A high frequency energy control system and control method

Abstract

The application discloses a high-frequency energy control system and a control method, wherein the system comprises: a module for detecting the impedance value of human tissue to generate a current target power value P according to the detection result; a module for sampling the voltage value at the load end to obtain a sampling voltage value V1 and a module for sampling the current value at the load end to obtain a sampling current value I1; a module for multiplying the sampling voltage value V1 and the sampling current value I1 to obtain a feedback power value P m ; a module for calculating a current power error value W m ; a module for calculating a phase difference φ of a phase-shifted full bridge; a module for generating an output power control instruction according to the phase difference φ of the phase-shifted full bridge; and a module for outputting corresponding high-frequency energy according to the output power control instruction. The application can automatically output adaptive energy in a surgical process, and reduces the professional requirements for medical staff and the pain degree of patients.

Description

Technical Field

[0001] This invention relates to the field of medical devices, and more particularly to a high-frequency energy control system and control method. Background Technology

[0002] An ultrasonic scalpel is a high-frequency electrosurgical device primarily used for cutting biological tissues and closing blood vessels. It features minimal bleeding, less damage to surrounding tissues, and faster postoperative recovery. It cuts and coagulates human tissue and is widely used in operating rooms. The entire ultrasonic scalpel system mainly consists of a main unit, a transducer handle, an ultrasonic scalpel head, and a foot pedal. The main unit primarily consists of a high-frequency energy generator, responsible for providing a stable ultrasonic frequency electrical signal that meets surgical requirements. Traditional ultrasonic scalpels typically have their output energy set to one or two fixed power and time modes. Surgeons need to rely on their professional experience, the different coagulation characteristics of different tissues, and the differences in the coagulation process of the same tissue at different stages. They must observe tissue discoloration, smoke, etc., to determine whether coagulation is complete, and manually adjust the technique during coagulation to achieve rapid coagulation, minimal bleeding, low tissue damage, minimal adhesion, and rapid healing. This places high demands on the surgeon's professional experience.

[0003] On April 14, 2026, the State Intellectual Property Office of China disclosed a surgical scalpel coagulation control method, electronic device, medium, and program product, with publication number CN121845728A. The method includes: acquiring basic parameters of the surgical scalpel during operation; obtaining the real-time impedance of the surgical scalpel based on the basic parameters; determining a control strategy for the surgical scalpel when the real-time impedance meets a trigger condition, wherein the control strategy includes stopping the operation of the surgical scalpel or shutting down the surgical equipment corresponding to the surgical scalpel; and controlling the surgical scalpel based on the control strategy. This method calculates the real-time impedance using basic parameters and determines the control strategy for the surgical scalpel based on the real-time impedance meeting the trigger condition. The control strategy includes stopping the operation of the surgical scalpel or shutting down the surgical equipment corresponding to the surgical scalpel. This achieves the technical objective of intelligent self-stopping after coagulation is completed or emergency shutdown in case of short-circuit abnormalities through real-time impedance, reducing thermal damage to the human body and minimizing the risk of electric shock or tissue burns. However, to accommodate real-time impedance changes, the host's energy control module needs to have a sensitive dynamic response capability and a high-precision output energy control capability, which places higher design requirements on the energy control module of the ultrasonic surgical scalpel host. Summary of the Invention

[0004] The purpose of this invention is to provide a high-frequency energy control system and control method.

[0005] The high-frequency energy control system provided by this invention includes: A module for detecting the impedance value of human tissue and generating the current target power value P based on the detection result; a module for sampling the voltage value at the load terminal to obtain the sampled voltage value V1; and a module for sampling the current value at the load terminal to obtain the sampled current value I1. The feedback power value P is obtained by multiplying the sampled voltage value V1 and the sampled current value I1. m The module; Used to calculate the current power error value W m The module; The module used to calculate the phase difference φ of the phase-shifted full-bridge; Module used to generate output power control commands based on the phase difference φ of the phase-shifted full-bridge; A module used to output corresponding high-frequency energy according to the output power control command; Used to set the current power error value W m Including the previous power error value W m-1 The module.

