Hemodynamics-based in-aorta balloon counterpulsation system control method

Abstract

The invention provides an in-aorta balloon counterpulsation system control method based on hemodynamics, and relates to the technical field of medical system control. According to the method, hemodynamic monitoring signals of a target user are obtained in real time, and then the heart index of the target user is determined; under the condition that the heart index of the target user is smaller than a first threshold value, the counterpulsation proportion of the in-aorta balloon counterpulsation system is set to be 1: 1, and the balloon inflation volume of the in-aorta balloon counterpulsation system is increased. According to the method provided by the invention, the cardiac output of the target user is obtained through the hemodynamics monitoring module, and then the cardiac index of the target user is determined according to the cardiac output, so that real-time automatic control of the counterpulsation proportion and the inflation volume of the balloon of the in-aorta balloon counterpulsation system can be realized based on the cardiac index and the first threshold value; the treatment efficiency is improved and the use cost is reduced.

Description

Technical Field

[0001] This invention relates to the field of medical system control technology, and in particular to a control method for an intra-aortic balloon counterpulsation system based on hemodynamics. Background Technology

[0002] The intra-aortic balloon pump (IABP) system is a key component in interventional treatment of cardiovascular diseases. The IABP system controls blood flow through the user's aorta by inflating and deflating a balloon, thereby assisting the heart through counterpulsation.

[0003] Currently, IABP systems assist the heart by using electrocardiographic triggering, which can be understood as synchronizing the inflation and deflation of the balloon based on the user's cardiac electrophysiological activity. During each cardiac cycle, a series of electrocardiographic signals are generated. By monitoring these signals, the IABP system can accurately identify the systolic and diastolic phases of the heart and control the inflation and deflation of the balloon accordingly. However, the inflation and deflation process of the IABP balloon is controlled by various parameters, including the counterpulsation ratio, inflation volume, and inflation / deflation time. During the use of the IABP system, operators often need to adjust these control parameters to meet the user's needs. Since this adjustment relies on the operator's experience and judgment, and real-time control of the IABP system consumes significant manpower and time, it suffers from low efficiency and high cost.

[0004] Therefore, there is an urgent need for a hemodynamic-based control method for intra-aortic balloon counterpulsation systems that can achieve precise and automatic control of the intra-aortic balloon counterpulsation system, improve processing efficiency, and reduce usage costs. Summary of the Invention

[0005] This invention provides a hemodynamically based control method for an intra-aortic balloon counterpulsation system, which enables precise automatic control of the intra-aortic balloon counterpulsation system, improves processing efficiency, and reduces usage costs.

[0006] To achieve the above objectives, the embodiments of the present invention adopt the following technical solutions: In a first aspect, a control method for an intra-aortic balloon counterpulsation (IABC) system based on hemodynamics is provided. The IBC system includes a gas cylinder, a cylinder, a balloon, a hemodynamic monitoring module, a processor, and a motor. The gas cylinder, cylinder, and balloon are connected via a pneumatic circuit. The processor is electrically connected to both the motor and the hemodynamic monitoring module, and the motor is connected to the cylinder. The method includes: the hemodynamic monitoring module acquiring real-time hemodynamic monitoring signals of the target user, including cardiac output; the processor determining the target user's cardiac index based on the target user's cardiac output; and, if the target user's cardiac index is less than a first threshold, the processor setting the counterpulsation ratio of the IBC system to 1:1 and changing the balloon inflation volume from a first value to a second value, wherein the ratio of the second value to the first value is a preset inflation volume increase ratio, and the first threshold is determined based on the target user's age, blood pressure, and ventilation status.

[0007] The method provided by this invention obtains the cardiac output of the target user through a hemodynamic monitoring module, and then determines the cardiac index of the target user based on the cardiac output. This enables real-time automatic control of the counterpulsation ratio and inflation volume of the balloon in the intra-aortic balloon counterpulsation system based on the cardiac index and a first threshold, thereby improving processing efficiency and reducing usage costs.

[0008] In one possible implementation of the first aspect, the formula for determining the target user's cardiac index (CI) is: Where CO is the target user's cardiac output and BSA is the target user's body surface area per unit area.

[0009] In one possible implementation of the first aspect, the first threshold CI threshold The formula for determining CI is: threshold = (αA1 + βA2 + γA3) × CI base ; A1 = Age / 70; Where α is the first weighting coefficient, β is the second weighting coefficient, and γ is the third weighting coefficient; A1 is the age influence factor; Age is the target user's age; A2 is the blood pressure influence factor; BP is the target user's maximum blood pressure; A3 is the ventilation status influence factor; and when the target user's ventilation status is mechanical ventilation, A3 = 1.5, and when the target user's ventilation status is non-mechanical ventilation, A3 = 1, CI base Preset heart rate index.

