A pressure monitoring system for hysteroscopic surgery and its adaptive flow rate control method

Abstract

The present invention discloses a pressure monitoring system for hysteroscopic surgery and an adaptive flow rate control method thereof, and relates to the technical field of hysteroscopic surgery pressure monitoring and flow rate control. By obtaining the internal pressure value of the uterine cavity and the pressure value of the infusion line, and based on the pressure of the infusion line, analyzing the influence of liquid flow resistance, dynamic viscosity, density and flow rate change on the pressure, an infusion line pressure dynamic compensation model is established to calculate the real pressure value of the infusion line, and compare it with the internal pressure value of the uterine cavity to obtain the pressure deviation index. If the deviation index exceeds the threshold, the excess value is calculated, and the abnormal classification is performed, the feedback level is set, and a PID control equation is constructed to adjust the flow rate of the infusion pump. Through the PID control equation, the flow rate of the infusion pump is adjusted in real time, and the adjusted uterine cavity pressure is monitored and fed back, thereby achieving accurate flow rate control and pressure regulation, and improving the safety of the operation.

Description

Technical Field

[0001] The present invention relates to the technical field of hysteroscopic surgery pressure monitoring and flow rate control thereof, in particular to a hysteroscopic surgery pressure monitoring system and an adaptive flow rate control method thereof. Background Art

[0002] Hysteroscopic surgery is a minimally invasive surgery that is widely used to treat intrauterine lesions, such as endometrial polyps, endometriosis, uterine fibroids, etc. With the advancement of medical technology and the popularity of minimally invasive surgery, hysteroscopic surgery is becoming more and more widely used. During hysteroscopic surgery, excessive or low pressure in the uterine cavity can cause adverse effects on patients, such as uterine perforation and postoperative adhesions. Therefore, accurate monitoring and control of uterine cavity pressure to avoid intraoperative complications has become an urgent need in the medical industry.

[0003] For example, the uterine cavity pressure monitoring device and surgical system with the publication number CN116439848A includes a first pressure sensor, a second pressure sensor and a controller. The first pressure sensor is installed at the insertion end of the hysteroscope sheath and detects the first pressure value of the uterine cavity inside the uterine cavity. The second pressure sensor is installed in the infusion line of the perfusion device and detects the pressure value of the infusion line. The controller obtains the first pressure value and the pressure value of the infusion line, so as to determine the second pressure value of the uterine cavity through the pressure value of the infusion line, and to determine whether the detection result of the first pressure sensor is unreliable based on the first pressure value with the second pressure value as a reference value. The installation position of the second pressure sensor is different from that of the first pressure sensor, so it is difficult to be affected by the same interference factors, and avoids the interruption of surgery and damage to the uterine cavity caused by the measurement error caused by the failure of the pressure sensor or the interference of the environment.

[0004] However, the second pressure sensor in this method is located far away from the uterine cavity, which means that the pressure value measured by it may be affected by factors such as liquid resistance and bubbles in the infusion line, resulting in the accumulation of measurement errors. The line pressure value measured by the sensor is not completely equivalent to the actual uterine cavity pressure. If the error is too large, it may cause the controller to make an incorrect judgment on the detection result of the first pressure sensor, thereby affecting the surgical operation. Summary of the invention

[0005] In view of the deficiencies of the prior art, the present invention provides a pressure monitoring system for hysteroscopic surgery and an adaptive flow rate control method thereof, which solve the problems of the above-mentioned background technology.

[0006] To achieve the above objectives, the present invention is implemented through the following technical solutions: a hysteroscopic surgery pressure monitoring system, comprising the following modules: a pressure data acquisition module, a pressure data analysis module, a pressure judgment module, and a display warning module; the pressure data acquisition module is used to obtain the internal pressure value of the uterine cavity and the pressure value of the infusion pipeline through a pressure sensor; the pressure data analysis module is used to analyze the influence of the flow resistance of the liquid in the infusion pipeline, the dynamic viscosity of the liquid, the liquid density, and the change of the liquid flow rate on the pressure of the infusion pipeline based on the infusion pipeline pressure, and establish an infusion pipeline pressure dynamic compensation model; the pressure judgment module is used to obtain the true value of the infusion pipeline pressure based on the infusion pipeline pressure dynamic compensation model, and compare it with the internal pressure value of the uterine cavity to obtain the pressure deviation index. If the pressure deviation index exceeds the set threshold range, a warning message is generated and sent to the display warning module. If the pressure deviation index is within the threshold range, the internal pressure value of the uterine cavity is monitored and analyzed in real time; the display warning module is used to receive the warning message sent by the pressure judgment module, the warning message includes the flow rate of the infusion pump, and is visually displayed.

[0007] Furthermore, the specific process of analyzing the influence of liquid flow resistance, liquid dynamic viscosity, liquid density, and liquid flow rate changes in the infusion pipeline on the infusion pipeline pressure is as follows: obtain the geometric parameters of the infusion pipeline and the physical parameters of the liquid; analyze the influence of liquid dynamic viscosity and flow rate on pressure through the Hagen-Poiseuille equation, and obtain the pressure drop value caused by flow resistance in the pipeline; analyze the influence of liquid density and flow rate on pressure through the Bernoulli equation, and obtain the pressure drop value caused by flow rate changes and cross-sectional area changes in the pipeline.

