Intracavity radiofrequency ablation system

Abstract

The invention relates to the field of medical equipment, and discloses an intracavity radiofrequency ablation system. The system includes a radio frequency generator, a catheter with a heating element, a pressure sensor, and a temperature sensor, a processor, and a display. By monitoring the temperature and the pressure in real time and dynamically adjusting the radio frequency energy output power, the safety and the accuracy of the treatment process are ensured. The system can automatically adjust treatment parameters according to the real-time contraction condition of the cavity tissue, prevent overheating, reduce damage to normal tissue, provide visual tissue contraction feedback and improve the treatment effect.

Description

Technical Field

[0001] The present application relates to the field of medical equipment, and in particular to radiofrequency ablation technology. Background Art

[0002] As a minimally invasive treatment method, radiofrequency ablation technology has been widely used in the treatment of various diseases such as heart disease and tumors in recent years. The radiofrequency ablation system is usually composed of a radiofrequency generator, a catheter, a temperature sensor and other monitoring equipment. The system heats the heating element of the catheter through radiofrequency energy and transfers the heat energy to the target tissue, thereby achieving ablation of the diseased tissue. However, the existing radiofrequency ablation system still has some technical limitations and hidden dangers in actual application, which makes it difficult to fully guarantee the safety and accuracy of the treatment process.

[0003] First, traditional radiofrequency ablation systems mainly rely on temperature sensors to feedback control the temperature of the catheter heating element. However, temperature feedback often only has single-point monitoring. When the temperature sensor fails or the feedback is delayed, the system cannot timely sense the contact between the catheter and the tissue, which may cause the heating element to continue to output energy, eventually causing excessive heating, burning the surrounding normal tissue, and bringing serious medical risks.

[0004] Secondly, most existing radiofrequency ablation systems use fixed treatment temperatures and treatment times, which cannot be dynamically adjusted according to the real-time contraction of the cavity tissue. Since each patient's tissue characteristics and reactions are different, fixed temperature and time settings may lead to over-treatment or under-treatment, affecting the treatment effect. For example, when the cavity tissue has completely contracted, the system continues to heat according to the preset target temperature and time, which can easily cause excessive heat energy, thereby damaging normal tissue and increasing the risk of complications.

[0005] In addition, the existing system lacks intuitive feedback on the contraction of cavity tissue. During the operation, doctors can only rely on external imaging equipment such as ultrasound to observe the contact between the catheter and the cavity tissue, and cannot obtain the contraction changes of the tissue before and after treatment in real time. This indirect feedback mechanism not only increases the difficulty of doctors' operation, but also makes the monitoring during the treatment process less accurate, increasing the complexity and uncertainty of the operation.

[0006] In view of the above problems, the existing radiofrequency ablation technology needs to be improved urgently to enhance the system's real-time monitoring capability of temperature and pressure during treatment to ensure the safety and accuracy of the contact between the catheter and the tissue. In addition, the system should have the ability to dynamically adjust the treatment parameters according to the actual contraction of the tissue to prevent damage to normal tissue due to excessive heating. At the same time, the system should also provide intuitive tissue contraction feedback so that doctors can clearly understand the tissue changes before and after treatment, thereby improving the surgical effect and reducing surgical risks. Summary of the invention

[0007] The purpose of the present application is to provide an intracavitary radiofrequency ablation system to solve the problems raised in the above-mentioned background technology.

[0008] The present application discloses an intracavitary radiofrequency ablation system, the system comprising:

[0009] a radio frequency generator for generating and transmitting radio frequency energy to the heating element of the catheter;

[0010] The catheter comprises: a heating element for receiving the radio frequency energy and heating the cavity tissue; a pressure sensor disposed at the heating element for detecting the contact pressure between the heating element and the cavity tissue; and a temperature sensor disposed at the heating element for detecting the temperature of the heating element;

[0011] A processor is electrically connected to the RF generator, the pressure sensor, and the temperature sensor, and the processor is configured to:

[0012] (a) obtaining an initial pressure value P1 and an initial temperature value T1;

[0013] (b) controlling the RF generator to output RF energy to the heating element so that the temperature thereof rises to a second temperature value T2, and obtaining a second pressure value P2 at this time;

[0014] (c) calculating a pressure-temperature function relationship according to the initial pressure value P1, the initial temperature value T1, the second pressure value P2 and the second temperature value T2;

[0015] (d) calculating a first pressure threshold value P3 and a second pressure threshold value P4 at a preset target temperature based on the pressure-temperature function relationship, wherein P4 is greater than P3;

[0016] (e) controlling the heating element to heat up to the preset target temperature and monitoring the current pressure value P in real time;

[0017] (f) when the current pressure value P reaches the first pressure threshold value P3, lowering the target temperature of the heating element to a new target temperature lower than the preset target temperature;

[0018] (g) when the current pressure value P exceeds the second pressure threshold value P4 and the current temperature is lower than the preset target temperature, controlling the RF generator to stop outputting RF energy;

[0019] The display is electrically connected to the processor and is used to display the pressure value changes before and after treatment to reflect the contraction of the cavity tissue.

[0020] In a preferred embodiment, the processor is further configured to:

[0021] According to the initial pressure value P1, the initial temperature value T1, the second pressure value P2 and the second temperature value T2, the pressure value P at the current temperature T is calculated using the pressure-temperature function relationship, and the pressure-temperature function relationship is:

[0022] P=[(P2-P1) / (T2-T1)]×T+[(P1×T2-P2×T1) / (T2-T1)]+a

[0023] Where a is the correction constant and T is the current temperature.

[0024] In a preferred embodiment, the processor is further configured to:

[0025] In step (d), the second pressure threshold P4 is calculated according to the formula P4=P3×K, where K is a preset constant greater than 1.

[0026] In a preferred embodiment, the processor is further configured to:

[0027] In step (f), the new target temperature Tp is calculated according to the formula Tp=b×Ts, where Ts is the preset target temperature and b is a preset coefficient greater than 0 and less than 1.

[0028] In a preferred embodiment, the processor is further configured to:

[0029] In step (f), after the target temperature of the heating element is lowered to the new target temperature, the heating element is controlled to maintain the new target temperature until the preset treatment time ends; wherein,

[0030] The processor is further configured to continuously monitor the current pressure value P during the period of maintaining the new target temperature, and execute step (g) when the current pressure value P exceeds the second pressure threshold value P4.