[0006] The high-frequency energy control method provided by this invention includes the following steps: S1 is the step used to detect the impedance value of human tissue and generate the current target power value P based on the detection result; S2 is used to sample the voltage value at the load terminal to obtain the sampled voltage value V1, and simultaneously sample the current value at the load terminal to obtain the sampled current value I1. S3 is used to multiply the sampled voltage value V1 and the sampled current value I1 to obtain the feedback power value P. m Steps; S4 is used to calculate the current power error value W. m Steps; S5 is used to set the proportional gain K. p and integral gain K i Read the previous power error value W m-1 And based on the current power error value W m Compared with the previous power error value W m-1 The steps to calculate the phase difference φ of the phase-shifted full-bridge; S6 is the step used to generate output power control commands based on the phase difference φ of the phase-shifted full-bridge; S7 is used to output corresponding high-frequency energy according to the output power control command; S8 is used to set the current power error value W. m Including the previous power error value W m-1 This is to prepare the steps for use in the next calculation.

[0007] The high-frequency energy control system and control method provided by this invention can not only achieve intelligent adaptive energy output control according to different human tissues and the impedance values ​​of human tissues at different coagulation stages, but also have a more sensitive dynamic response capability and a higher precision output energy control capability. It can automatically output appropriate energy during the operation, reduce the professional requirements of medical staff, improve the accuracy of the operation, reduce tissue damage, shorten the healing time, improve the efficiency of the operation, and reduce the degree of patient pain. Attached Figure Description

[0008] Figure 1 This is a flowchart illustrating the high-frequency energy control method described in Example 1. Figure 2 This is a schematic diagram of the steps in the high-frequency energy control method described in Example 2, which involves detecting human tissue and generating a current target power value P based on the detection results. Detailed Implementation

[0009] To make the objectives, technical solutions, and advantages of the embodiments of the present invention clearer, the technical solutions of the embodiments of the present invention will be clearly and completely described below with reference to the accompanying drawings. Obviously, the described embodiments are only some embodiments of the present invention, not all embodiments. Based on the embodiments of the present invention, all other embodiments obtained by those skilled in the art without creative effort are within the scope of protection of the present invention. Example

[0010] This embodiment provides a high-frequency energy control system, comprising: This module is used to detect the impedance value of human tissue and generate the current target power value P based on the detection result. Those skilled in the art will understand that different parts of the human body, such as the stratum corneum, muscle, fat, or blood vessels, have different impedance values. The same human tissue also has different impedance values ​​at different stages of the coagulation process, such as when the tissue is moist, dehydrated, denatured, fused, or excessively dry. Therefore, the location or stage of the human tissue being cut or coagulated can be determined based on the detected impedance value, thereby outputting energy corresponding to the state of the human tissue. This not only automates the output of appropriate energy during surgery, reducing the professional requirements for medical personnel, but also improves surgical precision, reduces tissue damage, shortens healing time, increases surgical efficiency, and reduces patient suffering.

[0011] A module for sampling the voltage value at the load end to obtain the sampled voltage value V1 and a module for sampling the current value at the load end to obtain the sampled current value I1; those skilled in the art will understand that the load end refers to the tip end of the high-frequency ultrasonic scalpel.

[0012] The feedback power value P is obtained by multiplying the sampled voltage value V1 and the sampled current value I1. m The module; Used to calculate the current power error value W m The module; The module used to calculate the phase difference φ of the phase-shifted full-bridge; Module used to generate output power control commands based on the phase difference φ of the phase-shifted full-bridge; A module used to output corresponding high-frequency energy according to the output power control command; Used to set the current power error value W m Including the previous power error value W m-1 The module.

[0013] Those skilled in the art will understand that the digital signal processing circuit can determine the current power error value W based on this value. m Compared with the previous power error value W m-1 The phase difference φ of the phase-shifted full-bridge is calculated, and the phase difference of the switching transistors in the phase-shifted full-bridge drive circuit is adjusted to a state corresponding to the phase difference φ of the phase-shifted full-bridge, thereby adjusting the output voltage of the phase-shifted full-bridge drive circuit. This completes the step of generating an output power control command based on the phase difference φ of the phase-shifted full-bridge, and thus realizes the adjustment of the output power.

[0014] Furthermore, the method for calculating the current power error value W m The module is implemented using the following algorithm: Current power error value W m =|Current target power value P - Feedback power value P m |; Furthermore, the module used to calculate the phase difference φ of the phase-shifted full-bridge is implemented using the following algorithm: Phase difference φ of phase-shifted full-bridge = proportional gain K p ×Current power error value (W) m + Integral gain K i ×Previous power error value W m-1 Those skilled in the art will understand that the K p The value of K can be set to 0.1. i The value can be set to 0.01.

