dialysate discharge port 10d of the dialyzer 10 and recovering and discharging the dialysate from the dialyzer 10; and a bypass flow path 54 connected to the dialysate supply flow path 52 and the dialysate discharge flow path 53 before and after the dialyzer 10, bypassing (bypassing) the dialyzer 10 and connecting the dialysate supply flow path 52 and the dialysate discharge flow path 53. That is, the dialysate circuit 41 is configured to transport the dialysate by either a main liquid transport method for transporting the dialysate from the dialysate supply flow path 52 to the dialysate discharge flow path 53 via the dialyzer 10, or a bypass liquid transport method for transporting the dialysate from the dialysate supply flow path 52 to the dialysate discharge flow path 53 not via the dialyzer 10 but via the bypass flow path 54. The main liquid transport method is an example of the first liquid transport method, and the bypass liquid transport method is an example of the second liquid transport method.

[0065] The dialysate preparation unit 51 prepares the dialysate from the supplied pure water and the dialyzing agent composed of the concentrated solution or the powder. The pure water supplied to the dialysate preparation unit 51 may be supplied from the pure water production unit mounted on the dialysate supply and discharge unit 12, or may be supplied from the pure water production device provided outside the dialysate supply and discharge unit 12. In addition, the dialysate preparation unit 51 may be omitted, for example, the dialysate may be supplied to the dialysate supply and discharge unit 12 from an external dialysate supply device or the like.

[0066] In the dialysate supply flow path 52, a liquid supply pump 63, a liquid supply side flow meter 64, and a first electromagnetic valve 66 are arranged in order from the upstream side. The liquid supply pump 63 is a liquid delivery pump (positive displacement diaphragm pump) that delivers the dialysate in the dialysate supply flow path 52. By driving the liquid supply pump 63, the dialysate is supplied to the dialyzer 10.

[0067] The liquid supply side flow meter 64 is disposed on the downstream side of the liquid supply pump 63 and is a flow meter for detecting the flow rate of the dialysate supply flow path 52 (that is, the flow rate of the liquid supplied to the dialyzer 10 ).

[0068] The first solenoid valve 66 is disposed on the downstream side of the connection position to the bypass flow path 54 and is one of the solenoid valves for switching the liquid supply mode (flow path) between the main liquid supply mode and the bypass liquid supply mode.

[0069] The dialysate discharge flow path 53 is provided with a second electromagnetic valve 71, a dialysate pressure detector 72, a pressure pump 73, a discharge pump 74, and a discharge flow meter 75 in order from the upstream side. The pressure pump 73 is an example of a feed pump and an auxiliary pump.

[0070] The second solenoid valve 71 is disposed on the upstream side of the connection position to which the bypass flow path 54 is connected, and is one of the solenoid valves for switching the liquid supply mode (flow path) between the main liquid supply mode and the bypass liquid supply mode.

[0071] The dialysate pressure detector 72 detects the pressure of the dialysate discharge flow path 53 . The dialysate pressure detector 72 is an example of a pressure detection mechanism for detecting the pressure of the dialysate circuit 41 , and detects the pressure of the dialysate circuit 41 by detecting the pressure of the dialysate discharge flow path 53 .

[0072] The discharge pump 74 is a liquid delivery pump (positive displacement diaphragm pump) for conveying the dialysate in the dialysate discharge flow path 53. The booster pump 73 is a cascade pump (non-positive displacement pump) for conveying the dialysate in the dialysate discharge flow path 53 and assisting the discharge pump 74 in delivering the dialysate. The dialysate from the dialyzer 10 is discharged by driving the discharge pump 74 and the booster pump 73. The flow rate of the supply liquid relative to the dialyzer 10 and the flow rate of the discharge liquid are adjusted by controlling the supply pump 63 and the discharge pump 74, thereby controlling the amount of water removed from the patient C's blood. In the present blood purification device 1, the amount of water removed is controlled, so that dialysis treatment without water removal and dialysis treatment with water removal can be performed.

[0073] The discharge-side flow meter 75 is disposed on the downstream side of the discharge pump 74 and is a flow meter for detecting the flow rate of the dialysate discharge flow path 53 (that is, the flow rate of the dialysate from the dialyzer 10 ).

[0074] One end of the bypass flow path 54 is connected between the flow meter 64 on the supply side of the dialysate supply flow path 52 and the first electromagnetic valve 66, and the other end is connected between the dialysate side pressure detection unit 72 and the pressure pump 73. Thus, the bypass flow path 54 bypasses the dialyzer 10 without passing through the dialyzer 10, and connects the dialysate supply flow path 52 and the dialysate discharge flow path 53. In addition, a third electromagnetic valve 55 is provided on the bypass flow path 54. The third electromagnetic valve 55, together with the first electromagnetic valve 66 and the second electromagnetic valve 71, is an electromagnetic valve for switching the liquid supply mode between the main liquid supply mode and the bypass liquid supply mode. That is, the first electromagnetic valve 66, the second electromagnetic valve 71 and the third electromagnetic valve 55 are an example of a flow path switching mechanism for switching the liquid supply mode between the main liquid supply mode and the bypass liquid supply mode. By opening the third electromagnetic valve 55 and closing the first electromagnetic valve 66 and the second electromagnetic valve 71, the liquid supply mode from the main liquid supply mode to the bypass liquid supply mode is switched. On the other hand, by closing the third electromagnetic valve 55 and opening the first electromagnetic valve 66 and the second electromagnetic valve 71 , the liquid supply mode is switched from the bypass liquid supply mode to the main liquid supply mode.

[0075] The sub-controller 42 communicates with the main control unit 22 of the extracorporeal circulation unit 11, and controls the liquid supply pump 63, the liquid discharge pump 74, the pressure pump 73, and the electromagnetic valves 55, 66, and 71 according to the instructions of the main control unit 22. The sub-controller 42 is implemented by appropriately combining computing elements such as a CPU, memory, software, interfaces, communication mechanisms, and the like.

[0076] (Description of the main control unit and its control)

[0077] Here, the main control unit 22 and the control performed by the main control unit 22 are described. The main control unit 22 is realized by appropriately combining a computing element such as a CPU, a memory, software, an interface, a communication mechanism, etc., receives the detection value of the blood side pressure detection unit 35, and controls the drive of the blood pump 34. In addition, the main control unit 22 communicates with the sub-control unit 42, receives the detection values ​​of each flow meter 64, 75 and the dialysate side pressure detection unit 72 through the sub-control unit 42, and controls the drive of the liquid supply pump 63, the pressure pump 73, and the discharge pump 74. In addition, the main control unit 22 communicates with the sub-control unit 42, and controls the opening and closing of each electromagnetic valve 55, 66, 71 through the sub-control unit 42. The main control unit 22 is an example of a drive control unit. In addition, in the present embodiment, the master-slave relationship between the control units 22 and 42 mounted on the extracorporeal circulation unit 11 and the dialysate supply and discharge unit 12 is configured such that the main control unit 22 mounted on the extracorporeal circulation unit 11 is the main control unit, and the sub-control unit 42 mounted on the dialysate supply and discharge unit 12 operates according to the instructions of the main control unit 22. However, the master-slave relationship between the control units 22 and 42 may also be configured such that the sub-control unit 42 mounted on the dialysate supply and discharge unit 12 is the main control unit, and the main control unit 22 mounted on the extracorporeal circulation unit 11 operates according to the instructions of the sub-control unit 42, or the control units 22 and 42 may have no master-slave relationship.

[0078] The main control unit 22 performs dialysis treatment by driving the blood pump 34, the liquid supply pump 63, the pressure pump 73 and the liquid discharge pump 74, while the liquid supply mode is switched from the bypass liquid supply mode to the main liquid supply mode by opening and closing the electromagnetic valves 55, 66 and 71. That is, during the dialysis treatment, the blood pump 34 is driven to circulate blood through the dialyzer 10, and the liquid supply pump 63 is driven to supply dialysate to the dialyzer 10, and the pressure pump 73 and the liquid discharge pump 74 are driven to discharge the dialysate from the dialyzer 10. During the dialysis treatment operation, the liquid supply pump 63, the pressure pump 73 and the liquid discharge pump 74 are controlled to adjust the flow rate of the liquid supply (supply of the dialysate) to the dialyzer 10 and the flow rate of the liquid discharge (discharge of the dialysate) from the dialyzer 10, thereby controlling the water removal amount of the patient C's blood. In the present embodiment, the pressure pump 73 is driven at a set pump speed (rotation speed), and the liquid supply pump 63 is driven to achieve a target flow rate by feedback control based on the detection value of the liquid supply side flow meter 64, and the liquid discharge pump 74 is driven to achieve a target flow rate by feedback control based on the detection value of the liquid discharge side flow meter 75. The pump speed is an example of a command value of the liquid supply pump.

[0079] In addition, in preparation before dialysis treatment and when dialysis treatment is temporarily stopped, the main control unit 22 drives the supply pump 63, the pressure pump 73, and the discharge pump 74 in a state where the liquid supply mode is switched from the main liquid supply mode to the bypass liquid supply mode by opening and closing the electromagnetic valves 55, 66, and 71, so that the dialysate flows in the dialysate circuit 41. This action is called a dialysate flow action. In the dialysate flow action, the pressure pump 73 is driven at a set pump speed, and the supply pump 63 is driven to achieve a target flow rate by feedback control based on the detection value of the supply side flow meter 64, and the discharge pump 74 is driven to achieve a target flow rate by feedback control based on the detection value of the discharge side flow meter 75.