[0031] In a preferred embodiment, the processor is further configured to:

[0032] In step (g), when the RF generator is controlled to stop outputting RF energy, the following operations are performed simultaneously:

[0033] (i) displaying abnormal warning information on the display, wherein the abnormal warning information includes a prompt indicating that the current pressure value P exceeds the second pressure threshold value P4;

[0034] (ii) generating an audible alarm sound; and

[0035] (iii) Record the time when the abnormality occurs, the current pressure value P and the current temperature value in the system log.

[0036] In a preferred example, the system further includes:

[0037] A user input interface, electrically connected to the processor, and the user input interface is configured to:

[0038] (i) Receive a preset target temperature Ts input by the user;

[0039] (ii) Receive a preset treatment time input by the user;

[0040] (iii) Receive a coefficient b input by the user, where 0 < b < 1, for calculating a new target temperature Tp;

[0041] (iv) Receive a constant K input by the user, where K > 1, for calculating a second pressure threshold P4;

[0042] Wherein, the processor is further configured to perform steps (a) to (g) in claim 1 according to the parameters received from the user input interface, and use these parameters for corresponding calculations and controls during the execution process.

[0043] In a preferred example, the display is configured to:

[0044] Real-time display the following information:

[0045] (i) The current pressure value P;

[0046] (ii) The current temperature value T;

[0047] (iii) The target temperature value, including the preset target temperature Ts and the new target temperature Tp (if applicable);

[0048] (iv) The remaining treatment time;

[0049] (v) The first pressure threshold P3 and the second pressure threshold P4;

[0050] (vi) The output power of the radio frequency generator;

[0051] (vii) The system operation status, including status indicators such as normal operation, cooling stage, or abnormal stop.

[0052] In a preferred example, the heating element includes:

[0053] (i) A thermocouple for real-time measuring the temperature of the heating element and transmitting the measurement result to the processor;

[0054] (ii) A heating element winding coaxially surrounding the thermocouple, and the heating element winding is configured to receive radio frequency energy from the radio frequency generator, convert it into heat and distribute it evenly;

[0055] (iii) an insulating layer, covering the outside of the heating element winding, for electrical insulation and heat retention;

[0056] (iv) A flexible housing, made of biocompatible material, enveloping the entire heating element structure.

[0057] In a preferred embodiment, the system further comprises: a tumescent fluid injection device electrically connected to the processor, wherein the tumescent fluid injection device is configured as follows:

[0058] (i) injecting a preset volume of tumescent fluid into the cavity tissue;

[0059] (ii) sending an injection completion signal to the processor;

[0060] Wherein, the processor is further configured to:

[0061] (a) receiving the injection completion signal;

[0062] (b) in response to the injection completion signal, continuously monitoring the contact between the heating element and the cavity tissue through the pressure sensor;

[0063] (c) calculating the contact area percentage between the heating element and the cavity tissue based on the measurement result of the pressure sensor;

[0064] (d) controlling the display to display the contact status in real time, including: numerical display of the contact area percentage, and / or graphical representation of the contact status;

[0065] (e) When the contact area percentage is lower than a preset threshold, controlling the display to send a warning signal.

[0066] In a preferred embodiment, the processor is further configured to dynamically adjust the RF energy output power, specifically including:

[0067] (a) Setting the initial RF output power value Pinitial;

[0068] (b) During the treatment process, the current temperature value T and the current pressure value P are continuously acquired at a preset sampling frequency;

[0069] (c) Based on the current temperature value T, the current pressure value P, the target temperature Ts and the first pressure threshold value P3, the power adjustment factor α is calculated, where:

[0070] α=f(T,P,Ts,P3), f is the preset power adjustment function;

[0071] (d) According to the power adjustment factor α, calculate the new RF output power value Pnew:

[0072] Pnew=Pcurrent×α

[0073] Wherein, Pcurrent is the current RF output power value;

[0074] (e) applying the new RF output power value Pnew to the RF generator to dynamically adjust the RF energy output;

[0075] (f) Set the upper limit Pmax and lower limit Pmin of power adjustment to ensure:

[0076] Pmin≤Pnew≤Pmax

[0077] Among them, Pmin and Pmax are pre-defined safe power ranges;

[0078] (g) Rapid power adjustment is triggered when any of the following conditions occurs:

[0079] (i) When the temperature rises rapidly and exceeds the preset safety temperature threshold Tsafe, the output power is immediately reduced to Pmin;

[0080] (ii) when the pressure rises rapidly and exceeds the first pressure threshold value P3, the output power is reduced to a preset percentage β% of the current power (where 0<β<100);

[0081] (h) after each power adjustment, record relevant data of the power adjustment, including but not limited to: adjustment time, power before adjustment, power after adjustment, current temperature, current pressure and power adjustment factor α;

[0082] (i) generating a power adjustment curve and a temperature and pressure change curve based on the recorded data, and displaying these curves to the user through the display after the treatment is completed for analysis;

[0083] (j) Based on historical treatment data and machine learning algorithms, the power adjustment function f is periodically optimized to improve the system's adaptability and treatment effect.

[0084] The implementation methods of this application have the following technical effects:

[0085] 1. Precisely control the radio frequency energy output to avoid tissue damage

[0086] By monitoring temperature and pressure in real time and dynamically adjusting the RF energy output power, the system can quickly respond to changes in tissue contact pressure, prevent excessive energy transmission, and avoid tissue burns caused by excessive heating. Especially when the temperature rises rapidly or the pressure exceeds the threshold, the system can immediately reduce the output power to ensure the safety and accuracy of the treatment.

[0087] 2. Real-time feedback on the contraction of cavity tissue to improve treatment effect

[0088] The system obtains the contact pressure between the catheter and the cavity tissue through the pressure sensor, and intuitively displays the contraction of the cavity tissue before and after treatment through the display. This real-time feedback not only helps doctors better understand the treatment process, but also allows doctors to take timely measures when the cavity tissue contracts abnormally, thereby reducing surgical risks.

[0089] 3. Automatically adjust the treatment temperature to avoid excessive heat energy

[0090] The system automatically calculates and adjusts the treatment temperature based on the pressure changes at different temperature points. When the pressure reaches the set threshold, the system will lower the target temperature and maintain the appropriate temperature level according to the treatment time to avoid overheating and reduce damage to normal tissues.

