Hemodialysis fluid balance control method, device, electronic device and medium

Abstract

The present invention discloses a hemodialysis fluid balance control method, device, electronic device, and medium, relating to the technical field of intelligent regulation. The hemodialysis fluid balance control method includes: in response to a patient experiencing a hypotensive event, determining whether the hypotensive event is caused by a hypoglycemic event; if the hypotensive event is caused by a hypoglycemic event, switching the patient's dialysate from a sugar-free dialysate to a sugar-containing dialysate; monitoring the patient's real-time blood glucose concentration; and controlling the dialysate flow rate during the patient's dialysis based on the real-time blood glucose concentration. The embodiments of the present application achieve the goal of reducing interference with hemodialysis while ensuring compensation for hypoglycemia.

Description

Technical Field

[0001] This invention relates to the field of intelligent regulation, and in particular to a method, device, electronic device, and medium for regulating fluid balance in hemodialysis. Background Art

[0002] In hemodialysis, hypoglycemia is a significant contributing factor to hypotension. Hypoglycemia can lead to insufficient sympathetic nerve response, resulting in a drop in blood pressure. Hypotension causes cerebral hypoxia, which can be life-threatening in severe cases.

[0003] Using glucose-containing dialysate can alleviate low blood pressure caused by hypoglycemia, but the addition of glucose can affect the effectiveness of hemodialysis, for example, by affecting osmotic pressure. Therefore, both aspects need to be considered simultaneously: ensuring that hypoglycemia is compensated for without interfering with hemodialysis.

[0004] Therefore, how to reduce interference with hemodialysis while ensuring compensation for hypoglycemia has become an urgent technical problem to be solved. Summary of the Invention

[0005] In view of the above problems, embodiments of this application provide a method for regulating fluid balance in hemodialysis, an electronic device, and a computer-readable storage medium to solve the problem in the prior art of balancing and compensating for hypoglycemia and minimizing interference with hemodialysis during CRRT.

[0006] According to one aspect of the embodiments of this application, a computer-readable storage medium is provided, on which a computer program is stored, which, when executed by a processor, implements a method for regulating the fluid balance in hemodialysis, the method comprising:

[0007] In response to a patient experiencing a hypotensive event, determine whether the hypotensive event was caused by a hypoglycemic event;

[0008] If the hypotension event is caused by the hypoglycemia event, the patient's dialysis solution is switched from glucose-free dialysis solution to glucose-containing dialysis solution.

[0009] Monitor the patient's real-time blood glucose concentration;

[0010] Controlling the dialysate flow rate during dialysis based on the real-time blood glucose concentration specifically includes: establishing an osmotic pressure compensation model based on the dialysate glucose concentration and the patient's real-time blood glucose concentration; establishing an ultrafiltration rate compensation model based on the osmotic pressure difference between the patient's blood and the dialysate during dialysis; establishing a glucose kinetic equation, which characterizes the relationship between the patient's blood glucose concentration and the dialysate flow rate; combining the osmotic pressure compensation model, the ultrafiltration rate compensation model, and the glucose kinetic equation to determine the target osmotic fluid flow rate when the patient's metabolic homeostasis, osmotic pressure balance, and ultrafiltration rate are stable based on the real-time blood glucose concentration; and controlling the dialysate flow rate during dialysis based on the target osmotic fluid flow rate.

[0011] Preferably, controlling the dialysate flow rate during dialysis based on real-time blood glucose concentration further includes: if the real-time blood glucose concentration is lower than a preset first low blood glucose concentration, then controlling the dialysate flow rate during dialysis to a high flow rate mode; if the real-time blood glucose concentration is not lower than the first low blood glucose concentration and not higher than a preset second low blood glucose concentration, then controlling the dialysate flow rate during dialysis to a medium flow rate mode, wherein the second low blood glucose concentration is higher than the first low blood glucose concentration; if the real-time blood glucose concentration is higher than the second low blood glucose concentration, then controlling the dialysate flow rate during dialysis to a low flow rate mode.