[0080] (Description of water removal error reduction action)

[0081] However, when the dialysate flow operation is switched to the dialysis treatment operation, the dialysate delivery mode is switched from the bypass delivery mode to the main delivery mode while the pumps 63, 73, 74 of the dialysate circuit 41 are driven. At this time, due to the difference between the pressure of the blood circuit 21 and the pressure of the dialysate circuit 41, a rapid pressure change occurs in the dialysate circuit 41. This rapid pressure change affects the flow rate adjustment of the dialysate supply flow path 52 and the dialysate discharge flow path 53, such as Figure 2A As shown in FIG. 1 , an error occurs in the amount of water removed from the patient C's blood. That is, when the pressure of the blood circuit 21 is greater than the pressure of the dialysate circuit 41, when the liquid feeding mode is switched from the bypass liquid feeding mode to the main liquid feeding mode, the pressure on the blood circuit 21 side is propagated to the dialysate circuit 41 side, and an error in the amount of water removed due to over-dehydration occurs. When the pressure of the dialysate circuit 41 is greater than the pressure of the blood circuit 21, when the liquid feeding mode is switched from the bypass liquid feeding mode to the main liquid feeding mode, the pressure on the dialysate circuit 41 side is propagated to the blood circuit 21 side, and an error in the amount of water removed due to fluid replacement occurs. In contrast, when the main control unit 22 switches from the dialysate flow action to the dialysis treatment action, it performs a water removal error reduction action to reduce the water removal error caused by pressure fluctuations when the liquid feeding mode is switched from the bypass liquid feeding mode to the main liquid feeding mode. In addition, the water removal error reduction action is an example of a control method for a drive control process and a liquid feeding pump.

[0082] In the water removal error reduction operation, the main control unit 22 adjusts the pump speed of the booster pump 73 in a manner to reduce the pressure difference based on the pressure difference between the blood circuit 21 and the dialysate circuit 41. In the present embodiment, TMP (Trans Membrane Pressure) is used as the pressure difference. TMP is the pressure difference between the pressure on the dialysate side and the pressure on the blood side in the dialyzer 10. Specifically, the main control unit 22 detects the pressures of the blood circuit 21 and the dialysate circuit 41 through the blood side pressure detection unit 35 and the dialysate side pressure detection unit 72, and calculates the TMP in the dialyzer 10 based on the detected pressures of the blood circuit 21 and the dialysate circuit 41. Then, the pump speed of the booster pump 73 is adjusted to reduce the calculated TMP. For example, the calculated TMP is multiplied by a predetermined coefficient to calculate a correction value, so that the pump speed of the booster pump 73 is increased or decreased by only the amount of the correction value.

[0083] In addition, in the present embodiment, before switching to the main liquid delivery mode and after the flow path switching, the pressure of the blood circuit 21 is basically higher than the pressure of the dialysate circuit 41. Figure 2B As shown in FIG. 1 , the pump speed of the pressure pump 73 is reduced from the original setting value according to the calculated correction value. As a result, the pressure of the dialysate circuit 41 is increased and the TMP is reduced. Figure 2C As shown, the error in the amount of water removed from the blood of patient C can be reduced.

[0084] In addition, in the present embodiment, after the liquid feeding mode is switched from the bypass liquid feeding mode to the main liquid feeding mode, when a certain pressure difference is generated between the blood circuit 21 and the dialysate circuit 41, the pump speed of the above-mentioned pressurizing pump 73 is adjusted. Specifically, the pressure of the dialysate circuit 41 related to the pressure difference is monitored by the dialysate side pressure detection unit 72, and when the pressure exceeds a predetermined threshold value (200 mmHg or 26.66 kPa in the present embodiment), the pump speed of the above-mentioned pressurizing pump 73 is adjusted. That is, the pump speed of the pressurizing pump 73 is adjusted with the increase of the pressure of the dialysate circuit 41 as a trigger. In addition, instead of the increase of the pressure of the dialysate circuit 41, the pump speed of the pressurizing pump 73 may be adjusted with the increase of TMP or the increase of the difference between the pressure of the blood circuit 21 and the pressure of the dialysate circuit 41 as a trigger.

[0085] Here, refer to Figure 3 , the action sequence of the water removal error reduction action is explained. Figure 3 As shown, when the liquid supply mode is switched from the bypass liquid supply mode to the main liquid supply mode, the water removal error reduction operation is performed due to this.

[0086] like Figure 3As shown, after the flow path switching from the bypass flow path 54 to the main flow path is performed, the main control unit 22 monitors the pressure of the dialysate circuit 41 through the dialysate side pressure detection unit 72 (S1). Then, when the pressure of the dialysate circuit 41 exceeds 200 mmHg (S1: Yes), the blood side pressure detection unit 35 detects the pressure of the blood circuit 21 (S2), and the dialysate side pressure detection unit 72 detects the pressure of the dialysate circuit 41 (S3). When the pressures of the blood circuit 21 and the dialysate circuit 41 are detected, the TMP in the dialyzer 10 is calculated based on the two detected pressures (S4). Then, based on the calculated TMP, the pump speed of the pressure pump 73 is adjusted to reduce the TMP (S5). Thus, the water removal error reduction operation is terminated.

[0087] (Functions and Effects of Implementation Methods)

[0088] As described above, according to the configuration of the above embodiment, when the liquid feeding mode is switched from the bypass liquid feeding mode to the main liquid feeding mode, when a pressure difference is generated between the blood circuit 21 and the dialysate circuit 41, the pump speed of the pressure pump 73 is adjusted to reduce the pressure difference, thereby reducing the pressure difference between the blood circuit 21 and the dialysate circuit 41 when the liquid feeding mode is switched from the bypass liquid feeding mode to the main liquid feeding mode. As a result, it is possible to reduce the water removal error (water removal amount error) caused by the pressure change when the liquid feeding mode is switched from the bypass liquid feeding mode to the main liquid feeding mode.

[0089] In addition, regarding the water removal error reduction operation, since the pump speed of the pressure pump 73 among the multiple pumps 63, 73, and 74 disposed in the dialysate circuit 41 is adjusted, the water removal error can be reduced without changing the control of the supply pump 63 and the drainage pump 74, which are jointly driven to control the water removal amount of the difference between the supply and drainage. As a result, the water removal amount control of the supply pump 63 and the drainage pump 74 and the water removal error reduction control of the pressure pump 73 can be easily and concurrently performed, and by changing the control, it is possible to prevent the situation in which the cooperation between the supply pump 63 and the drainage pump 74 is imperfect and the water removal amount control is adversely affected.

[0090] (Variation Example)

[0091] The embodiments of the present invention have been described above, but the embodiments described above do not limit the inventions involved in the claims. In addition, it should be noted that not all combinations of features described in the embodiments are essential to solving the problems of the invention.

[0092] For example, in the above embodiment, for the water removal error reduction operation, the pressure difference (TMP) between the blood circuit 21 and the dialysate circuit 41 is obtained, and the pump speed of the pressure pump 73 is adjusted based on the correction value of the pressure difference. However, as long as the pump speed of the pressure pump 73 is adjusted in a manner that reduces the pressure difference, the pump speed of the pressure pump 73 may be adjusted by a predetermined correction value. For example, Figure 4 As shown in FIG. 1 , the pressure detection (S2, S3), the pressure difference calculation (S4), and the pump speed adjustment based on the pressure difference (S5) are omitted, and instead, a step (S11) of reducing the pump speed of the pressurizing pump 73 by a predetermined correction value is performed. In this case, after the pump speed adjustment (S11), it is determined whether the pressure of the dialysate circuit 41 exceeds 200 mmHg (S12). When it is determined that the pressure of the dialysate circuit 41 does not exceed 200 mmHg (S12: No), an alarm is output (S13), and the dialysis treatment operation is stopped (S14).

[0093] In the above embodiment, the pump speed of the pressure pump 73 is adjusted in the water removal error reduction operation, but the present invention is not limited to this as long as the command value of the liquid delivery pump provided in the dialysate circuit 41 is adjusted. For example, the command value of the liquid delivery pump of any one of the liquid supply pump 63 and the liquid discharge pump 74 may be adjusted instead of the pressure pump 73. In addition, the command value of a plurality of liquid delivery pumps may be adjusted instead of adjusting the command value of a single liquid delivery pump.

[0094] In the above-described embodiment, the TMP in the dialyzer 10 is used as the pressure difference between the blood circuit 21 and the dialysate circuit 41 in the water removal error reduction operation, but the present invention is not limited thereto. For example, a difference between the pressure of the blood circuit 21 and the pressure of the dialysate circuit 41 may be used. In this case, the blood-side pressure detection unit 35 may detect the pressure of the blood circuit 21, and the dialysate-side pressure detection unit 72 may detect the pressure of the dialysate circuit 41.

[0095] Furthermore, in the above-described embodiment, the pressure detection of the blood circuit 21 and the dialysate circuit 41 and the adjustment of the command value of the pressurizing pump 73 based on the pressure detection are performed after the liquid supply mode is switched from the bypass liquid supply mode to the main liquid supply mode. However, the pressure detection of the blood circuit 21 and the dialysate circuit 41 and the adjustment of the command value of the pressurizing pump 73 based on the pressure detection may be performed before the liquid supply mode is switched from the bypass liquid supply mode to the main liquid supply mode.

[0096] In addition, in the above-mentioned embodiment, the present invention is applied to the blood purification device 1 for controlling the flow rate of the liquid supply and the discharge of the dialyzer 10 using the separate liquid supply pump 63 and the discharge pump 74, but the present invention can also be applied to the blood purification device for controlling the flow rate of the liquid supply and the discharge of the dialyzer 10 using the compound pump that integrates the liquid supply pump 63 and the discharge pump 74. In this case, in the dialysate circuit 41, a liquid supply pump is provided separately from the compound pump, and in the water removal error reduction operation, when a pressure difference is generated between the blood circuit 21 and the dialysate circuit 41, the command value of the liquid supply pump is adjusted to reduce the pressure difference.