[0091] 4. Abnormal detection and alarm functions to improve operational safety

[0092] When an abnormal situation occurs during treatment (such as pressure or temperature exceeding the set threshold), the system can stop the RF energy output in time and issue an abnormal warning through the display and alarm to prompt the doctor to take appropriate measures. This mechanism greatly improves the operational safety of the system and reduces medical accidents caused by equipment failure or operational errors.

[0093] 5. Efficient data recording and analysis to optimize treatment plans

[0094] The system records data such as temperature, pressure, and power changes during each treatment process and generates relevant curves for users to analyze. With these data, doctors can more accurately evaluate the treatment effect and optimize subsequent treatment plans based on historical data. In addition, the system can also combine machine learning algorithms to automatically optimize the power adjustment function to further improve the adaptive ability and effect of treatment.

[0095] 6. Flexible power adjustment mechanism to meet different clinical needs

[0096] The system sets the upper and lower limits of power adjustment and dynamically adjusts the RF output power through the power adjustment factor. This flexible power adjustment mechanism enables the system to adapt to different treatment environments and individual differences of patients, ensuring that the energy output during treatment is always within a safe and effective range.

[0097] 7. Reduce doctors’ manual operations and improve surgical efficiency

[0098] Through automated temperature and pressure monitoring, power adjustment, and exception handling, the system reduces the doctor's manual operations and displays key treatment-related data in real time on the display, helping doctors complete the operation more efficiently. This not only improves surgical efficiency, but also reduces errors caused by human operations.

[0099] In summary, the present application significantly improves the safety, accuracy and efficiency of radiofrequency ablation treatment, and provides a more reliable treatment tool for clinical practice.

[0100] A large number of technical features are recorded in the specification of this application, which are distributed in various technical solutions. If all possible combinations of technical features of this application (i.e., technical solutions) are to be listed, the specification will be too long. In order to avoid this problem, the various technical features disclosed in the above-mentioned invention content of this application, the various technical features disclosed in the various embodiments and examples below, and the various technical features disclosed in the accompanying drawings can be freely combined with each other to form various new technical solutions (these technical solutions are all deemed to have been recorded in this specification), unless the combination of such technical features is technically infeasible. For example, in one example, feature A+B+C is disclosed, and in another example, feature A+B+D+E is disclosed, and features C and D are equivalent technical means that play the same role. Technically, only one can be used, and it is impossible to use them at the same time. Feature E can be combined with feature C technically. Then, the solution of A+B+C+D should not be deemed to have been recorded because it is technically infeasible, and the solution of A+B+C+E should be deemed to have been recorded. BRIEF DESCRIPTION OF THE DRAWINGS

[0101] Figure 1 It is a schematic diagram of the heating element structure of the intracavitary radiofrequency ablation system according to the first embodiment of the present application.

[0102] Figure 2 It is a schematic diagram of the temperature and pressure change curves of the intracavitary radiofrequency ablation system according to the embodiment of the present application.

[0103] Figure 3 It is a schematic diagram of temperature control of an intracavitary radiofrequency ablation system according to an embodiment of the present application.

[0104] Throughout the drawings, the same reference numerals are used to denote the same elements or structures, wherein:

[0105] 10: Pressure sensor;

[0106] 20: Thermocouple;

[0107] 30: Heating element winding. DETAILED DESCRIPTION

[0108] In the following description, many technical details are provided to help readers better understand the present application. However, those skilled in the art can understand that the technical solution claimed in the present application can be implemented even without these technical details and various changes and modifications based on the following embodiments.

[0109] Description of some concepts:

[0110] In the present application, an intracavitary radiofrequency ablation system refers to a medical device system used for tissue ablation treatment in a human body cavity, which heats the catheter tip with radiofrequency energy to perform thermal ablation on specific tissues.

[0111] Radiofrequency generator: A device that produces high-frequency electrical current and is used to deliver radiofrequency energy to the catheter.

[0112] The heating element, in this application, refers to the component located at the tip of the catheter that receives RF energy and converts it into heat energy for ablating tissue.

[0113] The pressure sensor, in the present application, is disposed at the catheter heating element to detect the contact pressure between the heating element and the cavity tissue.

[0114] The temperature sensor, in the present application, is disposed at the catheter heating element to detect the temperature of the heating element.

[0115] The pressure-temperature function relationship, in this application, refers to a mathematical formula that describes the relationship between pressure and temperature, which is used to predict and control the treatment process.

[0116] The pressure thresholds (P3 and P4), in this application, refer to preset pressure values ​​used to trigger automatic adjustment or stop operation of the system. P3 is the first pressure threshold, and P4 is the second pressure threshold.

[0117] The target temperature (Ts), in this application, refers to the preset ideal treatment temperature.

[0118] The new target temperature (Tp), in this application, refers to a new target temperature to which the system automatically decreases when the pressure reaches the first threshold.

[0119] Tumescent fluid, as used in this application, refers to fluid that is injected into a cavity during certain surgeries to dilate tissue or improve visualization.

[0120] The power adjustment factor (α), in this application, refers to a calculation factor used to dynamically adjust the RF output power.

[0121] Thermocouple: A temperature sensor used to accurately measure the temperature of a heating element.

[0122] Heating Element Winding: This constitutes the main part of the heating element that receives the RF energy and converts it into heat.

[0123] The contact area percentage, in this application, refers to the percentage of the actual contact area between the heating element and the cavity tissue to the ideal contact area, which is used to evaluate the treatment effect.

[0124] The safety temperature threshold (Tsafe), in this application, refers to a preset maximum safety temperature, exceeding which triggers a rapid power adjustment of the system.

[0125] In order to make the objectives, technical solutions and advantages of the present application clearer, the implementation methods of the present application will be further described in detail below in conjunction with the accompanying drawings.

