Hemodialysis apparatus and storage medium

Abstract

The application discloses a hemodialysis device and a storage medium. The device comprises a memory and a processor. The memory stores a computer program, and the processor executes the computer program to realize a method. In a blood purification treatment stage, the heater is controlled to heat dialysis fluid in a dialysis fluid input pipeline. When the heating temperature of the heater is in a stable state, a first detection temperature obtained by the first temperature sensor for measuring the temperature of the dialysis fluid in a dialysis fluid bag and a second detection temperature obtained by the second temperature sensor for measuring the temperature of the heated dialysis fluid in the dialysis fluid input pipeline are acquired. The heating power of the heater is adjusted according to the temperature difference between the second detection temperature and the first detection temperature. In this way, the application can improve the feedback control accuracy of the heating power of the heating device and ensure the safety and comfort of the blood purification treatment of the patient.

Description

Technical Field

[0001] This application relates to the field of hemodialysis technology, and more particularly to a hemodialysis device and storage medium. Background Technology

[0002] When removing harmful substances from a patient's blood, hemodialysis equipment needs to replenish the extracorporeal blood with fresh dialysate to compensate for the loss of plasma and electrolytes, ensuring the safety of blood purification treatment. The temperature of the dialysate has an extremely important impact on the safety of blood purification treatment; clinically, heating methods are generally used to heat the dialysate.

[0003] When heating dialysate using a heating device, the actual heating effect is mainly affected by two factors: the heating contact area and the heating temperature of the device. The heating contact area is determined by the structure of the heating device itself and cannot be changed; the heating temperature of the device can be adjusted. However, the feedback control precision of adjusting the heating temperature of the device is not high, and the heated dialysate may be at low or high temperatures, reducing the safety of blood purification treatment. Summary of the Invention

[0004] Based on this, embodiments of this application provide a hemodialysis device and storage medium that can improve the feedback control accuracy of the heating power of the heating device, ensuring the safety and comfort of the patient's blood purification treatment.

[0005] In a first aspect, this application provides a hemodialysis device, comprising: a blood circuit, a first temperature sensor, a second temperature sensor, a dialyzer, a dialysate inlet line, a dialysate bag, and a heater; wherein the dialysate bag is used to pre-store dialysate, the blood inlet and blood outlet of the dialyzer are connected in series in the blood circuit, the heater is disposed on the dialysate inlet line, a first end of the dialysate inlet line is connected to the dialysate bag, a second end of the dialysate inlet line is connected to the dialysate inlet of the dialyzer, the first temperature sensor is disposed on the dialysate bag, and the second temperature sensor is disposed at the outlet of the heater; the hemodialysis device further comprises: a memory and a processor, the memory being used to store a computer program, and the processor being used to execute the computer program and, when executing the computer program, to implement the following heating control method for the hemodialysis device:

[0006] During the blood purification treatment, the heater is controlled to heat the dialysate in the dialysate inlet line. When the heating temperature of the heater is stable, the first detection temperature obtained by the first temperature sensor measuring the temperature of the dialysate in the dialysate bag and the second detection temperature obtained by the second temperature sensor measuring the temperature of the dialysate after heating in the dialysate inlet line are obtained.

[0007] The heating power of the heater is adjusted according to the temperature difference between the second detected temperature and the first detected temperature.

[0008] Secondly, this application provides a computer-readable storage medium storing a computer program that, when executed by a processor, causes the processor to implement the heating control method for a hemodialysis device as described above.

[0009] In this embodiment, during blood purification treatment in a hemodialysis device, a first detection temperature and a second detection temperature are obtained by detecting the temperature of the dialysate before heating and the temperature of the dialysate after heating, respectively, using a first temperature sensor and a second temperature sensor. The heating power of the heater is then controlled based on the temperature difference between these two temperatures. The first detection temperature represents the temperature of the dialysate before heating, and the second detection temperature represents the temperature of the dialysate after heating. This method quickly determines the optimal heating temperature of the heating device, simplifying the heating control steps. Furthermore, the heater can rapidly adjust the temperature of the dialysate to the user's desired target temperature, improving the accuracy of feedback control of the heating power of the heating device. After heating the patient's blood, the safety and comfort of the blood purification treatment can be ensured. Attached Figure Description

[0010] Figure 1 This is a schematic diagram of the overall structure of an embodiment of the hemodialysis device of this application;

[0011] Figure 2 This is a schematic diagram of the tubing in an embodiment of the hemodialysis device of this application for hemodialysis treatment;

[0012] Figure 3 This is a schematic flowchart of an embodiment of the heating control method for a hemodialysis device according to this application;

[0013] Figure 4 This is a schematic diagram showing the relationship between dialysate flow rate and heater heating efficiency in one embodiment of the hemodialysis device of this application;

[0014] Figure 5 This is a schematic diagram of the first and second change curves in one embodiment of the hemodialysis device of this application. Detailed Implementation

[0015] The technical solutions of the embodiments of this application will be clearly and completely described below with reference to the accompanying drawings. Obviously, the described embodiments are only some embodiments of this application, and not all embodiments. Based on the embodiments of this application, all other embodiments obtained by those of ordinary skill in the art without creative effort are within the scope of protection of this application.

[0016] The flowchart shown in the attached diagram is for illustrative purposes only and does not necessarily include all content and operations / steps, nor does it necessarily have to be performed in the order described. For example, some operations / steps can be broken down, combined, or partially merged, so the actual execution order may change depending on the actual situation.

[0017] In the following description, the use of suffixes such as "module," "part," or "unit" to denote elements is solely for the purpose of illustration and has no inherent meaning. Therefore, "module," "part," or "unit" may be used interchangeably.

[0018] CRRT (Continuous Renal Replacement Therapy) refers to a device that provides continuous extracorporeal blood purification for 12-24 hours or longer to replace impaired kidney function. Hemodialysis equipment, as a type of CRRT machine, works by drawing the patient's blood out of the body and continuously and slowly removing water and solutes through extracorporeal circulation. Metabolic waste and toxins are removed through diffusion, convection, and adsorption. The purified blood is then returned to the patient to complete the hemodialysis treatment. Figure 1 The diagram illustrates the overall structure of a hemodialysis device. Hemodialysis devices can be categorized into different blood purification modes based on clinical application, such as hemodialysis, hemofiltration, hemodiafiltration, and hemoperfusion. Different blood purification modes can be applied to different clinical symptoms. For example, hemodialysis can be used in the treatment of patients with acute and chronic renal failure. Currently, the blood purification modes implemented by hemodialysis devices can be widely used in the treatment of various types of cardiovascular instability, high catabolism, or acute and chronic renal failure accompanied by cerebral edema, as well as multiple organ dysfunction syndrome, acute respiratory distress syndrome, crush syndrome, acute necrotizing pancreatitis, chronic heart failure, hepatic encephalopathy, and drug and toxin poisoning.

