Pump-scale combined calibration control method for blood purification equipment, blood purification equipment, and storage medium

Abstract

The present application is applicable to the field of blood purification, and discloses a pump-scale joint calibration control method for blood purification equipment, blood purification equipment, and storage medium. Among them, the pump-scale joint calibration control method for blood purification equipment includes: emptying the priming liquid of the intravenous bottle until the bubble detector detects that the liquid changes to a gas state; starting the liquid pump to run at a first preset pump speed until the liquid level detector detects the liquid, stopping the liquid pump, and obtaining the running time of the liquid pump; calculating the first measurement change of the priming liquid based on the first preset pump speed and the running time of the liquid pump; obtaining the second measurement change of the priming liquid based on the change in weight of the priming liquid weighed by the balance during the running time; calibrating the balance based on the second measurement change and the preset change; calibrating the pump speed of the liquid pump based on the first measurement change and the preset change. The present application can calibrate the pump speed and balance of the liquid pump to ensure the effect of blood purification treatment and avoid affecting the life safety of the patient.

Description

Technical Field

[0001] The present application relates to the field of blood purification, and in particular to a pump-scale combined calibration control method for a blood purification device, a blood purification device, and a storage medium. Background Art

[0002] Blood purification equipment is a medical device that removes a patient's blood from the body, purifies it, and then reintroduces it into the body to achieve the desired treatment. Continuous blood purification equipment removes blood from the body through extracorporeal circulation, continuously and slowly removing water and solutes to replace kidney function.

[0003] In continuous blood purification systems, replacement fluid, dialysate, or waste fluid are typically equipped with a pump to direct the flow of fluids, along with a weighing system to measure changes in the fluids. During operation, the continuous blood purification system adjusts treatment parameters, such as the pump speed, based on the weighing results of the weighing system.

[0004] If there is a problem with the accuracy of either the liquid pump or the weighing system on the continuous blood purification device, the treatment parameter settings will not match the actual situation, affecting the blood purification treatment effect and directly affecting the patient's life safety. Summary of the Invention

[0005] The purpose of the present application is to provide a pump-scale combined calibration control method for a blood purification device, a blood purification device and a storage medium, which aims to solve the technical problem of accuracy of a liquid pump or weighing system.

[0006] To achieve the above-mentioned objectives, the present application provides a pump-scale combined calibration control method for a blood purification device, wherein the blood purification device is provided with an extracorporeal circulation circuit, an external piping, a liquid pump, a liquid storage device, and a balance. The extracorporeal circulation circuit includes an arterial line, a venous pot, and a venous line connected in sequence. The venous pot is provided with a liquid level detector, and the venous line is provided with a bubble detector. The balance is used to weigh the liquid storage device. The liquid storage device is connected to the arterial line or the venous pot via the external piping. The liquid pump is provided in the external piping. The method is characterized in that the extracorporeal circulation circuit, the external piping, and the liquid storage device are filled with a priming liquid. The control method comprises:

[0007] Emptying the priming liquid from the intravenous bottle until the bubble detector detects that the liquid changes to a gaseous state;

[0008] Starting the liquid pump to run at a first preset pump speed so that the priming liquid in the liquid storage device flows to the intravenous pot and then flows from the intravenous pot to the intravenous line until the liquid level detector detects liquid, stopping the liquid pump, and obtaining the running time of the liquid pump;

[0009] Calculating a first measured change in the priming liquid according to the first preset pump speed and the operating time of the liquid pump;

[0010] obtaining a second measured change in the priming liquid according to a change in weight of the priming liquid weighed by the balance during the operation time;

[0011] calibrating the balance according to the second measured change and the preset change;

[0012] calibrating a pumping speed of the liquid pump according to the first measured variation and a preset variation;

[0013] The preset change amount is the amount of priming liquid contained between the liquid level detector of the venous pot and the bubble detector of the venous line.

[0014] In the pump-scale combined calibration control method for the blood purification device of the present application, the step of calibrating the scale according to the second measured variation and the preset variation includes:

[0015] Calculating a first difference between the second measured variation and the preset variation, and determining whether the first difference exceeds a first tolerance;

[0016] If the first difference exceeds the first tolerance, calibrating the zero point of the balance according to the first difference;

[0017] If the first difference does not exceed the first tolerance, there is no need to calibrate the balance.

[0018] In the pump-scale joint calibration control method for the blood purification equipment of the present application, the first tolerance is positively correlated with the preset change; and / or, the first tolerance is 7-14g.

[0019] In the pump-scale combined calibration control method for the blood purification device of the present application, the step of calibrating the pump speed of the liquid pump according to the first measured variation and the preset variation includes:

[0020] Calculating a second difference between the first measured variation and the preset variation, and determining whether the second difference exceeds a second tolerance;

[0021] If the second difference exceeds the second tolerance, calculating a drift factor between the actual pumping speed of the liquid pump and the first preset pumping speed, and calibrating the pumping speed of the liquid pump according to the drift factor;

[0022] If the second difference does not exceed the second tolerance, there is no need to calibrate the pump speed of the liquid pump.

[0023] In the pump-scale combined calibration control method for the blood purification equipment of the present application, the second tolerance is ±10% of the preset variation.