[0015] Furthermore, the module for sampling the voltage value at the load terminal to obtain the sampled voltage value V1 includes: A submodule used to acquire the load terminal voltage value V0 using a high-frequency transformer; A submodule used to input the load voltage value V0 into a differential amplifier circuit for amplification and output the sampled voltage value V1.

[0016] Furthermore, the module for sampling the current value at the load terminal to obtain the sampled current value I1 includes: Used to acquire the primary current value I at the load terminal using a high-frequency current transformer. p Submodules; Used to measure the primary current value I at the load terminal p The submodule is a peak hold circuit that performs conversion processing to output the DC sampling current value I1.

[0017] Furthermore, the high-frequency energy control system provided in this embodiment also includes an overvoltage protection module, which includes: Used to send the sampled voltage value V1 to a voltage threshold V. m A submodule of the hardware comparator; Used to compare the sampled voltage value V1 with the voltage threshold V m A comparison is performed when the sampled voltage value V1 is equal to or greater than the voltage threshold V. m A submodule that cuts off power supply when necessary.

[0018] Furthermore, the high-frequency energy control system provided in this embodiment also includes an overcurrent protection module, which includes: Used to send the sampled current value I1 to a current threshold I. m A submodule of the hardware comparator; Used to compare the sampled current value I1 with the current threshold I m A comparison is made when the sampled current value I1 is equal to or greater than the current threshold I. m A submodule that cuts off power supply when necessary.

[0019] Furthermore, the module for detecting the impedance value of human tissue and generating the current target power value P based on the detection result includes: A submodule for setting the first threshold K1 of the impedance slope, setting the second threshold K2, and setting the initial target power value P0; A submodule used to monitor the impedance value Zt of human tissue in real time and calculate the current impedance slope value K. This submodule is used to compare the current impedance slope value K with the second impedance slope threshold K2 when the current impedance slope value K is greater than or equal to the first impedance slope threshold K1, and to add a set power value increment ΔP to the initial target power value P0 when the current impedance slope value K is less than the second impedance slope threshold K2, thereby obtaining the current target power value P. This submodule is used to compare the current impedance slope value K with the second impedance slope threshold K2 when the current impedance slope value K is greater than or equal to the first impedance slope threshold K1. When the current impedance slope value K is greater than or equal to the second impedance slope threshold K2, the set power value increment ΔP is reduced based on the initial target power value P0 to obtain the current target power value P.

[0020] Those skilled in the art will understand that when the current impedance slope value K is less than the first threshold K1 of the impedance slope, it can be determined that the current human tissue is in the initial stage of the coagulation process; in this stage, the human tissue is in a dehydrated state, and the impedance value Zt of the human tissue usually rises rapidly due to the evaporation of tissue fluid.

[0021] Those skilled in the art will understand that when the impedance slope is only equal to the first threshold K1, it can be determined that the current human tissue has completed dehydration and has begun to enter the second stage of the coagulation process. In this stage, the human tissue begins to undergo protein denaturation and then fusion. At this time, the impedance value Zt of the human tissue enters a plateau period of slow rise or slight fluctuation. If the output energy is adjusted by the manual judgment of medical personnel at this time, the accuracy and sensitivity are insufficient, and errors are very likely to occur. If the output energy is not reduced in time, it will lead to carbonization of the human tissue, prolonging the postoperative healing time and increasing the patient's pain. Through the high-frequency energy control method provided in this embodiment, the ultrasonic scalpel can achieve adaptive energy adjustment to changes in human tissue. When the impedance value Zt of the human tissue tends to stagnate, the output energy can be automatically increased slightly to maintain the thermal effect, thereby maintaining the coagulation process; when the impedance value Zt of the human tissue tends to rise too quickly, the output energy can be automatically reduced to prevent the human tissue from being carbonized; thus maintaining the continuous progress of the entire coagulation process.

[0022] Furthermore, the module for detecting the impedance value of human tissue and generating the current target power value P based on the detection result also includes: A submodule used to set the target impedance threshold Z0; This submodule is used to compare the impedance value Zt of human tissue monitored in real time with the target impedance threshold Z0. When the impedance value Zt is greater than or equal to the target impedance threshold Z0, the current target power value P is set to 0.