[0008] Furthermore, the specific process of establishing the dynamic compensation model for infusion pipeline pressure is as follows: comprehensively analyze the pressure drop value caused by flow resistance in the pipeline and the pressure drop value caused by flow velocity change and cross-sectional area change in the pipeline, and construct the built-in equation of the dynamic compensation model for infusion pipeline pressure; input the built-in equation of the dynamic compensation model for infusion pipeline pressure into the fluid mechanics model to construct the dynamic compensation model for infusion pipeline pressure.

[0009] Furthermore, based on the infusion line pressure dynamic compensation model, the actual value of the infusion line pressure is obtained as follows: the infusion line pressure compensation value is obtained through the infusion line pressure dynamic compensation model; the infusion line pressure compensation value and the infusion line pressure value are differenced to obtain the actual value of the infusion line pressure.

[0010] Furthermore, the pressure deviation index is obtained as follows: a difference operation is performed between the actual value of the infusion line pressure and the internal pressure value of the uterine cavity, and a comprehensive operation is performed with the allowable deviation value of the internal pressure of the uterine cavity to obtain the pressure deviation index.

[0011] A method for adaptive flow rate control in hysteroscopic surgery comprises the following steps: S1. obtaining a pressure deviation index through a pressure judgment module, and calculating a pressure excess value when the pressure deviation index exceeds a set threshold range; S2. classifying the pressure excess value as abnormal, setting a feedback level, and constructing a PID pressure control equation; S3. determining the flow rate of an infusion pump through the pressure control equation, and controlling the flow rate of the infusion pump; S4. monitoring the adjusted internal pressure value of the uterine cavity and performing feedback regulation.

[0012] Furthermore, the specific process of constructing the PID pressure control equation is as follows: taking the pressure excess value as the input of the PID controller, setting the proportional gain, integral gain and differential gain as the parameters of the PID controller; substituting the proportional gain, integral gain and differential gain into the PID control equation through the PID control algorithm, setting the flow rate of the infusion pump as the output, and constructing the PID pressure control equation.

[0013] Furthermore, the specific process of controlling the flow rate of the infusion pump is as follows: inputting the pressure excess value into the PID pressure control equation to obtain the flow rate of the infusion pump; based on the flow rate of the infusion pump, controlling the flow rate of the infusion pump through the PID controller.

[0014] Furthermore, the process of monitoring the adjusted internal uterine cavity pressure value and performing feedback adjustment is as follows: the adjusted internal uterine cavity pressure adjustment value is obtained in real time through the pressure sensor; the internal uterine cavity pressure adjustment value is compared with the actual value of the infusion line pressure to determine whether the pressure deviation index exceeds the set threshold range. If it exceeds, the flow rate of the infusion pump is adjusted through the PID controller.

[0015] The present invention has the following beneficial effects:

[0016] (1) This hysteroscopic surgery pressure monitoring system obtains the internal pressure value of the uterine cavity and the pressure value of the infusion line in real time through the pressure sensor, and analyzes the influence of the liquid flow resistance, dynamic viscosity, density and flow rate changes in the infusion line on the pressure. The established pressure dynamic compensation model can accurately determine the true value of the infusion line pressure, thereby improving the accuracy of monitoring, ensuring the real-time and reliability of pressure monitoring, and effectively monitoring the changes in the internal pressure of the uterine cavity during the operation to avoid surgical risks caused by pressure fluctuations. It can automatically determine the pressure deviation index and generate early warning information based on the set threshold. The display early warning module visualizes the early warning information so that medical staff can understand and deal with abnormal situations in a timely manner, thereby improving the safety of the operation. Multiple levels of pressure monitoring and feedback control are designed to ensure that the internal pressure of the uterine cavity is within a safe and stable range during hysteroscopic surgery.

[0017] (2) This adaptive flow rate control method for hysteroscopic surgery can accurately adjust the flow rate of the infusion pump by obtaining the pressure deviation index and constructing the PID pressure control equation based on the deviation index, thereby achieving accurate control of the internal pressure of the uterine cavity and ensuring the stability of the surgical environment. When the pressure deviation index exceeds the set threshold range, the system can quickly identify the abnormality and dynamically adjust the control strategy by setting the feedback level to ensure that the internal pressure of the uterine cavity can be restored to a safe range in time under abnormal conditions. Through the automatic adjustment and feedback mechanism of the PID control algorithm, the adaptive control of the flow rate of the infusion pump is achieved, the need for manual intervention is reduced, the efficiency and accuracy of the surgical process are improved, and the workload of medical staff is reduced. By dynamically controlling the flow rate of the infusion pump and continuously monitoring the internal pressure of the uterine cavity, this method effectively prevents surgical complications caused by improper pressure and ensures the safety of patients during surgery.