[0024] In the pump-scale combined calibration control method for the blood purification device of the present application, the blood purification device further includes an air pump connected to the intravenous pot, and the step of emptying the priming liquid of the intravenous pot includes:

[0025] The air pump is controlled to inject air into the intravenous bottle to empty the priming liquid in the intravenous bottle.

[0026] In the pump-scale combined calibration control method for the blood purification device of the present application, the blood purification device further includes an exhaust valve, and before the step of starting the liquid pump to operate at the first preset pump speed, the method further includes:

[0027] The exhaust valve is opened to allow the intravenous bottle to communicate with the atmosphere.

[0028] In the pump-scale joint calibration control method of the blood purification equipment of the present application, the control method further includes:

[0029] controlling the liquid pump to operate at a second preset pump speed for a first preset time;

[0030] calculating a theoretical change in the priming fluid according to the second preset pump speed and the first preset time;

[0031] Obtaining an actual change in weight of the priming liquid according to a change in weight of the priming liquid weighed by the balance within the first preset time;

[0032] calculating a third difference between the theoretical weight change and the actual weight change, and determining whether the third difference exceeds a third tolerance;

[0033] If the third difference exceeds the third tolerance, starting automatic calibration of the balance and the liquid pump;

[0034] If the third difference does not exceed the third tolerance, the automatic calibration of the balance and the liquid pump is not started.

[0035] The present application also provides a blood purification device, including a host and a display screen. The host is provided with a circuit board that can interactively communicate with the display screen. The circuit board is provided with a processor and a memory. The memory stores a computer program. When the computer program is executed by the processor, it implements the various steps of the pump-scale joint calibration control method of the blood purification device as described in any one of the above-mentioned methods.

[0036] The present application also provides a computer-readable storage medium having a computer program stored thereon. When the computer program is executed by a processor, the computer program implements the various steps of the pump-scale combined calibration control method for a blood purification device as described in any one of the above.

[0037] The pump-scale combined calibration control method, blood purification device, and storage medium provided in this application can utilize the existing structure of the blood purification device to simultaneously calibrate the pump speed and balance of the liquid pump, eliminating the need for additional structures such as a liquid reservoir to serve as an intermediate device to store pre-flushing liquid. This simplifies the structure of the blood purification device, while also simplifying operation and ensuring accurate detection. After calibrating the pump speed and balance of the liquid pump, it can be ensured that the treatment parameter settings of the blood purification device match the actual situation during subsequent treatment, thereby ensuring the effectiveness of blood purification treatment and avoiding affecting the patient's life safety. BRIEF DESCRIPTION OF THE DRAWINGS

[0038] In order to more clearly illustrate the embodiments of the present application or the technical solutions in the prior art, the following briefly introduces the drawings required for use in the embodiments or the description of the prior art. Obviously, the drawings described below are only some embodiments of the present application. For ordinary technicians in this field, other drawings can be obtained based on the structures shown in these drawings without paying any creative work.

[0039] Figure 1 This is one of the principle schematic diagrams of the blood purification device provided in the embodiment of the present application;

[0040] Figure 2 This is the second schematic diagram of the principle of the blood purification device provided in the embodiment of the present application;

[0041] Figure 3 This is the third principle diagram of the blood purification device provided in the embodiment of the present application;

[0042] Figure 4 This is one of the flow charts of the pump-scale joint calibration control method for the blood purification equipment provided in the embodiment of the present application;

[0043] Figure 5 This is the second flow chart of the pump-scale combined calibration control method for the blood purification equipment provided in the embodiment of the present application;

[0044] Figure 6 This is the third flow chart of the pump-scale combined calibration control method for the blood purification equipment provided in the embodiment of the present application;

[0045] Figure 7 This is a schematic structural diagram of a venous kettle of a blood purification device provided in an embodiment of the present application;

[0046] Figure 8 This is the fourth flow chart of the pump-scale combined calibration control method for the blood purification equipment provided in the embodiment of the present application;

[0047] Figure 9 It is a structural schematic diagram of the blood purification device provided in an embodiment of the present application.

[0048] Description of Figure Numbers:

[0049] 10: host;

[0050] 20: display screen;

[0051] 31: Extracorporeal circulation circuit;

[0052] 311: Arterial line; 3111: Filter; 3112: Arterial clamp; 3113: Blood pump; 3114: Arterial pressure detector; 3115: Prefilter pressure detector; 3116: Heparin pump;

[0053] 312: IV bottle; 3121: Liquid level detector; 3122: Venous pressure detector; 3123: Air pump; 3124: Exhaust valve;

[0054] 313: venous line; 3131: bubble detector; 3132: blood detector; 313: venous clamp;

[0055] 321: replacement fluid pump; 322: replacement fluid bag; 323: first balance; 3241: front replacement fluid tube; 3242: rear replacement fluid tube; 325: first interruption detector; 326: first heater;

[0056] 331: Filtration pump; 332: Waste liquid bag; 333: Second balance; 334: Waste liquid tube; 335: Extramembrane pressure detector; 336: Blood leakage detector;

[0057] 341: dialysate pump; 342: dialysate bag; 343: third balance; 344: dialysate tube; 345: second interruption detector; 346: second heater;

[0058] 351: priming liquid bag; 352: third interruption detector. DETAILED DESCRIPTION

[0059] The following will be combined with the drawings in the embodiments of this application to clearly and completely describe the technical solutions in the embodiments of this application. Obviously, the embodiments described are only part of the embodiments of this application, not all of the embodiments. Based on the embodiments of this application, all other embodiments obtained by ordinary technicians in this field without making creative efforts are within the scope of protection of this application.

