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

Abstract

The invention is suitable for the field of blood purification, and discloses a pump-scale combined calibration control method of blood purification equipment, the blood purification equipment and a storage medium. The pump and scale combined calibration control method of the blood purification equipment comprises the following steps: emptying pre-flushing liquid of a vein pot until a bubble detector detects that the liquid is changed into 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 duration of the liquid pump; according to the first preset pump speed and the operation duration of the liquid pump, the first measurement variable quantity of the pre-flushing liquid is calculated; obtaining a second measurement variable quantity of the pre-flushing liquid according to the change weight of the pre-flushing liquid weighed by the balance within the operation time length; calibrating the balance according to the second measurement variable quantity and the preset variable quantity; and the pump speed of the liquid pump is calibrated according to the first measurement variable quantity and the preset variable quantity. The pump speed and the balance of the liquid pump can be calibrated, the blood purification treatment effect is guaranteed, and the life safety of a patient is prevented from being affected.

Description

Technical Field

[0001] The present application relates to the field of blood purification, and in particular to a pump-scale joint 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 draws the patient's blood outside the body, purifies the blood outside the body, and then re-injects the purified blood into the human body to achieve the corresponding treatment. Among them, continuous blood purification equipment is a device that draws the patient's blood outside the body and continuously and slowly removes water and solutes through extracorporeal blood purification to replace the kidney function.

[0003] In continuous blood purification equipment, replacement fluid, dialysate or waste fluid is generally equipped with a liquid pump to guide the flow of the liquid, and a weighing system is also designed to weigh the changes in the liquid. When the continuous blood purification equipment is working, it will adjust the treatment parameters, such as the pumping speed of the liquid pump, according to 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 joint calibration control method for a blood purification device, a blood purification device and a storage medium, which is intended to solve the technical problem of accuracy of a liquid pump or a weighing system.

[0006] To achieve the above-mentioned purpose, the present application provides a pump-scale joint 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 comprises an arterial line, a venous pot and a venous line connected in sequence, wherein the venous pot is provided with a liquid level detector, and the venous line is provided with a bubble detector, wherein the balance is used to weigh the liquid storage device, wherein the liquid storage device is connected to the arterial line or the venous pot through the external pipe, wherein the liquid pump is provided in the external pipe, wherein the extracorporeal circulation circuit, the external pipe and the liquid storage device are filled with a priming liquid, and wherein the control method comprises:

[0007] Emptying the priming liquid in the intravenous bottle until the bubble detector detects that the liquid changes into a gas 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 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 of the priming liquid according to the first preset pump speed and the running 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 running time;

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

[0012] calibrating a pumping speed of the liquid pump according to the first measured variation and the 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 joint 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 amount; and / or the first tolerance is 7-14g.

[0019] In the pump-scale joint 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 pump speed of the liquid pump and the first preset pump speed, and calibrating the pump 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 joint 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 joint calibration control method of the blood purification device of the present application, the blood purification device further includes an air pump, the air pump is 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 joint calibration control method of 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 run at the first preset pump speed, it also 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 device 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 liquid 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 change and the actual change weight, and determining whether the third difference exceeds a third tolerance;

[0033] If the third difference exceeds the third tolerance, starting the 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, wherein 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, and 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 as described in any one of the above-mentioned methods are implemented.

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

[0037] The pump-scale joint calibration control method, blood purification equipment and storage medium provided by the present application can utilize the existing structure on the blood purification equipment to calibrate the pump speed and balance of the liquid pump at the same time, without the need to add additional structures such as a liquid reservoir as an intermediate device to store the pre-flushing liquid, thereby simplifying the structure of the blood purification equipment, while being simple to operate and accurate in 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 equipment match the actual situation during the subsequent treatment process, so as to ensure the effect of blood purification treatment and avoid 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 drawings required for use in the embodiments or the description of the prior art will be briefly introduced below. 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 schematic 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 device provided in the embodiment of the present application;

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

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

[0045] Figure 7 It is a schematic diagram of the structure 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 joint calibration control method for the blood purification device provided in the embodiment of the present application;

[0047] Fig. 9 It is a schematic diagram of the structure of the blood purification device provided in the 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: filter pre-pressure detector; 3116: heparin pump;

[0053] 312: intravenous pot; 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: membrane external 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 the present application to clearly and completely describe the technical solutions in the embodiments of the present application. Obviously, the described embodiments are only part of the embodiments of the present application, not all of the embodiments. Based on the embodiments in the present application, all other embodiments obtained by ordinary technicians in this field without creative work are within the scope of protection of this application.