[0018] Of course, any product implementing the present invention does not necessarily need to achieve all of the advantages described above at the same time. BRIEF DESCRIPTION OF THE DRAWINGS

[0019] Figure 1 The present invention is a flow chart of a hysteroscopic surgery pressure monitoring system.

[0020] Figure 2 This is a flow chart of a method for adaptive flow rate control in hysteroscopic surgery according to the present invention. DETAILED DESCRIPTION

[0021] The embodiment of the present application solves the problem of difficulty in accurately monitoring the internal pressure of the uterine cavity and controlling the flow rate of the infusion pump during hysteroscopic surgery by providing a pressure monitoring system for hysteroscopic surgery and an adaptive flow rate control method thereof.

[0022] The overall idea of ​​the problem in the embodiment of this application is as follows:

[0023] The internal pressure value of the uterine cavity and the pressure value of the infusion line are obtained through the pressure sensor. Based on the infusion line pressure, the influence of the liquid flow resistance, liquid dynamic viscosity, liquid density, and liquid flow rate changes in the infusion line on the infusion line pressure is analyzed, and an infusion line pressure dynamic compensation model is established.

[0024] Based on the dynamic compensation model of infusion line pressure, the true value of the infusion line pressure is obtained and compared with the internal pressure value of the uterine cavity to obtain the pressure deviation index. If the pressure deviation index is within the threshold range, the internal pressure value of the uterine cavity is monitored and analyzed in real time and displayed visually.

[0025] If the pressure deviation index exceeds the set threshold range, a pressure excess value at which the pressure deviation index exceeds the set threshold range is calculated.

[0026] Abnormal pressure excess values ​​are classified, feedback levels are set, and a PID pressure control equation is constructed. The flow rate of the infusion pump is determined by the pressure control equation, the flow rate of the infusion pump is controlled, and the adjusted internal uterine cavity pressure value is monitored and feedback is adjusted.

[0027] See also Figure 1 The embodiment of the present invention provides a technical solution: a hysteroscopic surgery pressure monitoring system, comprising the following modules: a pressure data acquisition module, a pressure data analysis module, a pressure judgment module, and a display warning module; the pressure data acquisition module is used to obtain the internal pressure value of the uterine cavity and the pressure value of the infusion pipeline through a pressure sensor; the pressure data analysis module is used to analyze the influence of the flow resistance of the liquid in the infusion pipeline, the dynamic viscosity of the liquid, the liquid density, and the change of the liquid flow rate on the infusion pipeline pressure based on the infusion pipeline pressure, and establish an infusion pipeline pressure dynamic compensation model; the pressure judgment module is used to obtain the true value of the infusion pipeline pressure based on the infusion pipeline pressure dynamic compensation model, and compare it with the internal pressure value of the uterine cavity to obtain the pressure deviation index. If the pressure deviation index exceeds the set threshold range, a warning message is generated and sent to the display warning module. If the pressure deviation index is within the threshold range, the internal pressure value of the uterine cavity is monitored and analyzed in real time; the display warning module is used to receive the warning message sent by the pressure judgment module, the warning message includes the flow rate of the infusion pump, and is displayed visually.

[0028] In this embodiment, the hysteroscopic surgery pressure monitoring system is a system for monitoring and controlling the internal pressure of the uterine cavity during hysteroscopic surgery. It includes multiple modules that work together to ensure that the pressure in the uterine cavity during surgery remains within a safe range. The pressure data acquisition module obtains the pressure value inside the uterine cavity and the pressure value in the infusion line in real time through a pressure sensor. The internal pressure of the uterine cavity refers to the liquid pressure in the uterine cavity, and the infusion line pressure refers to the pressure of the liquid in the infusion system in the line. The pressure sensor is a device for measuring pressure, which is used to capture the pressure value inside the uterine cavity and in the infusion line. It converts physical pressure into an electrical signal for subsequent analysis and processing. The pressure data analysis module is used to analyze and process the acquired pressure data, which is based on the infusion line pressure and evaluates the factors affecting the pressure, including the flow resistance of the liquid, dynamic viscosity (the inherent resistance of the liquid to flow), density (mass density of the liquid) and flow rate change. The purpose of the analysis is to construct a dynamic compensation model for accurately calculating the actual infusion line pressure. The infusion line pressure dynamic compensation model is a mathematical model used to correct the infusion line pressure data to reflect the real pressure condition. It takes into account the flow characteristics and other physical properties of the liquid in the pipeline, aiming to provide a more accurate pressure value. The pressure judgment module is used to calculate the true pressure value of the infusion pipeline using a dynamic compensation model and compare it with the pressure value inside the uterine cavity. Through this comparison, the "pressure deviation index", that is, the difference between the actual pressure and the expected pressure, is calculated. The pressure deviation index is an indicator that measures the difference between the actual pressure inside the uterine cavity and the preset safety pressure range. If the index exceeds the set threshold range, it means that there is abnormal pressure and adjustment or alarm is required. The display warning module is used to receive the warning information issued by the pressure judgment module and visualize the information. The warning information may include abnormal conditions detected by the system and the flow rate information of the infusion pump to prompt the operator to take corresponding measures.