[0023] Those skilled in the art will understand that when the impedance value Zt of human tissue is greater than or equal to the target impedance threshold Z0, it can be determined that the current human tissue has completed coagulation. At this time, the current target power value P can be set to 0 to end the high-frequency energy control process.

[0024] Those skilled in the art will understand that the first threshold K1 of the impedance slope can be set to 0.364, the second threshold K2 can be set to 0.836, the initial target power value P0 can be set to 30W, and the power value increment ΔP can be set to 0.1W. In this way, the target power value P can be increased from 30W to 135W at a rate of 1W every 30 milliseconds. Example

[0025] like Figure 1 , Figure 2 As shown, this embodiment provides a high-frequency energy control method, including the following steps: S1 is a step used to detect the impedance value of human tissue and generate the current target power value P based on the detection result. Those skilled in the art will understand that tissues in different parts of the human body, such as the stratum corneum, muscle, fat, or blood vessels, have different impedance values. The same human tissue also has different impedance values ​​at different stages of the coagulation process, such as when the human tissue is in a moist state, a dehydrated state, a protein denaturation state, a fused state, or an excessively dry state. Therefore, the location or coagulation stage of the human tissue being cut or coagulated can be determined based on the detected impedance value of the human tissue, thereby outputting energy corresponding to the state of the human tissue. This not only allows for the automated output of appropriate energy during surgery, reducing the professional requirements for medical personnel, but also improves surgical accuracy, reduces tissue damage, shortens healing time, increases surgical efficiency, and reduces patient suffering.

[0026] S2 is used to sample the voltage value at the load terminal to obtain the sampled voltage value V1, and simultaneously sample the current value at the load terminal to obtain the sampled current value I1. Those skilled in the art will understand that the load end refers to the tip end of the high-frequency ultrasonic scalpel.

[0027] S3 is used to multiply the sampled voltage value V1 and the sampled current value I1 to obtain the feedback power value P. m Steps; S4 is used to calculate the current power error value W. m Steps; S5 is used to set the proportional gain K. p and integral gain K i Read the previous power error value W m-1 And based on the current power error value W m Compared with the previous power error value W m-1 The steps to calculate the phase difference φ of the phase-shifted full-bridge; S6 is the step used to generate output power control commands based on the phase difference φ of the phase-shifted full-bridge; S7 is a step used to output corresponding high-frequency energy according to the output power control command.

[0028] S8 is used to set the current power error value W. m Including the previous power error value W m-1 This is to prepare the steps for use in the next calculation; Those skilled in the art will understand that the digital signal processing circuit can determine the current power error value W based on this value. m Compared with the previous power error value W m-1 The phase difference φ of the phase-shifted full-bridge is calculated, and the phase difference of the switching transistors in the phase-shifted full-bridge drive circuit is adjusted to a state corresponding to the phase difference φ of the phase-shifted full-bridge, thereby adjusting the output voltage of the phase-shifted full-bridge drive circuit. This completes the step of generating an output power control command based on the phase difference φ of the phase-shifted full-bridge, and thus realizes the adjustment of the output power.

[0029] Furthermore, S4 is used to calculate the current power error value W. m The steps, the current power error value W m The current target power value P and the feedback power value P m The absolute value of the difference between the two can be obtained using the following algorithm: Current power error value W m =|Current target power value P - Feedback power value P m |

[0030] Furthermore, S5 is used to set the proportional gain K. p and integral gain K i Read the previous power error value W m-1 And based on the current power error value W m Compared with the previous power error value W m-1 The steps for calculating the phase difference φ of the phase-shifted full-bridge are implemented using the following algorithm: Phase difference φ of phase-shifted full-bridge = proportional gain K p ×Current power error value (W) m + Integral gain K i ×Previous power error value W m-1 Those skilled in the art will understand that the K p The value of K can be set to 0.1. i The value can be set to 0.01.

[0031] Furthermore, the step of sampling the voltage value at the load terminal to obtain the sampled voltage value V1 in step S2 includes: S211 uses a high-frequency transformer to collect the load-side voltage value V0; S212 inputs the load voltage value V0 into the differential amplifier circuit for amplification, thereby outputting the sampled voltage value V1.

