Intelligent temperature-pressure linkage control system and control method thereof

Abstract

Disclosed in the present invention is an intelligent temperature-pressure linkage control system, which is suitable for an irrigation and suction system and comprises: a liquid irrigation module, used for controlling an irrigation flow rate into a cavity of a patient; an endoscope distal-end sensing module, used for sensing in real time intracavitary pressure and temperature data in the cavity of the patient and transmitting same to a central control module; a liquid suction module, used for controlling a suction flow rate of discharging a liquid medium suctioned from inside the cavity out of the cavity and monitoring a current pressure data; and the central control module, used for acquiring a first adjustment factor and a second adjustment factor that affect the irrigation flow rate and the suction flow rate. Under the influence of the adjustment factors, a temperature factor is introduced into the control process, and each module is controlled by means of an intelligent control algorithm, achieving dynamic balance of the intracavitary pressure of the patient under the influence of the temperature. The influences of parameters such as the temperature and the pressure are fully considered, and temperature and pressure data are integrated in the algorithm to form an effective control process, ensuring that the pressure and the temperature are harmoniously stable and fall within a safe range, thereby guaranteeing the safety of the patient.

Description

Temperature and pressure linkage intelligent control system and its control method Technical Field

[0001] This invention relates to the field of medical device technology, and in particular to a temperature and pressure linkage intelligent control system and its control method. Background Technology

[0002] Urinary tract stones are a common and frequently occurring disease in urology. Minimally invasive surgeries such as percutaneous nephrolithotomy and ureteroscopic lithotripsy have become the preferred treatment for stones. Currently, most perfusion suction platforms use laser lithotripsy.

[0003] The introduction of perfusion aspiration systems and laser lithotripsy treatment requires comprehensive consideration of the impact of multiple factors on patient safety: 1. Increased intrarenal pelvic pressure causing renal parenchymal reflux: The limit of renal parenchymal reflux pressure is 30 mmHg. Studies have shown that when the renal pelvic pressure is greater than 35 mmHg, it can cause persistent reflux in the renal pelvic veins and lymphatic vessels. When infection is present, pressures of 15–18 mmHg can cause reflux. Compared with high-pressure perfusion, low-pressure perfusion significantly reduces complications, proving that higher pressure leads to a higher infection rate. 2. Laser lithotripsy releases heat, causing an increase in the temperature of the intrarenal fluid, creating a risk of thermal damage to tissues.

[0004] In clinical practice, the most common cause of thermal injury and renal pelvic hypertension is insufficient coordination between perfusion and aspiration flow rates during surgery. If the perfusion and aspiration platform is not intelligently controlled, it cannot judge the intra-abdominal pressure. Insufficient perfusion flow and excessive aspiration flow result in inadequate perfusion, causing intra-abdominal contraction and preventing a clear surgical field. Conversely, excessive perfusion and insufficient aspiration flow lead to excessive intra-abdominal pressure, causing renal pelvis damage or reflux, thus affecting patient safety. If both perfusion and aspiration flow rates are insufficient, the intrarenal fluid temperature will become excessively high, resulting in thermal injury.

[0005] Currently, irrigation and aspiration systems used in endoscopic stone surgery are classified into three types: conventional, pressure-controlled, and temperature-controlled. Conventional system: Includes an irrigation module and an aspiration module. Irrigation and aspiration flow rates can be manually set. It lacks pressure and temperature sensing systems, making it unable to determine intracavitary pressure and temperature, relying entirely on the surgeon's clinical experience. Pressure-controlled system: Includes an irrigation module, an aspiration module, and a pressure sensor. While it can automatically control intracavitary pressure based on set pressure and irrigation flow rates, it cannot respond to temperature changes, increasing the risk of tissue thermal damage. Temperature-controlled system: Includes an irrigation module, an aspiration module, and a temperature sensor. It can collect and monitor current intracavitary temperature data, controlling the inflow of irrigation flow and the outflow of aspiration flow to ensure the temperature remains within a safe range. However, it lacks an effective mechanism for controlling intracavitary pressure, potentially leading to excessive pressure, renal pelvis damage, or reflux, affecting patient safety.

[0006] The intelligent pressure and temperature control linkage system disclosed in this invention fully considers the influence of parameters such as temperature and pressure. The algorithm integrates temperature and pressure data to form an effective control process, ensuring that pressure and temperature are harmonious and stable and within a safe range, thus guaranteeing patient safety.

[0007] In summary, existing technologies necessitate the development of an intelligent pressure and temperature control linkage system to provide the necessary field of vision and operating conditions, while protecting the patient's tissues from damage and improving the safety and success rate of the surgery. Summary of the Invention

[0008] The purpose of this invention is to provide a temperature and pressure linkage intelligent control system and its control method, which provides the necessary field of vision and operating conditions, while protecting the patient's tissues from damage and improving the safety and success rate of surgery.

[0009] This invention provides a temperature and pressure linkage intelligent control system, applicable to infusion and aspiration systems, characterized in that it includes at least a central control module and a liquid infusion module, a liquid aspiration module, and an endoscope tip sensing module respectively connected to the central control module;

[0010] The liquid perfusion module is used to control the perfusion flow rate into the patient cavity after startup and to monitor the perfusion flow rate under the current perfusion state.

[0011] The endoscope tip sensing module is mounted on the endoscope and is used to sense the first detection data inside the patient's cavity in real time and transmit it to the central control module. The first detection data includes intracavitary pressure data and temperature data.

[0012] The liquid suction module is used to control the suction flow rate of the liquid medium suctioned from the cavity and discharged from the cavity, and to monitor the second detection data under the current suction state, the second detection data being the pressure data of the negative pressure waste liquid bottle;

[0013] The central control module is used to acquire a first adjustment factor and a second adjustment factor that affect the perfusion flow rate and the suction flow rate. Under the influence of the first adjustment factor and the second adjustment factor, the temperature factor is introduced into the control process. Combined with the intelligent control algorithm, the liquid perfusion module and the liquid suction module are controlled to achieve dynamic balance of the patient's intracavitary pressure under the influence of temperature.

[0014] The first adjustment factor is a pressure-temperature factor, which is used to dynamically adjust the pressure of negative pressure suction according to the temperature change of the patient's intracavitary cavity, thereby adjusting the parameters of suction flow rate; the second adjustment factor is a flow-temperature factor, which is used to dynamically adjust the actual control value of perfusion flow rate according to the temperature change of the patient's intracavitary cavity, thereby adjusting the parameters of perfusion flow rate.

[0015] Preferably, the central control module is also used to acquire the patient's intracavitary pressure value, compare the current patient's intracavitary pressure with a preset intracavitary pressure value, obtain the pressure difference result after comparison, and perform corresponding algorithm calculations based on the pressure difference result to obtain the pulse frequency for controlling the peristaltic pump and the control duty cycle for controlling the suction flow rate of the air pump. At the same time, it ensures the flow balance between the perfusion flow rate flowing into the cavity and the suction flow rate flowing out of the cavity, so that the intracavitary pressure of the renal pelvis reaches dynamic balance, and the circulating water balance between perfusion inflow and suction outflow is achieved.

[0016] Preferably, the liquid perfusion module includes a peristaltic pump, a flow sensor, and a perfusion line. The peristaltic pump and the perfusion line are connected to control the perfusion flow rate into the patient's cavity after startup. The flow sensor is installed on the perfusion line to monitor the flow rate of the liquid medium flowing in the perfusion line.