[0029] Specifically, the specific process of analyzing the influence of liquid flow resistance, liquid dynamic viscosity, liquid density, and liquid flow rate changes in the infusion pipeline on the infusion pipeline pressure is as follows: obtain the geometric parameters of the infusion pipeline and the physical parameters of the liquid; analyze the influence of liquid dynamic viscosity and flow rate on pressure through the Hagen-Poiseuille equation, and obtain the pressure drop value caused by flow resistance in the pipeline; analyze the influence of liquid density and flow rate on pressure through the Bernoulli equation, and obtain the pressure drop value caused by flow rate changes and cross-sectional area changes in the pipeline.

[0030] In this embodiment, the geometric parameters of the infusion pipeline and the physical parameters of the liquid are obtained. The geometric parameters refer to the shape, size, length and diameter of the infusion pipeline. These parameters will directly affect the flow characteristics of the liquid in the pipeline. The physical parameters refer to the physical properties of the density, viscosity and temperature of the liquid, which determine how the liquid flows in the infusion pipeline. The Hagen-Poiseuille equation is used to analyze the influence of the dynamic viscosity and flow rate of the liquid on the pressure. The Hagen-Poiseuille equation is a classic fluid mechanics equation used to analyze the pressure drop when the viscous liquid flows under laminar flow conditions in a circular pipe. The main parameters of the equation include the dynamic viscosity of the liquid, the length and radius of the pipe, and the volume flow rate of the liquid. The dynamic viscosity of the liquid is a measure of the internal friction of the liquid, which affects the flow resistance of the liquid in the pipe. Higher viscosity increases the flow resistance, resulting in a greater pressure drop. Flow rate is the volume of liquid flowing through the pipe per unit time. An increase in flow rate usually leads to a greater pressure drop, especially in liquids with higher viscosity. Pressure drop value By calculating these parameters, the Hagen-Poiseuille equation can help us determine the pressure loss in the pipeline due to the viscosity and flow rate of the liquid. The degree of influence of liquid density and flow rate on pressure is analyzed through the Bernoulli equation. The Bernoulli equation is an energy conservation equation used to describe the energy conversion relationship of an ideal fluid in steady-state flow. The equation takes into account the relationship between the kinetic energy, potential energy and pressure energy of the liquid. Liquid density is the mass of liquid per unit volume. Changes in density will affect the flow rate and pressure of the liquid. Flow rate refers to the flow speed of the liquid in the pipe. According to the Bernoulli principle, where the flow rate increases, the pressure of the fluid decreases, and vice versa. The pressure drop value is used to calculate the pressure drop caused by changes in liquid density and flow rate. Especially when the cross-sectional area of ​​the pipe changes, the flow rate changes significantly, and the impact of the pressure drop is more significant. Calculate the pressure drop value caused by flow resistance, ,in, Indicates the pressure drop value caused by flow resistance, represents the dynamic viscosity of the liquid, represents the friction inside the liquid, Indicates the length of the infusion line. represents the volume flow rate of the liquid, The specific formula for calculating the pressure drop caused by the change in flow rate and cross-sectional area is as follows: ,in, Indicates the pressure drop value caused by changes in flow velocity and cross-sectional area. represents the density of the liquid, The flow rate before the pipe cross-sectional area changes, Indicates the cross-sectional area of ​​the pipeline before the cross-sectional area changes. Indicates the cross-sectional area of ​​the pipeline after the cross-sectional area changes. Indicates the flow rate after the pipe cross-sectional area changes.

[0031] Specifically, the specific process of establishing the dynamic compensation model for infusion pipeline pressure is as follows: comprehensively analyze the pressure drop value caused by flow resistance in the pipeline and the pressure drop value caused by flow velocity change and cross-sectional area change in the pipeline, and construct the built-in equation of the dynamic compensation model for infusion pipeline pressure; input the built-in equation of the dynamic compensation model for infusion pipeline pressure into the fluid mechanics model to construct the dynamic compensation model for infusion pipeline pressure.

[0032] In this embodiment, the pressure drop value refers to the pressure loss caused by various resistances and speed changes generated during the flow of liquid in the infusion pipeline. The pressure drop value caused by flow resistance comes from the pressure loss of the liquid in the pipeline due to factors such as viscosity and friction, and is usually calculated using the Hagen-Poiseuille equation. The pressure drop value caused by flow velocity change and cross-sectional area change comes from the pressure loss caused by the Bernoulli principle when the flow velocity or pipe cross-sectional area of ​​the liquid in the pipeline changes. When establishing a dynamic compensation model, it is necessary to conduct a comprehensive analysis of the pressure drop values ​​from these different sources to ensure that the model can accurately reflect the actual pressure in the pipeline. The built-in equation is the core of the dynamic compensation model for infusion pipeline pressure, which comprehensively considers factors such as flow resistance, flow velocity change, and pipe cross-sectional area change. Through the built-in equation, the pressure compensation value in the infusion pipeline can be dynamically calculated. The built-in equation is used as part of the fluid mechanics model to further construct a model that can dynamically adjust and compensate for pressure. The fluid mechanics model can simulate and predict the behavior of the fluid in the infusion pipeline, thereby helping the system to achieve real-time pressure monitoring and regulation. The built-in equation of the dynamic compensation model for infusion pipeline pressure can be expressed as: ,in, It represents the dynamic compensation value of the infusion line pressure, which is calculated by the built-in equation and combines the pressure drop value caused by the flow resistance and flow velocity change.