[0012] Preferably, the method combines an osmotic pressure compensation model, an ultrafiltration rate compensation model, and a glucose kinetic equation to determine the target permeate flow rate when the patient's metabolic homeostasis, osmotic pressure balance, and ultrafiltration rate are stable, based on real-time blood glucose concentration. This includes: determining a target optimization function based on the difference between a preset target blood glucose concentration and the patient's real-time blood glucose concentration, and the difference between a preset target ultrafiltration rate and the ultrafiltration rate; determining the constraints of the target optimization function; and combining the osmotic pressure compensation model, the ultrafiltration rate compensation model, and the glucose kinetic equation to determine the target permeate flow rate when the target optimization function reaches its optimum under the constraints, based on real-time blood glucose concentration.

[0013] Preferably, the osmotic pressure compensation model is as follows:

[0014] Δπ=R·T·(G b -G d );

[0015] In the osmotic pressure compensation model, Δπ is the osmotic pressure difference, R is the preset gas constant, T is the patient's body temperature, and G... b For the patient's blood glucose concentration, G d This refers to the glucose concentration in the dialysate.

[0016] The ultrafiltration rate compensation model is as follows:

[0017] Q uf =K uf·[(P b -P d )+Δπ];

[0018] In the ultrafiltration rate compensation model, Q uf K is the ultrafiltration rate. uf P is the preset membrane ultrafiltration coefficient. b P is the hydrostatic pressure on the patient's blood side. d Δπ is the hydrostatic pressure on the dialysate side, and Δπ is the osmotic pressure difference.

[0019] The glucose kinetic equation is:

[0020]

[0021] In the glucose kinetic equation, G b Q represents the patient's real-time blood glucose concentration, t represents time, and Q represents the blood glucose level. d Let Q be the dialysate flow rate, k be the glucose metabolism rate constant, and Q be the flow rate of the dialysate. uf V is the ultrafiltration rate. b Volume of blood distribution;

[0022] The objective optimization function is:

[0023] minimize|G b -G target |+λ·|Q uf -Q target |;

[0024] In the objective optimization function, G b For the patient's real-time blood glucose concentration, G target Let Q be the target blood glucose concentration, λ be a preset weighting coefficient, and Q be... uf Q is the ultrafiltration rate. target Target ultrafiltration rate;

[0025] The constraints of the objective function include:

[0026] Δπ≤Δπ max ;

[0027]

[0028] In the constraints, Δπ represents the osmotic pressure difference. max G is the preset maximum osmotic pressure difference. b t represents the patient's real-time blood glucose concentration, and t represents time.

[0029] Preferably, before determining the constraints of the objective optimization function, the hemodialysis fluid balance control method further includes: determining the flow rate mode of the dialysate, which includes a high flow rate mode, a medium flow rate mode, and a low flow rate mode, wherein any flow rate mode is used to limit the range of dialysate flow rate values; and determining the flow rate constraint condition of the dialysate flow rate based on the flow rate mode, wherein the flow rate constraint condition is Q. d ∈[Q d,min Q d,max ], Q d Q is the dialysate flow rate. d,min Q represents the minimum dialysate flow rate in flow rate mode. d,max This represents the maximum value of the dialysate flow rate in the flow rate mode; the flow rate constraint is added to the constraint conditions of the objective optimization function.

[0030] Preferably, the dialysate flow rate is set to 500 mL / min to 800 mL / min in high flow rate mode; 300 mL / min to 500 mL / min in medium flow rate mode; and 100 mL / min to 300 mL / min in low flow rate mode.

[0031] According to another aspect of the embodiments of this application, a hemodialysis fluid balance control device is also provided. This device includes: a processing module for determining whether a hypotension event is caused by a hypoglycemic event in response to a patient experiencing a hypotension event; a switching module for switching the patient's dialysate from glucose-free dialysate to glucose-containing dialysate if the hypotension event is caused by a hypoglycemic event; a monitoring module for monitoring the patient's real-time blood glucose concentration; and a control module for controlling the dialysate flow rate during dialysis based on the real-time blood glucose concentration. Controlling the dialysate flow rate during dialysis based on the real-time blood glucose concentration includes: controlling the dialysis fluid flow rate based on the real-time blood glucose concentration. An osmotic pressure compensation model is established based on the patient's blood glucose concentration and real-time blood glucose concentration. An ultrafiltration rate compensation model is established based on the osmotic pressure difference between the patient's blood and the dialysate during dialysis. A glucose kinetic equation is established to characterize the relationship between the patient's blood glucose concentration and the dialysate flow rate. The osmotic pressure compensation model, the ultrafiltration rate compensation model, and the glucose kinetic equation are combined to determine the target osmotic flow rate for the patient's metabolic homeostasis, osmotic pressure balance, and stable ultrafiltration rate based on the real-time blood glucose concentration. The dialysate flow rate during dialysis is controlled based on the target osmotic flow rate.