[0032] Furthermore, the step of sampling the current value at the load terminal to obtain the sampled current value I1 in S2 includes: S221 uses a high-frequency current transformer to collect the primary current value I at the load end. p ; S222, the primary current value I at the load terminal p The input peak hold circuit performs conversion processing to output the DC sampling current value I1.

[0033] Furthermore, the high-frequency energy control method provided in this embodiment also includes an overvoltage protection step; the overvoltage protection step includes: Used to send the sampled voltage value V1 to a voltage threshold V. m The steps of a hardware comparator; Used to compare the sampled voltage value V1 with the voltage threshold V m A comparison is performed when the sampled voltage value V1 is equal to or greater than the voltage threshold V. m When necessary, disconnect the power supply.

[0034] Furthermore, the high-frequency energy control method provided in this embodiment also includes an overcurrent protection step; the overcurrent protection step includes: Used to send the sampled current value I1 to a current threshold I. m The steps of a hardware comparator; Used to compare the sampled current value I1 with the current threshold I m A comparison is made when the sampled current value I1 is equal to or greater than the current threshold I. m When necessary, disconnect the power supply.

[0035] Furthermore, step S1, which involves detecting human tissue and generating a current target power value P based on the detection results, includes: S101 sets the first threshold K1 for impedance slope, sets the second threshold K2, and sets the initial target power value P0; S102 monitors the impedance value Zt of human tissue in real time and calculates the current impedance slope value K. S103 compares the current impedance slope value K with the first threshold K1 of impedance slope. When the current impedance slope value K is less than the first threshold K1 of impedance slope, the initial target power value P0 is used as the current target power value P. When the current impedance slope value K is greater than or equal to the first threshold K1 of impedance slope, S104 is executed. Those skilled in the art will understand that when the current impedance slope value K is less than the first threshold K1 of the impedance slope, it can be determined that the current human tissue is in the initial stage of the coagulation process; in this stage, the human tissue is in a dehydrated state, and the impedance value Zt of the human tissue usually rises rapidly due to the evaporation of tissue fluid.

[0036] S104 compares the current impedance slope value K with the second threshold K2 of the impedance slope. When the current impedance slope value K is less than the second threshold K2, the set power value increment ΔP is added to the initial target power value P0 to obtain the current target power value P. When the current impedance slope value K is greater than or equal to the second threshold K2, the set power value increment ΔP is reduced from the initial target power value P0 to obtain the current target power value P.

[0037] Those skilled in the art will understand that when the impedance slope is only equal to the first threshold K1, it can be determined that the current human tissue has completed dehydration and begun to enter the second stage of the coagulation process. In this stage, the human tissue begins to undergo protein denaturation and then fusion. At this time, the impedance value Zt of the human tissue enters a plateau period of slow rise or slight fluctuation. If the output energy is adjusted by the manual judgment of medical personnel at this time, the accuracy and sensitivity are insufficient, and errors are very likely to occur. If the output energy is not reduced in time, it can lead to carbonization of human tissue, prolonging postoperative healing time and increasing patient suffering. The high-frequency energy control method provided in this embodiment enables the ultrasonic scalpel to adapt its energy to changes in human tissue. When the impedance value Zt of the human tissue tends to stagnate, the output energy is automatically increased slightly to maintain the thermal effect, thus sustaining the coagulation process. When the impedance value Zt of the human tissue shows a tendency to rise too rapidly, the output energy is automatically reduced to prevent carbonization of the human tissue, thereby ensuring the continuous and consistent progress of the entire coagulation process.

[0038] Furthermore, the power increment ΔP is obtained using the following method: S1041 is used to set the target impedance slope K0 and calculate the current slope error value K. m The steps, the current slope error value K m The absolute value of the difference between the current impedance slope K and the target impedance slope K0 is used to derive the following: Current slope error value K m =|Target impedance slope K0 - Current impedance slope value K|; S1042 is used to set the proportional gain K. p and integral gain K i Read the previous slope error value K m-1， The step of calculating and obtaining the power increment value ΔP is performed using the following algorithm: Power increment ΔP = proportional gain K p ×Current slope error value K m - Integral gain Ki × Previous slope error value K m-1 .