[0097] In the above-mentioned embodiment, the water removal error reduction operation is performed by adjusting the driving of the pressure pump 73 provided in the dialysate circuit 41 to adjust the pressure of the dialysate circuit 41, but it may be replaced by a configuration to adjust the pressure of the blood circuit 21. However, if the pressure of the blood circuit 21 is actively changed, a load (hemolysis, etc.) is applied to the blood, and therefore it is preferable to adjust the pressure of the dialysate circuit 41.

[0098] (Second Embodiment)

[0099] Next, refer to Figures 5 to 8 , a blood purification device 101 according to a second embodiment of the present invention is described. The blood purification device 101 is a medical device that uses a dialyzer 110 to perform dialysis treatment to purify the blood of a patient C, and is a so-called hemodialysis device. In particular, the blood purification device 101 adopts a pump control that can reduce the water removal error when switching from the bypass liquid delivery mode to the main liquid delivery mode.

[0100] (Structure of the blood purification device according to the second embodiment)

[0101] like Figure 5 As shown, the blood purification device 101 has: a dialyzer 110 for purifying the blood of the patient C; an extracorporeal circulation unit 111 for circulating the blood of the patient C via the dialyzer 110; and a dialysate supply and discharge unit 112 connected to the dialyzer 110, supplying dialysate to the dialyzer 110, and discharging the dialysate from the dialyzer 110. The extracorporeal circulation unit 111 and the dialysate supply and discharge unit 112 are composed of separate bodies, and the dialyzer 110 is detachably mounted on the extracorporeal circulation unit 111 via a fixing clamp 113.

[0102] The dialyzer 110 has a blood purification membrane (hollow fiber hemodialysis membrane, or hemodialysis filtration membrane, flat membrane hemodialysis membrane, or hemofiltration membrane) inside. In addition, the dialyzer 110 has a blood inlet 110a for introducing blood and a blood outlet 110b for extracting the introduced blood, and has a dialysate inlet 110c for introducing dialysate and a dialysate outlet 110d for discharging the introduced dialysate. In the dialyzer 110, blood is contacted with the dialysate through the blood purification membrane, thereby purifying the blood. In addition, in the dialyzer 110, by controlling the liquid supply flow rate to the dialyzer 110 and the liquid discharge flow rate from the dialyzer 110, the blood of the patient C can be dehydrated. The dialyzer 110 is an example of a blood purifier.

[0103] The extracorporeal circulation unit 111 includes a blood circuit 121 that circulates the blood of the patient C through the dialyzer 110 , a storage unit 122 , and a main control unit 123 . The storage unit 122 and the main control unit 123 will be described later.

[0104] The blood circuit 121 includes an arterial blood flow path 131 connected to the blood inlet 110a of the dialyzer 110 to introduce blood collected from the blood vessel of the patient C into the dialyzer 110, and a venous blood flow path 132 connected to the blood outlet 110b of the dialyzer 110 to return the blood discharged from the dialyzer 110 to the blood vessel of the patient C. A blood pump 134 for circulating blood is provided on the arterial blood flow path 131. In addition, a blood pressure detection unit 135 for detecting the pressure of the venous blood flow path 132 is provided on the venous blood flow path 132. The blood pressure detection unit 135 is an example of a pressure detection mechanism for detecting the pressure of the blood circuit 121, and detects the pressure of the blood circuit 121 by detecting the pressure of the venous blood flow path 132.

[0105] In the blood circuit 121, by driving the blood pump 134, the blood from the patient C is introduced into the dialyzer 110 via the arterial blood flow path 131, and after being purified by the dialyzer 110, the blood is returned to the patient C via the venous blood flow path 132. Thus, the blood of the patient C is purified.

[0106] (Structure of Dialysate Supply and Drainage Unit of Second Embodiment)

[0107] The dialysate supply and discharge unit 112 includes a dialysate circuit 141 that supplies dialysate to the dialyzer 110 and discharges dialysate from the dialyzer 110 , and a sub-controller 142 .

[0108] The dialysate circuit 141 comprises: a dialysate preparation unit 151 for refining dialysate; a dialysate supply flow path 152 connected to the dialysate inlet 110c of the dialyzer 110 and supplying the dialysate refined by the dialysate preparation unit 151 to the dialyzer 110; a dialysate discharge flow path 153 connected to the dialysate discharge port 110d of the dialyzer 110 and recovering and discharging the dialysate from the dialyzer 110; and a bypass flow path 154 connected to the dialysate supply flow path 152 and the dialysate discharge flow path 153 before and after the dialyzer 110 and bypassing (bypassing) the dialyzer 110 to connect the dialysate supply flow path 152 and the dialysate discharge flow path 153. That is, the dialysate circuit 141 is configured to transport the dialysate by any one of a main liquid transport method in which the dialysate is transported from the dialysate supply flow path 152 to the dialysate discharge flow path 153 via the dialyzer 110, and a bypass liquid transport method in which the dialysate is transported from the dialysate supply flow path 152 to the dialysate discharge flow path 153 via the bypass flow path 154 without the dialyzer 110. The main liquid transport method is an example of the first liquid transport method, and the bypass liquid transport method is an example of the second liquid transport method.

[0109] The dialysate preparation unit 151 prepares the dialysate from the supplied pure water and the dialyzing agent composed of the concentrated solution or the powder. The pure water supplied to the dialysate preparation unit 151 may be supplied from the pure water production unit mounted on the dialysate supply and discharge unit 112, or may be supplied from the pure water production device provided outside the dialysate supply and discharge unit 112. In addition, the dialysate preparation unit 151 may be omitted, for example, the dialysate may be supplied to the dialysate supply and discharge unit 112 from an external dialysate supply device or the like.

[0110] In the dialysate supply flow path 152, a liquid supply pump 163, a liquid supply side flow meter 164, and a first electromagnetic valve 166 are arranged from the upstream side. The liquid supply pump 163 is a liquid delivery pump (positive displacement diaphragm pump) that delivers the dialysate in the dialysate supply flow path 152. By driving the liquid supply pump 163, the dialysate is supplied to the dialyzer 110.

[0111] The supply-side flow meter 164 is disposed on the downstream side of the supply pump 163 and is a flow meter for detecting the flow rate of the dialysate supply flow path 152 (that is, the flow rate of the supply liquid to the dialyzer 110 ).

[0112] The first solenoid valve 166 is disposed on the downstream side of the connection position to the bypass flow path 154 and is one of the solenoid valves for switching the liquid supply mode (flow path) between the main liquid supply mode and the bypass liquid supply mode.

[0113] The dialysate discharge flow path 153 is provided with a second electromagnetic valve 171, a dialysate pressure detector 172, a pressure pump 173, a discharge pump 174, and a discharge flow meter 175 in order from the upstream side. The pressure pump 173 is an example of a feed pump and an auxiliary pump.

[0114] The second solenoid valve 171 is disposed on the upstream side of the connection position with the bypass flow path 154 and is one of the solenoid valves for switching the liquid supply mode (flow path) between the main liquid supply mode and the bypass liquid supply mode.

[0115] The dialysate pressure detector 172 detects the pressure of the dialysate discharge flow path 153 . The dialysate pressure detector 172 is an example of a pressure detection mechanism for detecting the pressure of the dialysate circuit 141 , and detects the pressure of the dialysate circuit 141 by detecting the pressure of the dialysate discharge flow path 153 .

[0116] The discharge pump 174 is a liquid delivery pump (positive displacement diaphragm pump) for conveying the dialysate in the dialysate discharge flow path 153. The booster pump 173 is a cascade pump (non-positive displacement pump) for conveying the dialysate in the dialysate discharge flow path 153 and assisting the discharge pump 174 in delivering the dialysate. The dialysate from the dialyzer 110 is discharged by driving the discharge pump 174 and the booster pump 173. The flow rate of the supply liquid relative to the dialyzer 110 and the flow rate of the discharge liquid are adjusted by controlling the supply pump 163 and the discharge pump 174, thereby controlling the amount of water removed from the patient C's blood. In the present blood purification device 101, the amount of water removed is controlled, so that dialysis treatment without water removal and dialysis treatment with water removal can be performed.

[0117] The discharge-side flow meter 175 is disposed on the downstream side of the discharge pump 174 and is a flow meter for detecting the flow rate of the dialysate discharge flow path 153 (that is, the flow rate of the dialysate from the dialyzer 110 ).

[0118] One end of the bypass flow path 154 is connected between the flow meter 164 on the supply side of the dialysate supply flow path 152 and the first electromagnetic valve 166, and the other end is connected between the dialysate side pressure detection unit 172 and the pressure pump 173. Thus, the bypass flow path 154 bypasses the dialyzer 110 without passing through the dialyzer 110, and connects the dialysate supply flow path 152 and the dialysate discharge flow path 153. In addition, the third electromagnetic valve 155 is provided in the bypass flow path 154. The third electromagnetic valve 155, together with the first electromagnetic valve 166 and the second electromagnetic valve 171, is an electromagnetic valve for switching the liquid supply mode between the main liquid supply mode and the bypass liquid supply mode. That is, the first electromagnetic valve 166, the second electromagnetic valve 171 and the third electromagnetic valve 155 are an example of a flow path switching mechanism for switching the liquid supply mode between the main liquid supply mode and the bypass liquid supply mode. The liquid supply mode is switched from the main liquid supply mode to the bypass liquid supply mode by closing the first solenoid valve 166 and the second solenoid valve 171 while opening the third solenoid valve 155. On the other hand, the liquid supply mode is switched from the bypass liquid supply mode to the main liquid supply mode by opening the first solenoid valve 166 and the second solenoid valve 171 while closing the third solenoid valve 155.