[0017] Preferably, the endoscope tip sensing module includes an integrated temperature and pressure sensor for simultaneously acquiring and real-time monitoring the patient's current intracavitary pressure and temperature data.

[0018] Preferably, the liquid aspiration module includes a negative pressure waste liquid bottle and a suction tube. The suction tube is connected to the negative pressure waste liquid bottle and is used to guide the liquid medium in the patient's cavity into the negative pressure waste liquid bottle. An air pump is provided between the suction tube and the negative pressure waste liquid bottle to generate negative pressure suction, so as to aspirate the liquid medium from the patient's cavity and expel it from the body. A pressure sensor is provided on the suction tube to monitor the pressure in the suction tube and the negative pressure waste liquid bottle.

[0019] As a preferred working mode

[0020] Start the temperature and pressure linkage intelligent control system;

[0021] The central control module collects real-time intracavitary temperature data obtained by the endoscope's advanced sensing module, compares the current intracavitary temperature data with the preset tissue thermal damage temperature threshold, and determines and calculates the first adjustment factor for optimizing the suction pressure under the current state. The first adjustment factor is the pressure-temperature factor.

[0022] The initial negative pressure suction pressure threshold is determined according to the preset suction flow rate level. The initial negative pressure suction pressure threshold is multiplied by the first adjustment factor to obtain the temperature-calibrated control suction pressure threshold, which is used to control the suction flow rate, thereby ensuring effective suction flow rate control under different temperature conditions.

[0023] The central control module collects the negative pressure waste liquid bottle pressure obtained by the liquid suction module and determines whether the control suction pressure threshold is less than the negative pressure waste liquid bottle pressure.

[0024] When the pressure of the negative pressure waste bottle is less than or equal to the control suction pressure threshold, the central control module collects the current patient cavity pressure obtained by the endoscope tip sensing module, compares the current patient cavity pressure with the user-preset cavity pressure, and calculates the control pulse frequency of the second perfusion peristaltic pump.

[0025] When the pressure in the negative pressure waste bottle is greater than the control suction pressure threshold, the real-time intracavitary temperature data of the endoscope tip sensing module is collected by the central control module. The current intracavitary temperature data is compared with the preset tissue thermal damage temperature threshold, and the second adjustment factor for optimizing the perfusion flow rate under the current state is calculated. The second adjustment factor is the flow rate temperature factor.

[0026] Obtain the user-preset infusion flow rate, multiply the infusion flow rate setting value by the second adjustment factor, and obtain the actual control value of the infusion flow rate;

[0027] The central control module acquires the actual infusion flow rate value obtained by the liquid infusion module, uses the actual control value of the infusion flow rate and the actual infusion flow rate value as input parameters, calculates the control pulse frequency of the first infusion peristaltic pump, and outputs it to the infusion peristaltic pump to control the infusion flow rate.

[0028] The central control module collects the current patient intracavitary pressure from the endoscope's advanced sensing module, compares the current intracavitary pressure with the user-preset intracavitary pressure, calculates the duty cycle of the negative pressure suction pump control signal, and controls the suction flow rate to achieve dynamic balance of the patient's intracavitary pressure and ensure that the pressure and temperature are within a safe range.

[0029] Preferably, the step of acquiring real-time temperature data from the endoscope's advanced sensing module via the central control module, comparing the current temperature data with a preset tissue thermal damage temperature threshold, and determining and calculating a first adjustment factor for optimizing the suction pressure under the current state includes:

[0030] If the current intracavitary temperature is less than or equal to the preset tissue thermal damage temperature threshold, then the current intracavitary temperature is within the normal range, and the current first adjustment factor does not affect the control of the suction flow rate.

[0031] If the current intracavitary temperature data is greater than the preset tissue thermal damage temperature threshold, the first adjustment factor is corrected for the first time based on the temperature difference between the current intracavitary temperature data and the preset tissue thermal damage temperature threshold.

[0032] Preferably, when the pressure in the negative pressure waste bottle is greater than the control suction pressure threshold, the real-time intracavitary temperature data of the endoscope tip sensing module is collected by the central control module, and the current intracavitary temperature data is compared with the preset tissue thermal damage temperature threshold to calculate the second adjustment factor for optimizing the perfusion flow rate under the current state, including:

[0033] If the current intracavitary temperature is less than or equal to the preset tissue thermal damage temperature threshold, then the current intracavitary temperature is within the normal range, and the current first adjustment factor does not affect the control of the perfusion flow rate.

[0034] If the current intracavitary temperature data is greater than the preset tissue thermal damage temperature threshold, the second adjustment factor is corrected for the second time based on the temperature difference between the current intracavitary temperature data and the preset tissue thermal damage temperature threshold.

[0035] Preferably, the step of acquiring the actual infusion flow rate value obtained by the liquid infusion module through the central control module, using the actual control value of the infusion flow rate and the actual infusion flow rate value as input parameters, calculating the first infusion peristaltic pump control pulse frequency, and outputting it to the infusion peristaltic pump to control the infusion flow rate further includes:

[0036] When the pressure of the negative pressure waste bottle is less than or equal to the control suction pressure threshold, and the suction flow rate reaches the increase threshold, the peristaltic pump speed is adjusted by calculating the updated peristaltic pump control pulse frequency based on the actual pressure in the patient's cavity and the user-preset target cavity pressure, thereby controlling the peristaltic flow rate.

[0037] When the pressure of the negative pressure waste liquid bottle is greater than the control suction pressure threshold, the actual control value of the infusion flow rate is used as the target flow rate value. The target flow rate value and the actual infusion flow rate value are used as input parameters to perform PID control calculation to obtain the updated control pulse frequency of the infusion peristaltic pump, thereby adjusting the speed of the peristaltic pump and controlling the infusion flow rate.

[0038] The implementation steps of the fuzzy logic algorithm include input quantization, fuzzification, rule base establishment, inference engine, precision refinement, and engineering quantization.

[0039] Quantization of input quantities: The patient's intraluminal pressure and the set intraluminal pressure deviation e are used as input parameters and mapped to preset numerical levels through a quantization function. Let the universe of discourse of e be [a, b], and the quantization be divided into 7 levels E = {-3, -2, -1, 0, 1, 2, 3}. The quantization function is:

[0040] Fuzzification: Divide the deviation e into a preset number of fuzzy sets, and establish a fuzzy table corresponding to the deviation e based on the membership function of the deviation e;

[0041] At the same time, the control quantity u is divided into a preset number of fuzzy sets, and a fuzzy table corresponding to the control quantity u is established according to the membership function of the control quantity u. A negative u indicates a decrease in the control pulse frequency, and a positive u indicates an increase in the control pulse frequency.

[0042] Rule base establishment: Based on preset fuzzy rules, perform corresponding fuzzy set operations to obtain a fuzzy relation set R. The preset fuzzy rules are configured as the corresponding control actions to be taken for the control pulse frequency u under different deviation conditions.

[0043] Inference engine: Utilizing information from the knowledge base and fuzzy computation methods, based on the current deviation input and fuzzy rules in the rule base, it obtains an appropriate fuzzy control output, u, which is synthesized from the deviation matrix e and the fuzzy relation matrix R: u = eοR,

[0044] [Corrected according to Rule 91 25.09.2025] Precision: The fuzzy control output is converted into a precise control signal through defuzzification operations, including the maximum membership method, the centroid method, and the weighted average method;

[0045] Engineering quantization: This involves converting precise control signals into physical quantities that can be used to control the object. Let the universe of discourse for u be [a, b], and the quantization be divided into 7 levels U = {-3, -2, -1, 0, 1, 2, 3}. Then the engineering quantization function is:

[0046] The present invention also provides a temperature and pressure linkage intelligent control method, applicable to the temperature and pressure linkage intelligent control system as described in the embodiments of the present invention. The control system includes at least a central control module and a liquid infusion module, a liquid aspiration module, and an endoscope tip sensing module respectively connected to the central control module.