[0033] Specifically, based on the infusion line pressure dynamic compensation model, the actual value of the infusion line pressure is obtained as follows: the infusion line pressure compensation value is obtained through the infusion line pressure dynamic compensation model; the infusion line pressure compensation value and the infusion line pressure value are differenced to obtain the actual value of the infusion line pressure.

[0034] In this implementation scheme, the pressure compensation value is calculated through the infusion pipeline pressure dynamic compensation model, which reflects the pressure loss caused by factors such as resistance encountered by the liquid when flowing in the pipeline, flow velocity changes, and changes in the cross-sectional area of ​​the pipeline. The compensation value is used to correct the measured infusion pipeline pressure value to make it closer to the actual pressure situation. In order to obtain the true pressure value of the infusion pipeline, it is necessary to calculate the actually measured infusion pipeline pressure value and the compensation value. The main purpose of this step is to eliminate the pressure error caused by the above factors, so that the final true pressure value can more accurately reflect the actual pressure in the pipeline. Calculate the pressure compensation value. According to the previous infusion pipeline pressure dynamic compensation model, the pressure compensation value is the pressure drop caused by flow resistance The pressure drop caused by the change of flow velocity and cross-sectional area The sum of is as follows: , get the real value of the infusion line pressure, the real value of the pressure The actual measured pressure value of the infusion pipeline is Subtract pressure compensation value The calculated formula is as follows: ,in, Indicates the actual measured pressure value of the infusion pipeline. It represents the pressure compensation value calculated by the dynamic compensation model, which is used to correct the pressure error caused by various physical factors.

[0035] Specifically, the pressure deviation index is obtained as follows: a difference operation is performed between the actual value of the infusion line pressure and the internal pressure value of the uterine cavity, and a comprehensive operation is performed with the allowable deviation value of the internal pressure of the uterine cavity to obtain the pressure deviation index.

[0036] In this implementation scheme, the difference between the actual pressure value of the infusion line and the internal pressure value of the uterine cavity is calculated. The purpose of this step is to determine the deviation between the infusion line pressure and the actual pressure inside the uterine cavity. The above-calculated pressure difference and the allowable deviation value of the internal uterine cavity pressure are comprehensively calculated. The allowable deviation value of the internal uterine cavity pressure is a preset threshold value, which indicates the maximum error range that the internal uterine cavity pressure can withstand during the operation. The result obtained by comprehensive calculation is the pressure deviation index. This index reflects the degree of deviation between the current infusion line pressure and the internal uterine cavity pressure, and is used to determine whether it is necessary to adjust the flow rate of the infusion pump or take other adjustment measures. Pressure difference The actual value of the infusion line pressure and intrauterine pressure The difference between is calculated as follows: ; The calculation process of the pressure deviation index obtained by comprehensive operation is as follows: By using the pressure difference The allowable deviation from the internal pressure of the uterine cavity After calculation, the formula is as follows:

[0037] ,in, , the actual value of the infusion line pressure, Indicates the internal pressure value of the uterine cavity. , the allowable deviation value of internal uterine cavity pressure.

[0038] See also Figure 2, a method for adaptive flow rate control in hysteroscopic surgery, comprising the following steps: S1. obtaining a pressure deviation index through a pressure judgment module, and calculating a pressure excess value when the pressure deviation index exceeds a set threshold range; S2. classifying the pressure excess value as abnormal, setting a feedback level, and constructing a PID pressure control equation; S3. determining the flow rate of an infusion pump through the pressure control equation, and controlling the flow rate of the infusion pump; S4. monitoring the adjusted internal pressure value of the uterine cavity and performing feedback regulation.