[0060] The flowcharts shown in the accompanying drawings are only examples and do not necessarily include all the contents and operations / steps, nor must they be executed in the order described. For example, some operations / steps may also be decomposed, combined or partially merged, so the actual execution order may change according to actual conditions.

[0061] In addition, the descriptions of "first", "second", etc. in this application are only for descriptive purposes and cannot be understood as indicating or implying their relative importance or implicitly indicating the number of the indicated technical features. Therefore, the features defined as "first" and "second" may explicitly or implicitly include at least one of the features. In addition, the technical solutions between the various embodiments can be combined with each other, but they must be based on the ability of ordinary technicians in this field to implement them. 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 joint 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 pipeline, 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 pipeline, and the liquid pump is provided in the external pipeline. The input port of the arterial line 311 is used to connect with the artery of the human body to draw out the blood of the human body, and the output port of the venous line 313 is used to connect with the vein of the human body to input the treated blood into the human body.

[0063] In the 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 realize a variety of treatment modes, for example, 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 rescue treatment for critically ill patients. The filter 3111 can be replaced with other structures, for example, a plasma separator, according to treatment needs.

[0064] Exemplarily, the blood purification device also 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 . The arterial clamp 3112 is arranged at the input port of the arterial line 311 to control the blood flow drawn out from the human body; the blood pump 3113 is arranged at the arterial line 311 and located at the front end of the filter 3111 to guide the blood in the human body out of the body; the arterial pressure detector 3114 and the filter pre-pressure detector 3115 are respectively located at the front end and the rear end of the blood pump 3113 to detect the pressure; the heparin pump 3116 is connected to the arterial line 311 and located between the blood pump 3113 and the filter 3111, and is used to input heparin into the blood; the venous pressure detector 3122 is connected to the venous pot 312 to detect the pressure; the blood detector 3132 is arranged in the venous line 313 and located at the rear end of the bubble detector 3131, and is used to detect the color of the liquid in the venous line 313; the venous clamp 313 is arranged 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 is 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] Exemplarily, the balance includes a first balance 323 , and is disposed below the replacement fluid bag 322 to detect the change of the fluid in the replacement fluid bag 322 by weight.

[0067] Exemplarily, 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, so as to timely detect whether the replacement fluid in the replacement fluid bag 322 is interrupted during replacement.

[0068] Exemplarily, 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 so as to heat the replacement fluid to ensure that its temperature is appropriate and meets 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 includes a filtration pump 331, and an external pipeline includes a waste liquid pipe 334. The waste liquid bag 332 can be connected to the filter 3111 through the waste liquid pipe 334 to guide through 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 body's water, electrolytes, and medium and large molecular substances through the membrane, and flow into the waste liquid bag 332 under the guidance of the filtration pump 331.

[0070] Exemplarily, the balance includes a second balance 333 , and is disposed below the waste liquid bag 332 to detect changes in 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 close to the filter 3111 so as to timely detect whether the membrane of the filter 3111 leaks blood cells, etc., to prevent blood leakage 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] Exemplarily, a second flow interruption detector 345 is also 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] Exemplarily, the dialysate tube 344 is further provided with a second heater 346, and is located at one end of the dialysate pump 341 away from the dialysate bag 342, so as to heat the dialysate to ensure that its temperature is appropriate and meets the temperature conditions of human blood.

[0077] In the embodiment of the present application, the blood purification device further includes a priming liquid bag 351 and a priming pipeline, and the priming liquid bag 351 is connected to the position of the arterial pipeline 311 near the input port through the priming pipeline. The priming liquid bag 351 can fill the extracorporeal circulation circuit 31, the external pipeline and the liquid storage device with priming liquid through the priming pipeline. For example, the priming liquid includes physiological saline to prevent the priming liquid from affecting the subsequent treatment effect.

[0078] Exemplarily, 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 a variety of treatment modes, such as Figure 1 As shown, in the mode of continuous venovenous hemofiltration (CVVH) treatment cycle, 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 bag 332 through the waste pipe 334, and 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] Another 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 molecular substances) in the body through the dialysate tube 344 and replenish the required substances in the body, and the waste liquid in the filter 3111 is discharged to the waste liquid bag 332 through the waste liquid tube 334.