[0010] The method provided by this invention sets different weighting coefficients for the target user's age, blood pressure, and ventilation status, and then determines a first threshold based on the target user's age, blood pressure, and ventilation status. This first threshold is lowered for target users who are older, have lower blood pressure, or have poorer ventilation status, making the first threshold adaptable to users with different states or characteristics. This meets the usage needs of different users in different usage scenarios, thereby effectively improving the accuracy and safety of the intra-aortic balloon counterpulsation system.

[0011] In one possible implementation of the first aspect, when the target user's cardiac index is less than a first threshold, the processor sets the counterpulsation ratio of the intra-aortic balloon counterpulsation system to 1:1 and changes the balloon inflation volume of the intra-aortic balloon counterpulsation system from a first value to a second value, including: when the target user's cardiac index is less than the first threshold, the processor displays a first request on a preset interface, the first request being used to request a change in the counterpulsation ratio and balloon inflation volume of the intra-aortic balloon counterpulsation system; in response to a confirmation operation of the first request, the processor sets the counterpulsation ratio of the intra-aortic balloon counterpulsation system to 1:1 and changes the balloon inflation volume of the intra-aortic balloon counterpulsation system from the first value to the second value.

[0012] The method provided by this invention, by displaying a first request on a preset interface, enables operators to quickly and accurately understand the current target user's cardiac index, and then promptly adjust the intra-aortic balloon counterpulsation system based on the target user's cardiac index. Furthermore, the method provided by this invention allows the processor to rapidly control the counterpulsation ratio and balloon inflation volume of the intra-aortic balloon counterpulsation system upon receiving confirmation information input by the operator, effectively improving the accuracy and safety of the intra-aortic balloon counterpulsation system control.

[0013] In one possible implementation of the first aspect, the hemodynamic monitoring signal further includes stroke volume, and the method further includes: the processor determining the stroke volume variability of the target user based on the stroke volume of the target user; if the stroke volume variability of the target user is greater than a second threshold, the processor advances the inflation and deflation times of each balloon in the future time period according to a preset time advance, wherein the second threshold is determined based on the target user's positive end-expiratory pressure level, baseline left ventricular ejection fraction, and heart rate variability.

[0014] The method provided by this invention obtains the stroke volume of a target user through a hemodynamic monitoring module, and then determines the stroke volume variability of the target user based on the stroke volume. This enables real-time automatic control of the inflation and deflation timing of the balloon in the intra-aortic balloon counterpulsation system based on the stroke volume variability, thereby improving processing efficiency and reducing usage costs.

[0015] In one possible implementation of the first aspect, the formula for determining the stroke volume variability (SVV) is: Among them, SV max SV represents the maximum stroke volume of the target user within one respiratory cycle. min The minimum stroke volume for the target user within one respiratory cycle; The formula for determining the second threshold is: SVV threshold = (λB1 + μB2 + vB3) × SVV base ; B2 = LVEF / 50; B3 = 1.2 - 0.005 × HRV; Wherein, λ is the fourth weighting coefficient, μ is the fifth weighting coefficient, and υ is the sixth weighting coefficient; B1 is the positive end-expiratory pressure level influencing factor; PEEP is the positive end-expiratory pressure level of the target user; B2 is the baseline left ventricular ejection fraction influencing factor; LVEF is the baseline left ventricular ejection fraction of the target user; B3 is the heart rate variability influencing factor; HRV is the heart rate variability of the target user; and SVVbase is the preset stroke volume variability.

[0016] The method provided by this invention sets different weighting coefficients for the target user's positive end-expiratory pressure (PEEP) level, baseline left ventricular ejection fraction (LVEF), and heart rate variability (HRV). Then, it determines a second threshold based on the target user's PEEP level, LVEF, and HRV. This allows the second threshold to be adapted to users with different states and characteristics, thereby meeting the usage needs of different users in different usage scenarios and effectively improving the accuracy and safety of the intra-aortic balloon counterpulsation (IACP) system.

[0017] In one possible implementation of the first aspect, when the stroke volume variability of the target user is greater than a second threshold, the processor advances the inflation and deflation times of the intra-aortic balloon counterpulsation system for each balloon in a future time period according to a preset time advance, including: when the stroke volume variability of the target user is greater than the second threshold, the processor displays a second request on a preset interface, the second request being used to request a change in the inflation and deflation times of the intra-aortic balloon counterpulsation system for each balloon in a future time period; in response to a confirmation operation of the second request, the processor advances the inflation and deflation times of the intra-aortic balloon counterpulsation system for each balloon in a future time period according to the preset time advance.

[0018] The method provided by this invention displays a second request through a preset interface, enabling operators to quickly and accurately understand the stroke volume variability of the current target user, and then adjust the intra-aortic balloon counterpulsation system in a timely manner based on the stroke volume variability of the target user. Furthermore, the method provided by this invention allows the processor to rapidly control the balloon inflation and deflation time of the intra-aortic balloon counterpulsation system upon receiving confirmation information input by the operator, effectively improving the accuracy and safety of the intra-aortic balloon counterpulsation system control.