[0060] The flowcharts shown in the accompanying drawings are for illustrative purposes only and do not necessarily include all contents and operations / steps, nor must they be executed in the order described. For example, some operations / steps may be decomposed, combined, or partially merged, so the actual execution order may vary depending on the actual situation.

[0061] In addition, the descriptions of "first", "second", etc. in this application are for descriptive purposes only and should not be understood as indicating or implying their relative importance or implicitly indicating the number of the technical features indicated. Therefore, the features defined as "first" or "second" may explicitly or implicitly include at least one of such features. In addition, the technical solutions between the various embodiments can be combined with each other, but this must be based on the fact that they can be implemented by ordinary technicians in this field. When the combination of technical solutions is contradictory or cannot be implemented, it should be deemed that such combination of technical solutions does not exist and is not within the scope of protection required by this application.

[0062] The pump-scale combined calibration control method of the blood purification equipment of the embodiment of the present application is applied to the blood purification equipment, especially the continuous blood purification equipment. Among them, the blood purification equipment is provided with an extracorporeal circulation circuit 31, an external pipe, a liquid pump, a liquid storage device and a balance. The extracorporeal circulation circuit 31 includes an arterial line 311, a venous pot 312 and a venous line 313 connected in sequence. The venous pot 312 is provided with a liquid level detector 3121, and the venous line 313 is provided with a bubble detector 3131. The balance is used to weigh the liquid storage device. The liquid storage device is connected to the arterial line 311 or the venous pot 312 through an external pipe, and the liquid pump is provided in the external pipe. The input port of the arterial line 311 is used to connect with the human artery to draw out the human body's blood, and the output port of the venous line 313 is used to connect with the human body's vein to input the treated blood into the human body.

[0063] In an embodiment of the present application, a filter 3111 is provided on the arterial line 311 for filtering and / or dialyzing the blood drawn from the patient. The blood purification device of the embodiment of the present application can implement a variety of treatment modes, such as continuous hemodialysis, continuous hemofiltration, continuous hemodiafiltration, hemoperfusion, plasma adsorption, and plasma exchange. It can be used to treat patients with acute and chronic renal and liver failure, as well as for emergency treatment of critically ill patients. The filter 3111 can be replaced with other structures, such as a plasma separator, according to treatment needs.

[0064] Exemplarily, the blood purification device further includes an arterial clamp 3112 , an arterial pressure detector 3114 , a pre-filter pressure detector 3115 , a blood pump 3113 , a heparin pump 3116 , a venous pressure detector 3122 , a blood detector 3132 , and a venous clamp 313 . An arterial clamp 3112 is provided at the input port of the arterial line 311 to control the blood flow drawn out of the human body; a blood pump 3113 is provided in the arterial line 311 and is located at the front end of the filter 3111 to guide the blood in the human body out of the body; an arterial pressure detector 3114 and a pre-filter pressure detector 3115 are respectively located at the front end and the rear end of the blood pump 3113 to detect pressure; a heparin pump 3116 is connected to the arterial line 311 and is located between the blood pump 3113 and the filter 3111 to input heparin into the blood; a venous pressure detector 3122 is connected to the venous pot 312 to detect pressure; a blood detector 3132 is provided in the venous line 313 and is located at the rear end of the bubble detector 3131 to detect the color of the liquid in the venous line 313; a venous clamp 313 is provided at the output port of the venous line 313 to control the blood flow input into the human body.

[0065] The fluid storage device in the embodiment of the present application includes a replacement fluid bag 322, the liquid pump includes a replacement fluid pump 321, and the external pipeline includes a front replacement fluid tube 3241 and / or a rear replacement fluid tube 3242. The replacement fluid bag 322 can be connected to the arterial pipeline 311 through the front replacement fluid tube 3241 and located at the front end of the filter 3111 so that the replacement fluid, for example, useful components such as plasma, can be replenished before the filter 3111, and / or the replacement fluid storage device can be connected to the intravenous pot 312 through the rear replacement fluid tube 3242 so that the replacement fluid can be replenished after the filter 3111.

[0066] Illustratively, the balance includes a first balance 323 , and is disposed below the replacement fluid bag 322 to detect changes in the liquid in the replacement fluid bag 322 by weight.

[0067] Illustratively, a first flow interruption detector 325 is provided on the external pipe connected to the replacement fluid bag 322 and is located at one end of the replacement fluid pump 321 close to the replacement fluid bag 322 to promptly detect whether the replacement fluid in the replacement fluid bag 322 is interrupted during replacement.

[0068] Illustratively, a first heater 326 is provided on the external pipe connected to the replacement fluid bag 322 and is located at the end of the replacement fluid pump 321 away from the replacement fluid bag 322 to heat the replacement fluid and ensure that its temperature is appropriate to meet the temperature conditions of human blood.