[0019] In clinical practice, hemodialysis equipment removes harmful substances from a patient's blood. Fresh dialysate is then added to the extracorporeal circulation to replenish lost plasma and electrolytes. This replenishment ensures electrolyte balance during the blood purification treatment, guaranteeing its safety. Because a single hemodialysis session typically lasts around 24 hours, the fresh dialysate used for storage and transportation is generally kept at a lower temperature than human blood. The temperature of the fresh dialysate returning to the patient after hemodialysis can be lower than the patient's blood temperature. If the returned blood temperature is too low, it can cause chills, cold extremities, and even shivering, leading to various complications such as vasoconstriction, spasms, joint pain, and stomach pain, potentially endangering the patient's life. Therefore, the temperature of the fresh dialysate replenished during extracorporeal circulation has a crucial impact on the safety of the patient's blood purification treatment.

[0020] To compensate for heat loss during extracorporeal circulation, clinical practice generally involves heating the fresh dialysate to prevent the blood returned to the patient after blood purification treatment from being too cold. Currently, various manufacturers on the market equip their hemodialysis equipment with heating devices. For example, the heating devices for hemodialysis machines in the United States and Germany employ heating methods such as wrapping the blood catheter with an infrared heating sleeve and spirally winding the blood catheter around an electrically heated heating module, respectively. Furthermore, current patent literature is also beginning to explore the design of heating devices on hemodialysis equipment.

[0021] In related technologies, when replenishing fresh dialysate in hemodialysis equipment, the actual heating effect of the heating device is mainly affected by two factors: the heating contact area of ​​the dialysate and the heating temperature of the device. The heating contact area is determined by the structure of the heating device itself and cannot be changed during clinical application. Technicians can usually adjust the temperature of the heated dialysate by adjusting the heating temperature of the device. However, the method of adjusting the heating temperature of the heating device in related technologies has the following technical problems: detecting the temperature of the heated fresh dialysate and using feedback control of the heating device based on the detected temperature to stabilize the temperature of the heated dialysate results in a long control response time. This feedback control method leads to a large feedback control error in the heating temperature, requiring a long time to set the heating temperature to a suitable level to achieve the user's desired temperature for the heated dialysate. The related technology has low precision in the feedback control of the heating device's temperature, which leads to the risk of low or high temperature in the freshly heated dialysate, reducing the safety of patients undergoing blood purification treatment.

[0022] In this embodiment, during blood purification treatment in a hemodialysis device, a first detection temperature and a second detection temperature are obtained by detecting the temperature of the dialysate before heating and the temperature of the dialysate after heating, respectively, using a first temperature sensor and a second temperature sensor. The heating power of the heater is then controlled based on the temperature difference between these two temperatures. The first detection temperature represents the temperature of the dialysate before heating, and the second detection temperature represents the temperature of the dialysate after heating. This method quickly determines the optimal heating temperature of the heating device, simplifying the heating control steps. Furthermore, the heater can rapidly adjust the temperature of the dialysate to the user's desired target temperature, improving the accuracy of feedback control of the heating power of the heating device. After heating the patient's blood, the safety and comfort of the blood purification treatment can be ensured.

[0023] The embodiments of this application will now be described in detail with reference to the accompanying drawings.

[0024] To better illustrate the embodiments of this application, Figure 2A schematic diagram of the tubing for hemodialysis treatment is shown. The hemodialysis device includes: a blood circuit, a first temperature sensor, a second temperature sensor, a dialyzer, a dialysate inlet line, a dialysate bag, and a heater. The heater is located on the dialysate inlet line. The first end of the dialysate inlet line is connected to the dialysate bag. The blood inlet and blood outlet of the dialyzer are connected in series in the blood circuit. The second end of the dialysate inlet line is connected to the dialysate inlet of the dialyzer. The first temperature sensor is located on the dialysate bag, which is used to pre-store dialysate. The second temperature sensor is located at the outlet of the heater.

[0025] The blood circuit includes an arterial line and a venous line. The arterial line is connected in series between the blood input end of the dialyzer and the user's artery, and the venous line is connected in series between the blood output end of the dialyzer and the user's vein. The dialysate bag is used to pre-store a certain volume of dialysate, for example, the dialysate bag is used to store 3L of dialysate. The hemodialysis device may also include a blood pump, a dialysate pump, and a filtration pump. The blood pump is installed on the blood circuit and provides driving force to the blood circuit by rotating, so that the blood circuit can transmit blood at a specific flow rate. The dialysate pump is installed on the dialysate input line. The hemodialysis device may also include a waste liquid output line, a waste liquid bag, and a third temperature sensor. The first end of the waste liquid output line is connected to the waste liquid bag, the second end of the waste liquid output line is connected to the waste liquid output end of the dialyzer, and the third temperature sensor is installed on the waste liquid output line.

[0026] When a patient undergoes blood purification treatment, the blood pump is controlled to deliver blood to the dialyzer via the arterial tubing; the dialysate pump is controlled to deliver dialysate to the dialyzer via the dialysate inlet tubing. Inside the dialyzer is a hollow fiber membrane, with blood and dialysate on opposite sides of the membrane. They flow in opposite directions on either side of the membrane, and through the solute gradient, osmotic gradient, and water pressure gradient on both sides, the dialysate and blood exchange substances to remove toxins and excess water while replenishing the patient's body with necessary substances.

[0027] During the exchange of substances between blood and dialysate across the hollow fiber membrane, heat transfer occurs between them. According to basic thermodynamics, a higher-temperature liquid transfers heat to a lower-temperature liquid. Typically, during blood purification treatment, if the dialysate in the infusion tubing is not heated, the fresh dialysate will be relatively cold. Inside the dialyzer, heat from the blood will be transferred to the colder dialysate, resulting in a lower temperature of the blood output from the dialyzer. If the blood output from the dialyzer is too cold, it will compromise the safety of the patient's blood purification treatment. Therefore, it is necessary to… A heater needs to be installed in the flow path of the fresh dialysate to heat it. This ensures the temperature of the heated dialysate remains within the normal range. After the fresh dialysate and blood exchange substances across the hollow fiber membrane, there will be no sharp drop in blood temperature after blood purification treatment, and the blood temperature output from the dialyzer will meet the patient's safe blood temperature requirements. Therefore, installing a heater in the dialysate inlet line to heat the dialysate is an essential step in the blood purification treatment process.

[0028] It should be noted that in hemodialysis equipment, the heater is placed on the dialysate inlet line to heat the dialysate. After heating, the dialysate and blood undergo heat transfer across the hollow fiber membrane, ensuring that the temperature of the blood output from the dialyzer remains within the normal range. However, in hemodialysis equipment, besides placing the heater on the dialysate inlet line, it is also possible to place the heater on the blood circuit. Both methods have their advantages and disadvantages. For example, if the heater is placed on the blood circuit, although this method directly heats the blood in the blood circuit with high heating efficiency, the heated blood is more prone to hypothermia or hyperthermia. Moreover, placing the heater on the blood circuit requires a longer blood circuit, resulting in a larger volume of blood stored in the blood circuit during the blood purification treatment phase, and a larger volume of blood remaining outside the body, which increases the risk of bacterial infection for the patient.