[0119] The sub-controller 142 communicates with the main control unit 123 of the extracorporeal circulation unit 111, and controls the liquid supply pump 163, the liquid discharge pump 174, the pressure pump 173, and the electromagnetic valves 155, 166, and 171 according to the instructions of the main control unit 123. The sub-controller 142 is implemented by appropriately combining computing elements such as a CPU, memory, software, interfaces, communication mechanisms, and the like.

[0120] (Description of Storage Unit and Main Control Unit)

[0121] Here, the storage unit 122 and the main control unit 123 of the extracorporeal circulation unit 111 are described. The storage unit 122 is composed of a memory such as a flash ROM, and stores various data. Figure 5 As shown, the storage unit 122 stores a switching operation database 181 .

[0122] The switching action database 181 is a database of the pressure of the blood circuit 121, the pressure of the dialysate circuit 141, the pump speed adjustment coefficient and the water removal error (hereinafter referred to as the water removal error) in the past liquid feeding mode switching action, which is about the liquid feeding mode switching action of switching the liquid feeding mode from the bypass liquid feeding mode to the main liquid feeding mode. That is, for the past liquid feeding mode switching action, the pressure of the blood circuit 121, the pressure of the dialysate circuit 141, the pump speed adjustment coefficient and the water removal error of each liquid feeding mode switching action are stored. The pump speed adjustment coefficient is an example of the drive adjustment amount of adjusting the pump speed of the booster pump 173 during the liquid feeding mode switching action, and is a numerical value representing the drive adjustment amount by a multiple relative to the original pump speed. The details will be described later. In the present blood purification device 101, there is a structure as follows: when the liquid feeding mode is switched from the bypass liquid feeding mode to the main liquid feeding mode, the water removal error is reduced by adjusting the pump speed of the booster pump 173. That is, the pump speed adjustment coefficient is a coefficient representing the increase or decrease in the adjustment of the pump speed for reducing the water removal error. In addition, these information stored in the switching operation database 181 are used for calculation (prediction) of the optimum pump speed adjustment coefficient in the liquid delivery mode switching operation.

[0123] The main control unit 123 is realized by appropriately combining a computing element such as a CPU, a memory, software, an interface, a communication mechanism, etc., receives the detection value of the blood side pressure detection unit 135, and controls the driving of the blood pump 134. In addition, the main control unit 123 communicates with the sub-control unit 142, receives the detection values ​​of each flow meter 164, 175 and the dialysate side pressure detection unit 172 through the sub-control unit 142, and controls the driving of the liquid supply pump 163, the pressure pump 173, and the liquid discharge pump 174. In addition, the main control unit 123 communicates with the sub-control unit 142, and controls the opening and closing of each electromagnetic valve 155, 166, and 171 through the sub-control unit 142. The main control unit 123 is an example of a drive control unit. In addition, in the present embodiment, the master-slave relationship between the control units 123 and 142 mounted on the extracorporeal circulation unit 111 and the dialysate supply and discharge unit 112 is configured such that the main control unit 123 mounted on the extracorporeal circulation unit 111 is the main control unit, and the sub-control unit 142 mounted on the dialysate supply and discharge unit 112 operates according to the instructions of the main control unit 123. However, the master-slave relationship between the control units 123 and 142 may also be configured such that the sub-control unit 142 mounted on the dialysate supply and discharge unit 112 is the main control unit, and the main control unit 123 mounted on the extracorporeal circulation unit 111 operates according to the instructions of the sub-control unit 142, or the control units 123 and 142 may have no master-slave relationship.

[0124] After the main control unit 123 performs the above-mentioned liquid feeding mode switching operation of switching the liquid feeding mode from the bypass liquid feeding mode to the main liquid feeding mode, in this state, the blood pump 134, the liquid supply pump 163, the pressure pump 173 and the liquid discharge pump 174 are driven to perform dialysis treatment. That is, during the dialysis treatment, the blood pump 134 is driven to circulate blood through the dialyzer 110, and the liquid supply pump 163 is driven to supply dialysate to the dialyzer 110, and the pressure pump 173 and the liquid discharge pump 174 are driven to discharge the dialysate from the dialyzer 110. During the dialysis treatment operation, the liquid supply pump 163, the pressure pump 173 and the liquid discharge pump 174 are controlled to adjust the flow rate of the liquid supply (supply of the dialysate) to the dialyzer 110 and the flow rate of the liquid discharge (discharge of the dialysate) from the dialyzer 110, thereby controlling the water removal amount of the patient C's blood. In the present embodiment, the pressure pump 173 is driven at a set pump speed (rotation speed), and the liquid supply pump 163 is driven to achieve a target flow rate by feedback control based on the detection value of the liquid supply side flow meter 164, and the liquid discharge pump 174 is driven to achieve a target flow rate by feedback control based on the detection value of the liquid discharge side flow meter 175. The pump speed is an example of a command value of the liquid supply pump.

[0125] In addition, in preparation before dialysis treatment and when dialysis treatment is temporarily stopped, the main control unit 123 drives the supply pump 163, the pressure pump 173, and the discharge pump 174 in a state where the liquid supply mode is switched from the main liquid supply mode to the bypass liquid supply mode by opening and closing the electromagnetic valves 155, 166, and 171, so that the dialysate flows in the dialysate circuit 141. This action is called a dialysate flow action. In the dialysate flow action, as in the dialysis treatment, the pressure pump 173 is driven at a set pump speed, and the supply pump 163 is driven to achieve a target flow rate by feedback control based on the detection value of the supply side flow meter 164, and the discharge pump 174 is driven to achieve a target flow rate by feedback control based on the detection value of the discharge side flow meter 175.

[0126] However, when the dialysate flow operation is switched to the dialysis treatment operation, the dialysate delivery mode is switched from the bypass delivery mode to the main delivery mode while driving the pumps 163, 173, and 174 of the dialysate circuit 141. At this time, due to the difference between the pressure of the blood circuit 121 and the pressure of the dialysate circuit 141, a rapid pressure change occurs in the dialysate circuit 141. This rapid pressure change affects the flow rate adjustment of the dialysate supply flow path 152 and the dialysate discharge flow path 153, such as Fig. 6AAs shown, an error occurs in the amount of water removed from the patient C's blood. That is, when the pressure of the blood circuit 121 is greater than the pressure of the dialysate circuit 141, when the liquid delivery mode is switched from the bypass liquid delivery mode to the main liquid delivery mode, the pressure on the blood circuit 121 side is transmitted to the dialysate circuit 141 side, resulting in a water removal error caused by over-dehydration. When the pressure of the dialysate circuit 141 is greater than the pressure of the blood circuit 121, when the liquid delivery mode is switched from the bypass liquid delivery mode to the main liquid delivery mode, the pressure on the dialysate circuit 141 side is transmitted to the blood circuit 121 side, resulting in a water removal error caused by fluid replacement. In contrast, in the present embodiment, the main control unit 123 performs control to reduce the water removal error caused by pressure changes when the liquid delivery mode is switched from the bypass liquid delivery mode to the main liquid delivery mode during the liquid delivery mode switching action. In connection with this, as Figure 5 As shown, the main control unit 123 functions as a receiving unit 191, a model generating unit 192, an adjustment amount predicting unit 193, a drive adjusting unit 194, a liquid supply method switching unit 195 and a data recording unit 196 as a structure related to the liquid supply method switching action.

[0127] The receiving unit 191 receives the detection value of the blood-side pressure detecting unit 135, receives the pressure of the blood circuit 121, and receives the detection value of the dialysate-side pressure detecting unit 172, and receives the pressure of the dialysate circuit 141. In the present embodiment, in the liquid supply mode switching operation, before switching the liquid supply mode from the bypass liquid supply mode to the main liquid supply mode, the pressure of the blood circuit 121 and the pressure of the dialysate circuit 141 are received. For example, the pressures of the blood circuit 121 and the dialysate circuit 141 are received when an instruction to start dialysis treatment is given.

[0128] The model generation unit 192 performs machine learning using the pressure of the blood circuit 121, the pressure of the dialysate circuit 141, the pump speed adjustment coefficient, and the water removal error in the past liquid delivery mode switching actions stored in the switching action database 181 as training data, generates a prediction model M of the pressure of the input blood circuit 121 and the pressure of the dialysate circuit 141, and outputs a pump speed adjustment coefficient that suppresses the water removal error (see Figure 7). As described above, the water removal error in the liquid feeding mode switching action is caused by the flow change caused by the pressure difference between the pressure of the blood circuit 121 and the pressure of the dialysate circuit 141. Therefore, there is a strong correlation between the pressure of the blood circuit 121 and the pressure of the dialysate circuit 141 during the liquid feeding mode switching action and the water removal error during the liquid feeding mode switching action. In addition, the water removal error during the liquid feeding mode switching action changes by adjusting the pump speed of the booster pump 173 when switching from the main liquid feeding mode to the bypass liquid feeding mode. Therefore, the prediction model M predicts the relationship between the water removal error and the pump speed adjustment coefficient at the input pressure of the blood circuit 121 and the pressure of the dialysate circuit 141, for example, based on the data of the past liquid feeding mode switching action (the pressure of the blood circuit 121, the pressure of the dialysate circuit 141, the pump speed adjustment coefficient, and the water removal error) extracted from the switching action database 181, and calculates the pump speed adjustment coefficient that suppresses the water removal error based on the relationship, and outputs it. For example, the prediction model M predicts that when the pressure of the blood circuit 121 is greater than the pressure of the dialysate circuit 141, it is excessive dehydration, and thus a value (less than 1) that reduces the pump speed is predicted as a pump speed adjustment coefficient for suppressing the dehydration error. When the pressure of the dialysate circuit 141 is greater than the pressure of the blood circuit 121, it is water replenishment, and thus a value (greater than 1) that increases the pump speed is predicted as a pump speed adjustment coefficient for suppressing the dehydration error. In addition, the prediction model M preferably predicts a pump speed adjustment coefficient with a dehydration error of 50 ml / h or less (preferably 0). In addition, in the present embodiment, the pressure of the blood circuit 121 and the pressure of the dialysate circuit 141 as input data and training data are configured to be the pressures of the blood circuit 121 and the dialysate circuit 141 when the start instruction of the dialysis treatment is given, but it may also be configured to be the pressures of the blood circuit 121 and the dialysate circuit 141 several seconds after the start instruction of the dialysis treatment is given. In addition, in the present embodiment, the pressure of the blood circuit 121 and the pressure of the dialysate circuit 141 as input data and training data are configured to use the detection value of the blood side pressure detection unit 135 and the detection value of the dialysate side pressure detection unit 172, but it may also be configured to use the detection value or predicted value of other detection means. In addition, it is preferred that the data of the past liquid delivery mode switching action only be the data of a certain period of time in the past (for example, 1 year) as training data for machine learning. Machine learning refers to a technology in which a computer learns a large amount of data and automatically constructs an algorithm and model that completes tasks such as classification and prediction. As a technology and algorithm that enables machine learning to function, for example, a neural network can be used.