[0069] The liquid storage device in the embodiment of the present application includes a waste liquid bag 332, a liquid pump including a filtration pump 331, and an external pipeline including a waste liquid tube 334. The waste liquid bag 332 can be connected to the filter 3111 via the waste liquid tube 334 to be guided by the filtration pump 331 and receive the waste liquid filtered by the filter 3111. For example, when blood flows through the filter 3111, the filter 3111 can remove most of the water, electrolytes, and medium and large molecular substances in the body through the membrane, and then flow into the waste liquid bag 332 under the guidance of the filtration pump 331.

[0070] Exemplarily, the balance includes a second balance 333 , which is disposed below the waste liquid bag 332 to detect changes in the liquid in the waste liquid bag 332 by weight.

[0071] Exemplarily, a blood leakage detector 336 is also provided on the waste liquid pipe 334 and is located near the filter 3111 so as to timely detect whether the membrane of the filter 3111 leaks blood cells, etc., to prevent bleeding from affecting the treatment effect.

[0072] Exemplarily, an extramembrane pressure detector 335 is also provided on the waste liquid pipe 334 and is located at the end of the filtration pump 331 away from the waste liquid bag 332 to avoid back suction during the treatment process, which causes the waste liquid to enter the extracorporeal circulation pipeline and affect the treatment effect.

[0073] The liquid storage device in the embodiment of the present application includes a dialysate bag 342, the liquid pump includes a dialysate pump 341, and the external pipeline includes a dialysate tube 344. The dialysate bag 342 can be connected to the filter 3111 through the dialysate tube 344 to guide the dialysate pump 341 to diffuse the substances in the dialysate into the blood, thereby achieving the purpose of removing harmful substances in the body (mainly small and medium-molecule substances) and replenishing the required substances in the body.

[0074] Exemplarily, the scale includes a third scale 343 , and is disposed below the dialysate bag 342 to detect changes in the liquid in the dialysate bag 342 by weight.

[0075] Illustratively, a second flow interruption detector 345 is further provided on the dialysate tube 344 and is located at one end of the dialysate pump 341 close to the dialysate bag 342 so as to timely detect whether the dialysate in the dialysate bag 342 is interrupted during dialysis.

[0076] Illustratively, the dialysate tube 344 is further provided with a second heater 346 , which is located at one end of the dialysate pump 341 away from the dialysate bag 342 , so as to heat the dialysate and ensure that its temperature is appropriate to meet the temperature conditions of human blood.

[0077] In this embodiment of the present application, the blood purification device further includes a priming fluid bag 351 and a priming line. The priming fluid bag 351 is connected to the arterial line 311 near the inlet via the priming line. The priming fluid bag 351 can be used to fill the extracorporeal circulation circuit 31, the external line, and the fluid reservoir with priming fluid via the priming line. For example, the priming fluid may include saline to prevent the priming fluid from affecting subsequent treatment outcomes.

[0078] Illustratively, a third flow interruption detector 352 is further provided on the priming pipeline to timely detect whether the priming liquid in the priming liquid bag 351 is interrupted when flowing to the extracorporeal circulation circuit 31, the external pipeline and the liquid storage device.

[0079] Based on the above structure, the blood purification device of the present application can realize multiple treatment modes, such as Figure 1 As shown, in the continuous venovenous hemofiltration (CVVH) treatment cycle mode, the filter 3111 can remove most of the body's water, electrolytes, and medium and large molecular substances through the membrane, and discharge them to the waste liquid bag 332 through the waste liquid pipe 334. Then, the replacement fluid bag 322 is supplemented with a similar volume of liquid and plasma and other useful components (called replacement fluid) through the replacement pipeline, thereby achieving the effect of eliminating waste and excess water in the body.

[0080] For example Figure 2 As shown, in the continuous venovenous hemodialysis (CVVHD) treatment cycle mode, the dialysate bag 342 can remove harmful substances (mainly small and medium-molecule substances) in the body through the dialysate tube 344 and replenish the body's required substances. The waste liquid in the filter 3111 is discharged to the waste liquid bag 332 through the waste liquid tube 334.

[0081] For example Figure 3 As shown in the figure, the continuous venovenous hemodiafiltration (CVVHDF) treatment cycle mode combines the combined treatment methods of CVVH and CVVHD, which can remove small, medium and large molecular substances and water at the same time.

[0082] For another example, in the plasma exchange (PE) treatment cycle model, the filter 3111 is replaced by a plasma separator. The treatment principle is to draw the patient's whole blood out of the body and separate it into plasma and cell components through a blood separator, discard the patient's plasma, and then return the separated plasma to the body with fresh plasma, albumin solution, balanced solution and other plasma substitutes at the same speed, so as to achieve the purpose of reducing pathological damage and removing pathogenic substances.

[0083] When calibrating the balance and the liquid pump of the blood purification device of the embodiment of the present application, it is necessary to fill the extracorporeal circulation circuit 31, the external pipe and the liquid storage device with a priming liquid, such as Figures 1 to 4 As shown, the pump-scale joint calibration control method of the blood purification equipment provided in the embodiment of the present application includes:

[0084] S501, emptying the priming liquid in the intravenous pot 312 until the bubble detector 3131 detects that the liquid changes to a gas state.