[0047] The liquid perfusion module controls the perfusion flow rate into the patient cavity after startup and monitors the perfusion flow rate under the current perfusion status.

[0048] The first detection data inside the patient's cavity is sensed in real time by the endoscope's advanced sensing module and transmitted to the central control module. The first detection data includes intracavitary pressure data and temperature data.

[0049] The liquid suction module controls the suction flow rate of the liquid medium drawn from inside the cavity and discharged outside the cavity, and monitors the second detection data under the current suction state. The second detection data is the pressure data of the negative pressure waste liquid bottle.

[0050] The central control module obtains the first and second adjustment factors that affect the perfusion flow and suction flow. Under the influence of the first and second adjustment factors, the temperature factor is introduced into the control process. Combined with the intelligent control algorithm, the liquid perfusion module and the liquid suction module are controlled to achieve dynamic balance of the patient's intracavitary pressure under the influence of temperature.

[0051] The first adjustment factor is a pressure-temperature factor, which is used to dynamically adjust the pressure of negative pressure suction according to the temperature change of the patient's intracavitary cavity, thereby adjusting the parameters of suction flow rate; the second adjustment factor is a flow-temperature factor, which is used to dynamically adjust the actual control value of perfusion flow rate according to the temperature change of the patient's intracavitary cavity, thereby adjusting the parameters of perfusion flow rate.

[0052] Because the present invention adopts the above technical solution, it has the following advantages and positive effects compared with the prior art:

[0053] 1. This invention provides a temperature and pressure linkage intelligent control system suitable for perfusion and aspiration systems. It is an intelligent pressure and temperature control linkage system comprising a perfusion module, an aspiration module, a central control module, and an endoscope-mounted sensing module. The perfusion module uses a liquid medium to pressurize and expand the patient's intracavitary cavity to create a visible area and clean impurities, providing clear observation and surgical visibility for the doctor. The aspiration module removes waste fluid from the patient's intracavitary cavity. The endoscope-mounted parameter acquisition module collects temperature and pressure data from the patient's intracavitary cavity. The central control module, based on preset pressure and temperature parameters and the current pressure and temperature parameters collected by the endoscope, uses an intelligent control algorithm to control the perfusion and aspiration modules, ensuring harmonious and stable pressure and temperature within a safe range to guarantee patient safety. The system can inject liquid medium into the patient's intracavitary cavity according to a preset perfusion flow rate. The endoscope-mounted sensor is equipped with pressure and temperature sensors. Based on the aforementioned pressure and temperature parameters, the system can intelligently link and control the liquid perfusion and aspiration modules to maintain the pressure and temperature within the patient's intracavitary cavity.

[0054] 2. This invention discloses an intelligent linkage control algorithm. The liquid perfusion module perfuses the liquid medium according to a preset perfusion flow rate. The central control module collects pressure and temperature data at the endoscope tip and determines the suction flow rate based on the preset pressure and the current patient intracavitary pressure. When the heat from laser lithotripsy causes the liquid medium temperature to approach or reach the preset temperature, the central control module increases the perfusion flow rate and the suction flow rate according to the current temperature and the temperature rise trend. This maintains pressure balance while enhancing the circulation of the liquid medium, thereby reducing the temperature of the liquid medium.

[0055] 3. In performing minimally invasive surgeries such as percutaneous nephrolithotomy and ureteroscopic lithotripsy, this invention requires a fluid circulation system: a certain flow rate of fluid is infused to pressurize and expand the patient's intracavitary cavity, facilitating the surgery. Simultaneously, a suction device is used to aspirate a certain flow rate of fluid, maintaining a dynamic balance of fluid flow within the patient's intracavitary cavity. This serves three purposes: firstly, it flushes the patient's intracavitary cavity, removing stone fragments after laser lithotripsy while maintaining a clean endoscopic view; secondly, the flowing fluid can carry away the heat generated during laser lithotripsy, preventing thermal damage to the kidney tissue; and thirdly, it maintains a fluid pressure balance within the patient's intracavitary cavity, preventing renal parenchymal reflux and subsequent kidney tissue damage. Attached Figure Description

[0056] Figure 1 is a schematic diagram of the temperature and pressure linkage intelligent control system in an embodiment of the present invention;

[0057] Figure 2 is a schematic diagram of the working process of the temperature and pressure linkage intelligent control system in an embodiment of the present invention. Detailed Implementation

[0058] The following specific examples illustrate the embodiments of the present invention. Those skilled in the art can easily understand other advantages and effects of the present invention from the content disclosed in this specification. The present invention can also be implemented or applied through other different specific embodiments, and various details in this specification can be modified or changed based on different viewpoints and applications without departing from the spirit of the present invention. It should be understood that the terms "center," "longitudinal," "lateral," "upper," "lower," "front," "rear," "left," "right," "vertical," "horizontal," "top," "bottom," "inner," and "outer," etc., indicate the orientation or positional relationship based on the orientation or positional relationship shown in the accompanying drawings, and are only for the convenience of describing the present invention and simplifying the description, and do not indicate or imply that the device or element referred to must have a specific orientation, or be constructed and operated in a specific orientation, and therefore should not be construed as a limitation of the present invention. Furthermore, the terms "first," "second," etc., are used for descriptive purposes only and should not be construed as indicating or implying relative importance or implicitly specifying the number of indicated technical features. Thus, features defined with "first," "second," etc., may explicitly or implicitly include one or more of that feature. In the description of the present invention, unless otherwise stated, "a plurality of" means two or more.

[0059] It should be noted that, unless otherwise explicitly specified and limited, the terms "installation," "connection," and "linking" should be interpreted broadly. For example, they can refer to fixed connections, detachable connections, or integral connections; they can refer to mechanical connections or electrical connections; they can refer to direct connections or indirect connections through an intermediate medium; and they can refer to the internal connection between two components. Those skilled in the art will understand the specific meaning of the above terms in this invention based on the specific circumstances.

[0060] As shown in Figures 1-2, this embodiment of the invention provides a temperature and pressure linkage intelligent control system. This system can inject a fluid medium into the patient's intracavitary cavity according to a preset perfusion flow rate. The endoscope tip of this system is equipped with pressure and temperature sensors. Based on the aforementioned pressure and temperature parameters, the system can intelligently link and control the fluid perfusion module and the fluid aspiration module to maintain the pressure and temperature within the patient's intracavitary cavity, ensuring surgical safety.

[0061] The temperature and pressure linkage intelligent control system provided in this embodiment is applicable to perfusion and aspiration systems. It includes at least a central control module 1 and a liquid perfusion module 2, a liquid aspiration module 3, and an endoscope tip sensing module 4, all connected to the central control module 1. The central control module 1 includes a touchscreen user interface. Through this interface, users can preset the perfusion flow rate, patient intracavitary pressure, and aspiration level. The central control module 1 can then perform automatic control based on the inputs.

[0062] The liquid perfusion module 2 is used to control the perfusion flow rate into the patient cavity after startup and to monitor the perfusion flow rate under the current perfusion state.