[0129] In the present embodiment, the prediction model M is generated assuming that the pump speed before adjustment of the pressure pump 173 during the liquid feeding mode switching operation is constant. That is, the prediction model M is generated taking into account the numerical value of the constant pump speed before adjustment.

[0130] The adjustment amount prediction unit 193 uses the prediction model M generated by the model generation unit 192 to predict the pump speed adjustment coefficient for suppressing the water removal error based on the pressure of the blood circuit 121 and the pressure of the dialysate circuit 141. That is, the adjustment amount prediction unit 193 inputs the pressure of the blood circuit 121 and the pressure of the dialysate circuit 141 received by the receiving unit 191 to the prediction model M, and obtains the pump speed adjustment coefficient output from the prediction model M.

[0131] When the liquid delivery mode is switched from the bypass liquid delivery mode to the main liquid delivery mode, the drive adjustment unit 194 adjusts the drive of the pressurizing pump 173 according to the pump speed adjustment coefficient predicted by the adjustment amount prediction unit 193 when there is a certain pressure difference between the blood circuit 121 and the dialysate circuit 141. That is, the predicted pump speed adjustment coefficient is multiplied by the pump speed of the pressurizing pump 173, and the set value of the pump speed of the pressurizing pump 173 is changed to the multiplied value, so that the pump speed of the pressurizing pump 173 is increased or decreased. For example, Figure 6B As shown, when the pressure of the blood circuit 121 is greater than the pressure of the dialysate circuit 141, since water is over-dewatered, the prediction model M predicts a value (a value less than 1) that will reduce the pump speed as a pump speed adjustment coefficient that suppresses water removal errors. Based on the predicted pump speed adjustment coefficient, the set value of the pump speed of the booster pump 173 is reduced (the pressure of the dialysate circuit 141 is increased). Figure 6C As shown, it is possible to reduce the water removal error in the blood of the patient C. In addition, for example, when the pressure of the dialysate circuit 141 is greater than the pressure of the blood circuit 121, water is replenished, and therefore, the prediction model M predicts a value (greater than 1) that increases the pump speed as a pump speed adjustment coefficient that suppresses the water removal error, and the set value of the pump speed of the pressurizing pump 173 is increased (the pressure of the dialysate circuit 141 is reduced) based on the predicted pump speed adjustment coefficient.

[0132] The liquid supply mode switching unit 195 switches the liquid supply mode from the bypass liquid supply mode to the main liquid supply mode by controlling the opening and closing of each electromagnetic valve 155, 166, and 171. That is, the liquid supply mode switching unit 195 controls each electromagnetic valve 155, 166, and 171 to close the third electromagnetic valve 155 and open the first electromagnetic valve 166 and the second electromagnetic valve 171, thereby switching the liquid supply mode from the bypass liquid supply mode to the main liquid supply mode.

[0133] The data recording unit 196 records the data of the liquid supply mode switching action (pressure of the blood circuit 121, pressure of the dialysate circuit 141, pump speed adjustment coefficient, and water removal error) in the switching action database 181. That is, the detection values ​​of each flow meter 164 and 175 are received, the flow rate of the liquid supplied to the dialyzer 110 and the flow rate of the liquid discharged from the dialyzer 110 are obtained, and the water removal error is calculated based on them. Then, the pressure of the blood circuit 121 and the pressure of the dialysate circuit 141 received by the receiving unit 191, the pump speed adjustment coefficient predicted by the adjustment amount prediction unit 193, the calculated water removal error, and the implementation date of the liquid supply mode switching action are associated and recorded in the switching action database 181. In addition, the water removal error is calculated based on the cumulative flow rate from the time when the liquid supply mode is switched to the main liquid supply mode to a predetermined second later (for example, 45 seconds later), and the value of the water removal error accumulated before the predetermined second later is recorded.

[0134] (Description of the liquid delivery method switching action)

[0135] Here, refer to Figure 8 , the action sequence of the liquid delivery mode switching action is explained. The liquid delivery mode switching action is executed based on the start instruction of the dialysis treatment, and is executed from the state of the dialysate flow action. In addition, the liquid delivery mode switching action is an example of a control method for a drive control process and a liquid delivery pump.

[0136] like Figure 8 As shown, in the liquid delivery mode switching operation, first, the pressure of the blood circuit 121 and the pressure of the dialysate circuit 141 are received (S101) (receiving step). That is, the pressure of the blood circuit 121 is received by receiving the detection value of the blood side pressure detection unit 135, and the pressure of the dialysate circuit 141 is received by receiving the detection value of the dialysate side pressure detection unit 172.

[0137] When the pressures of the blood circuit 121 and the dialysate circuit 141 are received, the model generation unit 192 generates a prediction model M (S102) (model generation step). That is, the data of past liquid delivery mode switching actions (pressure of the blood circuit 121, pressure of the dialysate circuit 141, pump speed adjustment coefficient, and water removal error) are extracted from the switching action database 181, and the extracted data of past liquid delivery mode switching actions are used as training data to perform machine learning, thereby generating a prediction model M.

[0138] After the prediction model M is generated, the adjustment amount prediction unit 193 uses the prediction model M to predict the pump speed adjustment coefficient for suppressing the water removal error based on the pressures of the blood circuit 121 and the dialysate circuit 141 (S103) (adjustment amount prediction step). That is, the pressures of the blood circuit 121 and the dialysate circuit 141 received in S101 are input to the prediction model M generated by the model generation unit 192, and the pump speed adjustment coefficient output from the prediction model M is obtained as a predicted value.

[0139] When the pump speed adjustment coefficient that suppresses the water removal error is predicted, the drive adjustment unit 194 adjusts the drive of the pressure pump 173 according to the predicted pump speed adjustment coefficient (S104) (drive adjustment process). That is, the predicted pump speed adjustment coefficient is multiplied by the pump speed of the pressure pump 173, and the set value of the pump speed of the pressure pump 173 is changed to the multiplied value, so that the pump speed of the pressure pump 173 is increased or decreased. Then, the liquid delivery mode switching unit 195 controls each solenoid valve 155, 166, and 171 to switch the liquid delivery mode from the bypass liquid delivery mode to the main liquid delivery mode (S105). In addition, the adjustment amount prediction process (S103) and the drive adjustment process (S104) are performed only when there is a certain pressure difference between the blood circuit 121 and the dialysate circuit 141. That is, when there is no certain pressure difference between the blood circuit 121 and the dialysate circuit 141, it is preferable to omit the adjustment amount prediction process (S103) and the drive adjustment process (S104).

[0140] After the liquid supply mode is switched to the main liquid supply mode, a certain number of seconds (for example, 45 seconds) is waited for, and the data of the liquid supply mode switching action is recorded in the switching action database 181 (S106). That is, the water removal error is calculated based on the detection values ​​of each flow meter 164, 175, and the pressure of the blood circuit 121 and the pressure of the dialysate circuit 141 received in S101, the pump speed adjustment coefficient predicted in S103, the calculated water removal error, and the implementation date of the liquid supply mode switching action are associated and recorded in the switching action database 181. In addition, when S103 is omitted, the pump speed adjustment coefficient is set to 1. Thus, the liquid supply mode switching action is terminated. In addition, in the present embodiment, the prediction model M is generated after the liquid supply mode switching action is started, but the prediction model M may be generated in advance before the liquid supply mode switching action is started. For example, the prediction model M for the next liquid supply mode switching action may be generated at the end of the liquid supply mode switching action. In addition, a common prediction model M may be used in multiple liquid supply mode switching actions.

[0141] (Functions and Effects of Implementation Methods)

[0142] As described above, according to the configuration of the second embodiment, the pump speed adjustment coefficient for suppressing the water removal error is predicted based on the prediction model M generated from the data of the past liquid feeding mode switching operation, and when the liquid feeding mode is switched from the bypass liquid feeding mode to the main liquid feeding mode, the driving of the pressurizing pump 173 is adjusted by the pump speed adjustment coefficient, so that the water removal error caused by the pressure change when the liquid feeding mode is switched from the bypass liquid feeding mode to the main liquid feeding mode can be reduced. In addition, since the pump speed adjustment coefficient for suppressing the water removal error is predicted based on the pressure of the blood circuit 121 and the dialysate circuit 141 using the prediction model M, the optimal pump speed adjustment coefficient can be used in consideration of the piping condition or the condition of the patient C.