[0019] In one possible implementation of the first aspect, when the hemodynamic monitoring module and the balloon are placed in the same artery of the target user, after the hemodynamic monitoring module acquires the hemodynamic monitoring signal of the target user in real time, the method further includes: the processor filtering signals in the hemodynamic monitoring signal with a frequency less than or equal to a preset threshold.

[0020] The method provided by this invention, when the hemodynamic monitoring module and the balloon are placed in the same artery of the target user, allows the processor to filter signals with frequencies less than or equal to a preset threshold. This effectively avoids interference from noise generated by mechanical vibration during the operation of the intra-aortic balloon counterpulsation system on the hemodynamic monitoring signal, improves the accuracy of the hemodynamic monitoring signal, and thus enhances the accuracy and safety of the control of the intra-aortic balloon counterpulsation system.

[0021] Secondly, embodiments of the present invention provide an intra-aortic balloon counterpulsation (IACP) system, comprising a gas cylinder, a cylinder, a balloon, a hemodynamic monitoring module, a processor, and a motor; the gas cylinder, cylinder, and balloon are connected via a gas path; the processor is electrically connected to the motor and the hemodynamic monitoring module, and the motor is connected to the cylinder; the hemodynamic monitoring module is used to: acquire the hemodynamic monitoring signal of the target user in real time, the hemodynamic monitoring signal including cardiac output; the processor is used to: determine the target user's cardiac index based on the target user's cardiac output; the processor is also used to: set the counterpulsation ratio of the IACP system to 1:1 when the target user's cardiac index is less than a first threshold, and change the balloon inflation volume of the IACP system from a first value to a second value, the ratio of the second value to the first value being a preset inflation volume increase ratio, wherein the first threshold is determined based on the target user's age, blood pressure, and ventilation status.

[0022] Understandably, the beneficial effects that the system of the second aspect described above can achieve can be referenced from the beneficial effects of the first aspect and any of its possible design methods, which will not be repeated here. Attached Figure Description

[0023] Figure 1This is a schematic diagram of the structure of an intra-aortic balloon counterpulsation system according to an embodiment of the present invention; Figure 2 This is a schematic flowchart illustrating a control method for an intra-aortic balloon counterpulsation system according to an embodiment of the present invention; Figure 3 This is a schematic flowchart illustrating another control method for an intra-aortic balloon counterpulsation system according to an embodiment of the present invention; Figure 4 This is a schematic flowchart illustrating another control method for an intra-aortic balloon counterpulsation system according to an embodiment of the present invention. Detailed Implementation

[0024] The technical solutions of the embodiments of the present invention will be described below with reference to the accompanying drawings. In the description of the present invention, unless otherwise stated, " / " indicates that the objects before and after are in an "or" relationship. For example, A / B can represent A or B. The "or" in the present invention is merely a description of the relationship between the related objects, indicating that three relationships can exist. For example, A or B can represent: A alone, A and B simultaneously, and B alone. A and B can be singular or plural. Furthermore, in the description of the present invention, unless otherwise stated, "multiple" refers to two or more. "At least one of the following" or similar expressions refer to any combination of these items, including any combination of single or plural items.

[0025] Furthermore, to facilitate a clear description of the technical solutions of the embodiments of the present invention, the terms "first" and "second" are used in the embodiments of the present invention to distinguish identical or similar items with essentially the same function and effect. Those skilled in the art will understand that the terms "first" and "second" do not limit the quantity or execution order, and the terms "first" and "second" are not necessarily different.

[0026] In this embodiment of the invention, the terms "exemplary" or "for example" are used to indicate that something is being described as an example, illustration, or illustration. Any embodiment or design described as "exemplary" or "for example" in this embodiment of the invention should not be construed as being more preferred or advantageous than other embodiments or designs. Specifically, the use of terms such as "exemplary" or "for example" is intended to present the relevant concepts in a concrete manner for ease of understanding.

[0027] The intra-aortic balloon pump (IABP) system is a key component in interventional treatment of cardiovascular diseases. The IABP system controls blood flow through the user's aorta by inflating and deflating a balloon, thereby assisting the heart through counterpulsation.

[0028] Currently, IABP systems assist the heart by using electrocardiographic triggering, which can be understood as synchronizing the inflation and deflation of the balloon based on the user's cardiac electrophysiological activity. During each cardiac cycle, a series of electrocardiographic signals are generated. By monitoring these signals, the IABP system can accurately identify the systolic and diastolic phases of the heart and control the inflation and deflation of the balloon accordingly. However, the inflation and deflation process of the IABP balloon is controlled by various parameters, including the counterpulsation ratio, inflation volume, and inflation / deflation time. During the use of the IABP system, operators often need to adjust these control parameters to meet the user's needs. Since this adjustment relies on the operator's experience and judgment, and real-time control of the IABP system consumes significant manpower and time, it suffers from low efficiency and high cost.

[0029] Therefore, there is an urgent need for a hemodynamic-based control method for intra-aortic balloon counterpulsation systems that can achieve precise and automatic control of the intra-aortic balloon counterpulsation system, improve processing efficiency, and reduce usage costs.