[0063] The endoscope tip sensing module 4 is mounted on the endoscope and is used to sense the first detection data inside the patient cavity in real time and transmit it to the central control module 1. The first detection data includes intracavitary pressure data and temperature data.

[0064] The liquid suction module 3 is used to control the suction flow rate of the liquid medium suctioned from the cavity and discharged from the cavity, and to monitor the second detection data under the current suction state. The second detection data is the pressure data of the negative pressure waste liquid bottle.

[0065] The central control module 1 is used to acquire a first adjustment factor and a second adjustment factor that affect the perfusion flow rate and the suction flow rate. Under the influence of the first adjustment factor and the second adjustment factor, the temperature factor is introduced into the control process. Combined with the intelligent control algorithm, the perfusion module and the suction module are controlled to achieve dynamic balance of the patient's intracavitary pressure under the influence of temperature.

[0066] The first adjustment factor is a pressure-temperature factor, used to dynamically adjust the pressure of negative pressure suction based on changes in the temperature of the patient's intracavitary cavity, thereby adjusting the suction flow rate parameter. The second adjustment factor is a flow-temperature factor, used to dynamically adjust the actual control value of the perfusion flow rate based on changes in the temperature of the patient's intracavitary cavity, thereby adjusting the perfusion flow rate parameter. By introducing pressure-temperature and flow-temperature factors, the system can dynamically adjust the perfusion flow rate and suction flow rate according to the actual temperature of the patient's intracavitary cavity. Precise control helps maintain the pressure of the patient's intracavitary cavity within a safe range, reducing the risk of complications caused by excessively high or low pressure. By monitoring the pressure and temperature of the patient's intracavitary cavity in real time and automatically adjusting in conjunction with user-preset parameters, tissue thermal damage and other potential surgical risks can be effectively avoided.

[0067] The intelligent pressure and temperature control linkage system provided by this invention includes a liquid infusion module 2, a liquid aspiration module 3, a central control module 1, and an endoscope tip sensing module 4. The liquid infusion module 2 uses a liquid medium to pressurize and expand the patient's internal cavity to create a visible area and clean impurities within the cavity, providing a clear view for the doctor and the surgical field. The liquid aspiration module 3 is used to suction waste fluid from the patient's internal cavity. The endoscope tip sensing module 4 collects temperature and pressure data from the patient's internal cavity. The central control module 1, based on preset pressure and temperature parameters and the current pressure and temperature parameters collected by the tip, combines an intelligent control algorithm to control the infusion and aspiration modules, ensuring harmonious and stable pressure and temperature within a safe range, thus ensuring patient safety.

[0068] Specifically, the liquid perfusion module 2 includes a peristaltic pump 21, a flow sensor 23, and an perfusion tubing 22. The peristaltic pump 21 and the perfusion tubing 22 are connected to control the perfusion flow rate into the patient's cavity after startup. The flow sensor 23 is installed on the perfusion tubing 22 to monitor the flow rate of the liquid medium flowing in the perfusion tubing 22. The central control module 1 can control the peristaltic pump 21 to inject liquid into the patient's cavity according to the perfusion flow rate set by the user, and collect flow data in real time as feedback information to form a closed-loop control of the perfusion flow rate. In this embodiment, the combination of a peristaltic pump 21 and a flow sensor 23 enables precise control of the perfusion flow rate. The peristaltic pump 21 can adjust its rotation speed according to the instructions of the central control module 1, thereby changing the perfusion flow rate. The flow sensor monitors the actual perfusion flow rate in real time and feeds the data back to the central control module 1. This closed-loop control mechanism ensures the accuracy and stability of the perfusion flow rate. Precise perfusion flow rate control helps maintain the pressure within the patient's intracavitary space within a safe range, reducing the risk of complications caused by excessively high or low pressure. At the same time, by maintaining an appropriate perfusion flow rate, the system helps improve the clarity of the surgical field, enabling surgeons to perform surgical operations more accurately.

[0069] Specifically, the endoscope-mounted sensing module 4 includes an integrated temperature and pressure sensor 41, used to simultaneously acquire and monitor the patient's current intracavitary pressure and temperature data in real time. The central control module 1 acquires pressure and temperature data through the endoscope-mounted sensing module 4. Through the integrated temperature and pressure sensor 41, the system can simultaneously and accurately monitor the pressure and temperature of the patient's intracavitary space. This dual monitoring function ensures the real-time nature and accuracy of key parameters during surgery, helping doctors make more precise decisions.

[0070] Specifically, the liquid aspiration module 3 includes an air pump 31 and a suction tube 32 connected to the air pump 31, a negative pressure waste liquid bottle 33, and a pressure sensor 34. The suction tube 32 is connected to the negative pressure waste liquid bottle 33 and is used to guide the liquid medium in the patient's cavity into the negative pressure waste liquid bottle 33. An air pump 31 is provided between the suction tube 32 and the negative pressure waste liquid bottle 33 to generate negative pressure suction to aspirate the liquid medium from the patient's cavity and expel it from the body. A pressure sensor 34 is provided on the suction tube 32 to monitor the pressure in the suction tube and the negative pressure waste liquid bottle 33. The central control module 1 controls the air pump to extract air from the negative pressure waste liquid bottle 33 based on data such as perfusion flow rate, patient cavity pressure, and temperature. The suction tube 32 connected to the negative pressure waste liquid bottle 33 aspirates the liquid medium in the patient's cavity, so that the pressure in the patient's cavity reaches dynamic equilibrium. The above solution, through the combination of negative pressure waste liquid bottle 33 and suction tubing 32, enables the system to efficiently guide the liquid medium in the patient's cavity into the negative pressure waste liquid bottle 33, which helps to keep the surgical area clean and dry, reduce the risk of infection, and provide a clear surgical field of vision. The pressure sensor on the suction tubing monitors the pressure changes during the suction process in real time and feeds the data back to the central control module 1. Combined with intelligent algorithms, the system can automatically adjust the operating status of the air pump to maintain an appropriate negative pressure level, ensuring that the suction process is both effective and safe. Appropriate suction pressure is crucial to prevent tissue damage. Too high a negative pressure may cause tissue damage, while too low a pressure may not be able to effectively remove the liquid. This module protects the patient from unnecessary harm through precise pressure control.

[0071] Specifically, the central control module 1 is also used to acquire the patient's intracavitary pressure value, compare the current intracavitary pressure with a preset intracavitary pressure value, obtain the pressure difference result, and perform corresponding algorithm calculations based on the pressure difference result to obtain the pulse frequency of the peristaltic pump 21 and the control duty cycle of the air pump controlling the suction flow. Simultaneously, it ensures the flow balance between the inflow of perfusion into the cavity and the outflow of suction into the cavity, so that the intracavitary pressure reaches dynamic equilibrium, achieving a balance between inflow of perfusion and outflow of suction. By acquiring the patient's intracavitary pressure value in real time and comparing it with the preset intracavitary pressure value, the system can accurately calculate the pressure difference. This precise pressure monitoring and adjustment helps maintain the stability of the patient's intracavitary pressure during surgery, reducing the risk of complications caused by pressure fluctuations. The corresponding algorithm calculation based on the pressure difference result can intelligently adjust the pulse frequency of the peristaltic pump 21 and the control duty cycle of the air pump. This intelligent control not only improves the system's response speed and accuracy but also dynamically adjusts the suction and perfusion flow rates according to actual needs to adapt to different surgical situations. Ensuring a balance between the inflow rate into the renal pelvis and the outflow rate into the renal pelvis is crucial for maintaining a stable intraluminal environment. By precisely controlling these two key parameters, the system can effectively prevent over-perfusion or under-absorption, thereby maintaining a dynamic balance of intraluminal pressure.