[0032] According to another aspect of the embodiments of this application, an electronic device, a computer-readable storage medium, and a processor are also provided, wherein the processor executes the computer program.

[0033] This application embodiment controls the dialysate flow rate during dialysis based on real-time blood glucose concentration after switching the patient's dialysate from glucose-free dialysate to glucose-containing dialysate. This ensures that hypoglycemia is compensated for without causing abnormal ultrafiltration rate due to changes in osmotic pressure, thereby reducing interference with hemodialysis. Attached Figure Description

[0034] Figure 1 A schematic flowchart of the hemodialysis fluid balance regulation method provided in the embodiments of this application is shown;

[0035] Figure 2 The embodiments provided in this application are shown. Figure 1 A flowchart illustrating the sub-steps of S140. Detailed Implementation

[0036] To make the above-mentioned objects, features and advantages of the present invention more apparent and understandable, the specific embodiments of the present invention will be described in detail below with reference to the accompanying drawings. Obviously, the described embodiments are only some embodiments of the present invention, and not all embodiments.

[0037] Example 1, referring to Figure 1 As one embodiment of the present invention, a computer-readable storage medium is provided, on which a computer program is stored, which, when executed by a processor, implements a method for regulating the fluid balance in hemodialysis, including:

[0038] S110, in response to a patient experiencing a hypotensive event, determines whether the hypotensive event is caused by a hypoglycemic event.

[0039] This application provides solutions for hypotension caused by hypoglycemia in its embodiments.

[0040] In one alternative approach, it can be determined whether the blood glucose concentration is below 70 mg / dL, or whether a blood glucose concentration below 90 mg / dL and rapidly decreasing (the rate of decrease in blood glucose concentration < -20 mg / dL / h) may also trigger hypotension.

[0041] S120, if the hypotension event is caused by a hypoglycemic event, the patient's dialysate is switched from glucose-free dialysate to glucose-containing dialysate.

[0042] The dialysate concentration is set at 1.5% glucose or 2.5% glucose. 1.5% glucose is a commonly used starting concentration in clinical practice, which can rapidly raise blood glucose levels while avoiding drastic changes in osmotic pressure caused by excessively high glucose concentrations. This concentration is safe for most patients and is less likely to induce reverse ultrafiltration or electrolyte disturbances.

[0043] S130 monitors the patient's real-time blood glucose concentration.

[0044] S140 controls the dialysate flow rate during dialysis based on real-time blood glucose concentration.

[0045] Table 1:

[0046]

[0047] Table 1 shows that glucose-containing dialysate can significantly alleviate hypoglycemia-related hypotension (p<0.01), but it leads to a 45% increase in ultrafiltration rate deviation (due to changes in osmotic pressure).

[0048] In hemodialysis, using glucose-containing dialysate can alleviate hypoglycemia, but the addition of glucose affects osmotic pressure, which in turn affects the ultrafiltration rate. Ultrafiltration rate refers to the rate at which fluid is removed from the blood, and changes in osmotic pressure can alter the movement of fluid between the blood and dialysate. Therefore, adjusting the dialysate flow rate can take both aspects into account, ensuring that hypoglycemia is compensated for without causing abnormal ultrafiltration rates due to changes in osmotic pressure.

[0049] Table 2:

[0050]

[0051] Table 2 shows that dynamic flow rate control reduced the glycemic variability (CV%) by 56% (p<0.001), reduced ultrafiltration rate deviation by 60% (p=0.008), and avoided the risk of hyperglycemia (p=0.02).

[0052] This application embodiment determines whether a patient's hypotension event is caused by a hypoglycemic event when the hypotension event occurs. If the hypoglycemic event causes the hypotension event, the patient's dialysate is switched from glucose-free dialysate to glucose-containing dialysate to replenish the patient's blood glucose through the dialysate, thereby improving the patient's hypotension in a timely manner by improving the patient's blood glucose level. After switching the patient's dialysate from glucose-free dialysate to glucose-containing dialysate, the dialysate flow rate during dialysis is controlled according to the real-time blood glucose concentration to ensure that hypoglycemia is compensated for without causing abnormal ultrafiltration rate due to changes in osmotic pressure.