[0081] Another example Figure 3 As shown, the continuous venovenous hemodiafiltration (CVVHDF) treatment cycle mode combines the combined treatment methods of CVVH and CVVHD to remove small, medium and large molecular substances, as well as water.

[0082] For another example, in the plasma exchange (PE) treatment cycle mode, 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 reduce pathological damage and eliminate pathogenic substances.

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

[0084] S501, empty 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 pipe and the liquid storage device are filled with priming liquid. In this way, when the priming liquid of the venous pot 312 is emptied, the priming liquid of the venous pot 312 and the venous line 313 connected to the venous pot 312 will be gradually emptied. When the bubble detector 3131 detects that the liquid changes to a gas state, it means that the venous pot 312 and the section of the venous pot 312 to the venous line 313 where the bubble detector 3131 is provided are in an empty state.

[0086] like Figure 7 As shown, specifically, the air pump 3123 is connected to the inlet end of the venous pot 312, the venous clamp 313 of the venous line 313 is opened, and the air pump 3123 is controlled to inject air into the venous pot 312. The priming liquid in the venous pot 312 is pressed into the venous line 313 under the action of air pressure, and is discharged from the output port of the venous line 313 along the venous 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 an instruction to control the air pump 3123 to stop inflating the venous pot 312, and at the same time 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 venous pot 312, and flows from the venous pot 312 to the venous line 313 until the liquid level detector 3121 detects liquid, stops the liquid pump, and obtains the running time of the liquid pump.

[0088] It should be noted that the liquid pump here can be one of the replacement liquid pump 321, the waste liquid pump and the dialysate pump 341, and the liquid storage device is one of the corresponding replacement liquid bag 322, the waste liquid bag 332 and the dialysate bag 342. When the liquid pump is started, the priming liquid filled in the liquid storage device can be guided to flow into the extracorporeal circulation circuit 31. The priming liquid will flow along the flow direction of the extracorporeal circulation circuit 31 and will flow to the venous line 313 to replenish the section from the venous pot 312 to the venous line 313 where the bubble detector 3131 is provided. Then the priming liquid will gradually rise and fill the emptied venous pot 312 until the priming liquid reaches the position of the liquid level detector 3121. It can be understood that the priming liquid discharged from the liquid storage device guided by the liquid pump is a preset change amount, that is, the amount of priming liquid contained between the liquid 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 the air pressure inside and outside the intravenous pot 312 is balanced.

[0090] Exemplarily, the exhaust valve 3124 is a three-way valve, and the inlet end of the venous pot 312 is connected to one end of the branch pipe of the venous pressure detector 3122, and is connected to the inflation pump 3123 through the three-way valve structure. The inflation pump 3123 is turned on and the three-way valve is opened to inflate the venous pot 312; the air pressure in the venous pot 312 can be detected by turning off the inflation pump 3123 and the three-way valve; the venous pot 312 can be connected to the atmospheric environment by turning off the inflation pump 3123 and opening the three-way valve.

[0091] Specifically, in some embodiments, when calibrating the replacement fluid pump 321 and the first level 323, the replacement fluid pump 321 is started to run at a first preset pump speed, and the replacement fluid pump 321 provides infusion power, prompting the priming fluid in the replacement fluid bag 322 to be replenished into the venous pot 312 and a section of the venous pot 312 to the venous 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 venous pot 312 can re-detect the liquid level, and 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 pump speed and running time of the liquid pump.

[0093] It should be noted that the first preset pump speed of the liquid pump at this time 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, of course, it can also be the weight of the discharged priming liquid, specifically, it can refer to the preset change.

[0094] Exemplarily, the first preset pump speed is v1, the running time is t1, the first measured change is the weight of the discharged priming liquid, and the first measured change ΔP1=v1×t1×β. The volume of the discharged priming liquid can be calculated by v1×t1, where β is the density of the priming liquid.

[0095] S504, obtaining a second measured change amount of 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 volume of the discharged priming liquid obtained by calculation, or may be the change in weight of the priming liquid obtained directly 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, calibrating the balance according to the second measured variation and the preset variation.

[0099] Among them, the preset change amount is predictable, and 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. It can be a volume change amount or a weight change amount, without limitation. When the preset change amount is the weight of the priming liquid, it can be obtained 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 liquid. 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 the only constant, and the volume can change according to the installation position of the liquid level detector 3121 and the bubble detector 3131, but for the case where the pipeline structure remains unchanged and the positions of the liquid level detector 3121 and the bubble detector 3131 remain unchanged, the volume can be regarded as a constant.