[0072] The principle of temperature and pressure linkage intelligent control based on intelligent control algorithm provided in this embodiment of the invention is as follows: The liquid perfusion module 2 perfuses the liquid medium according to the preset perfusion flow rate. The central control module 1 collects the pressure and temperature data of the endoscope tip and determines the suction flow rate based on the preset pressure and the current patient intracavitary pressure. When the heat from laser lithotripsy causes the liquid medium temperature to approach or reach the preset temperature, the central control module 1 increases the perfusion flow rate and the suction flow rate according to the current temperature and the temperature rise trend. This maintains pressure balance while enhancing the circulation of the liquid medium, thereby reducing the temperature of the liquid medium and avoiding thermal damage during laser lithotripsy. The implementation steps are as follows:

[0073] S1: Start the temperature and pressure linkage intelligent control system;

[0074] S2: The central control module 1 collects real-time intracavitary temperature data obtained by the endoscope tip sensing module 4, compares the current intracavitary temperature data with the preset tissue thermal damage temperature threshold, and determines and calculates the first adjustment factor for optimizing the suction pressure under the current state. The first adjustment factor is pressure-temperature factor = f(patient intracavitary temperature, preset thermal damage temperature threshold). The pressure-temperature factor is adjusted according to the temperature change of the patient's intracavitary cavity. The higher the temperature, the larger the factor. It is used to adjust and increase the suction flow rate, accelerate the circulation of fluid in the patient's intracavitary cavity, and achieve the purpose of reducing the temperature.

[0075] Specifically, in step S2, the current temperature data is compared with a preset tissue thermal damage temperature threshold to determine whether the current intracavitary temperature data is greater than the tissue thermal damage temperature. The first adjustment factor for optimizing the suction pressure under the current state is determined and calculated, including:

[0076] If the current intracavitary temperature data is less than or equal to the preset tissue thermal damage temperature threshold, then the current intracavitary temperature is within the normal range, and the current first adjustment factor does not affect the control of the suction flow rate. For example, below 30 degrees, the pressure-temperature factor value is 1, and at this time, the pressure-temperature factor does not affect the control of the suction flow rate.

[0077] If the current intracavitary temperature data is greater than the preset tissue thermal damage temperature threshold, the first adjustment factor is corrected for the first time based on the temperature difference between the current intracavitary temperature data and the preset tissue thermal damage temperature threshold. For example, the pressure temperature factor value will be greater than 1. The larger the value, the greater the influence of temperature on the control of suction flow.

[0078] S3: Determine the corresponding initial negative pressure suction threshold based on the preset suction flow rate setting; this can be understood as the central control module 1 calculating the corresponding negative pressure suction threshold based on the user-preset suction flow rate setting. The intelligent temperature and pressure control injection system determines the preset negative pressure suction threshold based on the user-set suction flow rate setting, where the negative pressure suction threshold = f(set flow rate setting).

[0079] S4: Multiply the initial negative pressure suction pressure threshold by the first adjustment factor to obtain the temperature-calibrated control suction pressure threshold, which is used to control the suction flow rate, thereby ensuring effective suction flow rate control under different temperature conditions. It can be understood that the product of the negative pressure suction pressure threshold and the pressure-temperature factor is the control suction pressure threshold. The control suction pressure threshold is the temperature-calibrated negative pressure suction pressure threshold, which ultimately determines the suction flow rate. The control suction pressure threshold determines the suction capacity of the liquid suction module 3.

[0080] S5: The pressure sensor data obtained by the liquid suction module 3 through the central control module 1 is collected, namely the pressure of the negative pressure waste liquid bottle;

[0081] S6: Determine whether the control suction pressure threshold is less than the pressure of the negative pressure waste liquid bottle. When the pressure of the negative pressure waste liquid bottle to which the liquid suction module 3 belongs is greater than the control suction pressure threshold, it indicates that the air in the negative pressure waste liquid bottle can continue to be drawn by the air pump, the pressure of the negative pressure waste liquid bottle can be further reduced, and the suction flow rate can be further increased.

[0082] S7: When the pressure of the negative pressure waste bottle is greater than the control suction pressure threshold, the real-time intracavitary temperature data of the endoscope tip sensing module 4 is collected by the central control module 1, and the current intracavitary temperature data is compared with the preset tissue thermal damage temperature threshold. The second adjustment factor for optimizing the perfusion flow rate under the current state is calculated. The second adjustment factor is the flow rate temperature factor, and the flow rate temperature factor = f(patient intracavitary temperature, preset thermal damage temperature threshold).

[0083] In step S7, the current intracavitary temperature data is compared with a preset tissue thermal damage temperature threshold to determine whether the current intracavitary temperature data is greater than the tissue thermal damage temperature, and a second adjustment factor for optimizing perfusion flow rate under the current state is calculated, including:

[0084] If the current intracavitary temperature data is less than or equal to the preset tissue thermal damage temperature threshold, then the current intracavitary temperature is within the normal range, and the current first adjustment factor does not affect the control of the perfusion flow rate. For example, below 30 degrees, the flow rate temperature factor value is 1, and at this time, the flow rate temperature factor does not affect the control of the perfusion flow rate.

[0085] If the current intracavitary temperature data is greater than the preset tissue thermal damage temperature threshold, the second adjustment factor will be corrected for the second time based on the temperature difference between the current intracavitary temperature data and the preset tissue thermal damage temperature threshold. For example, the flow rate temperature factor value will be greater than 1. The larger the value, the greater the influence of temperature on the control of perfusion flow rate.

[0086] S8: Obtain the user-preset infusion flow rate, multiply the infusion flow rate setting value by the second adjustment factor to obtain the actual control value of the infusion flow rate. This can be understood as the product of the infusion flow rate setting value and the flow rate temperature factor being the actual control value of the infusion flow rate. The actual control value of the infusion flow rate is the target value for control. The actual control value of the infusion flow rate includes the influence of the intracavitary temperature on the infusion flow rate.

[0087] S9: The actual infusion flow rate value obtained by the liquid infusion module 2 is collected by the central control module 1. This can be understood as the central control module 1 collecting the flow sensor data of the infusion module in this embodiment, and the flow sensor data is the actual infusion flow rate value.

[0088] S10: Using the actual control value of the infusion flow rate and the actual infusion flow rate as input parameters, perform PID control calculations to obtain the control pulse frequency of the first infusion peristaltic pump 21 and output it to the infusion peristaltic pump 21 to control the infusion flow rate. The actual control value of the infusion flow rate is the target value, and the actual infusion flow rate is the current flow rate value. The control pulse frequency of the first infusion peristaltic pump 21 (forward rotation) = PID(actual control value of infusion flow rate, actual infusion flow rate value). Using PID control calculations, adjust the control pulse frequency of the infusion peristaltic pump 21 according to the difference between the actual infusion flow rate value and the target value.

[0089] Specifically, step S10, using the actual control value of the infusion flow rate and the actual infusion flow rate value as input parameters, performs PID control calculations to obtain the control pulse frequency of the first infusion peristaltic pump 21 and outputs it to the infusion peristaltic pump 21 to control the infusion flow rate, further includes:

[0090] The PID control described is a control strategy based on three parameters: proportional (P), integral (I), and derivative (D). Its basic principle is to compare the deviation between the actual and desired values ​​of the system, and then adjust the control input using proportional, integral, and derivative operations to eliminate the deviation and achieve the control objective.