[0053] Preferably, S140 further includes:

[0054] S142, if the real-time blood glucose concentration is lower than the preset first low blood glucose concentration, the dialysate flow rate during the patient's dialysis is controlled in high flow rate mode.

[0055] S144, if the real-time blood glucose concentration is not lower than the first low blood glucose concentration and not higher than the preset second low blood glucose concentration, then the dialysate flow rate during the patient's dialysis is controlled in medium flow rate mode, and the second low blood glucose concentration is higher than the first low blood glucose concentration.

[0056] S146, if the real-time blood glucose concentration is higher than the second low blood glucose concentration, the dialysate flow rate during dialysis is controlled in low flow rate mode.

[0057] S142–S146 enables a flow rate adjustment strategy based on blood glucose concentration grading. When the real-time blood glucose concentration is <70 mg / dL (hypoglycemia), the dialysate flow rate during dialysis can be controlled in a high-flow mode, set at 500 mL / min–800 mL / min, to rapidly replenish glucose, increase osmotic pressure, and prioritize alleviating the risk of hypotension. When the real-time blood glucose concentration is between 70 mg / dL and 90 mg / dL (critical hypoglycemia), the dialysate flow rate during dialysis can be controlled in a medium-flow mode, set at 300 mL / min–500 mL / min, to balance glucose replenishment rate and osmotic pressure changes and avoid blood volume fluctuations. When the real-time blood glucose concentration is >90 mg / dL (normal blood glucose level), the dialysate flow rate during dialysis can be controlled in a low-flow mode, set at 100 mL / min–300 mL / min, to maintain baseline solute clearance efficiency and reduce unnecessary glucose load.

[0058] Regarding the setting of the dialysate flow rate, specifically, Figure 2 The embodiments provided in this application are shown. Figure 1 Please refer to the flowchart of the sub-steps in S140. Figure 2 S140 includes sub-steps S141 to S149:

[0059] S141, an osmotic pressure compensation model was established based on the dialysate glucose concentration and the patient's blood glucose concentration.

[0060] According to van Toff's law, the osmotic pressure compensation model can be set as follows:

[0061] Δπ=R·T·(G b -G d );

[0062] In the osmotic pressure compensation model, Δπ is the osmotic pressure difference, R is the preset gas constant, T is the patient's body temperature, and G... b G represents the patient's real-time blood glucose concentration. d This refers to the glucose concentration in the dialysate.

[0063] S143. An ultrafiltration rate compensation model is established based on the osmotic pressure difference between the patient's blood and the dialysate during dialysis.

[0064] The ultrafiltration rate is determined by the transmembrane pressure; therefore, the ultrafiltration rate compensation model can be set as follows:

[0065] Q uf =K uf·[(P b -P d )+Δπ];

[0066] In the ultrafiltration rate compensation model, Q uf K is the ultrafiltration rate. uf P is the preset membrane ultrafiltration coefficient. b P is the hydrostatic pressure on the patient's blood side. d Δπ represents the hydrostatic pressure on the dialysate side, and Δπ represents the osmotic pressure difference.

[0067] S145, Establish the glucose kinetic equation, which is used to characterize the relationship between the patient's blood glucose concentration and the dialysate flow rate.

[0068] Assuming that, under ideal conditions, the dynamic changes in a patient's blood glucose concentration are determined by external input and metabolic balance, a glucose kinetic equation can be established:

[0069]

[0070] In the glucose kinetic equation, G b Q represents the patient's real-time blood glucose concentration, t represents time, and Q represents the blood glucose level. d Let Q be the dialysate flow rate, k be the glucose metabolism rate constant, and Q be the flow rate of the dialysate. uf V is the ultrafiltration rate. b This refers to the blood distribution volume.

[0071] S147 combines the osmotic pressure compensation model, the ultrafiltration rate compensation model, and the glucose kinetic equation to determine the target permeate flow rate when the patient's metabolic homeostasis, osmotic pressure balance, and ultrafiltration rate are stable, based on real-time blood glucose concentration.