[0029] The hemodialysis device may further include a display screen, which can display relevant information about the patient's blood purification treatment. The hemodialysis device may also include a memory and a processor, the memory storing a computer program and the processor executing the computer program to implement the following heating control method for the hemodialysis device.

[0030] The heating control method for hemodialysis equipment in this application embodiment is applicable to the heating method where "the heater is set in the dialysate inlet pipeline", but not to the heating method where "the heater is set in the blood circuit".

[0031] See Figure 3 The heating control method in this application embodiment includes the following steps:

[0032] Step S101: During the blood purification treatment stage, the heater is controlled to heat the dialysate in the dialysate inlet pipeline. When the heating temperature of the heater is stable, the first detection temperature obtained by the first temperature sensor measuring the temperature of the dialysate in the dialysate bag and the second detection temperature obtained by the second temperature sensor measuring the temperature of the heated dialysate in the dialysate inlet pipeline are obtained.

[0033] To ensure the safety of blood purification treatment, both the first and second temperature sensors are typically non-contact temperature sensors. For example, both the first and second temperature sensors can use infrared wireless temperature measurement as their temperature detection principle.

[0034] During the blood purification treatment, the first temperature sensor is used to periodically sample the temperature of the dialysate in the dialysate bag, and the second temperature sensor is used to periodically sample the temperature of the heated dialysate in the dialysate inlet pipeline. The sampling period of the first temperature sensor and the sampling period of the second temperature sensor are the same.

[0035] The heater controls the dialysate in the dialysate inlet line to heat it. The heater temperature gradually rises, and once it reaches a normal heating level, it stabilizes. When the heater temperature is stable, the dialysate in the dialysate inlet line is heated to a normal level, ensuring that the temperature of the heated dialysate meets the safe temperature requirements for the patient's blood purification treatment. Although the heater's heating meets the patient's safe temperature requirements and the heater temperature is stable, the temperature of the dialysate in the dialysate inlet line after heating can still be affected by external factors (such as fluctuations in the dialysate flow rate in the dialysate inlet line and the ambient temperature of the heater).

[0036] Among them, judging that the heating temperature of the heater is in a stable state is a judgment condition. This "stable state" does not mean that the heater will necessarily be in a stable state in the subsequent heating process. In fact, the heating power of the heater will be adjusted in the subsequent heating process, and the heating temperature of the heater will change.

[0037] How to determine whether the heating temperature of the heater is in a stable state can be determined according to the specific actual situation; for example, if the temperature fluctuation range of the heater is less than 2°C within 6 consecutive sampling periods, it can be determined that the heating temperature of the heater is in a stable state.

[0038] Step S102: Adjust the heating power of the heater according to the temperature difference between the second detected temperature and the first detected temperature.

[0039] The heating power of the heater can be adaptively adjusted based on the temperature difference between the second and first detection temperatures. The difference between the second and first detection temperatures represents the increase in dialysate temperature after heating by the heater. A larger difference indicates a greater temperature increase in the dialysate after heating. Therefore, to improve the heating efficiency of the dialysate in the dialysate in the input line, the heating power of the heater can be increased, resulting in a higher heating temperature.

[0040] Therefore, this embodiment can adaptively adjust the heating power of the heater based on the temperature difference between the dialysate temperature after heating and the dialysate temperature before heating. Regardless of any changes in the temperature of the dialysate in the dialysate bag, the heater can quickly heat the dialysate in the dialysate input line to the user's expected safe temperature, thus ensuring the heating safety of the dialysate in the dialysate input line. The heated dialysate is then output to the dialyzer, ensuring that the blood in the blood circuit is always in a normal flow state.

[0041] The heating power of the heater can be adjusted according to the temperature difference between the second and the first detected temperatures. There are many ways to achieve this, such as adjusting the heater to different heating powers based on different temperature differences, etc., which will not be elaborated here.

[0042] In some embodiments, if the hemodialysis device starts from the startup phase, step S101, before controlling the heater to heat the dialysate in the dialysate inlet line, may further include:

[0043] Step S103: Detect the blood flow rate of the blood circuit. When the blood flow rate of the blood circuit is greater than or equal to the preset flow rate, determine that the hemodialysis device is in the blood purification treatment stage, and set the target temperature of the heater according to the blood flow rate of the blood circuit.

[0044] Specifically, the entire operation of a hemodialysis device can be divided into three stages: startup, blood purification treatment, and termination. During startup, the hemodialysis device begins operation, with the blood pump speed slowly increasing from 0 and the blood flow rate in the blood circuit slowly increasing from 0. During blood purification treatment, the blood pump speed stabilizes, and the blood flow rate in the blood circuit remains within a stable range, allowing the dialyzer to purify the patient's blood. In the termination stage, the hemodialysis device gradually stops, the blood pump speed decreases from a stable speed to 0, and the blood flow rate in the blood circuit decreases from a stable flow rate to 0. Therefore, by monitoring the blood flow rate in the blood circuit, it is possible to determine which stage the hemodialysis device is in (startup, blood purification treatment, or termination).

[0045] The preset flow rate is used to determine whether the hemodialysis equipment is in the blood purification treatment stage. When the blood flow rate in the blood circuit is greater than or equal to the preset flow rate, the hemodialysis equipment is determined to be in the blood purification treatment stage; when the blood flow rate in the blood circuit is less than the preset flow rate, the hemodialysis equipment is determined to be in the start-up or end-of-stage stage. When the hemodialysis equipment is in the blood purification treatment stage, the dialysate in the dialysate inlet line is heated by a heater; when the hemodialysis equipment is in the start-up or end-of-stage stage, it is not necessary to heat the dialysate in the dialysate inlet line by a heater.

[0046] The target temperature of the heater is related to the blood flow rate in the blood circuit. The greater the blood flow rate in the blood circuit, the shorter the time the patient's blood flows in the blood circuit, and the slower the blood temperature will drop after blood purification treatment. Therefore, there is a correlation between the blood flow rate in the blood circuit and the heating requirements of the heater. By setting the target temperature of the heater according to the blood flow rate in the blood circuit, the temperature of the dialysate after being heated by the heater can be just right to meet the temperature rise requirements of the blood in the blood circuit.

[0047] The target temperature of the heater refers to the standard temperature during the heating process.

[0048] In some embodiments, step S102, adjusting the heating power of the heater according to the temperature difference between the second detected temperature and the first detected temperature, may include: adjusting the heating power of the heater to a first heating power when the temperature difference is greater than a preset temperature value; and adjusting the heating power of the heater to a second heating power when the temperature difference is less than or equal to the preset temperature value; wherein the first heating power is greater than the second heating power.

[0049] Among them, the first heating power is greater than the second heating power.

[0050] The system determines whether the temperature increase of the dialysate after heating by the heater is too large by using a preset temperature value. If the second detection temperature minus the first detection temperature is greater than the preset temperature value, the heating power of the heater is set to the first heating power, which is greater than the second heating power. For example, the first heating power is 100W and the second heating power is 80W. If heating is performed according to the first heating power, the heating temperature of the heater can be higher, and the temperature of the dialysate after heating by the heater will rise faster.