[0126] The first embodiment of the present application relates to an intracavitary radiofrequency ablation system, the structure of the heating element of the core component is as follows: Figure 1 As shown, the system includes:

[0127] a radio frequency generator for generating and transmitting radio frequency energy to the heating element of the catheter;

[0128] The catheter comprises: a heating element for receiving the radio frequency energy and heating the cavity tissue; a pressure sensor 10, arranged at the heating element, for detecting the contact pressure between the heating element and the cavity tissue; a temperature sensor, arranged at the heating element, for detecting the temperature of the heating element;

[0129] The processor is electrically connected to the RF generator, the pressure sensor 10 and the temperature sensor, see Figure 2 and Figure 3 , the processor is configured to:

[0130] (a) obtaining an initial pressure value P1 and an initial temperature value T1;

[0131] (b) controlling the RF generator to output RF energy to the heating element so that the temperature thereof rises to a second temperature value T2, and obtaining a second pressure value P2 at this time;

[0132] (c) calculating a pressure-temperature function relationship according to the initial pressure value P1, the initial temperature value T1, the second pressure value P2 and the second temperature value T2;

[0133] (d) calculating a first pressure threshold value P3 and a second pressure threshold value P4 at a preset target temperature based on the pressure-temperature function relationship, wherein P4 is greater than P3;

[0134] (e) controlling the heating element to heat up to the preset target temperature and monitoring the current pressure value P in real time;

[0135] (f) when the current pressure value P reaches the first pressure threshold value P3, lowering the target temperature of the heating element to a new target temperature lower than the preset target temperature;

[0136] (g) when the current pressure value P exceeds the second pressure threshold value P4 and the current temperature is lower than the preset target temperature, controlling the RF generator to stop outputting RF energy;

[0137] The display is electrically connected to the processor and is used to display the pressure value changes before and after treatment to reflect the contraction of the cavity tissue.

[0138] Specifically, this embodiment describes a system for intracavitary radiofrequency ablation, the core component of which is a heating element, and its structure is as follows: Figure 1 The main components of the system include the RF generator, catheter, pressure sensor, temperature sensor, processor and display.

[0139] First, the RF generator is responsible for generating and transmitting RF energy to the heating element of the catheter. After receiving the energy, the heating element of the catheter heats the tissue in the cavity to achieve tissue ablation. The catheter is also equipped with a pressure sensor 10 and a temperature sensor, which are used to detect the contact pressure between the heating element and the cavity tissue and the temperature of the heating element, respectively. Real-time feedback from the pressure sensor and the temperature sensor is an important guarantee for the safety and accuracy of the system.

[0140] Secondly, the processor is the core control unit of the system and is connected to the RF generator, pressure sensor and temperature sensor. The working principle of the processor can be found in Figure 2 and Figure 3 , which can dynamically adjust the output of RF energy according to the preset control logic. The processor first obtains the initial pressure value P1 and temperature value T1, then controls the RF generator to output RF energy to the heating element, raising its temperature to the second temperature value T2, and records the second pressure value P2 at this time.

[0141] Next, the processor calculates a pressure-temperature function relationship based on the initial pressure value P1, the initial temperature value T1, the second pressure value P2, and the second temperature value T2. The function relationship is used to further calculate the first pressure threshold value P3 and the second pressure threshold value P4 at the preset target temperature, where P4 is greater than P3. Based on these calculations, the processor can accurately control the working state of the heating element.

[0142] During the treatment, the processor controls the heating element to heat up to the preset target temperature and monitors the current contact pressure value P in real time. When the current pressure value reaches the first pressure threshold value P3, in order to prevent overheating, the processor will reduce the target temperature of the heating element to a new target temperature lower than the preset target temperature. If the current pressure value exceeds the second pressure threshold value P4 and the current temperature is lower than the preset target temperature, the processor will stop the output of RF energy to ensure the safety of the treatment.

[0143] In addition, the display is electrically connected to the processor and is responsible for showing the user the changes in pressure values ​​during the treatment process. Through the display, the operator can intuitively understand the contraction of the cavity tissue, thereby providing real-time feedback to help improve the accuracy and effectiveness of the treatment.

[0144] This implementation ensures safety and tissue protection during radiofrequency ablation through a dual monitoring mechanism of temperature and pressure. At the same time, by adjusting the temperature of the heating element and the output of radiofrequency energy in real time, tissue damage caused by overheating is avoided, thus improving the accuracy and reliability of the entire treatment process.

[0145] Optionally, the processor is further configured to:

[0146] According to the initial pressure value P1, the initial temperature value T1, the second pressure value P2 and the second temperature value T2, the pressure value P at the current temperature T is calculated using the pressure-temperature function relationship, and the pressure-temperature function relationship is:

[0147] P=[(P2-P1) / (T2-T1)]×T+[(P1×T2-P2×T1) / (T2-T1)]+a

[0148] in,

[0149] P is the current pressure value, that is, the pressure value calculated at the current temperature T.

[0150] P1 is the initial pressure value, that is, the pressure value measured at the initial temperature T1.

[0151] P2 is the second pressure value, that is, the pressure value measured when the temperature rises to T2.

[0152] T1 is the initial temperature value.

[0153] T2 is a second temperature value, which is higher than T1.

[0154] T is the current temperature, which is used to calculate the current pressure value.

[0155] [(P2-P1) / (T2-T1)] represents the rate of change of pressure with temperature, that is, the slope of the change of pressure with temperature.

[0156] [(P1×T2-P2×T1) / (T2-T1)] is the intercept term of the linear equation.

[0157] a is a correction constant, which is used to adjust the deviation between the theoretical calculated value and the actual measured value.

[0158] Specifically, this optional implementation further expands the functionality of the processor by calculating the pressure value P at the current temperature T through the pressure-temperature function. This calculation process is based on the measurement results of the initial and second temperature and pressure values, and aims to achieve more precise control and dynamic adjustment of the system state.

[0159] Specifically, the processor first obtains the initial pressure value P1 and the initial temperature value T1, then controls the RF generator to increase the temperature of the heating element, and records the second pressure value P2 when the temperature reaches the second temperature value T2. Through these temperature and pressure data in the initial and second states, the processor can establish a functional relationship between pressure and temperature to predict the pressure value PP at the current temperature T.

[0160] In the above formula, a is a correction constant, which is used to fine-tune the deviation between the theoretical calculated value and the actual measured value to ensure that the formula is closer to the actual situation. Its existence allows the system to flexibly adjust the pressure calculation results according to different operating environments and patient characteristics.

[0161] By calculating the pressure value at the current temperature, the system can accurately monitor the contact between the catheter and the tissue during treatment. This dynamic monitoring process can effectively prevent overheating or overpressure and ensure the safety of the radiofrequency ablation process. In addition, using this pressure-temperature function relationship, the system can automatically adjust the output power or temperature of the heating element according to real-time feedback, thereby optimizing the treatment effect and reducing damage to normal tissue.

[0162] This implementation method clearly expresses the relationship between pressure and temperature through a mathematical model, which not only improves the control accuracy of the system, but also provides a theoretical basis for the adaptive regulation of the system.

[0163] Optionally, the processor is further configured to:

[0164] In step (d), the second pressure threshold value P4 is calculated according to the formula P4=P3×K, where:

[0165] P4 is the second pressure threshold, which represents the upper pressure limit at which the system stops outputting radio frequency energy.