[0072] The problem of determining the target permeate flow rate can be transformed into an optimization problem for solution. Therefore, S147 further includes sub-steps S147a to S147c:

[0073] S147a, determine the target optimization function based on the difference between the preset target blood glucose concentration and the patient's blood glucose concentration, and the difference between the preset target ultrafiltration rate and the ultrafiltration rate.

[0074] The objective optimization function is:

[0075] minimize|G b -G target |+λ·|Q uf -Q target |;

[0076] In the objective optimization function, G b G represents the patient's real-time blood glucose concentration. target Let Q be the target blood glucose concentration, λ be a preset weighting coefficient, and Q be... ufQ is the ultrafiltration rate. target Target ultrafiltration rate;

[0077] Design an objective optimization function to minimize the risk of hypoglycemia and ultrafiltration bias, where G target The target blood glucose concentration can be set according to actual usage, for example, 5 mmol / L; Q target The target ultrafiltration rate is set clinically; λ is a preset weighting coefficient to balance the priority of glycemic requirements and ultrafiltration rate requirements.

[0078] S147b, Determine the constraints of the objective function.

[0079] The constraints of the objective function include:

[0080] Δπ≤Δπ max

[0081]

[0082] In the constraints, Δπ represents the osmotic pressure difference. max G is the preset maximum osmotic pressure difference. b t represents the patient's real-time blood glucose concentration, and t represents time.

[0083] Furthermore, additional constraints can be added, such as flow rate constraints determined based on the flow rate pattern, where the flow rate constraint is Q. d ∈[Q d,min Q d,max ], Q d Q is the dialysate flow rate. d,min Q represents the minimum dialysate flow rate in flow rate mode. d,max This represents the highest possible flow rate of the dialysate in the flow rate mode; the flow rate mode can be determined from S162 to S166 as a high flow rate mode, a medium flow rate mode, or a low flow rate mode.

[0084] By setting a maximum osmotic pressure difference, osmotic pressure imbalance can be avoided.

[0085] At the patient's metabolic homeostasis, we have:

[0086]

[0087] Then we have:

[0088]

[0089] Equation 1 can be derived:

[0090]

[0091] S147c, combining the osmotic pressure compensation model, ultrafiltration rate compensation model, and glucose kinetic equation, determines the target permeate flow rate when the objective optimization function reaches its optimum under constraints based on real-time blood glucose concentration.

[0092] Substituting the osmotic pressure compensation model into the ultrafiltration rate compensation model yields Equation 2:

[0093] Q uf =K uf ·[(P b -P d )+R·T·(G b -G d )]

[0094] Substituting the equation for the patient's metabolic homeostasis into Equation 2 above, we obtain Equation 3:

[0095]

[0096] Equation 3 is a nonlinear equation, which can be solved numerically using methods such as Newton's iteration method. d and Q uf The equilibrium point is determined to determine the target permeate flow rate.

[0097] S149 controls the dialysate flow rate during patient dialysis based on the target dialysate flow rate.

[0098] In S141 to S149, the dialysate flow rate can be set to compensate for hypoglycemia without causing abnormal ultrafiltration rate due to changes in osmotic pressure, thereby avoiding adverse reactions in patients caused by blood glucose fluctuations and interference with dialysis effects.

[0099] According to another aspect of the embodiments of this application, a hemodialysis fluid balance control device is also provided. This device includes: a processing module for determining whether a hypotension event is caused by a hypoglycemic event in response to a patient experiencing a hypotension event; a switching module for switching the patient's dialysate from glucose-free dialysate to glucose-containing dialysate if the hypotension event is caused by a hypoglycemic event; a monitoring module for monitoring the patient's real-time blood glucose concentration; and a control module for controlling the dialysate flow rate during dialysis based on the real-time blood glucose concentration, specifically including: establishing an osmotic pressure compensation model based on the dialysate glucose concentration and the patient's real-time blood glucose concentration; establishing an ultrafiltration rate compensation model based on the osmotic pressure difference between the patient's blood and the dialysate during dialysis; and establishing a glucose kinetic equation, which characterizes the relationship between the patient's blood glucose concentration and the dialysate flow rate.

[0100] According to another aspect of the embodiments of this application, an electronic device is also provided, including a computer-readable storage medium and a processor, wherein the processor executes the computer program.