[0030] In view of this, embodiments of the present invention provide a control method for an intra-aortic balloon counterpulsation (IABC) system based on hemodynamics, applied to an IBC system. The IBC system includes a gas cylinder, a cylinder, a balloon, a hemodynamic monitoring module, a processor, and a motor. The gas cylinder, cylinder, and balloon are connected via a gas path. The processor is electrically connected to the motor and the hemodynamic monitoring module, and the motor is connected to the cylinder. The method includes: the hemodynamic monitoring module acquiring the hemodynamic monitoring signal of the target user in real time, the hemodynamic monitoring signal including cardiac output; the processor determining the target user's cardiac index based on the target user's cardiac output; when the target user's cardiac index is less than a first threshold, the processor sets the counterpulsation ratio of the IBC system to 1:1 and changes the balloon inflation volume of the IBC system from a first value to a second value, wherein the ratio of the second value to the first value is a preset inflation volume increase ratio, and the first threshold is determined based on the target user's age, blood pressure, and ventilation status.

[0031] The method provided by this invention acquires the cardiac output of a target user through a hemodynamic monitoring module, then determines the target user's cardiac index based on the cardiac output. This enables real-time automatic control of the counterpulsation ratio and inflation volume of the intra-aortic balloon counterpulsation system based on the cardiac index and a first threshold, improving processing efficiency and reducing usage costs. Furthermore, the method sets different weighting coefficients for the target user's age, blood pressure, and ventilation status, and then determines the first threshold based on these factors. Specifically, it lowers the first threshold for the cardiac index of older users, those with lower blood pressure, and those with poorer ventilation. This allows the first threshold to adapt to users with different conditions and characteristics, meeting the usage needs of different users in different scenarios, and effectively improving the accuracy and safety of the intra-aortic balloon counterpulsation system control.

[0032] In some embodiments, the control method of the intra-aortic balloon counterpulsation system provided in this invention can be executed by the intra-aortic balloon counterpulsation system 100 (hereinafter referred to as the counterpulsation system 100). See also Figure 1 , Figure 1 This is a schematic diagram of an intra-aortic balloon counterpulsation system according to an embodiment of the present invention. The counterpulsation system 100 includes a gas cylinder 110, a cylinder 120, a balloon 130, a hemodynamic monitoring module 140, a processor 150, and a motor 160. The gas cylinder 110, the cylinder 120, and the balloon 130 are connected via a gas path. The processor 150 is electrically connected to the motor 160 and the hemodynamic monitoring module 140, respectively, and the motor 160 is connected to the cylinder 120. The method includes: the hemodynamic monitoring module 140 acquiring the target user's blood pressure in real time. The hemodynamic monitoring signal includes cardiac output. The processor 150 determines the target user's cardiac index based on the target user's cardiac output. If the target user's cardiac index is less than a first threshold, the processor 150 sets the counterpulsation ratio of the intra-aortic balloon counterpulsation system to 1:1 and changes the balloon inflation volume of the intra-aortic balloon counterpulsation system from a first value to a second value. The ratio of the second value to the first value is a preset inflation volume increase ratio. The first threshold is determined based on the target user's age, blood pressure, and ventilation status.

[0033] It should be noted that, in combination Figure 1 The counterpulsation system 100 also includes a voltage regulator 170, a solenoid valve 180, and an electrocardiogram monitoring module 190; the voltage regulator 170 is located between the gas cylinder 110 and the solenoid valve 180, and is used to control the gas pressure output from the gas cylinder 110 within a preset gas pressure threshold range; the processor 150 and the electrocardiogram monitoring module 190 are electrically connected, and the motor 160 is connected to the cylinder 160, wherein... Figure 1 The dashed lines in the diagram represent gas passages, while the solid lines represent electrical connections.

[0034] The processor 160 is also used to send the target user's electrocardiogram (ECG) signal to the processor 150 based on the ECG signal acquired by the ECG monitoring module 190, and to determine the target user's target cardiac cycle; the processor 160 is also used to generate control commands based on the target user's target cardiac cycle; and to control the motor 160 to operate according to the control commands, so that the motor 160 adjusts the internal pressure of the cylinder 120 to complete the contraction and expansion of the balloon 130; wherein, the target user's cardiac cycle is a time series composed of the time interval between two consecutive heartbeats of the target user.

[0035] For example, processor 150 may include one or more processing cores. Processor 150 connects to various parts within counterpulsation system 100 using various interfaces and lines, and performs various functions of counterpulsation system 100 and processes data by running or executing instructions, programs, code sets, or instruction sets, and by calling data. Optionally, processor 150 may be implemented using at least one of the following hardware forms: Central Processing Unit (CPU), Graphics Processing Unit (GPU), Digital Signal Processing (DSP), Field-Programmable Gate Array (FPGA), and Programmable Logic Array (PLA).