[0039] S1043 is used to set the current slope error value K of this calculation. m Including the previous slope error value K m-1， This is to prepare the steps for the next calculation.

[0040] Those skilled in the art will understand that by iteratively processing the above method, continuously monitoring the impedance value Zt of human tissue in real time, and continuously obtaining the current impedance slope value K and its error with the target impedance slope K0, the power value increment ΔP matching the error value is calculated. As the current impedance slope value K and its error with the target impedance slope K0 gradually decrease, the corresponding power value increment ΔP continuously decreases until the error between the current impedance slope value K and the target impedance slope K0 is zero, that is, when the current impedance slope value K is equal to the target impedance slope K0, the power value increment ΔP is zero, thereby enabling the current target power value P to reach the target power.

[0041] Furthermore, the step S1, which involves detecting the impedance value of human tissue and generating the current target power value P based on the detection result, further includes: S105 sets the target impedance threshold Z0; those skilled in the art will understand that the target impedance threshold Z0 can be set to be obtained by increasing the human tissue impedance value by 190 ohms at the end of the previous stage.

[0042] S106 compares the real-time monitored impedance value Zt of human tissue with the target impedance threshold Z0. When the impedance value Zt is greater than or equal to the target impedance threshold Z0, the current target power value P is set to 0. When the impedance value Zt is less than the target impedance threshold Z0, the process returns to execute S102.

[0043] Those skilled in the art will understand that when the impedance value Zt of human tissue is greater than or equal to the target impedance threshold Z0, it can be determined that the current human tissue has completed coagulation. At this time, the current target power value P can be set to 0 to end the high-frequency energy control process.

[0044] Those skilled in the art will understand that the first threshold K1 of the impedance slope can be set to 0.364, the second threshold K2 can be set to 0.836, the initial target power value P0 can be set to 30W, and the power value increment ΔP can be set to 0.1W. In this way, the target power value P can be increased from 30W to 135W at a rate of 1W every 30 milliseconds.

[0045] Finally, it should be noted that the above embodiments are only used to illustrate the technical solutions of the present invention, and not to limit them; although the present invention has been described in detail with reference to the foregoing embodiments, those skilled in the art should understand that modifications can still be made to the technical solutions described in the foregoing embodiments, or equivalent substitutions can be made to some of the technical features; and these modifications or substitutions do not cause the essence of the corresponding technical solutions to deviate from the spirit and scope of the technical solutions of the embodiments of the present invention.

Claims

1. A high-frequency energy control system, characterized in that, include: This module is used to detect the impedance value of human tissue and generate the current target power value P based on the detection result. A module for sampling the voltage value at the load terminal to obtain the sampled voltage value V1 and a module for sampling the current value at the load terminal to obtain the sampled current value I1. The feedback power value P is obtained by multiplying the sampled voltage value V1 and the sampled current value I1. m The module; Used to calculate the current power error value W m The module; The module used to calculate the phase difference φ of the phase-shifted full-bridge; Module used to generate output power control commands based on the phase difference φ of the phase-shifted full-bridge; A module used to output corresponding high-frequency energy according to the output power control command; Used to set the current power error value W m Including the previous power error value W m-1 The module.

2. A high-frequency energy control method, characterized in that, Includes the following steps: S1 is the step used to detect the impedance value of human tissue and generate the current target power value P based on the detection result; S2 is used to sample the voltage value at the load terminal to obtain the sampled voltage value V1, and simultaneously sample the current value at the load terminal to obtain the sampled current value I1. S3 is used to multiply the sampled voltage value V1 and the sampled current value I1 to obtain the feedback power value P. m Steps; S4 is used to calculate the current power error value W. m Steps; S5 is used to set the proportional gain K. p and integral gain K i Read the previous power error value W m-1 And based on the current power error value W m Compared with the previous power error value W m-1 The steps to calculate the phase difference φ of the phase-shifted full-bridge; S6 is the step used to generate output power control commands based on the phase difference φ of the phase-shifted full-bridge; S7 is used to output corresponding high-frequency energy according to the output power control command; S8 is used to set the current power error value W. m Including the previous power error value W m-1 This is to prepare the steps for use in the next calculation.