[0091] The proportionality (P) mentioned reflects the current deviation of the system. The control quantity is adjusted by multiplying it by the proportional coefficient. The larger the proportional coefficient, the faster the system response.

[0092] The integral (I) mentioned above reflects the cumulative deviation of the system. The steady-state error of the system is eliminated through integral operation, thereby improving the error-freeness of the system.

[0093] The differential (D) reflects the rate of change of the system deviation signal. It is predictive and can be adjusted before the deviation is formed, thereby improving the dynamic performance of the system.

[0094] The calculation formula for PID control is as follows:

[0095] Where: Kp, Ki, and Kd are the proportional coefficient, integral coefficient, and differential coefficient, respectively;

[0096] The deviation between the actual value and the expected value of e(k);

[0097] It is the accumulation of deviations;

[0098] e(k)-e(k-1) is the change in deviation;

[0099] U(k) is the control value obtained from PID calculation.

[0100] The control pulse frequency (forward rotation) is calculated as follows: PID (actual control value of infusion flow rate, actual infusion flow rate value). The actual control value of infusion flow rate is used as the expected value of system control, and the actual infusion flow rate value is used as the actual value of system control. Substituting these values ​​into the calculation formula of PID control, and supplementing with appropriate proportional coefficients, integral coefficients, and derivative coefficients, the control pulse frequency (forward rotation) is obtained.

[0101] S11: When the pressure in the negative pressure waste bottle is less than or equal to the control suction pressure threshold, the central control module 1 acquires the current patient intracavitary pressure obtained by the endoscope tip sensing module 4, compares the current patient intracavitary pressure with the user-preset intracavitary pressure, and calculates the control pulse frequency of the second perfusion peristaltic pump 21. The control pulse frequency of the second perfusion peristaltic pump 21 (reverse) = f(patient intracavitary pressure, set intracavitary pressure). This can be understood as follows: when the pressure in the negative pressure waste bottle is less than or equal to the control suction pressure threshold, the suction flow rate cannot be further increased. The central control module 1 performs fuzzy calculations based on the patient intracavitary pressure and the user-preset intracavitary pressure to obtain the control pulse frequency of the perfusion peristaltic pump 21.

[0102] The fuzzy computing algorithm described above primarily addresses fuzzy or uncertain problems by transforming human fuzzy concepts and language into mathematical expressions. Its basic idea is to introduce a membership function to describe the degree of membership of an object. This membership degree can be any value between 0 and 1, representing the degree to which an object belongs to a certain fuzzy set.

[0103] The implementation steps of the fuzzy algorithm include input quantization, fuzzification, rule base, inference engine, precisionization, and engineering quantization.

[0104] The quantization of the input quantity refers to projecting the input data to a certain digital level through a quantization function, which is usually a digital range symmetrical with respect to 0.

[0105] The input quantities are the patient's intraluminal pressure and the set intraluminal pressure deviation e. Let the universe of discourse for e be [a, b], and quantized into 7 levels E = {-3, -2, -1, 0, 1, 2, 3}. Its quantization function is:

[0106] The fuzzification process involves dividing the deviation e into five fuzzy sets: negative large (NB), negative small (NS), zero (ZO), positive small (PS), and positive large (PB). A fuzzy table corresponding to the deviation e is then established based on its membership function.

[0107] Similarly, the control quantity u is divided into 5 fuzzy sets: negative large (NB), negative small (NS), zero (ZO), positive small (PS), and positive large (PB). A negative u indicates a decrease in the control pulse frequency, and a positive u indicates an increase in the control pulse frequency. A fuzzy table corresponding to the control quantity u is established based on the membership function of the control quantity u.

[0108] The aforementioned rule base, based on the fuzzification of control variables, forms the foundation for fuzzy reasoning and largely relies on experience. The rules are as follows:

[0109] (1) If e is negative, then u is negative.

[0110] (2) If e is negative and small, then u is negative and small;

[0111] (3) If e is zero, then u is zero;

[0112] (4) If e is positively small, then u is positively small;

[0113] (5) If e is positive, then u is positive;

[0114] Based on the specified fuzzy rules, the fuzzy relation set R can be obtained through the corresponding fuzzy set operations.

[0115] The inference engine described above utilizes information from a knowledge base and fuzzy computation to simulate human reasoning and decision-making processes. Under certain input conditions, it activates corresponding control rules to provide appropriate fuzzy control outputs. u can be synthesized from the deviation matrix e and the fuzzy relation matrix R.

[0116] symbol This typically represents a specific fuzzy logic operator, called a composition operation or Max-Min composition. In fuzzy logic, this operation is used to combine two fuzzy relations, such as deviation and control rules, to produce a fuzzy output, which can be represented as: Where ui is the i-th element of the output fuzzy set, ej is the j-th element of the input fuzzy set, and Rij is the element in the i-th row and j-th column of the fuzzy relation matrix.

[0117] The aforementioned refinement involves obtaining precise data through defuzzification. Commonly used defuzzification methods include the maximum membership method, the centroid method, and the weighted average method.

[0118] The aforementioned engineering quantization: The system control output is a precise number, but it is not a physical quantity that can be directly used for object control. Therefore, it needs to be converted according to our needs at the end. Let the universe of discourse of u be [a, b], and the quantization be 7 levels U = {-3, -2, -1, 0, 1, 2, 3}. Then the engineering quantization function is:

[0119] S12: When the pressure of the negative pressure waste liquid bottle is greater than the control suction pressure threshold, the peristaltic pump 21 is controlled by the control pulse frequency obtained in step S10. When the pressure of the negative pressure waste liquid bottle is less than or equal to the control suction pressure threshold, the peristaltic pump 21 is controlled by the control pulse frequency obtained in step S11.

[0120] S13: The central control module 1 acquires the current patient intracavitary pressure from the endoscope's advanced sensing module 4, compares the current intracavitary pressure with the user-preset intracavitary pressure, and calculates the duty cycle of the negative pressure suction pump's control signal. This controls the suction flow rate, ensuring dynamic balance of the patient's intracavitary pressure and maintaining pressure and temperature within safe ranges. The pump's control signal duty cycle = f(patient intracavitary pressure, set intracavitary pressure). This can be understood as the central control module 1 acquiring the patient's intracavitary pressure and the user-preset intracavitary pressure to calculate the control duty cycle of the negative pressure suction pump.

[0121] S14: The control duty cycle of the negative pressure suction air pump is output to the air pump through the control interface to realize the pressure control of the negative pressure waste liquid bottle, thereby realizing the control of the suction flow rate, so that the pressure in the patient's cavity reaches dynamic balance.

[0122] The working scenario of the intrarenal pelvis temperature and pressure linkage control system provided in this embodiment is as follows:

[0123] The system includes three operating modes: sheath insertion, lithotripsy, and lithotripsy removal. In lithotripsy mode, the laser lithotripsy process generates heat, causing the renal pelvis temperature to gradually rise. This example describes the workflow of the temperature-pressure linkage control system using lithotripsy mode.

[0124] In lithotripsy mode, the infusion flow rate is generally set to 50 mL / min, the suction flow rate is generally set to level 2, and the cavity pressure is generally set to 20 mmHg. These three parameters can be modified according to actual conditions.