[0036] The following description, in conjunction with the accompanying drawings, illustrates a hemodynamically based intra-aortic balloon counterpulsation system control method provided by an embodiment of the present invention.

[0037] Figure 2 This is a flowchart illustrating a hemodynamically based intra-aortic balloon counterpulsation system control method provided in an embodiment of the present invention. Optionally, this method can be... Figure 1 The counterpulsation system 100 shown is executed. The method may include the following steps: S1, the hemodynamic monitoring module acquires the hemodynamic monitoring signal of the target user in real time, the hemodynamic monitoring signal including cardiac output.

[0038] Specifically, the hemodynamic monitoring module includes an arterial catheter based on Pulse-induced Contour Cardiac Output (PiCCO) technology (hereinafter referred to as PiCCO catheter). The PiCCO catheter is placed inside the target user's artery and can acquire the target user's hemodynamic monitoring signals, obtain the target user's dynamic blood pressure waveform, and then obtain the target user's cardiac output (CO) and stroke volume (SV).

[0039] Cardiac output is the total amount of blood pumped by the heart per minute. It reflects the heart's overall pumping capacity and is a core indicator for assessing the function of the circulatory system.

[0040] In some embodiments, where the hemodynamic monitoring module and the balloon are positioned in the same artery as the target user, after S1, the method further includes: the processor filtering signals in the hemodynamic monitoring signal with frequencies less than or equal to a preset threshold.

[0041] It should be understood that during the measurement process of the hemodynamic monitoring module, the noise generated by the intra-aortic balloon counterpulsation system can affect the accuracy of the hemodynamic monitoring signal. However, the frequency of the hemodynamic monitoring signal is relatively high, while the frequency of the mechanical noise generated by the intra-aortic balloon counterpulsation system is relatively low. Therefore, filtering out the lower-frequency signals in the hemodynamic monitoring signal through a filter can effectively prevent the mechanical noise generated by the intra-aortic balloon counterpulsation system from interfering with the hemodynamic monitoring signal.

[0042] It should be noted that the preset threshold of the signal frequency can be flexibly set according to the actual working scenario, and the embodiments of the present invention do not impose any special restrictions on this.

[0043] The method provided by this invention, when the hemodynamic monitoring module and the balloon are placed in the same artery of the target user, allows the processor to filter signals with frequencies less than or equal to a preset threshold. This effectively avoids interference from noise generated by mechanical vibration during the operation of the intra-aortic balloon counterpulsation system on the hemodynamic monitoring signal, improves the accuracy of the hemodynamic monitoring signal, and thus enhances the accuracy and safety of the control of the intra-aortic balloon counterpulsation system.

[0044] S2. The processor determines the target user's cardiac index based on the target user's cardiac output.

[0045] Specifically, the cardiac index is the ratio of cardiac output to body surface area per unit area (BSA). It is used to eliminate the influence of individual body size differences on cardiac output assessment, reflects the overall pumping capacity of the heart, and is a core indicator for assessing circulatory system function.

[0046] In one possible implementation, the formula for determining the target user's cardiac index (CI) is: Where CO is the target user's cardiac output and BSA is the target user's body surface area per unit area.

[0047] In one possible implementation, the above S2 specifically includes: The processor determines the target user's cardiac index based on the target user's cardiac output at a preset frequency.

[0048] Specifically, the preset frequency is once per millisecond.

[0049] The method provided in this invention determines the cardiac index of a target user every millisecond based on the target user's cardiac output. This enables millisecond-level control of the intra-aortic balloon counterpulsation system, specifically, it allows for millisecond-level (real-time) automatic control of the balloon's counterpulsation ratio and inflation volume based on the cardiac index and a first threshold, improving processing efficiency and reducing operating costs.

[0050] S3. When the target user's cardiac index is less than the first threshold, the processor sets the counterpulsation ratio of the intra-aortic balloon counterpulsation system to 1:1 and changes the balloon inflation volume of the intra-aortic balloon counterpulsation system from the first value to the second value.

[0051] The intra-aortic balloon counterpulsation (IACP) system works by inflating the balloon during diastole and deflating it during systole. The counterpulsation ratio is the ratio of the number of balloon inflations / deflations to the user's heart rate, or the ratio of the number of assisted heartbeats by the IACP system to the user's heart rate. A 1:1 counterpulsation ratio means that for every heartbeat of the target user, the IACP system will perform one assisted heartbeat (balloon inflation / deflation).

[0052] Specifically, the ratio of the second value to the first value is the preset inflation volume growth ratio.

[0053] In one example, the preset inflation volume increase ratio is 115%. That is, the ratio of the second value to the first value is 115%. In other words, if the target user's cardiac index is less than the first threshold, the processor will change the balloon inflation volume of the intra-aortic balloon counterpulsation system from the current first value to the second value, which is increased by 15%.

[0054] It should be understood that the above preset inflation volume growth ratio is only an illustrative example, and the specific value of the preset inflation volume growth ratio is not particularly limited in the embodiments of the present invention.