[0085] It should be noted that before emptying, the extracorporeal circulation circuit 31, the external tubing, and the fluid reservoir are filled with priming fluid. Thus, when the priming fluid in the intravenous pot 312 is emptied, the priming fluid in the intravenous pot 312 and the venous tubing 313 connected thereto is gradually emptied. When the bubble detector 3131 detects that the liquid has changed to a gaseous state, this means that the intravenous pot 312 and the section of the tubing from the intravenous pot 312 to the venous pot 313, where the bubble detector 3131 is located, are empty.

[0086] like Figure 7 Specifically, an air pump 3123 is connected to the inlet of the intravenous pot 312, the venous clamp 313 of the intravenous line 313 is opened, and the air pump 3123 is controlled to inject air into the intravenous pot 312. Under the action of air pressure, the priming liquid in the intravenous pot 312 is pressed into the intravenous line 313 and discharged from the outlet of the intravenous line 313 along the intravenous line 313. As the air pressure increases, the liquid level gradually decreases until it reaches the position of the bubble detector 3131. Once the bubble detector 3131 detects air, it immediately issues a command to control the air pump 3123 to stop inflating the intravenous pot 312 and simultaneously close the venous clamp 313 to prevent the priming liquid from flowing back.

[0087] S502, start the liquid pump to run at a first preset pump speed so that the priming liquid in the liquid storage device flows to the intravenous pot 312, and flows from the intravenous pot 312 to the intravenous line 313 until the liquid level detector 3121 detects liquid, stop the liquid pump, and obtain the running time of the liquid pump.

[0088] It should be noted that the liquid pump herein can be one of the replacement fluid pump 321, the waste fluid pump, or the dialysate pump 341, and the liquid reservoir can be one of the corresponding replacement fluid bag 322, the waste fluid bag 332, or the dialysate bag 342. When the liquid pump is activated, the priming fluid filled in the liquid reservoir can be directed to flow into the extracorporeal circulation circuit 31. The priming fluid will flow along the flow direction of the extracorporeal circulation circuit 31 and into the venous line 313 to replenish the section between the venous pot 312 and the bubble detector 3131 of the venous line 313. The priming fluid will then gradually rise back up and fill the emptied venous pot 312 until the priming fluid reaches the level detector 3121. It will be understood that the priming fluid discharged from the liquid reservoir by the liquid pump represents a predetermined amount, that is, the amount of priming fluid contained between the level detector 3121 of the venous pot 312 and the bubble detector 3131 of the venous line 313.

[0089] like Figure 7As shown, in order to ensure that the pre-filled liquid in the intravenous pot 312 can be smoothly restored, before starting the liquid pump, it is necessary to open the exhaust valve 3124 connected to the inlet end of the intravenous pot 312 so that the intravenous pot 312 is connected to the atmospheric environment and balance the air pressure inside and outside the intravenous pot 312.

[0090] Exemplarily, the exhaust valve 3124 is a three-way valve. The inlet end of the intravenous pot 312 is connected to one end of the branch pipe of the venous pressure detector 3122 and connected to the inflation pump 3123 through the three-way valve structure. Turn on the inflation pump 3123 and open the three-way valve to inflate the intravenous pot 312; turn off the inflation pump 3123 and the three-way valve to detect the air pressure in the intravenous pot 312; turn off the inflation pump 3123 and open the three-way valve to connect the intravenous pot 312 to the atmospheric environment.

[0091] Specifically, in some embodiments, when calibrating the replacement fluid pump 321 and the first balance 323, the replacement fluid pump 321 is started to run at a first preset pump speed. The replacement fluid pump 321 provides infusion power, prompting the priming fluid in the replacement fluid bag 322 to be replenished into the intravenous pot 312 and the section from the intravenous pot 312 to the intravenous pot 313 provided with a bubble detector 3131 through the rear replacement pipeline or the front replacement pipeline. As the priming fluid is replenished, the liquid level gradually rises until the liquid level detectors 3121 installed on both sides of the intravenous pot 312 can re-detect the liquid level. Then, an instruction is immediately issued to control the replacement fluid pump 321 to stop infusion, and the running time of the replacement fluid pump 321 in this process is recorded.

[0092] S503: Calculate a first measured change of the priming liquid according to a first preset pumping speed and operating time of the liquid pump.

[0093] It should be noted that the first preset pump speed of the liquid pump is the pump speed displayed and adjustable on the blood purification device, which is not necessarily the actual pump speed. The first measured change here can be the calculated volume of the discharged priming liquid, or of course, the weight of the discharged priming liquid. Specifically, the preset change can be referred to.

[0094] For example, the first preset pump speed is v1, the operating time is t1, and the first measured change is the weight of the priming fluid discharged: ΔP1 = v1 × t1 × β. The volume of the priming fluid discharged can be calculated using v1 × t1, where β is the density of the priming fluid.

[0095] S504 : Obtain a second measured change in the priming liquid according to a change in weight of the priming liquid weighed by the balance during the operation period.

[0096] It should be noted that the second measured change here may be the calculated volume of the discharged priming liquid, or may be the weight change of the priming liquid directly obtained by weighing. Specifically, the preset change may be referred to.

[0097] Exemplarily, the second measured change is the change in weight of the priming liquid in the liquid storage device, which is set to ΔM1.

[0098] S505: Calibrate the balance according to the second measured variation and the preset variation.