[0143] In addition, since the prediction model M is configured to mechanically learn only the data of the liquid delivery mode switching operation in the past certain period (e.g., the past year) with respect to the data of the liquid delivery mode switching operation in the past, it is possible to predict the pump speed adjustment coefficient taking into account the deterioration of the piping, pump, and sensor over time. Thus, the pump speed adjustment coefficient that suppresses the water removal error can be predicted with high accuracy.

[0144] Furthermore, in the switching operation of the liquid delivery mode, since the pump speed of the pressure pump 173 among the plurality of pumps 163, 173, and 174 disposed in the dialysate circuit 141 is adjusted, the water removal error can be reduced without changing the control of the liquid supply pump 163 and the liquid discharge pump 174, which are jointly driven to control the water removal amount of the difference between the supply and discharge liquids. Thus, the control related to the water removal amount control of the liquid supply pump 163 and the liquid discharge pump 174 and the water removal error reduction of the pressure pump 173 can be easily and concurrently implemented, and by changing the control, it is possible to prevent the situation in which the cooperation between the liquid supply pump 163 and the liquid discharge pump 174 is imperfect and the water removal amount control is adversely affected.

[0145] (Variation of the Second Embodiment)

[0146] The embodiments of the present invention have been described above, but the embodiments described above do not limit the inventions involved in the claims. In addition, it should be noted that not all combinations of features described in the embodiments are essential to solving the problems of the invention.

[0147] For example, in the second embodiment described above, the prediction model M outputs the pump speed adjustment coefficient, and the adjustment amount prediction unit 193 uses the prediction model M to predict the pump speed adjustment coefficient, but the present invention is not limited thereto. For example, the configuration may be to output the adjusted pump speed obtained by multiplying the original pump speed by the pump speed adjustment coefficient and predict, or to output the adjustment value subtracted from or added to the original pump speed and predict.

[0148] In addition, in the above-mentioned second embodiment, the pressure of the blood circuit 121 and the pressure of the dialysate circuit 141 are used as input data and training data. However, instead, a numerical value representing the pressure difference between the pressure of the blood circuit 121 and the pressure of the dialysate circuit 141 (for example, a subtraction value or a division value between the pressure of the blood circuit 121 and the pressure of the dialysate circuit 141) may be used as input data and training data.

[0149] In addition, in the above-mentioned second embodiment, the data of the liquid delivery mode switching action of the blood purification device 101 itself is used as the training data of the prediction model M, but it can also be a structure in which when the number of implementation times of the liquid delivery mode switching action of the blood purification device 101 itself is small, the sample data supplemented thereto is stored in the switching action database 181.

[0150] In addition, in the above-mentioned second embodiment, the data of the liquid delivery mode switching action of the blood purification device 101 itself is used as the training data of the prediction model M, but it can also be a structure in which the data of the liquid delivery mode switching action implemented by other blood purification devices 101 are used as the training data of the prediction model M. However, if the pump speed adjustment coefficient incorporating the inherent characteristics of the device is considered in the prediction, it is preferred that only the data of the liquid delivery mode switching action of the blood purification device 101 itself be used as the training data of the prediction model M.

[0151] In addition, in the above-mentioned second embodiment, the structure is that in the liquid delivery mode switching action, before the liquid delivery mode is switched to the main liquid delivery mode, the pump speed of the pressure pump 173 is adjusted based on the pump speed adjustment coefficient, but it can also be a structure that in the liquid delivery mode switching action, after the liquid delivery mode is switched to the main liquid delivery mode, the pump speed of the pressure pump 173 is adjusted based on the pump speed adjustment coefficient.

[0152] In the second embodiment, the pump speed of the pressure pump 173 is adjusted during the liquid delivery mode switching operation, but the present invention is not limited to this as long as the command value of the liquid delivery pump provided in the dialysate circuit 141 is adjusted. For example, the command value of any one of the liquid supply pump 163 and the liquid discharge pump 174 may be adjusted instead of the pressure pump 173. In addition, the command value of a plurality of liquid delivery pumps may be adjusted instead of adjusting the command value of a single liquid delivery pump.

[0153] In the second embodiment, the pressure of the dialysate circuit 141 is adjusted by adjusting the driving of the fluid delivery pump provided in the dialysate circuit 141 in order to reduce the water removal error, but the pressure of the blood circuit 121 may be adjusted by adjusting the driving of the fluid delivery pump (e.g., the blood pump 134) provided in the blood circuit 121 instead. However, if the pressure of the blood circuit 121 is actively changed, a load (hemolysis, etc.) is applied to the blood, and therefore it is preferable to adjust the pressure of the dialysate circuit 141.

[0154] In addition, in the above-mentioned second embodiment, the present invention is applied to a blood purification device 101 that controls the flow rates of the supply and discharge of liquid in the dialyzer 110 using separate supply pumps 163 and discharge pumps 174, but the present invention can also be applied to a blood purification device that controls the flow rates of the supply and discharge of liquid in the dialyzer 110 using a compound pump that integrates the supply pump 163 and the discharge pump 174.

[0155] (Summary of Implementation Methods)

[0156] Next, the technical ideas grasped from the above-described embodiments are described by referring to the reference numerals in the embodiments. However, the reference numerals in the following description are not limited to the components in the embodiments that specifically represent the constituent elements in the claims.

[0157] 《1》A blood purification device (1), the blood purification device (1) comprising:

[0158] a blood circuit (21) for circulating the patient's blood (C) through a blood purifier (10) for purifying the patient's blood (C);

[0159] A dialysate circuit (41), the dialysate circuit (41) comprising: a dialysate supply flow path (52), the dialysate supply flow path (52) supplying dialysate to the above-mentioned blood purifier (10); a dialysate discharge flow path (53), the dialysate discharge flow path (53) discharging dialysate from the above-mentioned blood purifier (10); and a bypass flow path (54), the bypass flow path (54) connecting the above-mentioned dialysate supply flow path (52) and the above-mentioned dialysate discharge flow path (53), and transporting liquid according to any one of a first liquid transporting method of transporting liquid from the above-mentioned dialysate supply flow path (52) to the above-mentioned dialysate discharge flow path (53) via the above-mentioned blood purifier (10) and a second liquid transporting method of transporting liquid from the above-mentioned dialysate supply flow path (52) to the above-mentioned dialysate discharge flow path (53) without passing through the above-mentioned blood purifier and via the above-mentioned bypass flow path;

[0160] A liquid delivery pump (73), which is disposed in the dialysate circuit (41) and delivers liquid in the dialysate circuit (41);

[0161] a flow path switching mechanism (55, 66, 76) which is disposed in the dialysate circuit (41) and switches the liquid delivery mode between the first liquid delivery mode and the second liquid delivery mode; and

[0162] A drive control unit (22), the drive control unit (22) controls the liquid delivery pump (73) and the flow path switching mechanism (55, 66, 76);

[0163] The drive control unit (22) adjusts the drive of the liquid delivery pump (73) in such a manner as to reduce the pressure difference when a pressure difference is generated between the blood circuit (21) and the dialysate circuit (41) when the flow path switching mechanism (55, 66, 76) switches the liquid delivery mode from the second liquid delivery mode to the first liquid delivery mode.

[0164] This makes it possible to reduce water removal errors caused by pressure fluctuations when switching the liquid supply method from the bypass liquid supply method to the main liquid supply method.

[0165] "2" The blood purification device (1) according to "1", wherein the blood purification device (1) comprises: a liquid supply pump (63), which is arranged on the dialysate supply flow path (52) to transport the dialysate; a liquid discharge pump (74), which is arranged on the dialysate discharge flow path (53) to transport the dialysate; and an auxiliary pump (73), which is arranged on the upper side of the dialysate discharge flow path (53). On the upstream side of the drainage pump (74), the above-mentioned liquid delivery pump is used to assist the above-mentioned drainage pump (74) in delivering liquid; when the above-mentioned flow path switching mechanism (55, 66, 76) switches the liquid delivery mode from the above-mentioned second liquid delivery mode to the above-mentioned first liquid delivery mode, the above-mentioned drive control unit (22) adjusts the drive of the above-mentioned auxiliary pump (73) in a manner to reduce the above-mentioned pressure difference when the above-mentioned pressure difference is generated between the above-mentioned blood circuit (21) and the above-mentioned dialysate circuit (41).

[0166] Thus, the water removal error can be reduced without changing the control of the liquid supply pump and the liquid discharge pump driven in combination. Thus, by changing the control, it is possible to prevent the cooperation between the liquid supply pump and the liquid discharge pump from being imperfect.

[0167] "3" The blood purification device (1) according to "1" or "2", wherein the drive control unit (22) obtains the pressure difference, and when the flow path switching mechanism (55, 66, 76) switches the liquid delivery method from the second liquid delivery method to the first liquid delivery method, the drive of the liquid delivery pump (73) is adjusted based on the pressure difference.

[0168] "4" A blood purification device (1) according to any one of "1" or "3", wherein the drive control unit (22) obtains the inter-membrane pressure difference of the blood purifier (10) as the above-mentioned pressure difference, and when the above-mentioned flow path switching mechanism (55, 66, 76) switches the liquid delivery method from the above-mentioned second liquid delivery method to the above-mentioned first liquid delivery method, the drive of the above-mentioned liquid delivery pump (73) is adjusted based on the above-mentioned inter-membrane pressure difference.

[0169] This makes it possible to achieve a reduction in water removal error with higher accuracy.

[0170] "5" A blood purification device (1) according to any one of "1" to "4", wherein the drive control unit (22) adjusts the drive of the fluid delivery pump (73) in a manner that reduces the pressure difference when the pressure of the dialysate circuit (41) exceeds a prescribed threshold value when the flow path switching mechanism (55, 66, 76) switches the fluid delivery mode from the second fluid delivery mode to the first fluid delivery mode.