[0100] Exemplarily, the preset change amount M is the weight change amount, M=Q×β, where Q is the volume between the liquid level detector 3121 of the intravenous pot 312 and the bubble detector 3131 of the intravenous line 313, and β is the density of the pre-filled liquid. Therefore, the accuracy of the weighing of the balance can be determined by comparing the aforementioned ΔM1 and M, so as to calibrate 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] S5052, if the first difference exceeds the first tolerance, the zero point of the balance is calibrated according to the first difference. That is, when A>α1, it indicates that the error of the balance is large and needs to be calibrated. At this time, the zero point of the balance can be calibrated directly according to the first difference A, so that the balance is accurate in subsequent weight detection.

[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 avoid ensuring 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, a large error of the balance can be avoided and timely calibration of the balance can be ensured.

[0107] S506, calibrate the pumping speed of the liquid pump according to the first measured change and the preset change. Similarly, the pumping speed of the liquid pump can be determined to be accurate by comparing the aforementioned ΔP1 and M, so as to determine the pumping speed of the liquid pump. Of course, the comparison can also be made by comparing the volume 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 the second difference between the first measured variation and the preset variation, and determine whether the second difference exceeds the second tolerance. For example, the second difference B=|ΔP1-M| can be calculated and then compared with the second tolerance α2.

[0110] S5062, if the second difference exceeds the second tolerance, the drift factor between the actual pump speed of the liquid pump and the first preset pump speed is calculated, and the pump speed of the liquid pump is calibrated according to the drift factor. That is, when B>α2, it indicates that the pump speed error of the liquid pump is large and needs to be calibrated.

[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 linear equation group can be obtained through multiple groups 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 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 15 ml / min can be obtained.

[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 no calibration is required.

[0114] In the embodiment of the present application, the second tolerance is ±10% of the preset variation. In this way, a large error in the pumping speed of the liquid pump can be avoided, and the pumping speed of the liquid pump can be calibrated in time.

[0115] The pump-scale joint calibration control method of the blood purification device of the embodiment of the present application can utilize the existing structure on the blood purification device to calibrate the pump speed and balance of the liquid pump at the same time, without the need to add additional structures such as a liquid reservoir as an intermediate device to store the priming liquid, thereby simplifying the structure of the blood purification device, while being simple to operate and accurate in 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 the subsequent treatment process, so as to ensure the effect of the blood purification treatment and avoid affecting 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 device of the embodiment of the present application further includes:

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

[0118] S200, calculating a theoretical change in the priming liquid 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 at this time is the pump speed displayed and adjustable on the blood purification device, which is not necessarily the actual pump speed. The theoretical change here can be the calculated volume of the priming liquid discharged or input, of course, it can also be the weight of the priming liquid discharged or input, without limitation.

[0120] Exemplarily, the second preset pump speed is v2, the first preset time is t2, the theoretical change is the weight of the priming liquid discharged or input, and the theoretical change ΔP2=v2×t2×β. The volume of the priming liquid discharged can be calculated by v2×t2, where β is the density of the priming liquid.

[0121] S300, obtaining 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 change in weight here may be the volume of the discharged priming liquid obtained by calculation, and of course, may also be the change in weight of the priming liquid obtained directly by weighing. Specifically, the theoretical 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, calculating a third difference between the theoretical change and the actual change weight, and determining whether the third difference exceeds a third tolerance. For example, the third difference C=|ΔM2-ΔP2| can be calculated and then compared with the third tolerance α3.

[0125] S500, if the third difference exceeds the third tolerance, the automatic calibration of the balance and the liquid pump is started. That is, when C>α3, it indicates that the error between the change in the amount of priming liquid weighed by the balance and the change in the amount of priming liquid discharged or input by the liquid pump is large, and it is necessary to determine which of the balance or the pump speed of the liquid pump has an error. At this time, the aforementioned automatic calibration can be performed, that is, the aforementioned steps S501-S106 are performed.

[0126] S600, if the third difference does not exceed the third tolerance, the automatic calibration of the balance and the liquid pump is not started. That is, when C≤α3, it indicates that the change in the priming liquid weighed by the balance is basically consistent with the change in the 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, it can be a control method performed by the blood purification device during the blood purification process, and of course, it can also be a control method performed when the extracorporeal circulation circuit 31, the external pipe and the liquid storage device are filled with priming liquid. It is mainly used to determine whether there is an error in the pump speed of the balance or the liquid pump, and can be a pre-control method for automatic calibration of the balance and the liquid pump.