[0051] In some embodiments, when controlling the heater to heat the dialysate in the dialysate inlet line in step S101, the method may further include:

[0052] Step S104: Obtain the patient's body temperature and use the body temperature as the first initial temperature.

[0053] Step S105: Control the heater to heat the dialysate in the dialysate inlet pipeline according to the first initial temperature, and record the first initial power of the heater at the first initial temperature.

[0054] The first initial temperature represents the heating temperature of the heater at the very first instant. The heater starts heating the dialysate in the dialysate inlet line according to the first initial temperature. Please note that the first initial temperature is the heating temperature at the very first instant. Since the heating temperature of the heater is in a feedback regulation process, the heating temperature of the heater will also change accordingly over time.

[0055] Step S106: Control the heating power of the heater to increase from the first initial power, record the second detection temperature, and when the second detection temperature is equal to the target temperature, detect the heating power of the heater and use the detected heating power of the heater as the second heating power.

[0056] As the heating power of the heater increases from the first initial power, the heating temperature of the heater also increases. When the temperature of the dialysate after heating in the dialysate inlet pipeline is equal to the target temperature, the second heating power represents the heating power of the heater under standard temperature conditions.

[0057] Step S107: Control the heating power of the heater to continue to increase from the second heating power, record the second detection temperature, and when the second detection temperature is equal to the safe temperature, detect the heating power of the heater and take the detected heating power of the heater as the first heating power.

[0058] Wherein, safe temperature = target temperature + 3℃.

[0059] For example, the target temperature is 30°C and the safe temperature is 33°C. When the heater reaches the second heating power, the heating power of the heater is controlled to continue to increase, and the heating temperature of the heater will also continue to rise until the temperature of the dialysate after being heated by the heater reaches the safe temperature. The safe temperature represents the maximum safe temperature that the dialysate after heating can reach. If the dialysate in the dialysate inlet line is heated to the safe temperature, the dialysate is output to the dialysate inlet of the dialyzer. The higher the efficiency of the heat transfer from the heater to the dialysate in the dialysate inlet line, the higher the efficiency. Therefore, when the heater reaches the first heating power, it means that the heater is in a high-temperature heating state, but the heater is still in a normal heating state. The dialysate in the dialysate inlet line can be quickly heated to a specific temperature by the heater.

[0060] It should be noted that S104-S107 are mainly for obtaining the first heating power and the second heating power, which are test steps. Once the first heating power and the second heating power are obtained, it is convenient to quickly adjust the heating state of the heater in the later stage, thereby improving the accuracy of feedback control of the heating temperature of the heater.

[0061] In some embodiments, step S103, setting the target temperature of the heater based on the blood flow rate of the blood circuit, may include:

[0062] Sub-step S1031: Determine the dialysate flow rate of the dialysate inlet tubing based on the blood flow rate of the blood circuit.

[0063] The formula for calculating the dialysate flow rate is: dialysate flow rate = blood flow rate * (3 / 4). The above formula for calculating the dialysate flow rate can be summarized after multiple technical experiments. The specific principle of the formula for calculating the dialysate flow rate will not be discussed in detail here. For example, when the blood flow rate of the blood circuit is 20 ml / min, then the dialysate flow rate = 20 ml / min * (3 / 4) = 15 ml / min.

[0064] Sub-step S1032: Determine the heating efficiency of the heater based on the dialysate flow rate; obtain the patient's body temperature, and determine the target temperature of the heater based on the body temperature and the heating efficiency, wherein the formula for calculating the target temperature is: target temperature = body temperature / heating efficiency.

[0065] The heating efficiency of a heater refers to the efficiency with which the heater transfers heat to the dialysate in the dialysate inlet line. 0 < heating efficiency < 1. For example, if the heating efficiency of a heater is 60%, it means that the heater can transfer 60% of its own heat to the dialysate in the dialysate inlet line to complete the function of heating the dialysate in the dialysate inlet line.

[0066] The heating efficiency of the heater is related to the dialysate flow rate. Given a fixed dialysate flow rate, the heating efficiency can be determined. A higher dialysate flow rate in the inlet line results in a lower heating efficiency. Figure 4 The curve showing the relationship between dialysate flow rate and heater heating efficiency is illustrated; where... Figure 4 The relationship curves in the data were obtained after multiple clinical trials, and the specific source of the relationship curves will not be described in detail here.

[0067] After determining the dialysate flow rate, according to Figure 4 By examining the relationship curve in the diagram, we can find the heating efficiency corresponding to the dialysate flow rate. This heating efficiency is the true efficiency of the heater at the current dialysate flow rate.

[0068] Specifically, the patient's body temperature can be approximated as the temperature of the heated dialysate. For example, if the patient's body temperature is 36℃, the heating efficiency of the heater is 80%, and the target temperature is 36℃ / 0.8 = 45℃. The target temperature calculated in this way is the standard temperature of the heater under standard heating conditions.

[0069] In some embodiments, the hemodialysis device further includes: a first weighing sensor, with the dialysate bag suspended on the first weighing sensor; the method may further include:

[0070] Step S108: When the heating temperature of the heater is stable, obtain the first weighing detection value obtained by the first weighing sensor weighing the dialysate bag.

[0071] During the blood purification treatment, the dialysate in the dialysate bag is output to the dialysate input end of the dialyzer. The weight of the dialysate bag will gradually decrease. The weight of the dialysate bag is detected by the first weighing sensor. The actual safety of the patient's blood purification treatment can be determined based on the first weighing detection value.

[0072] At this point, step S102, where the heating power of the heater is adjusted to a first heating power when the temperature difference is greater than a preset temperature value, and the heating power of the heater is adjusted to a second heating power when the temperature difference is less than or equal to the preset temperature value, may further include: adjusting the heating power of the heater to a first heating power when the first weighing detection value is greater than or equal to a preset weight value and the temperature difference is greater than the preset temperature value; and adjusting the heating power of the heater to a second heating power when the first weighing detection value is greater than or equal to the preset weight value and the temperature difference is less than or equal to the preset temperature value.

[0073] At this point, the method may further include:

[0074] Step S109: When the first weighing detection value is less than the preset weight value, the heating power of the heater is adjusted according to the first weighing detection value so that the heating power of the heater is reduced according to the preset requirements.

[0075] Specifically, the preset weight value is used to determine whether the remaining dialysate in the dialysate bag is sufficient. When the first weight detection value is greater than or equal to the preset weight value, it indicates that the remaining dialysate in the dialysate bag is sufficient, and the dialysate can be continuously output to the dialysate input end of the dialyzer through the dialysate input tubing to maintain the normal hemodialysis process of the dialyzer. When the first weight detection value is less than the preset weight value, it indicates that the remaining dialysate in the dialysate bag is insufficient, and the flow rate of the dialysate output from the dialysate bag will gradually decrease until it reaches 0.