[0171] Thus, the driving of the fluid delivery pump is adjusted using the pressure of the dialysate circuit related to the pressure difference as a trigger instead of the pressure difference itself, so that acquisition of the blood circuit pressure can be omitted and the water removal error reduction operation can be performed more easily.

[0172] "6" A blood purification device (1) according to any one of "1" to "5", wherein the drive control unit (22) adjusts the drive of the liquid delivery pump (73) in a manner that reduces the pressure difference before the flow path switching mechanism (55, 66, 76) switches the liquid delivery method from the second liquid delivery method to the first liquid delivery method.

[0173] This makes it possible to reduce the pressure fluctuation itself when the liquid supply mode is switched from the bypass liquid supply mode to the main liquid supply mode.

[0174] 《7》A blood purification device (101), the blood purification device (101) comprising:

[0175] a blood circuit (121) for circulating the blood of a patient (C) through a blood purifier (110) for purifying the blood;

[0176] A dialysate circuit (141), the dialysate circuit (141) comprising a dialysate supply flow path (152), the dialysate supply flow path (152) supplying dialysate to the blood purifier (110); a dialysate discharge flow path (153), the dialysate discharge flow path (153) discharging the dialysate from the blood purifier (110); and a bypass flow path (154), the bypass flow path (154) communicating with the dialysate supply flow path (152) and the dialysate discharge flow path (153) transports liquid according to any one of a first liquid transporting method of transporting liquid from the dialysate supply flow path (152) to the dialysate discharge flow path (153) via the blood purifier (110) and a second liquid transporting method of transporting liquid from the dialysate supply flow path (152) to the dialysate discharge flow path (153) not via the blood purifier (110) but via the bypass flow path (154);

[0177] A liquid delivery pump (173), which is disposed in the dialysate circuit (141) and delivers liquid in the dialysate circuit (141);

[0178] a flow path switching mechanism (155, 166, 176) which is disposed in the dialysate circuit (141) and switches the liquid delivery mode between the first liquid delivery mode and the second liquid delivery mode; and

[0179] a drive control unit (122) which controls the liquid delivery pump (173) and the flow path switching mechanism (155, 166, 176) to perform a liquid delivery mode switching operation of switching the liquid delivery mode from the second liquid delivery mode to the first liquid delivery mode;

[0180] The drive control unit (122) comprises:

[0181] A receiving portion (191), the receiving portion (191) receiving the pressure of the blood circuit (121) and the pressure of the dialysate circuit (141);

[0182] an adjustment amount prediction unit (193) which uses a prediction model that performs machine learning using the pressure of the blood circuit (121), the pressure of the dialysate circuit (141), and the error in the amount of water removed in the past switching action of the liquid delivery method as training data, and predicts a driving adjustment amount of the liquid delivery pump (173) that suppresses the error in the amount of water removed based on the pressure of the blood circuit (121) and the pressure of the dialysate circuit (141); and

[0183] A drive adjustment unit (194) adjusts the drive of the liquid delivery pump (173) according to the drive adjustment amount predicted by the adjustment amount prediction unit (193) when the liquid delivery method is switched from the second liquid delivery method to the first liquid delivery method.

[0184] This makes it possible to reduce the error in the amount of water removed due to pressure fluctuations when the liquid feeding method is switched from the bypass liquid feeding method to the main liquid feeding method.

[0185] "8" The blood purification device (101) described in "7", wherein the prediction model (M) uses the driving adjustment amount of the liquid delivery pump (173) in the past liquid delivery mode switching action as training data for machine learning in addition to the pressure of the blood circuit (121), the pressure of the dialysate circuit (141) and the error in the amount of water removed in the past liquid delivery mode switching action.

[0186] This makes it possible to predict with higher accuracy the drive adjustment amount of the liquid delivery pump that suppresses the water removal error.

[0187] "9" A blood purification device (101) according to "7" or "8", wherein the blood purification device comprises: a supply pump (163), which is arranged in the dialysate supply flow path (152) to transport the dialysate; a discharge pump (174), which is arranged in the dialysate discharge flow path (153) to transport the dialysate; and an auxiliary pump (173), which is arranged on the upstream side of the discharge pump (174) in the dialysate discharge flow path (152) and serves as the liquid delivery pump to assist the discharge pump (174) in delivering liquid. When the drive adjustment unit (194) switches the liquid delivery mode from the second liquid delivery mode to the first liquid delivery mode, it adjusts the drive of the auxiliary pump (173) according to the drive adjustment amount predicted by the adjustment amount prediction unit (193).

[0188] Thus, the water removal error can be reduced without changing the control of the liquid supply pump and the liquid discharge pump driven in combination. Thus, by changing the control, it is possible to prevent the cooperation between the liquid supply pump and the liquid discharge pump from being imperfect.

[0189] 《10》A method for controlling a liquid delivery pump (73), the method for controlling a liquid delivery pump (73) comprising a drive control step of controlling the drive of the liquid delivery pump (73) of a blood purification device (1), the blood purification device (1) comprising:

[0190] a blood circuit (21) for circulating the blood of a patient (C) through a blood purifier (10) for purifying the blood;

[0191] A dialysate circuit (41), the dialysate circuit (41) comprising: a dialysate supply flow path (52), the dialysate supply flow path (52) supplying dialysate to the above-mentioned blood purifier (10); a dialysate discharge flow path (53), the dialysate discharge flow path (53) discharging dialysate from the above-mentioned blood purifier; and a bypass flow path (54), the bypass flow path (54) connecting the above-mentioned dialysate supply flow path (52) and the above-mentioned dialysate discharge flow path (53), and transporting liquid according to any one of a first liquid transporting method of transporting liquid from the above-mentioned dialysate supply flow path (52) to the above-mentioned dialysate discharge flow path (53) via the above-mentioned blood purifier (10) and a second liquid transporting method of transporting liquid from the above-mentioned dialysate supply flow path (52) to the above-mentioned dialysate discharge flow path (53) without passing through the above-mentioned blood purifier (10) and via the above-mentioned bypass flow path (54); and

[0192] a liquid delivery pump (73) disposed in the dialysate circuit (41) and delivering liquid in the dialysate circuit (41); a flow path switching mechanism (55, 66, 76) disposed in the dialysate circuit and switching the liquid delivery mode between the first liquid delivery mode and the second liquid delivery mode;

[0193] In the drive control step, when the flow path switching mechanism (55, 66, 76) switches the liquid delivery mode from the second liquid delivery mode to the first liquid delivery mode, the command value of the liquid delivery pump (73) is adjusted in such a manner as to reduce the pressure difference when a pressure difference is generated between the blood circuit (21) and the dialysate circuit (41).

[0194] This makes it possible to reduce water removal errors caused by pressure fluctuations when switching the liquid supply method from the bypass liquid supply method to the main liquid supply method.

[0195] 《11》A method for controlling a liquid delivery pump, the method comprising a liquid delivery mode switching step of executing a liquid delivery mode switching action of switching a liquid delivery mode from a second liquid delivery mode to a first liquid delivery mode in a blood purification device (101), the blood purification device comprising:

[0196] a blood circuit (121) for circulating the blood of a patient (C) through a blood purifier (110) for purifying the blood;

[0197] A dialysate circuit (141) comprising: a dialysate supply flow path (152) for supplying dialysate to the blood purifier (11); a dialysate discharge flow path (153) for discharging dialysate from the blood purifier; and a bypass flow path (154) for connecting the dialysate supply flow path (152) and the blood purifier. The dialysate discharge flow path (153) transports liquid in accordance with any one of a first liquid transporting method of transporting liquid from the dialysate supply flow path (152) to the dialysate discharge flow path (153) via the blood purifier (110) and a second liquid transporting method of transporting liquid from the dialysate supply flow path (152) to the dialysate discharge flow path (153) via the bypass flow path (154) without transporting liquid from the dialysate supply flow path (152) to the dialysate discharge flow path (153) via the bypass flow path (154); and

[0198] a liquid delivery pump (173), which is arranged in the dialysate circuit (141) and delivers liquid in the dialysate circuit (141); a flow path switching mechanism (155, 166, 176), which is arranged in the dialysate circuit (141) and switches the liquid delivery mode between the first liquid delivery mode and the second liquid delivery mode;

[0199] In the liquid delivery method switching process, perform:

[0200] a receiving step (S101), in which the pressure of the blood circuit (121) and the pressure of the dialysate circuit (141) are received;

[0201] an adjustment amount prediction step (S103), in which a prediction model is used for machine learning using the pressure of the blood circuit (121), the pressure of the dialysate circuit (141), and the error of the water removal amount in the past switching action of the liquid delivery mode as training data, and a driving adjustment amount of the liquid delivery pump (173) that suppresses the error of the water removal amount is predicted based on the pressure of the blood circuit (121) and the pressure of the dialysate circuit (141); and

[0202] A drive adjustment step (S104), in which, when the liquid delivery method is switched from the second liquid delivery method to the first liquid delivery method, the command value of the liquid delivery pump (173) is adjusted according to the drive adjustment amount predicted by the adjustment amount prediction step (S103).

[0203] This makes it possible to reduce water removal errors caused by pressure fluctuations when switching the liquid supply method from the bypass liquid supply method to the main liquid supply method.

[0204] Explanation of symbols:

[0205] 1: blood purification device; 10: dialyzer; 21: blood circuit; 22: main control unit; 41: dialysate circuit; 52: dialysate supply flow path; 53: dialysate discharge flow path; 54: bypass flow path; 55: third solenoid valve; 63: liquid supply pump; 66: first solenoid valve; 71: second solenoid valve; 73: pressure pump; 74: liquid discharge pump; 101: blood purification device; 110: dialyzer; 121: blood circuit ; 123: main control unit; 141: dialysate circuit; 152: dialysate supply flow path; 153: dialysate discharge flow path; 154: bypass flow path; 155: third solenoid valve; 163: supply pump; 166: first solenoid valve; 171: second solenoid valve; 173: pressure pump; 174: discharge pump; 191: receiving unit; 193: adjustment amount prediction unit; 194: drive adjustment unit C: patient; M: prediction model.