[0125] Once the endoscope's tip sensing module enters the renal pelvis, it immediately senses the temperature and pressure within the pelvis. When the system is in lithotripsy mode and perfusion suction is initiated, the system calculates a pressure-temperature factor based on the deviation between the renal pelvis temperature and the thermal injury temperature (38°C). Different deviations result in different pressure-temperature factors, forming an empirical curve. This factor is used to determine the method for controlling the perfusion flow rate. Then, based on the set suction flow rate level, the system obtains the negative pressure suction threshold (at level 2, the threshold is -250 mmHg). The product of the negative pressure suction threshold and the pressure-temperature factor is the final threshold for controlling the suction pressure.

[0126] In lithotripsy mode, when the pressure in the negative pressure bottle exceeds the control suction pressure threshold, the system calculates the flow-temperature factor based on the deviation between the renal pelvis temperature and the thermal injury temperature (38℃). As the temperature deviation increases, the flow-temperature factor also increases. The product of the perfusion flow rate and the flow-temperature factor becomes the new final actual flow control value. The system employs a PID control method, running a PID control algorithm based on the actual flow rate and the actual flow control value to obtain the pulse frequency of the perfusion pump controlling the perfusion flow rate, and outputs this frequency to the perfusion pump to ensure the perfusion flow rate reaches the control value.

[0127] In lithotripsy mode, when the pressure in the negative pressure bottle is less than the control suction pressure threshold, the system will use a fuzzy control algorithm to perform fuzzy calculations based on the deviation between the patient's intracavitary pressure and the set intracavitary pressure to obtain the pulse frequency of the peristaltic pump and output it to the peristaltic pump, so that the patient's intracavitary pressure can be quickly restored to below the set intracavitary pressure, ensuring surgical safety.

[0128] In lithotripsy mode, the suction duty cycle of the perfusion pump is determined based on the deviation between the patient's intracavitary pressure and the set intracavitary pressure. This ensures a dynamic balance between perfusion and suction flow rates, keeping the patient's intracavitary pressure within a safe range.

[0129] The present invention also provides an infusion suction platform, including a temperature and pressure linkage intelligent control system as described in the embodiments of the present invention.

[0130] Based on the same inventive concept, the present invention provides a computer device, comprising: a memory for storing a processing program; and a processor, wherein the processor executes the processing program to implement the control steps of the temperature and pressure linkage intelligent control system.

[0131] Based on the same inventive concept, the present invention provides a readable storage medium storing a processing program, which, when executed by a processor, implements the control steps of the temperature and pressure linkage intelligent control system.

[0132] Those skilled in the art will understand that all or part of the steps of the above method embodiments can be implemented by hardware related to program instructions. The aforementioned program can be stored in a computer-readable storage medium. When the program is executed, it performs the steps of the above method embodiments. The aforementioned storage medium includes various media that can store program code, such as mobile storage devices, read-only memory (ROM), magnetic disks, or optical disks.

[0133] The embodiments of the present invention have been described in detail above with reference to the accompanying drawings, but the present invention is not limited to the above embodiments. Even if various changes are made to the present invention, if these changes fall within the scope of the claims of the present invention and their equivalents, they shall still fall within the protection scope of the present invention.

Claims

1. A temperature and pressure linkage intelligent control system, applicable to infusion and suction systems, characterized in that, It includes at least a central control module and a liquid infusion module, a liquid aspiration module, and an endoscope tip sensing module, which are respectively connected to the central control module. The liquid perfusion module is used to control the perfusion flow rate into the patient cavity after startup and to monitor the perfusion flow rate under the current perfusion state. The endoscope tip sensing module is mounted on the endoscope and is used to sense the first detection data inside the patient's cavity in real time and transmit it to the central control module. The first detection data includes intracavitary pressure data and temperature data. The liquid suction module is used to control the suction flow rate of the liquid medium suctioned from the cavity and discharged from the cavity, and to monitor the second detection data under the current suction state, the second detection data being the pressure data of the negative pressure waste liquid bottle; The central control module is used to acquire a first adjustment factor and a second adjustment factor that affect the perfusion flow rate and the suction flow rate. Under the influence of the first adjustment factor and the second adjustment factor, the temperature factor is introduced into the control process. Combined with the intelligent control algorithm, the liquid perfusion module and the liquid suction module are controlled to achieve dynamic balance of the patient's intracavitary pressure under the influence of temperature. The first adjustment factor is a pressure-temperature factor, which is used to dynamically adjust the pressure of negative pressure suction according to the temperature change of the patient's intracavitary cavity, thereby adjusting the parameters of suction flow rate; the second adjustment factor is a flow-temperature factor, which is used to dynamically adjust the actual control value of perfusion flow rate according to the temperature change of the patient's intracavitary cavity, thereby adjusting the parameters of perfusion flow rate.

2. The temperature and pressure linkage intelligent control system according to claim 1, characterized in that, The central control module is also used to acquire the patient's intracavitary pressure value, compare the current intracavitary pressure with the preset intracavitary pressure value, obtain the pressure difference result after comparison, and perform corresponding algorithm calculations based on the pressure difference result to obtain the pulse frequency of the peristaltic pump and the control duty cycle of the air pump that controls the suction flow rate. At the same time, it ensures the flow balance between the perfusion flow rate flowing into the cavity and the suction flow rate flowing out of the cavity, so that the intracavitary pressure of the renal pelvis reaches dynamic balance, and the circulating water balance between perfusion inflow and suction outflow is achieved.

3. The temperature and pressure linkage intelligent control system according to claim 1, characterized in that, The liquid perfusion module includes a peristaltic pump, a flow sensor, and a perfusion line. The peristaltic pump and the perfusion line are connected to control the perfusion flow rate into the patient's cavity after startup. The flow sensor is installed on the perfusion line to monitor the flow rate of the liquid medium flowing in the perfusion line.

4. The temperature and pressure linkage intelligent control system according to claim 1, characterized in that, The endoscope's advanced sensing module includes an integrated temperature and pressure sensor, used to simultaneously acquire and monitor the patient's current intracavitary pressure and temperature data in real time.

5. The temperature and pressure linkage intelligent control system according to claim 1, characterized in that, The liquid aspiration module includes a negative pressure waste liquid bottle and a suction tube. The suction tube is connected to the negative pressure waste liquid bottle and is used to guide the liquid medium in the patient's cavity into the negative pressure waste liquid bottle. An air pump is provided between the suction tube and the negative pressure waste liquid bottle to generate negative pressure suction, so as to aspirate the liquid medium from the patient's cavity and expel it from the body. A pressure sensor is provided on the suction tube to monitor the pressure in the suction tube and the negative pressure waste liquid bottle.