[0166] P3 is the first pressure threshold, indicating the pressure value at which the system starts to lower the target temperature.

[0167] K is a preset constant, whose value is greater than 1, and is used to determine the multiple relationship of the second pressure threshold with respect to the first pressure threshold.

[0168] P4>P3, ensuring that when the pressure continues to rise, the system has a buffer zone to adjust the treatment parameters and stop the treatment in time when necessary.

[0169] Specifically, in this optional embodiment, the processor is further configured to calculate the second pressure threshold value P4 by a formula. The core of this function is to dynamically adjust the behavior of the system according to the change of pressure to ensure the safety and accuracy during the treatment process.

[0170] In the above formula, P4 represents the second pressure threshold, which is the upper pressure limit at which the system stops the output of RF energy during treatment. When the pressure value reaches or exceeds this upper limit, the system will immediately stop energy transmission to prevent excessive pressure on the tissue and avoid damage. P3 represents the first pressure threshold. When the current pressure value reaches P3, the system begins to lower the target temperature of the heating element. This threshold is used to prevent the pressure from rising further, and also serves as an early warning mechanism to indicate that the pressure has entered a range that needs to be adjusted.

[0171] K is a preset constant, and K>1K>1. It is used to determine the multiple relationship of the second pressure threshold P4 relative to the first pressure threshold P3. By introducing this constant, the system can flexibly set the value of P4 to be higher than P3, thereby providing the system with sufficient buffer space to cope with pressure fluctuations during treatment.

[0172] The goal of this embodiment is to establish a hierarchical pressure control mechanism. First, when the pressure reaches the first threshold value P3, the system does not immediately stop the energy output, but alleviates the rising trend of pressure by lowering the target temperature of the heating element. This preventive mechanism allows the system to continue to work within a moderate pressure range while avoiding excessive temperature rise.

[0173] However, if the pressure continues to rise and reaches the second pressure threshold P4, the system will immediately stop the output of RF energy. This action is to provide a last line of defense when the pressure is too high to prevent the treatment process from causing irreversible damage to the patient's tissue.

[0174] The reason for introducing the K factor is that it provides flexibility and adjustability to the system. The tissue characteristics of different patients may be different, and the rate of change of pressure during treatment may also be different. By adjusting the value of K, the system can set the appropriate second pressure threshold according to the specific treatment needs, thereby avoiding stopping the output of RF energy too early or too late.

[0175] When P4 > P3, the system has a buffer range when the pressure continues to rise. When the pressure reaches P3, the system has enough time to adjust by reducing the temperature. When the adjustment fails or the pressure continues to rise to P4, the system will果断 stop the RF energy output. This hierarchical response mechanism significantly improves the safety of the system, ensuring that even under relatively complex treatment conditions, overheating or overpressure of tissues can be effectively prevented.

[0176] Through this mechanism, the RF ablation system can achieve a higher level of intelligent control during the treatment process, ensuring both the effectiveness of the treatment and minimizing damage to normal tissues.

[0177] Optionally, the processor is further configured to:

[0178] In step (f), calculate the new target temperature Tp according to the formula Tp = b × Ts, where Ts is the preset target temperature and b is a preset coefficient greater than 0 and less than 1.

[0179] Specifically, in this optional embodiment, the processor is further configured to calculate the new target temperature Tp through the formula Tp = b × Ts. The purpose of this function is to dynamically adjust the target temperature of the heating element during the treatment process according to specific conditions (such as the pressure reaching a certain threshold), so as to prevent the temperature from being too high during the treatment and ensure the safety of the treatment.

[0180] In the above formula, Tp is the new target temperature. When the system detects that the pressure reaches the first pressure threshold P3, the system does not immediately stop the energy output, but reduces the temperature of the heating element to this new target temperature Tp to slow down the further rise of the pressure. Ts is the preset target temperature. Ts is the temperature value set by the user or the system before the start of the treatment, usually the highest temperature to be reached during the treatment process. B is a preset coefficient, and 0 < b < 1. B controls the amplitude of the temperature reduction, indicating the percentage of the new target temperature relative to the preset target temperature. Since the value range of b is between 0 and 1, using this coefficient can ensure that the new target temperature Tp is always lower than the preset target temperature Ts.

[0181] The core purpose of the above optional embodiment is to provide a dynamic temperature adjustment mechanism. When the pressure reaches or approaches the first pressure threshold P3 during the treatment process, directly stopping the RF energy output may affect the treatment effect. Therefore, the system chooses to reduce the temperature of the heating element to relieve the rising trend of the pressure. This progressive adjustment allows the system to solve the problem of excessive pressure by reducing the temperature without completely interrupting the treatment.

[0182] Through the formula Tp = b × Ts, the processor can flexibly calculate an appropriate temperature reduction value:

[0183] When b is close to 1, the temperature reduction is smaller and the system selects a higher new target temperature, which is suitable for situations where smaller temperature adjustments are required.

[0184] When b is small (close to 0), the new target temperature drops more, which is suitable for situations where a large temperature reduction is required.

[0185] The b value in the formula can be adjusted according to specific treatment needs. For example, the system can select different b values ​​according to the tissue characteristics of different patients or different treatment stages in order to optimize the treatment effect.

[0186] By lowering the target temperature, the system can effectively prevent tissue damage caused by excessive temperature. Especially during treatment, when pressure increases, directly lowering the temperature of the heating element can quickly reduce the amount of energy transferred to the tissue, thereby avoiding excessive tissue contraction or burning.

[0187] In addition, since the range of b is limited to between 0 and 1, the new target temperature Tp is always less than the preset target temperature Ts, which provides additional safety for the system. Even in extreme cases, the system will not maintain the temperature at a high risk level.

[0188] By using the formula Tp = b × Ts, the system can flexibly adjust the temperature based on real-time pressure feedback to ensure the best treatment effect under different treatment conditions. This automated temperature regulation enables the system to have higher adaptability in complex treatment environments.

[0189] In addition, the processor can adjust the range of b values ​​according to different surgical scenarios or patient needs. For example, in some cases, the doctor may want to reduce the temperature only slightly, in which case a larger b value can be selected. In other cases, such as when the risk of tissue overheating is high, a smaller b value can be selected to reduce the temperature more significantly.