[0076] If the remaining dialysate in the dialysate bag is sufficient, S102 is executed normally to provide feedback adjustment for the heating temperature of the heater. If the remaining dialysate in the dialysate bag is insufficient, the flow rate of dialysate output from the dialysate inlet line will gradually decrease. In this case, the heating power of the heater needs to be reduced so that the heat emitted by the heater can decrease rapidly. This way, as the flow rate of dialysate output from the dialysate inlet line decreases, the heat emitted by the heater will also decrease. The heat transferred by the heater to the dialysate in the dialysate inlet line is just enough to meet the heating requirements of the dialysate, and the heating power of the heater will not be wasted.

[0077] If the remaining dialysate in the dialysate bag is insufficient and step S102 is still executed, this will result in a waste of heat transferred from the heater to the dialysate in the dialysate inlet line. For example, if the flow rate of dialysate output from the dialysate inlet line becomes 0, the heater will still transfer heat to the dialysate inlet line according to the first heating power or the second heating power, which will cause the dialysate inlet line to be damaged by excessive heat.

[0078] This embodiment sets the feedback adjustment method of the heater's heating power by measuring the weight of the dialysate bag. This improves the heating effect of the heater and ensures the heating safety and stability of the dialysate in the dialysate inlet pipeline, avoiding feedback control errors in the heater's heating power caused by changes in the amount of remaining dialysate in the dialysate bag.

[0079] In some embodiments, step S109, the feedback adjustment of the heating power of the heater based on the first weighing detection value, may further include: controlling the heater to heat the dialysate in the dialysate input pipeline according to a third heating power; wherein the third heating power varies according to the following formula:

[0080] Third heating power = Second heating power * (First weighing detection value / Preset weight value).

[0081] Specifically, when the weight of the dialysate bag changes, the first weighing detection value continuously decreases. The ratio of "first weighing detection value / preset weight value" is always less than 1, so the third heating power continuously decreases. The heating power of the heater continuously decreases, and the heat transferred to the dialysate in the dialysate input pipeline through the heater continuously decreases. By adjusting the heating power of the heater in this way, the heating requirements of the dialysate in the dialysate input pipeline can be met, while ensuring the heating safety of the dialysate input pipeline.

[0082] In some embodiments, the hemodialysis device further includes a venous reservoir, the blood circuit including an arterial line and a venous line, the arterial line being connected to the blood input end of the dialyzer, the venous line being connected to the blood output end of the dialyzer, and the venous reservoir being connected in series with the venous line. The method may further include:

[0083] Step S110: When the first weighing detection value is greater than or equal to the preset weight value, obtain the first weight reduction rate obtained by the first weighing sensor detecting the weight reduction rate of the dialysis bag.

[0084] Specifically, the first weight reduction rate represents the rate at which dialysate is output from the dialysate bag. The greater the first weight reduction rate, the greater the flow rate of dialysate output from the dialysate inlet of the dialyzer.

[0085] Step S111: Determine the rate of change of the liquid level in the vein vessel. When the ratio between the rate of change of the liquid level in the vein vessel and the first weight reduction rate is greater than a first preset ratio, issue a first alarm signal.

[0086] Specifically, the first weight reduction rate refers to the amount of weight reduction of the dialysate bag per unit time; the venous reservoir level change rate refers to the amount of increase or decrease in the venous reservoir level per unit time. During blood purification treatment, if the patient's blood purification process is normal, the pressure in the venous tubing will fluctuate within the user's acceptable error range; the rate of dialysate output from the dialysate bag is stable; then the ratio between the venous reservoir level change rate and the first weight reduction rate is less than or equal to the first preset ratio. This indicates that the blood in the blood circuit is always in a normal flow state. When the ratio between the rate of change of the fluid level in the venous reservoir and the first rate of weight reduction is greater than the first preset ratio, it indicates that there are drastic fluctuations in the fluid level of the venous reservoir and / or the weight of the dialysate bag. This indicates that the dialysate flow rate from the dialysate inlet tubing to the dialyzer is too low, or that the rate of change of the fluid level in the venous reservoir is too high. In this case, it is determined that there is a malfunction in the blood flow state within the blood circuit, and a first alarm signal (such as an audible and visual alarm signal) is issued. When the user notices the first alarm signal, they will immediately address the malfunction in the blood flow state of the blood circuit, thus maintaining the safety of the patient undergoing blood purification treatment.

[0087] It should be noted that the first preset ratio can be set based on clinical technical experience. The first preset ratio is an empirical value. For example, if the first preset ratio is 0.03, when the ratio between the rate of change of the fluid level in the venous chamber and the first rate of weight reduction is greater than 0.03, a first alarm signal will be issued to indicate that there is a malfunction in the blood flow status of the blood circuit.

[0088] This embodiment can simultaneously determine whether there is a malfunction in either the fluid level of the venous reservoir or the rate of dialysate output from the dialysate bag by monitoring the ratio between the rate of change of the fluid level in the venous reservoir and the rate of decrease of the first weight.

[0089] In some embodiments, the hemodialysis device further includes: a waste liquid output pipeline, a waste liquid bag, a third temperature sensor, and a second weighing sensor; a first end of the waste liquid output pipeline is connected to the waste liquid bag, a second end of the waste liquid output pipeline is connected to the waste liquid output end of the dialyzer, and the third temperature sensor is disposed on the waste liquid output pipeline; the waste liquid bag is suspended from the second weighing sensor. In this case, the method may further include:

[0090] Step S112: Obtain the first weight increase rate obtained by detecting the weight increase rate of the waste liquid bag using the second weighing sensor, and the third detection temperature obtained by measuring the temperature of the waste liquid in the waste liquid output pipeline using the third temperature sensor.

[0091] Specifically, when the arterial tubing delivers the patient's blood to the dialyzer, the blood is purified by the dialyzer, producing waste fluid. The waste fluid is output from the dialyzer's waste fluid output end and then through the waste fluid output tubing to a waste fluid bag, where it is stored. The weight increase of the waste fluid bag is affected by both the dialysate flow rate in the dialysate input tubing and the mass exchange efficiency inside the dialyzer. The first weight increase rate refers to the weight of waste fluid output from the dialyzer's waste fluid output end per unit time.

[0092] Step S113: Determine a first ratio between the third detection temperature and the first weight increase rate, and a second ratio between the second detection temperature and the first weight decrease rate.

[0093] Step S114: Determine whether the hemodialysis device is in a normal fluid balance state based on the first ratio and the second ratio.

[0094] Specifically, when waste fluid is discharged from the waste fluid output line, the dialysate input line also outputs dialysate to the dialysate input end of the dialyzer. Inside the dialyzer, the heated dialysate transfers heat to the dialyzer's interior. After mass exchange, the heat from the blood inside the dialyzer is lost to the waste fluid. In this case, the waste fluid in the waste fluid output line causes a loss of heat from the blood inside the dialyzer. The first ratio = third detection temperature / first weight gain rate; the second ratio = second detection temperature / first weight loss rate. The first ratio can be used as: the heat carried by each unit weight of waste fluid output by the dialyzer; the second ratio can be used as: the heat carried by each unit weight of dialysate received by the dialyzer. During blood purification treatment, when the patient's blood is purified using a dialyzer, both the efficiency of the dialyzer in receiving heat through the dialysate and the efficiency of the dialyzer in losing heat through the waste fluid need to be maintained at a stable state. This ensures that the temperature of the blood output by the dialyzer meets the patient's safe temperature requirements, improving the safety of blood flow within the blood circuit.