[0039] In this embodiment, step S1 obtains the pressure deviation index and calculates the pressure excess value. When the pressure deviation index exceeds the set safety threshold range, it means that the pressure in the uterine cavity may not meet the surgical requirements. At this time, it is necessary to further calculate the pressure excess value of the index exceeding the set threshold, that is, the degree of deviation from the ideal pressure. This value will serve as the basis for subsequent control and adjustment. Step S2. Classify the pressure excess value abnormally, set the feedback level, and construct the PID pressure control equation. The abnormal classification is to classify it into different levels of abnormal conditions according to the size of the pressure excess value. Each level corresponds to a different control strategy and response speed. Setting the feedback level is to set the corresponding feedback level for different abnormal classifications and determine the adjustment strength of the PID controller. According to the abnormal classification, a proportional-integral-differential (PID) control equation is constructed. The PID controller optimizes the response to the pressure excess value by adjusting the three parameters of proportional gain, integral gain and differential gain, so that the system can quickly and stably return to the ideal state. Step S3. Determine the flow rate of the infusion pump and control it. The most suitable flow rate of the infusion pump is calculated through the PID pressure control equation in S2. This flow rate adjustment is based on the current pressure excess value, ensuring that the liquid flow rate can quickly and effectively restore the pressure in the uterine cavity to the set range. The calculated flow rate value is directly applied to the infusion pump so that its output flow rate meets the current surgical requirements, thereby keeping the pressure in the uterine cavity within a safe range. Step S4 monitors the adjusted internal pressure value of the uterine cavity and performs feedback adjustment. After adjusting the flow rate of the infusion pump, the system continues to monitor the real-time pressure value inside the uterine cavity through the pressure sensor. Feedback adjustment means that if the monitored pressure still does not reach the ideal range, the system will recalculate the pressure deviation and adjust the flow rate again through the PID controller until the pressure stabilizes within the target range. This process ensures that the pressure in the uterine cavity can be continuously and stably maintained within a safe value, effectively reducing surgical risks.

[0040] Specifically, the specific process of constructing the PID pressure control equation is as follows: take the pressure excess value as the input of the PID controller, set the proportional gain, integral gain and differential gain as the parameters of the PID controller; substitute the proportional gain, integral gain and differential gain into the PID control equation through the PID control algorithm, set the flow rate of the infusion pump as the output, and construct the PID pressure control equation.

[0041] In this implementation, the process of constructing the PID pressure control equation uses the pressure excess value as the input signal, and uses the pressure excess value as the input signal of the PID controller. The pressure excess value represents the difference between the current measured pressure and the target pressure. Set controller parameters: proportional gain : The controller's response speed to the current error, that is, the direct amplification of the pressure excess value, the integral gain : The controller's response to the accumulated error is used to eliminate the steady-state error and ensure that the pressure eventually reaches the set value. The differential gain : The controller's response to the error change rate is used to predict the error change trend, reduce the overshoot and oscillation of the system, and construct the PID control equation as follows: The output signal of the PID controller (i.e., the flow rate of the infusion pump) is calculated by the following equation: ,in, represents the output of the PID controller (the flow rate of the infusion pump), Indicates that the pressure exceeds the value (error value), Represents the proportional gain, the controller's response speed to the current error, represents the integral gain, the cumulative effect of the control error, Represents the differential gain, which controls the rate of change of the error.

[0042] Specifically, the specific process of controlling the flow rate of the infusion pump is as follows: input the pressure excess value into the PID pressure control equation to obtain the flow rate of the infusion pump; based on the flow rate of the infusion pump, control the flow rate of the infusion pump through the PID controller.

[0043] In this embodiment, the pressure excess value is the difference between the actual pressure inside the uterine cavity and the preset target pressure, that is, the deviation between the current pressure and the ideal pressure. When the pressure excess value is large, it means that the pressure in the uterine cavity is far higher or lower than expected, which may affect the safety of the operation. This pressure excess value is used as an input signal and sent to the PID control equation. The PID control equation calculates an adjustment amount suitable for the current situation based on the input pressure excess value. The PID control equation refers to the PID (proportional-integral-differential) control equation, which is a classic control algorithm that adjusts the system output through three parts: Proportional (P): directly proportional to the current pressure excess value, with strong adjustment force and fast response. Integral (I): Adjust according to the cumulative deviation of the pressure excess value over time to eliminate long-standing steady-state errors. Differential (D): Predictive adjustment is performed based on the speed of change of the pressure excess value to reduce system oscillation and prevent over-adjustment. The PID control equation comprehensively calculates these adjustment factors and outputs an accurate infusion pump flow rate value. This flow rate value corresponds to the current pressure excess value, and the purpose is to correct the pressure deviation in the uterine cavity by adjusting the flow rate. The flow rate value calculated by the PID control equation is directly applied to the infusion pump control system. The infusion pump automatically adjusts the liquid delivery rate according to the received flow rate value. For example, if the current pressure excess value is positive and large, it means that the uterine cavity pressure is too high, and the PID controller may reduce the infusion flow rate; conversely, if the pressure is too low, the PID controller will increase the flow rate to replenish the amount of liquid in the uterine cavity.

[0044] Specifically, the process of monitoring the adjusted internal uterine cavity pressure value and performing feedback adjustment is as follows: the adjusted internal uterine cavity pressure adjustment value is obtained in real time through the pressure sensor; the internal uterine cavity pressure adjustment value is compared with the actual value of the infusion line pressure to determine whether the pressure deviation index exceeds the set threshold range. If exceeded, the flow rate of the infusion pump is adjusted through the PID controller.