[0101] Those skilled in the art will understand that embodiments of the present invention can be provided as methods, systems, or computer program products. Therefore, the present invention can take the form of a completely hardware embodiment, a completely software embodiment, or an embodiment combining software and hardware aspects. Furthermore, the present invention can take the form of a computer program product implemented on one or more computer-usable storage media containing computer-usable program code. The storage medium can be implemented by any type of volatile or non-volatile storage device or a combination thereof, such as Static Random Access Memory (SRAM), Electrically Erasable Programmable Read-Only Memory (EEPROM), Erasable Programmable Read-Only Memory (EPROM), Programmable Red-Only Memory (PROM), Read-Only Memory (ROM), magnetic storage, flash memory, magnetic disk, or optical disk. These computer program instructions may also be stored in a computer readable memory that can direct a computer or other programmable data processing device to work in a specific manner, so that the instructions stored in the computer readable memory produce an article of manufacture comprising an instruction device, which implements the process Figure 1 a process or multiple processes and / or boxes Figure 1 The function specified in one or more boxes.

[0102] It should be noted that the above embodiments are only used to illustrate the technical solutions of the present invention and are not intended to limit it. Although the present invention has been described in detail with reference to preferred embodiments, those skilled in the art should understand that modifications or equivalent substitutions can be made to the technical solutions of the present invention without departing from the spirit and scope of the technical solutions of the present invention, and all such modifications or substitutions should be covered within the scope of the claims of the present invention.

Claims

1. A computer-readable storage medium having a computer program stored thereon, characterized in that, When executed by a processor, the computer program implements a method for regulating fluid balance in hemodialysis, the method comprising: In response to a patient experiencing a hypotensive event, determine whether the hypotensive event was caused by a hypoglycemic event; If the hypotension event is caused by the hypoglycemia event, the patient's dialysis solution is switched from glucose-free dialysis solution to glucose-containing dialysis solution. Monitor the patient's real-time blood glucose concentration; Controlling the dialysate flow rate during dialysis based on the real-time blood glucose concentration specifically includes: An osmotic pressure compensation model was established based on the dialysate glucose concentration and the patient's real-time blood glucose concentration. An ultrafiltration rate compensation model is established based on the osmotic pressure difference between the patient's blood and the dialysate during dialysis. A glucose kinetic equation is established to characterize the relationship between the patient's blood glucose concentration and the dialysate flow rate. By combining the osmotic pressure compensation model, the ultrafiltration rate compensation model, and the glucose kinetic equation, the target permeate flow rate when the patient's metabolic homeostasis, osmotic pressure balance, and ultrafiltration rate are stable are determined based on the real-time blood glucose concentration. The dialysate flow rate during dialysis is controlled according to the target dialysate flow rate.

2. The computer-readable storage medium according to claim 1, characterized in that, The step of controlling the dialysate flow rate during dialysis based on the real-time blood glucose concentration further includes: If the real-time blood glucose concentration is lower than the preset first low blood glucose concentration, the dialysate flow rate during the patient's dialysis is controlled to a high flow rate mode. If the real-time blood glucose concentration is not lower than the first low blood glucose concentration and not higher than the preset second low blood glucose concentration, then the dialysate flow rate during the patient's dialysis is controlled to be in medium flow rate mode, and the second low blood glucose concentration is higher than the first low blood glucose concentration. If the real-time blood glucose concentration is higher than the second low blood glucose concentration, then the dialysate flow rate during the patient's dialysis is controlled to a low flow rate mode.

3. A computer-readable storage medium according to claim 2, characterized in that, The method of combining the osmotic pressure compensation model, the ultrafiltration rate compensation model, and the glucose kinetic equation to determine the target osmotic fluid flow rate when the patient's metabolic homeostasis, osmotic pressure balance, and ultrafiltration rate are stable based on the real-time blood glucose concentration includes: The target optimization function is determined based on the difference between the preset target blood glucose concentration and the patient's real-time blood glucose concentration, and the difference between the preset target ultrafiltration rate and the ultrafiltration rate. Determine the constraints of the objective optimization function; By combining the osmotic pressure compensation model, the ultrafiltration rate compensation model, and the glucose kinetic equation, the target permeate flow rate at which the objective optimization function reaches its optimum under the constraints is determined based on the real-time blood glucose concentration.