[0095] Optionally, the hemodialysis device is determined to be in a normal fluid balance state based on the first ratio and the second ratio. Specifically, the determination method can be as follows: if the second preset ratio < |first ratio - second ratio| ≤ third preset ratio, then the hemodialysis device is determined to be in a normal fluid balance state. If |first ratio - second ratio| ≤ second preset ratio, or if the third preset ratio < |first ratio - second ratio|, then the hemodialysis device is determined to be in an abnormal fluid balance state. When the hemodialysis device is determined to be in an abnormal fluid balance state, it indicates that a heat imbalance occurs in the blood as it passes through the dialyzer, causing the temperature of the blood output from the dialyzer to rise or fall suddenly. This leads to a faulty flow state of the blood in the blood circuit. Because the hemodialysis device is determined to be in an abnormal fluid balance state, it indicates that the heat transferred to the blood inside the dialyzer is too high, or that the heat lost by the blood inside the dialyzer is too high. In this case, a temperature fault in the blood circuit is determined.

[0096] This embodiment can identify whether there is an imbalance between the heat input to the dialyzer and the heat loss from the dialyzer based on the changes in the first ratio and the second ratio, thereby improving the temperature safety level when blood and dialysate exchange substances in the dialyzer.

[0097] In some embodiments, the hemodialysis device includes: a fourth temperature sensor; the fourth temperature sensor is disposed on the blood circuit and at the blood output end of the dialyzer, and the temperature of the blood output by the dialyzer can be detected by the fourth temperature sensor, the blood output by the dialyzer representing the blood after hemodialysis.

[0098] At this point, the method may further include:

[0099] Step S115: Obtain the fourth detection temperature obtained by measuring the temperature of the blood output from the blood output terminal of the dialyzer using the fourth temperature sensor.

[0100] Specifically, during the blood purification treatment phase, inside the dialyzer, after the blood and dialysate exchange substances, the fourth temperature measurement represents the temperature of the blood returning to the patient's body.

[0101] Step S116: When the fourth detected temperature is not within the preset safe temperature range, a second alarm signal is issued.

[0102] The preset temperature safety range represents the normal temperature range of human blood, for example, 31.2℃-38.7℃. This preset temperature safety range can be obtained in advance by statistically analyzing the normal temperature fluctuation range of the human body. When the fourth detection temperature is within the preset temperature safety range, it means that the blood temperature returning to the patient is within the preset temperature safety range, and the blood returning to the patient will meet the patient's blood temperature safety requirements. In this case, no second alarm signal (such as an audible and visual alarm signal) will be issued.

[0103] If the fourth detection temperature is not within the preset safe temperature range, it means that the temperature of the blood returned to the patient's body is too high or too low, and the blood returned to the patient's body is in an unsafe condition. In this case, a second alarm signal is issued. When the user notices the second alarm signal, he / she will immediately deal with the blood temperature fault at the blood output end of the dialyzer, so as to eliminate the blood temperature fault in the blood purification treatment stage in a timely manner.

[0104] In some embodiments, the hemodialysis device further includes: an arterial chamber and a venous chamber; the blood circuit includes: an arterial line and a venous line; the arterial line is connected to the blood input end of the dialyzer; the venous line is connected to the blood output end of the dialyzer; the arterial chamber is connected in series on the arterial line; and the venous chamber is connected in series on the venous line. The method may further include:

[0105] Step S117: Detect the fluid level of the arterial chamber and the fluid level of the venous chamber.

[0106] Step S118: When the heating temperature of the heater is stable, determine the absolute value of the liquid level difference between the liquid level of the arterial chamber and the liquid level of the venous chamber.

[0107] Step S119: When the absolute value of the liquid level difference is less than or equal to 1 / 2 of the liquid level of the arterial chamber and less than or equal to 1 / 2 of the liquid level of the venous chamber, a first change curve of the liquid level of the arterial chamber over time and a second change curve of the liquid level of the venous chamber over time are plotted, and the display screen is controlled to display the first change curve and the second change curve.

[0108] Step S120: When the absolute value of the liquid level difference is greater than 1 / 2 of the liquid level of the arterial chamber or greater than 1 / 2 of the liquid level of the venous chamber, a third alarm signal is issued.

[0109] Specifically, when there is flowing blood in the blood circuit, both the arterial reservoir and the venous reservoir contain a certain volume of blood. The function of the arterial reservoir in hemodialysis equipment is to facilitate the detection of blood pressure in the arterial tubing and to monitor the flow of blood within the arterial tubing. The function of the venous reservoir in hemodialysis equipment is to remove air bubbles from the blood in the venous tubing. During the blood purification treatment, the fluid level in the arterial reservoir is affected by the blood pressure in the arterial tubing, and the fluid level in the venous reservoir is affected by the blood pressure in the venous tubing. Generally, there is a direct proportional relationship between the fluid level in the arterial reservoir and the blood pressure in the arterial tubing, and a direct proportional relationship between the fluid level in the venous reservoir and the blood pressure in the venous tubing.

[0110] If the heater's heating temperature is stable, it indicates that the heater is at a normal heating level and the heater's heating power is not being adjusted. In this case, it is necessary to determine whether there is a malfunction in the levels of the arterial and venous reservoirs. The absolute value of the difference between the levels of the arterial and venous reservoirs represents the degree of pressure difference between the arterial and venous lines. If the blood in the blood circuit is flowing normally, the degree of pressure difference between the arterial and venous lines is normal. Correspondingly, if the absolute value of the level difference is ≤ the level of the arterial reservoir * (1 / 2) and the absolute value of the level difference is ≤ the level of the venous reservoir * (1 / 2), it indicates that the degree of level difference between the arterial and venous reservoirs is within the user-acceptable error range, and the blood in the blood circuit is flowing normally.

[0111] If the absolute value of the level difference is greater than half the level of the arterial reservoir or half the level of the venous reservoir, it indicates that the difference between the levels of the arterial and venous reservoirs exceeds the user's acceptable error range. The blood in the blood circuit is in a faulty flow state. A third alarm signal (e.g., an audible and visual alarm) can alert the user to the faulty blood flow in the blood circuit. Upon noticing the third alarm signal, the user will immediately address the blood circuit flow fault. It should be noted that the common causes of blood flow faults in the blood circuit are: leakage at the connection between the arterial tubing and the blood input end of the dialyzer; leakage at the connection between the venous tubing and the blood output end of the dialyzer; or leakage from the hollow fiber membrane inside the dialyzer. Therefore, this embodiment can determine whether a blood circuit flow fault has occurred by monitoring the difference between the levels of the arterial and venous reservoirs.