[0099] The preset change is predictable and can be determined based on the volume between the liquid level detector 3121 of the intravenous pot 312 and the bubble detector 3131 of the intravenous line 313. It can be a volume change or a weight change, without limitation. When the preset change is the weight of the priming solution, it can be determined based on the volume between the liquid level detector 3121 of the intravenous pot 312 and the bubble detector 3131 of the intravenous line 313 and the density of the priming solution. It should be noted that the volume between the liquid level detector 3121 of the intravenous pot 312 and the bubble detector 3131 of the intravenous line 313 is not unique and constant; it can vary depending on the installation position of the liquid level detector 3121 and the bubble detector 3131. However, if the pipeline structure remains unchanged and the positions of the liquid level detector 3121 and the bubble detector 3131 remain unchanged, this volume can be considered a constant.

[0100] Exemplarily, the preset change M is the weight change, M = Q × β, where Q is the volume between the liquid level detector 3121 of the intravenous bottle 312 and the bubble detector 3131 of the intravenous line 313, and β is the density of the priming solution. Therefore, by comparing ΔM1 with M, the accuracy of the balance's weighing can be determined, thereby calibrating the balance.

[0101] like Figure 5 As shown, step S505 specifically includes:

[0102] S5051: Calculate a first difference between the second measured variation and the preset variation, and determine whether the first difference exceeds a first tolerance. For example, the first difference A=|ΔM1-M| can be calculated and then compared with the first tolerance α1.

[0103] At step S5052, if the first difference exceeds the first tolerance, the zero point of the balance is calibrated based on the first difference. Specifically, when A > α1, the balance has a large error and requires calibration. In this case, the zero point of the balance can be calibrated directly based on the first difference A, ensuring accuracy in subsequent weight checks.

[0104] S5053: If the first difference does not exceed the first tolerance, the balance does not need to be calibrated. That is, when A≤α1, it indicates that the balance error is within the allowable range and no calibration is required.

[0105] In the embodiment of the present application, the first tolerance is positively correlated with the preset variation. That is, the larger M is, the larger α1 is. Since more priming liquid is discharged, the larger the surface error is. By making the first tolerance positively correlated with the preset variation, it is possible to ensure that the judgment of the balance is accurate.

[0106] In the embodiment of the present application, the first tolerance is 7-14g. In this way, large errors in the balance can be avoided and timely calibration of the balance can be ensured.

[0107] S506: Calibrate the pump speed of the liquid pump based on the first measured change and the preset change. Similarly, the accuracy of the pump speed can be determined by comparing ΔP1 and M, thereby determining the pump speed of the liquid pump. Alternatively, the comparison can be made by comparing the volumes of the priming liquid, that is, comparing the difference between v1 × t1 and Q.

[0108] like Figure 5 As shown, step S506 specifically includes:

[0109] S5061: Calculate a second difference between the first measured variation and the preset variation, and determine whether the second difference exceeds a second tolerance. For example, the second difference B = |ΔP1-M| can be calculated and then compared with the second tolerance α2.

[0110] At step S5062, if the second difference exceeds the second tolerance, a drift factor between the actual pumping speed of the liquid pump and the first preset pumping speed is calculated, and the pumping speed of the liquid pump is calibrated based on the drift factor. Specifically, when B>α2, the pumping speed error of the liquid pump is large and requires calibration.

[0111] In this embodiment, when calibrating the pump speed of the liquid pump, the actual pump speed of the replacement liquid pump 321 is calculated according to flow rate = flow rate / time. The actual pump speed And the first preset pump speed v1 is substituted into the linear equation y=kx+b. After multiple calibration operations, a set of linear equations can be obtained through multiple sets of data, and the drift factors k and b can be calculated. The drift factors k and b are written into the program to automatically calibrate the pump speed of the liquid pump.

[0112] For example, when the blood purification device performs a continuous venovenous hemofiltration (CVVH) treatment cycle, the pump speed of the replacement fluid pump 321 should meet 10-20 ml / min. Assuming that the first preset pump speed v1 is set to 15 ml / min, the drift factor k=1 and b=2 ml / min obtained by the above steps are found to be 2 ml / min, that is, the actual pump speed is In order to obtain the target pump speed, the blood purification device should immediately issue an instruction to set the first preset pump speed v1 in the preset program to 13 ml / min, and then the actual pump speed can be 15 ml / min.

[0113] S5063: If the second difference does not exceed the second tolerance, the pump speed of the liquid pump does not need to be calibrated. That is, when B ≤ α2, it indicates that the pump speed error of the liquid pump is within the allowable range, and calibration is not required.

[0114] In the embodiment of the present application, the second tolerance is ±10% of the preset variation, so as to avoid a large error in the pumping speed of the liquid pump and ensure timely calibration of the pumping speed of the liquid pump.

[0115] The pump-scale combined calibration control method for a blood purification device according to an embodiment of the present application utilizes the existing structure of the blood purification device to simultaneously calibrate the pump speed and scale of the liquid pump, eliminating the need for an additional structure such as a liquid reservoir to serve as an intermediate device for storing priming liquid. This simplifies the structure of the blood purification device, while also simplifying operation and ensuring accurate detection. After calibrating the pump speed and scale of the liquid pump, it is possible to ensure that the treatment parameter settings of the blood purification device match the actual conditions during subsequent treatment, thereby ensuring the effectiveness of blood purification treatment and avoiding any impact on the patient's life safety.