Claims

1. A blood purification device, comprising: a blood circuit that circulates the patient's blood through a blood purifier that purifies the patient's blood; A dialysate circuit, the dialysate circuit comprising: a dialysate supply flow path, the dialysate supply flow path supplies dialysate to the above-mentioned blood purifier; a dialysate discharge flow path, the dialysate discharge flow path discharges dialysate from the above-mentioned blood purifier; and a bypass flow path, the bypass flow path connects the above-mentioned dialysate supply flow path and the above-mentioned dialysate discharge flow path, and transports liquid according to any one of a first liquid transporting method of transporting liquid from the above-mentioned dialysate supply flow path to the above-mentioned dialysate discharge flow path via the above-mentioned blood purifier, and a second liquid transporting method of transporting liquid from the above-mentioned dialysate supply flow path to the above-mentioned dialysate discharge flow path without passing through the above-mentioned blood purifier and via the above-mentioned bypass flow path; a liquid delivery pump, which is disposed in the dialysate circuit and delivers liquid in the dialysate circuit; a flow path switching mechanism, which is disposed in the dialysate circuit and switches the liquid delivery mode between the first liquid delivery mode and the second liquid delivery mode; and A drive control unit, the drive control unit controls the liquid delivery pump and the flow path switching mechanism; The drive control unit adjusts the drive of the liquid feeding pump so as to reduce the pressure difference when a pressure difference occurs between the blood circuit and the dialysate circuit when the flow path switching mechanism switches the liquid feeding mode from the second liquid feeding mode to the first liquid feeding mode.

2. The blood purification device according to claim 1, wherein: The blood purification device has: A liquid supply pump, which is arranged in the dialysate supply flow path and transports the dialysate; A discharge pump, which is arranged in the dialysate discharge flow path and transports the dialysate; an auxiliary pump disposed on the upstream side of the drainage pump in the dialysate discharge flow path and serving as the liquid delivery pump for assisting the drainage pump in delivering liquid; The drive control unit adjusts the drive of the auxiliary pump so as to reduce the pressure difference when the pressure difference occurs between the blood circuit and the dialysate circuit when the flow path switching mechanism switches the liquid feeding mode from the second liquid feeding mode to the first liquid feeding mode.

3. The blood purification device according to claim 1 or 2, wherein: The drive control unit obtains the inter-membrane pressure difference of the blood purifier as the pressure difference, and adjusts the drive of the liquid delivery pump based on the inter-membrane pressure difference when the flow path switching mechanism switches the liquid delivery mode from the second liquid delivery mode to the first liquid delivery mode.

4. The blood purification device according to claim 1 or 2, wherein: The drive control unit adjusts the drive of the liquid feeding pump so as to reduce the pressure difference when the pressure of the dialysate circuit exceeds a predetermined threshold value when the flow path switching mechanism switches the liquid feeding mode from the second liquid feeding mode to the first liquid feeding mode.

5. The blood purification device according to claim 1 or 2, wherein: The drive control unit adjusts the driving of the liquid feeding pump so as to reduce the pressure difference before the flow path switching mechanism switches the liquid feeding mode from the second liquid feeding mode to the first liquid feeding mode.

6. A blood purification device, comprising: a blood circuit that circulates the patient's blood through a blood purifier that purifies the patient's blood; A dialysate circuit, the dialysate circuit having a dialysate supply flow path, the dialysate supply flow path supplies dialysate to the blood purifier; a dialysate discharge flow path for discharging dialysate from the blood purifier; and a bypass flow path for connecting the dialysate supply flow path and the dialysate discharge flow path, and for conveying liquid in accordance with any one of a first liquid conveying method for conveying liquid from the dialysate supply flow path to the dialysate discharge flow path via the blood purifier and a second liquid conveying method for conveying liquid from the dialysate supply flow path to the dialysate discharge flow path without passing through the blood purifier and via the bypass flow path; a liquid delivery pump, which is disposed in the dialysate circuit and delivers liquid in the dialysate circuit; a flow path switching mechanism, which is disposed in the dialysate circuit and switches the liquid delivery mode between the first liquid delivery mode and the second liquid delivery mode; and a drive control unit that controls the liquid feeding pump and the flow path switching mechanism to perform a liquid feeding mode switching operation of switching the liquid feeding mode from the second liquid feeding mode to the first liquid feeding mode; The drive control unit has: a receiving part, the receiving part receiving the pressure of the blood circuit and the pressure of the dialysate circuit; an adjustment amount prediction unit that uses a prediction model that performs machine learning using the pressure of the blood circuit, the pressure of the dialysate circuit, and the error in the amount of water removed in the past switching operation of the liquid feeding mode as training data, and predicts a drive adjustment amount of the liquid feeding pump that suppresses the error in the amount of water removed based on the pressure of the blood circuit and the pressure of the dialysate circuit; as well as a drive adjustment unit that adjusts the driving of the liquid feeding pump according to the drive adjustment amount predicted by the adjustment amount prediction unit when the liquid feeding method is switched from the second liquid feeding method to the first liquid feeding method.

7. The blood purification device according to claim 6, wherein: The prediction model performs machine learning using the driving adjustment amount of the fluid delivery pump in the past fluid delivery mode switching action as training data in addition to the errors in the pressure of the blood circuit, the pressure of the dialysate circuit and the amount of water removed in the past fluid delivery mode switching action.

8. The blood purification device according to claim 6 or 7, wherein: The blood purification device has: A liquid supply pump, which is arranged in the dialysate supply flow path and transports the dialysate; a discharge pump, which is disposed in the dialysate discharge flow path and transports the dialysate; and an auxiliary pump disposed on the upstream side of the drainage pump in the dialysate discharge flow path and serving as the liquid delivery pump for assisting the drainage pump in delivering liquid; The drive adjustment unit adjusts the drive of the auxiliary pump according to the drive adjustment amount predicted by the adjustment amount prediction unit when switching the liquid feeding method from the second liquid feeding method to the first liquid feeding method.

9. A method for controlling a liquid delivery pump, the method comprising a driving control step of controlling the driving of the liquid delivery pump of a blood purification device, wherein the blood purification device comprises: a blood circuit that circulates the patient's blood through a blood purifier that purifies the patient's blood; A dialysate circuit, the dialysate circuit comprising: a dialysate supply flow path, the dialysate supply flow path supplies dialysate to the above-mentioned blood purifier; a dialysate discharge flow path, the dialysate discharge flow path discharges dialysate from the above-mentioned blood purifier; and a bypass flow path, the bypass flow path connects the above-mentioned dialysate supply flow path and the above-mentioned dialysate discharge flow path, and transports liquid according to any one of a first liquid transporting method of transporting liquid from the above-mentioned dialysate supply flow path to the above-mentioned dialysate discharge flow path via the above-mentioned blood purifier, and a second liquid transporting method of transporting liquid from the above-mentioned dialysate supply flow path to the above-mentioned dialysate discharge flow path without passing through the above-mentioned blood purifier and via the above-mentioned bypass flow path; a liquid delivery pump, which is disposed in the dialysate circuit and delivers liquid in the dialysate circuit; and a flow path switching mechanism, which is disposed in the dialysate circuit and switches the liquid delivery mode between the first liquid delivery mode and the second liquid delivery mode; In the drive control step, when the flow path switching mechanism switches the liquid delivery mode from the second liquid delivery mode to the first liquid delivery mode, the command value of the liquid delivery pump is adjusted so as to reduce the pressure difference when a pressure difference occurs between the blood circuit and the dialysate circuit.

10. A method for controlling a liquid feeding pump, the method comprising a liquid feeding mode switching step of a blood purification device for performing a liquid feeding mode switching action of switching a liquid feeding mode from a second liquid feeding mode to a first liquid feeding mode, the blood purification device comprising: a blood circuit that circulates the patient's blood through a blood purifier that purifies the patient's blood; A dialysate circuit, the dialysate circuit comprising: a dialysate supply flow path, the dialysate supply flow path supplies dialysate to the blood purifier; a dialysate discharge flow path for discharging dialysate from the blood purifier; and a bypass flow path for connecting the dialysate supply flow path and the dialysate discharge flow path, and for conveying liquid in accordance with any one of a first liquid conveying method for conveying liquid from the dialysate supply flow path to the dialysate discharge flow path via the blood purifier and a second liquid conveying method for conveying liquid from the dialysate supply flow path to the dialysate discharge flow path without passing through the blood purifier and via the bypass flow path; a liquid delivery pump, which is disposed in the dialysate circuit and delivers liquid in the dialysate circuit; as well as a flow path switching mechanism, which is disposed in the dialysate circuit and switches a liquid delivery mode between the first liquid delivery mode and the second liquid delivery mode; In the liquid delivery method switching process, perform: a receiving step, in which the pressure of the blood circuit and the pressure of the dialysate circuit are received; an adjustment amount prediction step of predicting a driving adjustment amount of the fluid delivery pump that suppresses the error in the water removal amount based on the pressure of the blood circuit and the pressure of the dialysate circuit, using a prediction model that performs machine learning using the pressure of the blood circuit, the pressure of the dialysate circuit, and the error in the water removal amount in the past fluid delivery mode switching operation as training data; and and a drive adjustment step of adjusting a command value of the liquid feeding pump according to the drive adjustment amount predicted by the adjustment amount prediction step when the liquid feeding method is switched from the second liquid feeding method to the first liquid feeding method.

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