[0112] When the blood in the blood circuit is in a normal flow state, the first change curve and the second change curve are displayed on the screen, such as... Figure 5As shown, the user can see the first curve to monitor the blood flow in the arterial line; the user can see the second curve to monitor the blood flow in the venous line; based on the first and second curves, the blood flow in the blood circuit can be comprehensively monitored.

[0113] In some embodiments, the method may further include:

[0114] Step S121: Plot the third change curve of the second detected temperature over time, and control the display screen to display the third change curve.

[0115] Specifically, when the heater heats the dialysate in the dialysate inlet line, the user can see the third change curve on the display screen to know the actual temperature change of the dialysate after heating, so that the user can have a clearer understanding of the temperature change of the dialysate.

[0116] Step S122: Determine the first correlation coefficient between the third change curve and the first change curve, and the second correlation coefficient between the third change curve and the second change curve.

[0117] Step S123: Determine the blood flow safety of the blood circuit based on the absolute value of the difference between the first correlation coefficient and the second correlation coefficient.

[0118] Specifically, both the first and second curves have specific physical meanings. The first curve represents the fluctuation of the fluid level in the arterial reservoir over time, while the second curve represents the fluctuation of the fluid level in the venous reservoir over time. The correlation coefficient between the two curves indicates the degree of similarity between their changes. The larger the absolute value of the correlation coefficient, the greater the similarity between the two curves. -1 ≤ correlation coefficient ≤ 1. If the correlation coefficient between the two curves is greater than 0, it means that the two curves are positively correlated; when one curve rises, the other curve will also rise. If the correlation coefficient between the two curves is less than 0, it means that the two curves are negatively correlated; when one curve rises, the other curve will fall.

[0119] The formula for calculating the correlation coefficient between the two curves is as follows: Where β represents the correlation coefficient between the two curves, and Cov(X, Y) represents the covariance of the two curves. The standard deviation of a curve The standard deviation represents the value of the other curve; the covariance measures the overall error between the two curves. The formula for calculating the covariance is: Cov(X, Y) = E(XY) - E(X)E(Y), where E(XY) represents the expected value of the product of the corresponding values ​​of the two curves, E(X) represents the expected value of one curve, and E(Y) represents the expected value of the other curve; for example, the three values ​​of X are: 0.3, 0.4, 0... 0.5; The three values ​​of Y are: 0.4, 0.6, 0.5; E(X) = (0.3 + 0.4 + 0.5) / 3 = 0.4, E(Y) = (0.4 + 0.6 + 0.5) / 3 = 0.5, E(XY) = (0.3 * 0.4 + 0.4 * 0.6 + 0.5 * 0.5) / 3 = 0.203, Cov(X, Y) = 0.203 - 0.4 * 0.5 = 0.03.

[0120] Specifically, in this embodiment, the first correlation coefficient represents the correlation between the fluid level in the arterial chamber and the temperature of the heated dialysate, while the second correlation coefficient represents the correlation between the fluid level in the venous chamber and the temperature of the heated dialysate. After the heated dialysate exchanges substances with the blood inside the dialyzer, the temperature of the blood output from the dialyzer also rises. The blood temperature in the venous tubing affects the fluid pressure in the venous chamber, thus indirectly affecting the fluid level. If the heater is heating the dialysate in the dialysate inlet tubing normally, the heating temperature of the heater has a stable and regular effect on the fluid level change in the venous chamber, and the second correlation coefficient will fluctuate within a small range. However, the heating temperature of the heater has a very small effect on the fluid level in the arterial chamber, so the first correlation coefficient fluctuates within a small range close to 0. Therefore, the blood flow safety of the blood circuit can be determined based on the absolute value of the difference between the first and second correlation coefficients.

[0121] In some embodiments, if the absolute value of the difference between the first correlation coefficient and the second correlation coefficient is less than a preset difference, it is determined that the heater is in a normal heating state. After being heated by the heater, the temperature of the dialysate meets the heating safety requirements for blood purification treatment. The heating state of the heater has a normal correlation with the liquid levels of the arterial chamber and the venous chamber, respectively, and the blood in the blood circuit is in a normal flow state.

[0122] If the absolute value of the difference between the first correlation coefficient and the second correlation coefficient is greater than or equal to the preset difference, it is determined that the heating state of the heater and the liquid level of the venous reservoir are in a fault state. The heating state of the heater and the liquid levels of the arterial reservoir and the venous reservoir are respectively in fault correlation. The reason for this fault state is usually that the hollow fiber membrane in the dialyzer leaks blood, causing the heated dialysate to be directly transferred to the venous reservoir. At this time, it is determined that the blood circuit is in a fault flow state.

[0123] This embodiment can monitor the safety of blood flow in the blood circuit and detect blood flow faults in a timely manner by based on the correlation between the liquid level of the arterial chamber, the liquid level of the venous chamber, and the heating status of the heater.

[0124] It should be noted that the sequence numbers of the above steps (such as S101, S102, etc.) are only used to refer to each step and do not mean that the steps in this embodiment will be executed in the order of the sequence numbers. The steps in this embodiment will be executed in the logical order of the technical solution.

[0125] This application also provides a computer-readable storage medium storing a computer program that, when executed by a processor, causes the processor to implement the heating control method for the hemodialysis device as described above. For detailed descriptions of the related content, please refer to the relevant content of the above methods, which will not be repeated here.

[0126] The computer-readable storage medium can be an internal storage unit of the aforementioned hemodialysis device, such as a hard disk or memory. Alternatively, it can be an external storage device, such as an external hard disk, smart memory card, secure digital card, flash memory card, etc.

[0127] It should be understood that the terminology used in this application specification is for the purpose of describing particular embodiments only and is not intended to limit the application.

[0128] It should also be understood that the term “and / or” as used in this application specification and the appended claims means any combination of one or more of the associated listed items and all possible combinations, and includes such combinations.

[0129] The above description is merely a specific embodiment of this application, but the scope of protection of this application is not limited thereto. Any person skilled in the art can easily conceive of various equivalent modifications or substitutions within the technical scope disclosed in this application, and such modifications or substitutions should all be covered within the scope of protection of this application. Therefore, the scope of protection of this application should be determined by the scope of the claims.