[0190] This implementation provides a dynamic temperature adjustment mechanism based on pressure feedback for the radiofrequency ablation system by introducing the b coefficient and the formula Tp = b × Ts. It not only improves the safety during treatment, but also ensures that the system can adapt to different treatment scenarios through a flexible temperature adjustment mechanism, thereby optimizing the final treatment effect.

[0191] Optionally, the processor is further configured to:

[0192] In step (f), after the target temperature of the heating element is lowered to the new target temperature, the heating element is controlled to maintain the new target temperature until the preset treatment time ends; wherein,

[0193] The processor is further configured to continuously monitor the current pressure value P during maintaining the new target temperature, and execute step (g) when the current pressure value P exceeds the second pressure threshold P4.

[0194] Optionally, the processor is further configured to:

[0195] In step (g), when controlling the radio frequency generator to stop outputting radio frequency energy, the following operations are simultaneously performed:

[0196] (i) Display an abnormal warning message through the display, where the abnormal warning message includes a prompt that the current pressure value P exceeds the second pressure threshold P4;

[0197] (ii) Generate an audible alarm sound; and

[0198] (iii) Record the time of occurrence of the abnormality, the current pressure value P, and the current temperature value into the system log.

[0199] Optionally, the system further includes:

[0200] A user input interface, electrically connected to the processor, and the user input interface is configured to:

[0201] (i) Receive a preset target temperature Ts input by the user;

[0202] (ii) Receive a preset treatment time input by the user;

[0203] (iii) Receive a coefficient b input by the user, where 0 < b < 1, for calculating the new target temperature Tp;

[0204] (iv) Receive a constant K input by the user, where K > 1, for calculating the second pressure threshold P4;

[0205] Wherein, the processor is further configured to execute steps (a) to (g) in claim 1 according to the parameters received from the user input interface, and use these parameters for corresponding calculations and controls during the execution process.

[0206] Optionally, the display is configured to:

[0207] Display the following information in real time:

[0208] (i) The current pressure value P;

[0209] (ii) The current temperature value T;

[0210] (iii) The target temperature value, including the preset target temperature Ts and the new target temperature Tp (if applicable);

[0211] (iv) The remaining treatment time;

[0212] (v) a first pressure threshold value P3 and a second pressure threshold value P4;

[0213] (vi) output power of the RF generator;

[0214] (vii) System operating status, including normal operation, cooling stage or abnormal stop status indication.

[0215] Optionally, the heating element comprises:

[0216] (i) a thermocouple 20, for measuring the temperature of the heating element in real time and transmitting the measurement result to the processor;

[0217] (ii) a heating element winding coaxially surrounding the thermocouple 20, the heating element winding 30 being configured to receive RF energy from the RF generator, convert it into heat and evenly distribute it;

[0218] (iii) an insulating layer, covering the outside of the heating element winding 30, for electrical insulation and heat retention;

[0219] (iv) A flexible housing, made of biocompatible material, enveloping the entire heating element structure.

[0220] Optionally, the system further comprises: a tumescent fluid injection device electrically connected to the processor, wherein the tumescent fluid injection device is configured to:

[0221] (i) injecting a preset volume of tumescent fluid into the cavity tissue;

[0222] (ii) sending an injection completion signal to the processor;

[0223] Wherein, the processor is further configured to:

[0224] (a) receiving the injection completion signal;

[0225] (b) in response to the injection completion signal, continuously monitoring the contact between the heating element and the cavity tissue through the pressure sensor 10;

[0226] (c) calculating the contact area percentage between the heating element and the cavity tissue based on the measurement result of the pressure sensor 10;

[0227] (d) controlling the display to display the contact status in real time, including: numerical display of the contact area percentage, and / or graphical representation of the contact status;

[0228] (e) When the contact area percentage is lower than a preset threshold, controlling the display to send a warning signal.

[0229] Optionally, the processor is further configured to dynamically adjust the radio frequency energy output power, specifically including:

[0230] (a) Setting the initial RF output power value Pinitial;

[0231] (b) During the treatment process, the current temperature value T and the current pressure value P are continuously acquired at a preset sampling frequency;

[0232] (c) Based on the current temperature value T, the current pressure value P, the target temperature Ts and the first pressure threshold value P3, the power adjustment factor α is calculated, where:

[0233] α=f(T,P,Ts,P3), f is the preset power adjustment function;

[0234] (d) According to the power adjustment factor α, calculate the new RF output power value Pnew:

[0235] Pnew=Pcurrent×α

[0236] Wherein, Pcurrent is the current RF output power value;

[0237] (e) applying the new RF output power value Pnew to the RF generator to dynamically adjust the RF energy output;

[0238] (f) Set the upper limit Pmax and lower limit Pmin of power adjustment to ensure:

[0239] Pmin≤Pnew≤Pmax

[0240] Among them, Pmin and Pmax are pre-defined safe power ranges;

[0241] (g) Rapid power adjustment is triggered when any of the following conditions occurs:

[0242] (i) When the temperature rises rapidly and exceeds the preset safety temperature threshold Tsafe, the output power is immediately reduced to Pmin;

[0243] (ii) when the pressure rises rapidly and exceeds the first pressure threshold value P3, the output power is reduced to a preset percentage β% of the current power (where 0<β<100);

[0244] (h) after each power adjustment, record relevant data of the power adjustment, including but not limited to: adjustment time, power before adjustment, power after adjustment, current temperature, current pressure and power adjustment factor α;

[0245] (i) generating a power adjustment curve and a temperature and pressure change curve based on the recorded data, and displaying these curves to the user through the display after the treatment is completed for analysis;

[0246] (j) Based on historical treatment data and machine learning algorithms, the power adjustment function f is periodically optimized to improve the system's adaptability and treatment effect.

[0247] Specifically, in the above optional embodiment, the processor is configured to dynamically adjust the output power of the radio frequency energy to adapt to the changes in temperature and pressure during the treatment process, thereby ensuring the effectiveness and safety of the treatment. This process is achieved through a series of carefully designed steps, each of which has its specific purpose and function.

[0248] First, the system sets an initial RF output power value as a baseline for the start of treatment. During treatment, the system continuously monitors the current temperature and pressure values ​​at a preset frequency. These real-time data are the basis for subsequent dynamic adjustments. Based on this data, the system calculates a power adjustment factor that takes into account the current temperature, pressure, target temperature, and preset pressure threshold.

[0249] Next, the system uses this adjustment factor to calculate the new RF output power. This calculation method allows the system to optimize the power in real time based on the current treatment status. To ensure safety, the system also sets upper and lower limits for power adjustment to ensure that the new power value is always within the predefined safety range.