6. The temperature and pressure linkage intelligent control system according to claim 1, characterized in that, In work mode, Start the temperature and pressure linkage intelligent control system; The central control module collects real-time intracavitary temperature data obtained by the endoscope's advanced sensing module, compares the current intracavitary temperature data with the preset tissue thermal damage temperature threshold, and determines and calculates the first adjustment factor for optimizing the suction pressure under the current state. The first adjustment factor is the pressure-temperature factor. The initial negative pressure suction pressure threshold is determined according to the preset suction flow rate level. The initial negative pressure suction pressure threshold is multiplied by the first adjustment factor to obtain the temperature-calibrated control suction pressure threshold, which is used to control the suction flow rate, thereby ensuring effective suction flow rate control under different temperature conditions. The central control module collects the negative pressure waste liquid bottle pressure obtained by the liquid suction module and determines whether the control suction pressure threshold is less than the negative pressure waste liquid bottle pressure. When the pressure of the negative pressure waste bottle is less than or equal to the control suction pressure threshold, the central control module collects the current patient cavity pressure obtained by the endoscope tip sensing module, compares the current patient cavity pressure with the user-preset cavity pressure, and calculates the control pulse frequency of the second perfusion peristaltic pump. When the pressure in the negative pressure waste bottle is greater than the control suction pressure threshold, the real-time intracavitary temperature data of the endoscope tip sensing module is collected by the central control module. The current intracavitary temperature data is compared with the preset tissue thermal damage temperature threshold, and the second adjustment factor for optimizing the perfusion flow rate under the current state is calculated. The second adjustment factor is the flow rate temperature factor. Obtain the user-preset infusion flow rate, multiply the infusion flow rate setting value by the second adjustment factor, and obtain the actual control value of the infusion flow rate; The central control module acquires the actual infusion flow rate value obtained by the liquid infusion module, uses the actual control value of the infusion flow rate and the actual infusion flow rate value as input parameters, calculates the control pulse frequency of the first infusion peristaltic pump, and outputs it to the infusion peristaltic pump to control the infusion flow rate. The central control module collects the current patient intracavitary pressure from the endoscope's advanced sensing module, compares the current intracavitary pressure with the user-preset intracavitary pressure, calculates the duty cycle of the negative pressure suction pump control signal, and controls the suction flow rate to achieve dynamic balance of the patient's intracavitary pressure and ensure that the pressure and temperature are within a safe range.

7. The temperature and pressure linkage intelligent control system according to claim 6, characterized in that, The process involves acquiring real-time temperature data from the endoscope's advanced sensing module via the central control module, comparing the current temperature data with a preset tissue thermal damage temperature threshold, and determining and calculating a first adjustment factor for optimizing suction pressure under the current state. This includes: If the current intracavitary temperature is less than or equal to the preset tissue thermal damage temperature threshold, then the current intracavitary temperature is within the normal range, and the current first adjustment factor does not affect the control of the suction flow rate. If the current intracavitary temperature data is greater than the preset tissue thermal damage temperature threshold, the first adjustment factor is corrected for the first time based on the temperature difference between the current intracavitary temperature data and the preset tissue thermal damage temperature threshold.

8. The temperature and pressure linkage intelligent control system according to claim 6, characterized in that, When the pressure in the negative pressure waste bottle exceeds the control suction pressure threshold, the central control module collects real-time intracavitary temperature data from the endoscope's advanced sensing module. The current intracavitary temperature data is compared with a preset tissue thermal damage temperature threshold to calculate a second adjustment factor for optimizing the perfusion flow rate under the current condition. This factor includes: If the current intracavitary temperature is less than or equal to the preset tissue thermal damage temperature threshold, then the current intracavitary temperature is within the normal range, and the current first adjustment factor does not affect the control of the perfusion flow rate. If the current intracavitary temperature data is greater than the preset tissue thermal damage temperature threshold, the second adjustment factor is corrected for the second time based on the temperature difference between the current intracavitary temperature data and the preset tissue thermal damage temperature threshold.

9. [Corrected according to detailed rule 91 25.09.2025] The temperature and pressure linkage intelligent control system according to claim 6 is characterized in that, The process of acquiring the actual perfusion flow rate value from the liquid perfusion module through the central control module, using the actual control value of the perfusion flow rate and the actual perfusion flow rate value as input parameters, and calculating the first perfusion peristaltic pump control pulse frequency and outputting it to the perfusion peristaltic pump to control the perfusion flow rate further includes: when the pressure of the negative pressure waste bottle is less than or equal to the control suction pressure threshold, and the suction flow rate reaches the increase threshold, calculating the updated perfusion peristaltic pump control pulse frequency based on the actual pressure in the patient's cavity and the user-preset target cavity pressure, and adjusting the speed of the peristaltic pump to control the perfusion flow rate; when the pressure of the negative pressure waste bottle is greater than the control suction pressure threshold, the perfusion... The actual perfusion flow rate is used as the target flow rate. The target flow rate and the actual perfusion flow rate are used as input parameters. PID control calculations are performed to obtain the updated perfusion pump control pulse frequency, which is then used to adjust the pump's rotation speed, thereby controlling the perfusion flow rate. The implementation steps of the fuzzy logic algorithm include input quantization, fuzzification, rule base establishment, inference engine, precisionization, and engineering quantization. Input quantization involves mapping the patient's intraluminal pressure and the set intraluminal pressure deviation e as input parameters to preset numerical levels using a quantization function. Let the domain of e be [a, b], and quantization be performed into 7 levels E = {-3, -2, -1, 0, 1, 2, 3}. The quantization function is: Fuzzification: The deviation e is divided into a preset number of fuzzy sets, and a fuzzy table corresponding to the deviation e is established based on the membership function of the deviation e; simultaneously, the control quantity u is divided into a preset number of fuzzy sets, and a fuzzy table corresponding to the control quantity u is established based on the membership function of the control quantity u, where a negative u indicates a decrease in the control pulse frequency, and a positive u indicates an increase in the control pulse frequency; Rule base establishment: Based on preset fuzzy rules, corresponding fuzzy set operations are performed to obtain a fuzzy relation set R, where the preset fuzzy rules are configured as the corresponding control actions to be taken for control pulse frequencies u under different deviation conditions; Inference engine: Utilizing information in the knowledge base... Using fuzzy logic, based on the current deviation input and fuzzy rules in the rule base, an appropriate fuzzy control output is obtained. u is synthesized from the deviation matrix e and the fuzzy relation matrix R: u = eοR. The refinement process involves converting the fuzzy control output into a precise control signal through defuzzification operations, including the maximum membership method, centroid method, and weighted average method. Engineering quantization converts the precise control signal into a physical quantity that can be used to control the object. Let the universe of discourse of u be [a, b], and the quantization be divided into 7 levels U = {-3, -2, -1, 0, 1, 2, 3}. Then the engineering quantization function is:

10. A temperature and pressure linkage intelligent control method, characterized in that, The temperature and pressure linkage intelligent control system as described in any one of claims 1 to 9 is applicable, wherein the control system includes at least a central control module and a liquid infusion module, a liquid aspiration module, and an endoscope tip sensing module respectively connected to the central control module. The liquid perfusion module controls the perfusion flow rate into the patient cavity after startup and monitors the perfusion flow rate under the current perfusion status. The first detection data inside the patient's cavity is sensed in real time by the endoscope's advanced sensing module and transmitted to the central control module. The first detection data includes intracavitary pressure data and temperature data. The liquid suction module controls the suction flow rate of the liquid medium drawn from inside the cavity and discharged outside the cavity, and monitors the second detection data under the current suction state. The second detection data is the pressure data of the negative pressure waste liquid bottle. The central control module obtains the first and second adjustment factors that affect the perfusion flow and suction flow. Under the influence of the first and second adjustment factors, the temperature factor is introduced into the control process. Combined with the intelligent control algorithm, the liquid perfusion module and the liquid suction module are controlled to achieve dynamic balance of the patient's intracavitary pressure under the influence of temperature. The first adjustment factor is a pressure-temperature factor, which is used to dynamically adjust the pressure of negative pressure suction according to the temperature change of the patient's intracavitary cavity, thereby adjusting the parameters of suction flow rate; the second adjustment factor is a flow-temperature factor, which is used to dynamically adjust the actual control value of perfusion flow rate according to the temperature change of the patient's intracavitary cavity, thereby adjusting the parameters of perfusion flow rate.

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