[0128] like Fig. 9 As shown, the blood purification device of the embodiment of the present application includes a host 10 and a display screen 20. A circuit board that can realize interactive communication with the display screen 20 is provided in the host 10. A processor and a memory are provided on the circuit board. The memory stores a computer program. When the computer program is executed by the processor, each step of the pump-scale joint calibration control method of the blood purification device is implemented. Medical staff can input corresponding instructions on the display screen 20 so that the blood purification device can execute each step of the pump-scale joint calibration control method of the blood purification device according to the instructions, so as to ensure the accuracy of the liquid pump and the balance, and then ensure the therapeutic effect of blood purification.

[0129] The computer-readable storage medium of the embodiment of the present application stores a computer program, which, when executed by a processor, implements the various steps of the pump-scale joint calibration control method of the blood purification device to ensure the accuracy of the liquid pump and the scale, thereby ensuring the therapeutic effect of blood purification.

[0130] The processor referred to in this application may be a central processing unit (CPU), or 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, etc. The processor is the control center of the electrical appliance, and uses various interfaces and lines to connect the various parts of the entire electrical appliance.

[0131] The memory can be used to store computer programs and / or modules. The processor realizes various functions of the appliance by running or executing the computer programs and / or modules stored in the memory, and calling the data stored in the memory. The memory can mainly include a program storage area and a data storage area, wherein the program storage area can store an operating system, at least one application required for a function, etc.; the data storage area can store data created according to the use of the appliance, etc. In addition, the memory can include a high-speed random access memory, and can also include a non-volatile memory, such as a hard disk, a memory, a plug-in hard disk, a smart memory card (Smart Media Card, SMC), a secure digital (Secure Digital, SD) card, a flash card (Flash Card), at least one disk storage device, a flash memory device, or other volatile solid-state storage devices.

[0132] Among them, the computer program includes computer program code, which can be in source code form, object code form, executable file or some intermediate form, etc. Computer readable media may include: any entity or device capable of carrying computer program code, recording medium, USB flash drive, mobile hard disk, magnetic disk, optical disk, computer memory, read-only memory (ROM), random access memory (RAM), electric carrier signal, telecommunication signal and software distribution medium, etc. It should be noted that the content contained in the computer readable medium can be appropriately increased or decreased according to the requirements of legislation and patent practice in the jurisdiction. For example, in some jurisdictions, according to legislation and patent practice, computer readable media do not include electric carrier signals and telecommunication 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 changes made by using the contents of the present application specification and drawings under the application concept of the present application, or directly / indirectly used in other related technical fields are included in the patent protection scope of the present application.

Claims

1. A pump-scale joint 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 comprises an arterial line, a venous pot and a venous line connected in sequence, wherein the venous pot is provided with a liquid level detector, and the venous line is provided with a bubble detector, wherein the balance is used to weigh the liquid storage device, wherein the liquid storage device is connected to the arterial line or the venous pot through the external pipe, and wherein the liquid pump is provided in the external pipe ... 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 in the intravenous bottle until the bubble detector detects that the liquid changes into a gas 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 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 of the priming liquid according to the first preset pump speed and the running 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 running time; calibrating the balance according to the second measured variation and the preset variation; calibrating a pumping speed of the liquid pump according to the first measured variation and the preset variation; 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.

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

4. The pump-scale joint 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 comprises: 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 pump speed of the liquid pump and the first preset pump speed, and calibrating the pump 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 joint 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 joint calibration control method for blood purification equipment according to claim 1, characterized in that: The blood purification device further comprises an air pump, which is connected to the intravenous pot. The step of emptying the priming liquid of the intravenous pot comprises: 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 joint 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 run at the first preset pump speed, it also includes: The exhaust valve is opened to allow the intravenous bottle to communicate with the atmosphere.

8. The pump-scale joint calibration control method for blood purification equipment according to claim 1, characterized in that: The control method further comprises: Controlling the liquid pump to operate at a second preset pump speed for a first preset time; Calculating a theoretical change in the priming liquid 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 change weight, and determining whether the third difference exceeds a third tolerance; If the third difference exceeds the third tolerance, starting the 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, wherein the host is provided with a circuit board which can realize interactive communication 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, each step of the pump-scale joint calibration control method of the blood purification equipment as described in any one of claims 1 to 8 is implemented.

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

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