[0250] In addition, the system also includes a rapid power adjustment mechanism. When the temperature or pressure rises rapidly and exceeds the preset threshold, the system will immediately reduce the output power to prevent overheating or overpressure from damaging the tissue. This rapid response mechanism is a key factor in ensuring treatment safety.

[0251] After each power adjustment, the system will record relevant data in detail, including adjustment time, power values ​​before and after adjustment, current temperature and pressure, etc. These data are not only used to generate power adjustment curves and temperature and pressure change curves for doctors to analyze after treatment, but also provide valuable information for the continuous optimization of the system.

[0252] Finally, the system introduces a machine learning algorithm that uses historical treatment data to periodically optimize the power adjustment function. This self-learning and optimization mechanism can continuously improve the system's adaptive ability, enabling it to more accurately control RF energy output in future treatments.

[0253] In general, this dynamic power adjustment mechanism combines real-time data analysis, safety measures and machine learning technology to not only ensure the safety of the treatment process, but also improve the effect and efficiency of radiofrequency ablation treatment through continuous optimization. This intelligent power control method represents the trend of medical equipment towards more precise, safer and more personalized development.

[0254] The above embodiments have the following technical effects:

[0255] Precisely control RF energy output to avoid tissue damage: By real-time monitoring of temperature and pressure and dynamically adjusting RF energy output power, the system can quickly respond to changes in tissue contact pressure to prevent excessive energy transmission and avoid tissue burns caused by excessive heating. Especially when the temperature rises rapidly or the pressure exceeds the threshold, the system can immediately reduce the output power to ensure the safety and accuracy of the treatment.

[0256] Real-time feedback on the contraction of cavity tissue improves treatment effect: The system obtains the contact pressure between the catheter and the cavity tissue through the pressure sensor, and intuitively displays the contraction of the cavity tissue before and after treatment through the display. This real-time feedback not only helps doctors better understand the treatment process, but also allows them to take timely measures when the cavity tissue contracts abnormally, thus reducing surgical risks.

[0257] Automatically adjust the treatment temperature to avoid excessive heat energy: The system automatically calculates and adjusts the treatment temperature according to the pressure changes at different temperature points. When the pressure reaches the set threshold, the system will lower the target temperature and maintain the appropriate temperature level according to the treatment time to avoid overheating and reduce damage to normal tissues.

[0258] Abnormal detection and alarm function improves operational safety: When abnormal conditions occur during treatment (such as pressure or temperature exceeding the set threshold), the system can stop the RF energy output in time and issue abnormal warnings through the display and alarm to prompt doctors to take appropriate measures. This mechanism greatly improves the operational safety of the system and reduces medical accidents caused by equipment failure or operational errors.

[0259] Efficient data recording and analysis, optimized treatment plan: The system records the temperature, pressure, power change and other data during each treatment process, and generates relevant curves for users to analyze. With these data, doctors can more accurately evaluate the treatment effect and optimize subsequent treatment plans based on historical data. In addition, the system can also combine machine learning algorithms to automatically optimize the power adjustment function, further improving the adaptive ability and effect of treatment.

[0260] Flexible power adjustment mechanism to meet different clinical needs: The system sets the upper and lower limits of power adjustment, and dynamically adjusts the RF output power through the power adjustment factor. This flexible power adjustment mechanism enables the system to adapt to different treatment environments and individual differences of patients, ensuring that the energy output during treatment is always within a safe and effective range.

[0261] Reduce doctors' manual operations and improve surgical efficiency: Through automated temperature and pressure monitoring, power adjustment, and exception handling, the system reduces doctors' manual operations and displays key treatment-related data in real time on the display, helping doctors complete surgeries more efficiently. This not only improves surgical efficiency, but also reduces errors caused by human operations.

[0262] In summary, the present application significantly improves the safety, accuracy and efficiency of radiofrequency ablation treatment, and provides a more reliable treatment tool for clinical practice.

[0263] It should be noted that in the application documents of this patent, relational terms such as first and second are only used to distinguish one entity or operation from another entity or operation, and do not necessarily require or imply any such actual relationship or order between these entities or operations. Moreover, the terms "include", "comprise" or any other variants thereof are intended to cover non-exclusive inclusion, so that the process, method, article or device including a series of elements includes not only those elements, but also other elements not explicitly listed, or also includes elements inherent to such process, method, article or device. In the absence of further restrictions, the elements defined by the sentence "including one" do not exclude the existence of other identical elements in the process, method, article or device including the elements. In the application documents of this patent, if it is mentioned that an action is performed according to an element, it means that the action is performed at least according to the element, which includes two situations: performing the action only according to the element, and performing the action according to the element and other elements. Expressions such as multiple, multiple, and multiple include 2, 2 times, 2 kinds, and more than 2, more than 2 times, and more than 2 kinds.

[0264] All documents mentioned in this application are considered to be included in the disclosure of this application as a whole, so that they can be used as the basis for modification when necessary. In addition, it should be understood that after reading the above disclosure of this application, those skilled in the art can make various changes or modifications to this application, and these equivalent forms also fall within the scope of protection claimed in this application.

Claims

1. An intracavitary radiofrequency ablation system, characterized in that: The system comprises: a radio frequency generator for generating and transmitting radio frequency energy to the heating element of the catheter; The catheter comprises: a heating element for receiving the radio frequency energy and heating the cavity tissue; a pressure sensor disposed at the heating element for detecting the contact pressure between the heating element and the cavity tissue; and a temperature sensor disposed at the heating element for detecting the temperature of the heating element; A processor is electrically connected to the RF generator, the pressure sensor, and the temperature sensor, and the processor is configured to: (a) obtaining an initial pressure value P1 and an initial temperature value T1; (b) controlling the RF generator to output RF energy to the heating element so that its temperature rises to a second temperature value T2, and obtaining the second pressure value P2 at this time; (c) calculating a pressure-temperature function relationship according to the initial pressure value P1, the initial temperature value T1, the second pressure value P2 and the second temperature value T2; (d) calculating a first pressure threshold value P3 and a second pressure threshold value P4 at a preset target temperature based on the pressure-temperature function relationship, wherein P4 is greater than P3; (e) controlling the heating element to heat up to the preset target temperature and monitoring the current pressure value P in real time; (f) when the current pressure value P reaches the first pressure threshold value P3, reducing the target temperature of the heating element to a new target temperature lower than the preset target temperature; (g) when the current pressure value P exceeds the second pressure threshold value P4 and the current temperature is lower than the preset target temperature, controlling the RF generator to stop outputting RF energy; The display is electrically connected to the processor and is used to display the pressure value changes before and after treatment to reflect the contraction of the cavity tissue.