[0116] like Figures 1 to 3 as well as Figure 8 As shown, the pump-scale joint calibration control method for the blood purification equipment of the embodiment of the present application further includes:

[0117] S100, controlling the liquid pump to operate at a second preset pump speed for a first preset time.

[0118] S200 , calculating a theoretical change in the priming fluid according to the second preset pump speed and the first preset time.

[0119] It should be noted that the second preset pump speed of the liquid pump is the pump speed displayed and adjustable on the blood purification device, and is not necessarily the actual pump speed. The theoretical change here can be the calculated volume of the priming liquid discharged or input, or of course, the weight of the priming liquid discharged or input, without limitation.

[0120] For example, the second preset pump speed is v2, the first preset time is t2, and the theoretical change is the weight of the priming fluid discharged or supplied: theoretical change ΔP2 = v2 × t2 × β. The volume of the priming fluid discharged can be calculated using v2 × t2, where β is the density of the priming fluid.

[0121] S300: Obtain an actual change in weight of the priming liquid according to a change in weight of the priming liquid weighed by a balance within a first preset time.

[0122] It should be noted that the actual weight change here may be the calculated volume of the discharged priming liquid, or may be the weight change of the priming liquid directly obtained by weighing. Specifically, the theoretical weight change may be referred to.

[0123] Exemplarily, the actual weight change is the weight change of the priming liquid in the liquid storage device, which is set to ΔM2.

[0124] S400: Calculate a third difference between the theoretical weight change and the actual weight change, and determine whether the third difference exceeds a third tolerance. For example, the third difference C = |ΔM2 - ΔP2| can be calculated and compared with the third tolerance α3.

[0125] At step S500, if the third difference exceeds the third tolerance, automatic calibration of the balance and the liquid pump is initiated. Specifically, when C > α3, this indicates a significant error between the change in the amount of priming liquid measured by the balance and the change in the amount of priming liquid delivered or supplied by the liquid pump. It is necessary to determine whether the error is in the balance or the pumping speed of the liquid pump. At this point, the aforementioned automatic calibration is executed, i.e., steps S501-S106 are executed.

[0126] At step S600, if the third difference does not exceed the third tolerance, automatic calibration of the balance and the liquid pump is not initiated. That is, when C ≤ α3, the change in the amount of priming liquid measured by the balance is substantially consistent with the change in the amount of priming liquid discharged or input by the liquid pump, and no calibration is required.

[0127] It should be noted that when the blood purification device executes steps S100-S600, this control method can be performed during the blood purification process. Of course, it can also be performed when the extracorporeal circulation circuit 31, the external pipe, and the liquid storage device are filled with priming liquid. This method is mainly used to determine whether there is an error in the pump speed of the balance or liquid pump, and can serve as a pre-process control method for automatic calibration of the balance and liquid pump.

[0128] like Figure 9 As shown, the blood purification device of an embodiment of the present application includes a host 10 and a display screen 20. The host 10 is provided with a circuit board that can realize interactive communication with the display screen 20. The circuit board is provided with a processor and a memory. The memory stores a computer program. When the computer program is executed by the processor, the various steps of the pump-scale joint calibration control method of the blood purification device are implemented. Medical staff can enter corresponding instructions on the display screen 20 so that the blood purification device can execute the various steps of the pump-scale joint calibration control method of the blood purification device according to the instructions, thereby ensuring the accuracy of the liquid pump and the scale, and thus ensuring the therapeutic effect of blood purification.

[0129] The computer-readable storage medium of the present invention stores a computer program that, when executed by a processor, implements the steps of a pump-scale combined calibration control method for a blood purification device, thereby ensuring the accuracy of the liquid pump and scale, and thereby guaranteeing the therapeutic effect of blood purification.

[0130] The processor referred to in this application may be a central processing unit (CPU), other general-purpose processors, digital signal processors (DSP), application-specific integrated circuits (ASIC), field-programmable gate arrays (FPGA), or other programmable logic devices, discrete gate or transistor logic devices, discrete hardware components, etc. A general-purpose processor may be a microprocessor or any conventional processor. The processor is the control center of the appliance, connecting all parts of the appliance using various interfaces and lines.

[0131] The memory can be used to store computer programs and / or modules. The processor implements the various functions of the appliance by running or executing the computer programs and / or modules stored in the memory, as well as accessing data stored in the memory. The memory can primarily include a program storage area and a data storage area. The program storage area can store an operating system, at least one application required for a function, and the data storage area can store data generated based on the use of the appliance. Furthermore, the memory can include high-speed random access memory and non-volatile memory, such as a hard disk, internal memory, a plug-in hard disk, a Smart Media Card (SMC), a Secure Digital (SD) card, a flash card, at least one disk storage device, a flash memory device, or other volatile solid-state storage device.