3. The high-frequency energy control method as described in claim 2, characterized in that, S4 is used to calculate the current power error value W. m The steps are implemented using the following algorithm: Current power error value W m =|Current target power value P - Feedback power value P m | 4. The high-frequency energy control method as described in claim 3, characterized in that, S5 is used to set the proportional gain K. p and integral gain K i Read the previous power error value W m-1 And based on the current power error value W m Compared with the previous power error value W m-1 The steps for calculating the phase difference φ of the phase-shifted full-bridge are implemented using the following algorithm: Phase difference φ of phase-shifted full-bridge = proportional gain K p ×Current power error value (W) m +Integral gain K i ×Previous power error value W m-1 .

5. The high-frequency energy control method as described in claim 4, characterized in that, The step of sampling the voltage value at the load terminal to obtain the sampled voltage value V1 in S2 includes: S211 uses a high-frequency transformer to collect the load-side voltage value V0; S212 inputs the load terminal voltage value V0 into the differential amplifier circuit for amplification, thereby outputting the sampled voltage value V1.

6. The high-frequency energy control method as described in claim 5, characterized in that, The step of sampling the current value at the load terminal to obtain the sampled current value I1 in S2 includes: S221 uses a high-frequency current transformer to collect the primary current value I at the load end. p ; S222, the primary current value I at the load end p The input peak hold circuit performs conversion processing to output the DC sampling current value I1.

7. The high-frequency energy control method as described in claim 6, characterized in that, It also includes an overvoltage protection step; the overvoltage protection step includes: Used to send the sampled voltage value V1 to a voltage threshold V. m The steps of a hardware comparator; Used to compare the sampled voltage value V1 with the voltage threshold V m A comparison is performed when the sampled voltage value V1 is equal to or greater than the voltage threshold V. m When necessary, disconnect the power supply.

8. The high-frequency energy control method as described in claim 7, characterized in that, It also includes an overcurrent protection step; the overcurrent protection step includes: Used to send the sampled current value I1 to a current threshold I. m The steps of a hardware comparator; Used to compare the sampled current value I1 with the current threshold I m A comparison is made when the sampled current value I1 is equal to or greater than the current threshold I. m When necessary, disconnect the power supply.

9. The high-frequency energy control method as described in claim 8, characterized in that, The step S1, which involves detecting human tissue and generating a current target power value P based on the detection results, includes: S101 sets the first threshold K1 for impedance slope, sets the second threshold K2, and sets the initial target power value P0; S102 monitors the impedance value Z(t) of human tissue in real time and calculates the current impedance slope value K. S103 compares the current impedance slope value K with the first threshold K1 of impedance slope. When the current impedance slope value K is less than the first threshold K1 of impedance slope, the initial target power value P0 is used as the current target power value P. When the current impedance slope value K is greater than or equal to the first threshold K1 of impedance slope, S104 is executed. S104 compares the current impedance slope value K with the second threshold K2 of the impedance slope. When the current impedance slope value K is less than the second threshold K2, the set power value increment ΔP is added to the initial target power value P0 to obtain the current target power value P. When the current impedance slope value K is greater than or equal to the second threshold K2, the set power value increment ΔP is reduced from the initial target power value P0 to obtain the current target power value P.

10. The high-frequency energy control method as described in claim 9, characterized in that, The power increment ΔP is obtained using the following method: S1041 is used to set the target impedance slope K0 and calculate the current slope error value K. m The steps, the current slope error value K m It is derived from the absolute value of the difference between the current impedance slope value K and the target impedance slope K0; S1042 is used to set the proportional gain K. p and integral gain K i Read the previous slope error value K m-1 The step of calculating and obtaining the power increment value ΔP is performed using the following algorithm: Power increment ΔP = proportional gain K p ×Current slope error value K m - Integral gain K i ×Previous slope error value K m-1 ; S1043 is used to set the current slope error value K of this calculation. m Including the previous slope error value K m-1 This is to prepare the steps for the next calculation.

11. The high-frequency energy control method as described in claim 10, characterized in that, The step S1, which involves detecting the impedance value of human tissue and generating a current target power value P based on the detection result, further includes: S105 sets the target impedance threshold Z0; S106 compares the real-time monitored impedance value Z(t) of human tissue with the target impedance threshold Z0. When the impedance value Z(t) is greater than or equal to the target impedance threshold Z0, the current target power value P is set to 0. When the impedance value Z(t) is less than the target impedance threshold Z0, the process returns to execute S102.

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