[0055] The first threshold is determined based on the target user's age, blood pressure, and ventilation status.

[0056] In some embodiments, the first threshold CI threshold The formula for determining it is: CI threshold = (αA1 + βA2 + γA3) × CI base ; A1 = Age / 70; Where α is the first weighting coefficient, β is the second weighting coefficient, and γ is the third weighting coefficient; A1 is the age influence factor; Age is the target user's age; A2 is the blood pressure influence factor; BP is the target user's maximum blood pressure; A3 is the ventilation status influence factor; and when the target user's ventilation status is mechanical ventilation, A3 = 1.5, and when the target user's ventilation status is non-mechanical ventilation, A3 = 1, CI base Preset heart rate index.

[0057] For example, α is 0.4, β is 0.4, γ is 0.2, and the preset cardiac index is 2.2 L / min / m. 2 When the target user is 65 years old, has a systolic blood pressure of 85 mmHg, and is on mechanical ventilation, the first threshold is 1.94 L / min / m. 2 .

[0058] In another possible implementation, the first threshold can also be determined based on the target user's blood lactate level and body temperature, that is, different weighting coefficients are assigned to the blood lactate level and body temperature. This embodiment of the invention does not impose any particular restrictions on this.

[0059] The method provided in this invention sets different weighting coefficients for the target user's age, blood pressure, and ventilation status, and then determines a first threshold based on the target user's age, blood pressure, and ventilation status. This first threshold is lowered for target users who are older, have lower blood pressure, or have poorer ventilation status, making the first threshold adaptable to users with different statuses and characteristics. This meets the usage needs of different users in different usage scenarios and effectively improves the accuracy and safety of the intra-aortic balloon counterpulsation system.

[0060] In some embodiments, see Figure 3 The aforementioned S3 specifically includes: S31. When the target user's cardiac index is less than a first threshold, the processor displays a first request on a preset interface. The first request is used to request a change in the counterpulsation ratio and balloon inflation volume of the intra-aortic balloon counterpulsation system.

[0061] S32, In response to the confirmation operation of the first request, the processor sets the counterpulsation ratio of the intra-aortic balloon counterpulsation system to 1:1 and changes the balloon inflation volume of the intra-aortic balloon counterpulsation system from a first value to a second value.

[0062] In this way, the method provided by this invention, by displaying a first request on a preset interface, enables the operator to quickly and accurately understand the current target user's cardiac index, and then adjust the intra-aortic balloon counterpulsation system in a timely manner based on the target user's cardiac index. Furthermore, the method provided by this invention allows the processor to rapidly control the counterpulsation ratio and balloon inflation volume of the intra-aortic balloon counterpulsation system upon receiving confirmation information input by the operator, effectively improving the accuracy and safety of the intra-aortic balloon counterpulsation system control.

[0063] In one possible implementation, the method provided by the embodiments of the present invention further includes: If the target user's heart rate index is lower than a first threshold and the duration exceeds a preset time threshold, the processor generates a first alarm message to alert the operator.

[0064] In this way, the method provided by the embodiments of the present invention can enable the operator to quickly pay attention to the target user and take timely action when the counterpulsation ratio and balloon inflation volume of the intra-aortic balloon counterpulsation system are set, but the target user's cardiac index remains below a preset time threshold for an extended period of time.

[0065] As described in S1-S3 above, the method provided by this embodiment of the invention obtains the cardiac output of the target user through a hemodynamic monitoring module, then determines the target user's cardiac index based on the cardiac output. This enables real-time automatic control of the counterpulsation ratio and inflation volume of the intra-aortic balloon counterpulsation system based on the cardiac index and a first threshold, improving processing efficiency and reducing usage costs. Furthermore, by setting the counterpulsation ratio to 1:1 and increasing the balloon inflation volume when the cardiac index is less than the first threshold, the method provided by this invention effectively reduces the cardiac workload of the target user, improves the safety and stability of the intra-aortic balloon counterpulsation system, and meets the user's needs in different usage scenarios.

[0066] In one possible implementation, see Figure 4 The hemodynamic monitoring signal also includes stroke volume, and the method provided in this embodiment of the invention further includes: S41. The processor determines the stroke volume variability of the target user based on the stroke volume of the target user.

[0067] Specifically, stroke volume is the volume of blood ejected from the left ventricle into the aorta during a single heartbeat, reflecting the heart's pumping efficiency. Stroke volume variability refers to the dynamic variation in stroke volume across multiple consecutive heartbeats, used to predict volume responsiveness.

[0068] In one possible implementation, the formula for determining stroke volume variability (SVV) is: Among them, SV max SV represents the maximum stroke volume of the target user within one respiratory cycle. min The minimum stroke volume for the target user within one respiratory cycle.

[0069] S42. When the stroke volume variability of the target user is greater than the second threshold, the processor advances the inflation and deflation times of the intra-aortic balloon counterpulsation system in the future time period according to the preset time advance.

[0070] The second threshold is determined based on the target user's positive end-expiratory pressure level, baseline left ventricular ejection fraction, and heart rate variability.