2. The intracavitary radiofrequency ablation system according to claim 1, characterized in that: The processor is further configured to: According to the initial pressure value P1, the initial temperature value T1, the second pressure value P2 and the second temperature value T2, the pressure value P at the current temperature T is calculated using the pressure-temperature function relationship, and the pressure-temperature function relationship is: P=[(P2-P1) / (T2-T1)]×T+[(P1×T2-P2×T1) / (T2-T1)]+a Where a is the correction constant and T is the current temperature.

3. The intracavitary radiofrequency ablation system according to claim 1, characterized in that: The processor is further configured to: In step (d), the second pressure threshold P4 is calculated according to the formula P4=P3×K, where K is a preset constant greater than 1.

4. The intracavitary radiofrequency ablation system according to claim 1, characterized in that: The processor is further configured to: In step (f), the new target temperature Tp is calculated according to the formula Tp=b×Ts, where Ts is the preset target temperature and b is a preset coefficient greater than 0 and less than 1.

5. The intracavitary radiofrequency ablation system according to claim 1, characterized in that: The processor is further configured to: In step (f), after the target temperature of the heating element is lowered to the new target temperature, the heating element is controlled to maintain the new target temperature until the preset treatment time ends; wherein, The processor is further configured to continuously monitor the current pressure value P during the period of maintaining the new target temperature, and execute step (g) when the current pressure value P exceeds the second pressure threshold value P4.

6. The intracavitary radiofrequency ablation system according to claim 1, characterized in that: The processor is further configured to: In step (g), when controlling the RF generator to stop outputting RF energy, the following operations are simultaneously performed: (i) Display an abnormal warning message through the display, where the abnormal warning message includes a prompt that the current pressure value P exceeds the second pressure threshold P4; (ii) Generate an audible alarm sound; And (iii) Record the time of abnormal occurrence, the current pressure value P, and the current temperature value into the system log.

7. The intracavitary radiofrequency ablation system according to claim 1, characterized in that: The system further includes: A user input interface, electrically connected to the processor, and the user input interface is configured to: (i) Receive a preset target temperature Ts input by the user; (ii) Receive a preset treatment time input by the user; (iii) Receive a coefficient b input by the user, where 0 < b < 1, for calculating a new target temperature Tp; (iv) Receive a constant K input by the user, where K > 1, for calculating the second pressure threshold P4; Wherein, the processor is further configured to perform steps (a) to (g) in claim 1 according to the parameters received from the user input interface, and use these parameters for corresponding calculations and controls during the execution process.

8. The intracavitary radiofrequency ablation system according to claim 1, characterized in that: The display is configured to: Real-time display the following information: (i) The current pressure value P; (ii) The current temperature value T; (iii) The target temperature value, including the preset target temperature Ts and the new target temperature Tp (if applicable); (iv) The remaining treatment time; (v) The first pressure threshold P3 and the second pressure threshold P4; (vi) The output power of the RF generator; (vii) The system operation status, including status indicators such as normal operation, cooling stage, or abnormal stop.

9. The intracavitary radiofrequency ablation system according to claim 1, characterized in that: The heating element includes: (i) A thermocouple for real-time measuring the temperature of the heating element and transmitting the measurement result to the processor; (ii) A heating element winding coaxially surrounding the thermocouple, and the heating element winding is configured to receive RF energy from the RF generator, convert it into heat, and distribute it evenly; (iii) An insulating layer covering the outside of the heating element winding for electrical insulation and heat retention; (iv) A flexible housing made of a biocompatible material covering the entire heating element structure.

10. The intracavitary radiofrequency ablation system according to claim 1, characterized in that: The system further includes: a swelling liquid injection device, electrically connected to the processor, and the swelling liquid injection device is configured to: (i) Inject a preset volume of swelling liquid into the cavity tissue; (ii) Send an injection completion signal to the processor; Wherein, the processor is further configured to: (a) Receive the injection completion signal; (b) In response to the injection completion signal, continuously monitor the contact situation between the heating element and the cavity tissue through the pressure sensor; (c) Calculate the contact area percentage between the heating element and the cavity tissue based on the measurement result of the pressure sensor; (d) Control the display to real-time display the contact situation, including: numerical display of the contact area percentage, and / or graphical representation of the contact status; (e) When the contact area percentage is lower than a preset threshold, control the display to emit a warning signal.

11. The intracavitary radiofrequency ablation system according to claim 1, characterized in that: The processor is further configured to dynamically adjust the output power of the RF energy, specifically including: (a) Setting the initial RF output power value Pinitial; (b) During the treatment process, the current temperature value T and the current pressure value P are continuously acquired at a preset sampling frequency; (c) Based on the current temperature value T, the current pressure value P, the target temperature Ts and the first pressure threshold value P3, the power adjustment factor α is calculated, where: α=f(T,P,Ts,P3), f is the preset power adjustment function; (d) According to the power adjustment factor α, calculate the new RF output power value Pnew: Pnew=Pcurrent×α Wherein, Pcurrent is the current RF output power value; (e) applying the new RF output power value Pnew to the RF generator to dynamically adjust the RF energy output; (f) Set the upper limit Pmax and lower limit Pmin of power adjustment to ensure: Pmin≤Pnew≤Pmax Among them, Pmin and Pmax are pre-defined safe power ranges; (g) Rapid power adjustment is triggered when any of the following conditions occurs: (i) When the temperature rises rapidly and exceeds the preset safety temperature threshold Tsafe, the output power is immediately reduced to Pmin; (ii) when the pressure rises rapidly and exceeds the first pressure threshold value P3, the output power is reduced to a preset percentage β% of the current power (where 0<β<100); (h) after each power adjustment, record relevant data of the power adjustment, including but not limited to: adjustment time, power before adjustment, power after adjustment, current temperature, current pressure and power adjustment factor α; (i) generating a power adjustment curve and a temperature and pressure change curve based on the recorded data, and displaying these curves to the user through the display after the treatment is completed for analysis; (j) Based on historical treatment data and machine learning algorithms, the power adjustment function f is periodically optimized to improve the system's adaptability and treatment effect.

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