[0045] In this embodiment, the pressure sensor is one of the core components of the entire system and is responsible for measuring the actual pressure in the uterine cavity in real time. The adjusted internal pressure value of the uterine cavity refers to the current pressure in the uterine cavity measured again after system adjustment (such as adjusting the flow rate of the infusion pump through a PID controller). The pressure sensor continuously monitors the pressure inside the uterine cavity and transmits the adjusted pressure value obtained to the system as an important input data for the next feedback adjustment. The pressure adjustment value is the current actual pressure in the uterine cavity obtained by the pressure sensor. The true value of the infusion line pressure is the accurate pressure value corrected by the dynamic compensation model based on various influencing factors of the infusion line (such as flow resistance, liquid dynamic viscosity, etc.). It reflects the contribution of the liquid in the infusion line to the uterine cavity pressure. The pressure deviation index is the result of the above comparison process, which indicates the difference between the actual pressure in the uterine cavity and the theoretical pressure. If the pressure deviation index is within the set threshold range, it means that the uterine cavity pressure is maintained within a reasonable range; if it exceeds the threshold, it means that there is an abnormality and further adjustment may be required. The set threshold range is the allowable range of pressure deviation set according to the safety requirements of the operation. As long as the pressure deviation index is within this range, the system does not need to be adjusted; when it exceeds this range, immediate measures need to be taken. If the system determines that the pressure deviation index exceeds the set threshold range, it means that the uterine cavity pressure has deviated from the ideal control target. At this time, the PID controller will adjust the flow rate of the infusion pump according to the degree of deviation. The PID controller accurately controls the flow rate of the infusion pump through the aforementioned proportional, integral, and differential adjustment algorithms. Increase or decrease the liquid flow rate to correct the pressure in the uterine cavity and return it to the set safety range.

[0046] In summary, this application has at least the following effects:

[0047] A pressure monitoring system for hysteroscopic surgery and an adaptive flow rate control method thereof are provided, by setting a pressure data acquisition module, a pressure data analysis module, a pressure judgment module, and a display warning module. By acquiring the internal pressure value of the uterine cavity and the pressure value of the infusion line, and based on the pressure of the infusion line, analyzing the influence of liquid flow resistance, dynamic viscosity, density and flow rate change on the pressure, an infusion line pressure dynamic compensation model is established to calculate the true pressure value of the infusion line, and compare it with the internal pressure value of the uterine cavity to obtain the pressure deviation index. If the deviation index exceeds the threshold, the excess value is calculated, and the abnormal classification is performed, the feedback level is set, and a PID control equation is constructed to adjust the flow rate of the infusion pump. Through the PID control equation, the flow rate of the infusion pump is adjusted in real time, and the adjusted uterine cavity pressure is monitored and fed back, thereby achieving accurate flow rate control and pressure regulation, and improving the safety of the operation.

[0048] It will be appreciated by those skilled in the art that embodiments of the present invention may be provided as methods, systems, or computer program products. Therefore, the present invention may take the form of a complete hardware embodiment, a complete software embodiment, or an embodiment combining software and hardware. Furthermore, the present invention may take the form of a computer program product implemented on one or more computer-usable storage media (including but not limited to disk storage, CD-ROM, optical storage, etc.) containing computer-usable program code.

[0049] The present invention is described with reference to flowcharts and / or block diagrams of systems, devices (systems), and computer program products according to embodiments of the present invention. It should be understood that each process and / or block in the flowchart and / or block diagram, as well as the combination of processes and / or blocks in the flowchart and / or block diagram, can be implemented by computer program instructions. These computer program instructions can be provided to a processor of a general-purpose computer, a special-purpose computer, an embedded processor, or other programmable data processing device to produce a machine, so that the instructions executed by the processor of the computer or other programmable data processing device generate instructions for implementing the processes in the flowchart and / or block diagram. Figure 1 A process or multiple processes and / or boxes Figure 1 A device that provides the functions specified in a block or multiple blocks.

[0050] These computer program instructions may also be stored in a computer-readable memory capable of directing a computer or other programmable data processing device to operate 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 A function specified in one or more boxes.

[0051] These computer program instructions can also be loaded onto a computer or other programmable data processing device so that a series of operating steps are executed on the computer or other programmable device to produce a computer-implemented process, thereby providing instructions for implementing the process. Figure 1 A process or multiple processes and / or boxes Figure 1 The steps for the functions specified in one or more boxes.

[0052] Although the preferred embodiments of the present invention have been described, those skilled in the art may make other changes and modifications to these embodiments once they have learned the basic creative concept. Therefore, the appended claims are intended to be interpreted as including the preferred embodiments and all changes and modifications that fall within the scope of the present invention.

[0053] Obviously, those skilled in the art can make various changes and modifications to the present invention without departing from the spirit and scope of the present invention. Thus, if these modifications and variations of the present invention fall within the scope of the claims of the present invention and their equivalents, the present invention is also intended to include these modifications and variations.