[0071] In one possible implementation, the formula for determining the second threshold is: SVV threshold = (λB1 + μB2 + vB3) × SVV base ; B2 = LVEF / 50; B3 = 1.2 - 0.005 × HRV; Wherein, λ is the fourth weighting coefficient, μ is the fifth weighting coefficient, and υ is the sixth weighting coefficient; B1 is the positive end-expiratory pressure level influencing factor; PEEP is the positive end-expiratory pressure level of the target user; B2 is the baseline left ventricular ejection fraction influencing factor; LVEF is the baseline left ventricular ejection fraction of the target user; B3 is the heart rate variability influencing factor; HRV is the heart rate variability of the target user; and SVVbase is the preset stroke volume variability.

[0072] In one example, λ is 0.5, μ is 0.3, υ is 0.2, and SVVbase is 13%. With the target user's PEEP = 12 cmH2O, LVEF = 35%, and HRV = 50 ms, the second threshold is 13.65%.

[0073] The method provided by this invention sets different weighting coefficients for the target user's positive end-expiratory pressure (PEEP) level, baseline left ventricular ejection fraction (LVEF), and heart rate variability (HRV). Then, it determines a second threshold based on the target user's PEEP level, LVEF, and HRV. This allows the second threshold to be adapted to users with different states and characteristics, thereby meeting the usage needs of different users in different usage scenarios and effectively improving the accuracy and safety of the intra-aortic balloon counterpulsation (IACP) system.

[0074] Optionally, S42 above specifically includes the following steps: If the variability of the target user's stroke volume is greater than a second threshold, the processor displays a second request on a preset interface. The second request is used to request a change in the inflation and deflation times of the intra-aortic balloon counterpulsation system for each balloon in a future time period. In response to the confirmation operation of the second request, the processor advances the inflation and deflation times of the intra-aortic balloon counterpulsation system for each balloon in a future time period according to a preset time advance.

[0075] In this way, the method provided by the present invention, by displaying the second request through a preset interface, enables the operator to quickly and accurately understand the stroke volume variability of the current target user, and then make timely adjustments to the intra-aortic balloon counterpulsation system based on the stroke volume variability of the target user. Furthermore, the method provided by the present invention allows the processor to rapidly control the balloon inflation and deflation time of the intra-aortic balloon counterpulsation system upon receiving confirmation information input by the operator, effectively improving the accuracy and safety of the intra-aortic balloon counterpulsation system control.

[0076] In one possible implementation, the method provided by the embodiments of the present invention further includes: If the processor generates a second alarm message to alert the operator when the target user's stroke volume variability exceeds a second threshold and the duration exceeds a preset time threshold.

[0077] In this way, the method provided by the embodiments of the present invention can enable the operator to quickly pay attention to the target user and take timely action when the inflation and deflation time of the balloon of the intra-aortic balloon counterpulsation system is set, but the stroke volume variability of the target user continues to exceed a preset time threshold greater than a second threshold, by means of a first alarm message.

[0078] As can be seen from the above, the method provided by the embodiments of the present invention obtains the stroke volume of the target user through a hemodynamic monitoring module, and then determines the stroke volume variability of the target user based on the stroke volume. In this way, it can realize real-time automatic control of the inflation and deflation timing of the balloon of the intra-aortic balloon counterpulsation system based on the stroke volume variability, thereby improving processing efficiency and reducing usage costs.

[0079] Although embodiments of the present invention have been shown and described above, it is understood that the above embodiments are exemplary and should not be construed as limiting the present invention. Those skilled in the art can make changes, modifications, substitutions and variations to the above embodiments within the scope of the present invention.

Claims

1. A control method for an intra-aortic balloon counterpulsation system based on hemodynamics, characterized in that, An intra-aortic balloon counterpulsation system is used, comprising an air cylinder, an air cylinder, an air balloon, a hemodynamic monitoring module, a processor, and a motor; the air cylinder, air cylinder, and air balloon are connected via an air circuit. The processor is electrically connected to the motor and the hemodynamic monitoring module respectively, and the motor is connected to the cylinder; The method includes: The hemodynamic monitoring module acquires the hemodynamic monitoring signals of the target user in real time, and the hemodynamic monitoring signals include cardiac output. The processor determines the target user's cardiac index based on the target user's cardiac output. When the target user's cardiac index is less than a first threshold, the processor sets the counterpulsation ratio of the intra-aortic balloon counterpulsation system to 1:1 and changes the balloon inflation volume of the intra-aortic balloon counterpulsation system from a first value to a second value. The ratio of the second value to the first value is a preset inflation volume increase ratio, and the first threshold is determined based on the target user's age, blood pressure, and ventilation status.

2. The method according to claim 1, characterized in that, The formula for determining the cardiac index (CI) of the target user is as follows: Wherein, CO is the cardiac output of the target user, and BSA is the body surface area per unit area of ​​the target user.