[0132] Among them, computer programs include computer program code, which may be in source code form, object code form, executable files, or some intermediate form. Computer-readable media may include: any entity or device capable of carrying computer program code, recording media, USB flash drives, removable hard drives, magnetic disks, optical disks, computer memory, read-only memory (ROM), random access memory (RAM), electric carrier signals, telecommunications signals, and software distribution media. It should be noted that the content included in computer-readable media may be appropriately increased or decreased based on the requirements of legislation and patent practice within a jurisdiction. For example, in some jurisdictions, based on legislation and patent practice, computer-readable media does not include electric carrier signals and telecommunications signals.

[0133] The above description is only a preferred embodiment of the present application and does not limit the patent scope of the present application. All equivalent structural transformations made based on the contents of the present application specification and drawings, or direct / indirect application in other related technical fields, are included in the patent protection scope of the present application.

Claims

1. A pump-scale combined calibration control method for a blood purification device, wherein the blood purification device is provided with an extracorporeal circulation circuit, an external pipe, a liquid pump, a liquid storage device, and a balance, wherein the extracorporeal circulation circuit includes an arterial line, a venous pot, and a venous line connected in sequence, the venous pot is provided with a liquid level detector, the venous line is provided with a bubble detector, the balance is used to weigh the liquid storage device, the liquid storage device is connected to the arterial line or the venous pot via the external pipe, and the liquid pump is provided in the external pipe, characterized in that: The extracorporeal circulation circuit, the external pipe, and the liquid storage device are filled with priming liquid, and the control method includes: Emptying the priming liquid from the intravenous bottle until the bubble detector detects that the liquid changes to a gaseous state; Starting the liquid pump to run at a first preset pump speed so that the priming liquid in the liquid storage device flows to the intravenous pot and then flows from the intravenous pot to the intravenous line until the liquid level detector detects liquid, stopping the liquid pump, and obtaining the running time of the liquid pump; Calculating a first measured change in the priming liquid according to the first preset pump speed and the operating time of the liquid pump; obtaining a second measured change in the priming liquid according to a change in weight of the priming liquid weighed by the balance during the operation time; calibrating the balance according to the second measured change and the preset change; calibrating a pumping speed of the liquid pump according to the first measured variation and a preset variation; The preset change amount is predictable and is determined according to the volume between the liquid level detector of the venous pot and the bubble detector of the venous line.

2. The pump-scale combined calibration control method for blood purification equipment according to claim 1, characterized in that: The step of calibrating the balance according to the second measured variation and the preset variation comprises: Calculating a first difference between the second measured variation and the preset variation, and determining whether the first difference exceeds a first tolerance; If the first difference exceeds the first tolerance, calibrating the zero point of the balance according to the first difference; If the first difference does not exceed the first tolerance, there is no need to calibrate the balance.

3. The pump-scale combined calibration control method for blood purification equipment according to claim 2, characterized in that: The first tolerance is positively correlated with the preset variation; and / or the first tolerance is 7-14g.

4. The pump-scale combined calibration control method for blood purification equipment according to claim 1, characterized in that: The step of calibrating the pump speed of the liquid pump according to the first measured variation and the preset variation includes: Calculating a second difference between the first measured variation and the preset variation, and determining whether the second difference exceeds a second tolerance; If the second difference exceeds the second tolerance, calculating a drift factor between the actual pumping speed of the liquid pump and the first preset pumping speed, and calibrating the pumping speed of the liquid pump according to the drift factor; If the second difference does not exceed the second tolerance, there is no need to calibrate the pump speed of the liquid pump.

5. The pump-scale combined calibration control method for blood purification equipment according to claim 4, characterized in that: The second tolerance is ±10% of the preset variation.

6. The pump-scale combined calibration control method for blood purification equipment according to claim 1, characterized in that: The blood purification device further includes an air pump connected to the intravenous pot. The step of emptying the priming liquid of the intravenous pot includes: The air pump is controlled to inject air into the intravenous bottle to empty the priming liquid in the intravenous bottle.

7. The pump-scale combined calibration control method for blood purification equipment according to claim 1, characterized in that: The blood purification device further includes an exhaust valve, and before the step of starting the liquid pump to operate at the first preset pump speed, further includes: The exhaust valve is opened to allow the intravenous bottle to communicate with the atmosphere.

8. The pump-scale combined calibration control method for blood purification equipment according to claim 1, characterized in that: The control method further includes: controlling the liquid pump to operate at a second preset pump speed for a first preset time; calculating a theoretical change in the priming fluid according to the second preset pump speed and the first preset time; Obtaining an actual change in weight of the priming liquid according to a change in weight of the priming liquid weighed by the balance within the first preset time; Calculating a third difference between the theoretical change and the actual weight change, and determining whether the third difference exceeds a third tolerance; If the third difference exceeds the third tolerance, starting automatic calibration of the balance and the liquid pump; If the third difference does not exceed the third tolerance, the automatic calibration of the balance and the liquid pump is not started.

9. A blood purification device, characterized in that: It includes a host and a display screen, the host is provided with a circuit board that can interact with the display screen, the circuit board is provided with a processor and a memory, the memory stores a computer program, and when the computer program is executed by the processor, it implements the various steps of the pump-scale joint calibration control method of the blood purification equipment as described in any one of claims 1 to 8.

10. A computer-readable storage medium having a computer program stored thereon, characterized in that: When the computer program is executed by a processor, each step of the pump-scale combined calibration control method for a blood purification device according to any one of claims 1 to 8 is implemented.

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