4. A computer-readable storage medium according to claim 3, characterized in that, The osmotic pressure compensation model is as follows: Δπ=R·T·(G b -G d ); In the osmotic pressure compensation model, Δπ is the osmotic pressure difference, R is the preset gas constant, T is the patient's body temperature, and G... b G represents the patient's real-time blood glucose concentration. d The glucose concentration of the dialysate; The ultrafiltration rate compensation model is as follows: Q uf =K uf ·[(P b -P d )+Δπ]; In the ultrafiltration rate compensation model, Q uf K is the ultrafiltration rate. uf P is the preset membrane ultrafiltration coefficient. b P is the hydrostatic pressure on the blood side of the patient. d Δπ represents the hydrostatic pressure on the dialysate side, and Δπ represents the osmotic pressure difference. The glucose kinetic equation is as follows: In the glucose kinetic equation, G b Q represents the patient's real-time blood glucose concentration, t represents time, and Q represents the blood glucose level. d The flow rate of the dialysate is given by k, where k is the glucose metabolism rate constant, and Q is the flow rate of the dialysate. uf V is the ultrafiltration rate. b Volume of blood distribution; The objective optimization function is: minimize|G b -G target |+λ·|Q uf -Q target |; In the objective optimization function, G b G represents the patient's real-time blood glucose concentration. target Let Q be the target blood glucose concentration, λ be a preset weighting coefficient, and Q be... uf Q is the ultrafiltration rate. target The target ultrafiltration rate; The constraints of the objective optimization function include: Δπ≤Δμ max ; In the constraints, Δπ represents the osmotic pressure difference. max G is the preset maximum osmotic pressure difference. b t represents the patient's real-time blood glucose concentration, and t represents time.

5. A computer-readable storage medium according to claim 4, characterized in that, Before determining the constraints of the objective optimization function, the hemodialysis fluid balance regulation method further includes: The flow rate mode of the dialysate flow rate is determined, and the flow rate mode includes the high flow rate mode, the medium flow rate mode and the low flow rate mode. Any flow rate mode is used to limit the range of values ​​of the dialysate flow rate. The flow rate constraint condition for the dialysate flow rate is determined based on the flow rate pattern, and the flow rate constraint condition is Q. d ∈[Q d,min Q d,max ], Q d Q is the flow rate of the dialysate. d,min Q is the lowest value of the dialysate flow rate in the flow rate mode. d,max This is the highest value of the dialysate flow rate in the flow rate mode; The flow velocity constraint is added to the constraints of the objective optimization function.

6. A computer-readable storage medium according to claim 2, characterized in that, The dialysate flow rate in the high flow rate mode is set to 500 mL / min to 800 mL / min; the dialysate flow rate in the medium flow rate mode is set to 300 mL / min to 500 mL / min; and the dialysate flow rate in the low flow rate mode is set to 100 mL / min to 300 mL / min.

7. A hemodialysis fluid balance regulation device, characterized in that, The hemodialysis fluid balance control device includes: The processing module is used to determine whether the hypotension event is caused by the hypoglycemia event in response to a patient experiencing a hypotension event. The switching module, if the hypotension event is caused by the hypoglycemia event, switches the patient's dialysis solution from glucose-free dialysis solution to glucose-containing dialysis solution; The monitoring module is used to monitor the patient's real-time blood glucose concentration; The control module is used to control the dialysate flow rate during dialysis based on the real-time blood glucose concentration. Specifically, it includes: establishing an osmotic pressure compensation model based on the dialysate glucose concentration and the patient's real-time blood glucose concentration; establishing an ultrafiltration rate compensation model based on the osmotic pressure difference between the patient's blood and the dialysate during dialysis; establishing a glucose kinetic equation, which characterizes the relationship between the patient's blood glucose concentration and the dialysate flow rate; combining the osmotic pressure compensation model, the ultrafiltration rate compensation model, and the glucose kinetic equation to determine the target dialysate flow rate when the patient's metabolic homeostasis, osmotic pressure balance, and ultrafiltration rate are stable, based on the real-time blood glucose concentration; and controlling the dialysate flow rate during dialysis based on the target dialysate flow rate.

8. An electronic device comprising a computer-readable storage medium and a processor as described in any one of claims 1-6, characterized in that, The processor executes the computer program.

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