3. The method according to claim 2, characterized in that, The first threshold CI threshold The formula for determining it is: CI threshold =(αA1+βA2+γA3)×CI base ; A1 = Age / 70; Where α is the first weighting coefficient, β is the second weighting coefficient, and γ is the third weighting coefficient; A1 is the age influence factor; Age is the target user's age; A2 is the blood pressure influence factor; BP is the target user's maximum blood pressure; A3 is the ventilation status influence factor; and when the target user's ventilation status is mechanical ventilation, A3 = 1.5, and when the target user's ventilation status is non-mechanical ventilation, A3 = 1, CI base Preset heart rate index.

4. The method according to claim 3, characterized in that, When the target user's cardiac index is less than a first threshold, the processor sets the counterpulsation ratio of the intra-aortic balloon counterpulsation system to 1:1 and changes the balloon inflation volume of the intra-aortic balloon counterpulsation system from a first value to a second value, including: When the target user’s cardiac index is less than a first threshold, the processor displays a first request on a preset interface. The first request is used to request a change in the counterpulsation ratio and balloon inflation volume of the intra-aortic balloon counterpulsation system. In response to the confirmation operation of the first request, the processor sets the counterpulsation ratio of the intra-aortic balloon counterpulsation system to 1:1 and changes the balloon inflation volume of the intra-aortic balloon counterpulsation system from a first value to a second value.

5. The method according to claim 4, characterized in that, The hemodynamic monitoring signal also includes stroke volume, and the method further includes: The processor determines the stroke volume variability of the target user based on the stroke volume of the target user. When the stroke volume variability of the target user is greater than a second threshold, the processor advances the inflation and deflation times of the intra-aortic balloon counterpulsation system for each balloon in the future time period according to a preset time advance amount. The second threshold is determined based on the target user's positive end-expiratory pressure level, baseline left ventricular ejection fraction, and heart rate variability.

6. The method according to claim 5, characterized in that, The formula for determining the stroke volume variability (SVV) is as follows: Among them, SV max SV is the maximum stroke volume of the target user within one respiratory cycle. min The minimum stroke volume of the target user within one respiratory cycle; The formula for determining the second threshold is: SVV threshold =(λB1+μB2+υB3)×SVV base ; B2 = LVEF / 50; B3 = 1.2 - 0.005 × HRV; Wherein, λ is the fourth weighting coefficient, μ is the fifth weighting coefficient, and υ is the sixth weighting coefficient; B1 is the positive end-expiratory pressure level influencing factor; PEEP is the positive end-expiratory pressure level of the target user; B2 is the baseline left ventricular ejection fraction influencing factor; LVEF is the baseline left ventricular ejection fraction of the target user; B3 is the heart rate variability influencing factor; HRV is the heart rate variability of the target user; and SVVbase is the preset stroke volume variability.

7. The method according to claim 6, characterized in that, When the stroke volume variability of the target user exceeds a second threshold, the processor advances the inflation and deflation times of the intra-aortic balloon counterpulsation system for each balloon in a future time period according to a preset time advance, including: When the stroke volume variability of the target user is greater than a second threshold, the processor displays a second request on a preset interface. The second request is used to request a change in the inflation and deflation times of the balloon in the intra-aortic balloon counterpulsation system in the future time period. In response to the confirmation operation of the second request, the processor advances the inflation and deflation times of the intra-aortic balloon counterpulsation system for each balloon in a future time period according to a preset time advance.

8. The method according to claim 7, characterized in that, When the hemodynamic monitoring module and the balloon are positioned within the same artery of the target user, after the hemodynamic monitoring module acquires the target user's hemodynamic monitoring signal in real time, the method further includes: The processor filters out signals in the hemodynamic monitoring signal whose frequency is less than or equal to a preset threshold.

9. An intra-aortic balloon counterpulsation system, characterized in that, The intra-aortic balloon counterpulsation system includes an air cylinder, an air cylinder, an air balloon, a hemodynamic monitoring module, a processor, and a motor; the air cylinder, air cylinder, and air balloon are connected via an air circuit; the processor is electrically connected to the motor and the hemodynamic monitoring module respectively, and the motor is connected to the air cylinder; The hemodynamic monitoring module is used for: Real-time acquisition of hemodynamic monitoring signals of the target user, including cardiac output; The processor is used for: The cardiac index of the target user is determined based on the target user's cardiac output. The processor is also used for: If the target user's cardiac index is less than a first threshold, the counterpulsation ratio of the intra-aortic balloon counterpulsation system is set to 1:1, and the balloon inflation volume of the intra-aortic balloon counterpulsation system is changed from a first value to a second value. The ratio of the second value to the first value is a preset inflation volume increase ratio, and the first threshold is determined based on the target user's age, blood pressure, and ventilation status.

10. An electronic device, characterized in that, include: processor; Memory used to store the processor's executable instructions; The processor is configured to execute the instructions to implement the hemodynamic-based intra-aortic balloon counterpulsation system control method as described in any one of claims 1-8.

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