Claims

1. A hemodialysis device, characterized in that, The hemodialysis device includes: a blood circuit, a first temperature sensor, a second temperature sensor, a dialyzer, a dialysate inlet line, a dialysate bag, and a heater; wherein the dialysate bag is used to pre-store dialysate, the blood inlet and blood outlet of the dialyzer are connected in series in the blood circuit, the heater is disposed on the dialysate inlet line, the first end of the dialysate inlet line is connected to the dialysate bag, the second end of the dialysate inlet line is connected to the dialysate inlet of the dialyzer, the first temperature sensor is disposed on the dialysate bag, and the second temperature sensor is disposed at the outlet of the heater; the hemodialysis device further includes: a memory and a processor, the memory being used to store a computer program, and the processor being used to execute the computer program and, when executing the computer program, to implement the following heating control method for the hemodialysis device: During the blood purification treatment, the heater is controlled to heat the dialysate in the dialysate inlet line. When the heating temperature of the heater is stable, the first detection temperature obtained by the first temperature sensor measuring the temperature of the dialysate in the dialysate bag and the second detection temperature obtained by the second temperature sensor measuring the temperature of the dialysate after heating in the dialysate inlet line are obtained. The heating power of the heater is adjusted according to the temperature difference between the second detected temperature and the first detected temperature; The processor is used to execute the computer program and, when executing the computer program, to implement the following heating control method for a hemodialysis device: The blood flow rate of the blood circuit is detected. When the blood flow rate of the blood circuit is greater than or equal to the preset flow rate, the hemodialysis device is determined to be in the blood purification treatment stage, and the target temperature of the heater is set according to the blood flow rate of the blood circuit. When the temperature difference is greater than a preset temperature value, the heating power of the heater is adjusted to a first heating power; when the temperature difference is less than or equal to the preset temperature value, the heating power of the heater is adjusted to a second heating power; wherein the first heating power is greater than the second heating power. The processor is used to execute the computer program and, when executing the computer program, to implement the following heating control method for a hemodialysis device: Acquire the patient's body temperature and use the body temperature as the first initial temperature; The heater is controlled to heat the dialysate in the dialysate inlet line at the first initial temperature, and the first initial power of the heater at the first initial temperature is recorded. The heating power of the heater is controlled to increase from the first initial power, the second detection temperature is recorded, and when the second detection temperature is equal to the target temperature, the heating power of the heater is detected and the detected heating power of the heater is taken as the second heating power. The heating power of the heater is controlled to continue to increase from the second heating power, and the second detection temperature is recorded. When the second detection temperature is equal to the safe temperature, the heating power of the heater is detected, and the detected heating power of the heater is taken as the first heating power.

2. The hemodialysis device according to claim 1, characterized in that, The processor is used to execute the computer program and, when executing the computer program, to implement the following heating control method for a hemodialysis device: The dialysate flow rate of the dialysate inlet tubing is determined based on the blood flow rate of the blood circuit. The heating efficiency of the heater is determined based on the dialysate flow rate; the patient's body temperature is obtained, and the target temperature of the heater is determined based on the body temperature and the heating efficiency, wherein the target temperature is calculated using the formula: target temperature = body temperature / heating efficiency.

3. The hemodialysis device according to claim 1, characterized in that, The hemodialysis device further includes: a first weighing sensor, and the dialysate bag is suspended on the first weighing sensor; The processor is used to execute the computer program and, when executing the computer program, to implement the following heating control method for a hemodialysis device: When the heating temperature of the heater is stable, the first weighing value obtained by the first weighing sensor weighing the dialysate bag is acquired. When the first weighing detection value is greater than or equal to the preset weight value, and the temperature difference value is greater than the preset temperature value, the heating power of the heater is adjusted to the first heating power; when the first weighing detection value is greater than or equal to the preset weight value, and the temperature difference value is less than or equal to the preset temperature value, the heating power of the heater is adjusted to the second heating power. When the first weighing detection value is less than the preset weight value, the heating power of the heater is adjusted according to the first weighing detection value so that the heating power of the heater is reduced according to the preset requirements.

4. The hemodialysis device according to claim 3, characterized in that, The hemodialysis device further includes a venous chamber, and the blood circuit includes an arterial line and a venous line. The arterial line is connected to the blood input end of the dialyzer, and the venous line is connected to the blood output end of the dialyzer. The venous chamber is connected in series with the venous line. The processor is used to execute the computer program and, when executing the computer program, to implement the following heating control method for a hemodialysis device: When the first weighing detection value is greater than or equal to the preset weight value, the first weight reduction rate is obtained by the first weighing sensor detecting the weight reduction rate of the dialysis bag. The rate of change of the liquid level in the vein vessel is determined. When the ratio between the rate of change of the liquid level in the vein vessel and the first weight reduction rate is greater than a first preset ratio, a first alarm signal is issued.

5. The hemodialysis device according to claim 4, characterized in that, The hemodialysis device further includes: a waste liquid output pipeline, a waste liquid bag, a third temperature sensor, and a second weighing sensor; the first end of the waste liquid output pipeline is connected to the waste liquid bag, the second end of the waste liquid output pipeline is connected to the waste liquid output end of the dialyzer, the third temperature sensor is disposed on the waste liquid output pipeline, and the waste liquid bag is suspended on the second weighing sensor; The processor is used to execute the computer program and, when executing the computer program, to implement the following heating control method for a hemodialysis device: The first weight increase rate is obtained by detecting the weight increase rate of the waste liquid bag using the second weighing sensor, and the third detection temperature is obtained by measuring the temperature of the waste liquid in the waste liquid output pipeline using the third temperature sensor. Determine a first ratio between the third detection temperature and the first weight gain rate, and a second ratio between the second detection temperature and the first weight loss rate; The hemodialysis device is determined to be in a normal fluid balance state based on the first ratio and the second ratio.

6. The hemodialysis device according to claim 1, characterized in that, The hemodialysis equipment further includes: an arterial chamber and a venous chamber. The blood circuit includes: an arterial line and a venous line. The arterial line is connected to the blood input end of the dialyzer, and the venous line is connected to the blood output end of the dialyzer. The arterial chamber is connected in series on the arterial line, and the venous chamber is connected in series on the venous line. The processor is used to execute the computer program and, when executing the computer program, to implement the following heating control method for a hemodialysis device: Detect the fluid level in the arterial chamber and the fluid level in the venous chamber; When the heating temperature of the heater is stable, determine the absolute value of the liquid level difference between the liquid level of the arterial chamber and the liquid level of the venous chamber; When the absolute value of the liquid level difference is less than or equal to 1 / 2 of the liquid level of the arterial chamber and less than or equal to 1 / 2 of the liquid level of the venous chamber, a first change curve of the liquid level of the arterial chamber over time and a second change curve of the liquid level of the venous chamber over time are plotted, and the display screen is controlled to display the first change curve and the second change curve. A third alarm signal is issued when the absolute value of the liquid level difference is greater than 1 / 2 of the liquid level of the arterial chamber or greater than 1 / 2 of the liquid level of the venous chamber.

7. The hemodialysis device according to claim 6, characterized in that, The processor is used to execute the computer program and, when executing the computer program, to implement the following heating control method for a hemodialysis device: Plot a third curve showing the change of the second detected temperature over time, and control the display screen to show the third curve. Determine the first correlation coefficient between the third change curve and the first change curve, and the second correlation coefficient between the third change curve and the second change curve; The blood flow safety of the blood circuit is determined based on the absolute value of the difference between the first correlation coefficient and the second correlation coefficient.

8. A computer-readable storage medium, characterized in that, The computer-readable storage medium stores a computer program that, when executed by a processor, causes the processor to implement the heating control method for a hemodialysis device as described in any one of claims 1-7.

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