Claims

1. A hysteroscopic surgery pressure monitoring system, characterized in that: It includes the following modules: pressure data acquisition module, pressure data analysis module, pressure judgment module, display warning module; The pressure data acquisition module is used to acquire the internal pressure value of the uterine cavity and the pressure value of the infusion pipeline through the pressure sensor; The pressure data analysis module is used to analyze the influence of the flow resistance of the liquid in the infusion line, the dynamic viscosity of the liquid, the liquid density, and the change of the liquid flow rate on the pressure of the infusion line based on the pressure of the infusion line, and establish a dynamic compensation model for the pressure of the infusion line; The pressure judgment module is used to obtain the real value of the infusion line pressure based on the infusion line pressure dynamic compensation model, and compare it with the internal pressure value of the uterine cavity to obtain the pressure deviation index. If the pressure deviation index exceeds the set threshold range, an early warning message is generated and sent to the display early warning module. If the pressure deviation index is within the threshold range, the internal pressure value of the uterine cavity is monitored and analyzed in real time; The display warning module is used to receive the warning information sent by the pressure judgment module, the warning information includes the flow rate of the infusion pump, and display it visually; The details of obtaining the pressure deviation index are as follows: The actual value of the infusion line pressure is calculated by difference with the internal pressure value of the uterine cavity, and the difference is calculated by comprehensive calculation with the allowable deviation value of the internal pressure of the uterine cavity to obtain the pressure deviation index; Pressure difference The actual value of the infusion line pressure and intrauterine pressure The difference between is calculated as follows: ; The calculation process of the pressure deviation index obtained by comprehensive operation is as follows: By using the pressure difference The allowable deviation from the internal pressure of the uterine cavity ) is calculated and the formula is as follows: ,in, , the actual value of the infusion line pressure, Indicates the internal pressure of the uterine cavity. , the allowable deviation value of internal uterine cavity pressure.

2. A hysteroscopic surgery pressure monitoring system according to claim 1, characterized in that: The specific process of analyzing the influence of the liquid flow resistance, liquid dynamic viscosity, liquid density, and liquid flow rate changes in the infusion line on the pressure of the infusion line is as follows: Obtaining geometric parameters of the infusion pipeline and physical parameters of the liquid; The influence of liquid dynamic viscosity and flow rate on pressure is analyzed by the Hagen-Poiseuille equation to obtain the pressure drop value caused by flow resistance in the pipeline; The Bernoulli equation is used to analyze the influence of liquid density and flow rate on pressure, and the pressure drop value caused by the change of flow rate and cross-sectional area in the pipeline is obtained.

3. A hysteroscopic surgery pressure monitoring system according to claim 2, characterized in that: The specific process of establishing the dynamic compensation model of infusion pipeline pressure is as follows: Comprehensively analyze the pressure drop value caused by flow resistance in the pipeline and the pressure drop value caused by flow velocity change and cross-sectional area change in the pipeline, and construct the built-in equation of the dynamic compensation model of the infusion pipeline pressure; The built-in equations of the infusion line pressure dynamic compensation model are input into the fluid mechanics model to construct the infusion line pressure dynamic compensation model.

4. A hysteroscopic surgery pressure monitoring system according to claim 3, characterized in that: Based on the dynamic compensation model of infusion line pressure, the actual value of infusion line pressure is obtained as follows: Obtaining the infusion line pressure compensation value through the infusion line pressure dynamic compensation model; The infusion line pressure compensation value and the infusion line pressure value are difference calculated to obtain the true value of the infusion line pressure.

5. A computer storage medium for adaptive flow rate control in hysteroscopic surgery, applied to a hysteroscopic surgery pressure monitoring system according to any one of claims 1 to 4, characterized in that: The following steps are involved: S1. Obtain the pressure deviation index through the pressure judgment module, and calculate the pressure excess value when the pressure deviation index exceeds the set threshold range; S2. Classify the pressure exceeding value abnormally, set the feedback level, and construct the PID pressure control equation; S3. Determine the flow rate of the infusion pump by the pressure control equation and control the flow rate of the infusion pump; S4. Monitor the adjusted internal uterine cavity pressure value and perform feedback regulation.

6. A computer storage medium for adaptive flow rate control in hysteroscopic surgery according to claim 5, characterized in that: The specific process of constructing the PID pressure control equation is as follows: The pressure excess value is used as the input of the PID controller, and the proportional gain, integral gain and differential gain are set as the parameters of the PID controller; The proportional gain, integral gain and differential gain are substituted into the PID control equation through the PID control algorithm, the flow rate of the infusion pump is set as the output, and the PID pressure control equation is constructed.

7. A computer storage medium for adaptive flow rate control in hysteroscopic surgery according to claim 6, characterized in that: The specific process of controlling the flow rate of the infusion pump is as follows: Input the excess pressure value into the PID pressure control equation to obtain the flow rate of the infusion pump; Based on the flow rate of the infusion pump, the flow rate of the infusion pump is controlled by a PID controller.

8. A computer storage medium for adaptive flow rate control in hysteroscopic surgery according to claim 7, characterized in that: The process of monitoring the adjusted uterine cavity internal pressure value and performing feedback regulation is as follows: The adjusted internal pressure value of the uterine cavity is obtained in real time through the pressure sensor; The adjusted value of the internal uterine cavity pressure is compared with the actual value of the infusion line pressure to determine whether the pressure deviation index exceeds the set threshold range. If so, the flow rate of the infusion pump is adjusted through the PID controller.

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