WO2024046321A1

WO2024046321A1 - Method and system for automatic power adjustment, ablation control device, and storage medium

Info

Publication number: WO2024046321A1
Application number: PCT/CN2023/115536
Authority: WO
Inventors: 崔长杰; 高永相; 刘志宇; 徐宏
Original assignee: 杭州堃博生物科技有限公司
Priority date: 2022-09-02
Filing date: 2023-08-29
Publication date: 2024-03-07
Also published as: CN117679147A; TW202410866A; TWI843390B

Abstract

The present application relates to the technical field of radiofrequency ablation, and specifically, to a method and system for automatic power adjustment, an ablation control device, and a storage medium. The method and system are used for adjusting an output power of the ablation control device, and the ablation control device comprises a plurality of electrodes. The method comprises: acquiring real-time current values and real-time voltage values of the electrodes of the ablation control device during the ablation; determining, according to the real-time current values and the real-time voltage values, real-time impedances of the electrodes, and determining, on the basis of the real-time impedances, one specified electrode from the electrodes; determining, on the basis of the real-time impedance of the specified electrode and a preset single-electrode power, a target single-electrode power of at least one of the electrodes; and adjusting, on the basis of a real-time power of the at least one electrode and the target single-electrode power, an input voltage of the ablation control device, so as to adjust the output power of the ablation control device. The present application adjusts the output power according to the target single-electrode power of at least one of the electrodes, thus possessing higher accuracy in adjusting the output power.

Description

Method, system, ablation control device and storage medium for automatically adjusting power

Technical field

This application belongs to the technical field of radiofrequency ablation, and specifically relates to a method, system, ablation control equipment and storage medium for automatically adjusting power.

Background technique

Radiofrequency ablation is a treatment method that applies high-frequency alternating current to the affected area of the target object until a set energy is reached to kill specific tissues such as tumors or cancer cells. This method is usually used in the treatment of common diseases of the respiratory system to solve the problems of incomplete and inefficient treatment with traditional drug treatments.

At present, in radiofrequency ablation methods, each electrode is usually connected in parallel and outputs a constant voltage until the set ablation energy is reached. However, during the ablation process, the temperature of electronic components, including electrodes, usually increases, causing the impedance of the electronic components to also increase. The increase in impedance will cause the output power of the electrode to decrease, thus affecting the ablation efficiency.

Contents of the invention

This application provides a method, system, ablation control device and storage medium for automatically adjusting power to solve the problem in the prior art that the relationship between temperature and impedance is not considered, resulting in reduced ablation efficiency.

The basic solution of this application is: a method for adjusting power, the method is used to adjust the output power of an ablation control device, the ablation control device includes a plurality of electrodes; the method includes:

Obtain the real-time current value and real-time voltage value of each electrode of the ablation control device during the ablation process;

Determine the real-time impedance of each electrode according to the real-time current value and the real-time voltage value, and determine a designated electrode from each of the electrodes based on the real-time impedance;

Determine the target monopolar power of at least one of the electrodes based on the real-time impedance of the designated electrode and the set preset monopolar power;

Based on the real-time power of the at least one electrode and the target monopolar power, the input voltage of the ablation control device is adjusted to adjust the output power of the ablation control device.

This application also provides an ablation system, including a power output board and an ablation control device; the ablation control device includes a central processing unit, a sampling unit, and a plurality of electrodes, wherein,

The electrode is connected to one or more ablation objects and is used to ablate the connected ablation objects;

The sampling unit is used to detect the real-time current value and real-time voltage value of each electrode and send them to the central processing unit;

The central processing unit is configured to: determine the real-time impedance of each electrode based on the real-time current value and real-time voltage value sent by the sampling unit, and determine a designated electrode from each of the electrodes based on the real-time impedance; and, Determine the target electrode monopolar power of at least one of the electrodes based on the real-time impedance of the designated electrode and the set preset monopolar power; and, based on the real-time power of the at least one electrode, and the Target monopolar power, determine the control voltage signal that the ablation control device needs to send, and send the control voltage signal to the power output board;

The power output board is used to determine the target voltage according to the control voltage signal sent by the central processing unit, and adjust the output power of the electrode according to the control voltage signal.

The present application also provides an ablation control device, including a memory, a processor, and a computer program stored on the memory and executable on the processor. When the processor executes the computer program, it implements a method of adjusting power. method, the method includes:

adjusting the input voltage of the ablation control device based on the real-time power of the at least one electrode and the target monopolar power, to adjust the output power of the ablation control device.

This application also provides a computer-readable storage medium on which a computer program is stored. When the computer program is executed by a processor, a method for adjusting power is implemented. The method includes:

Description of drawings

Figure 1 is a schematic flowchart of a method for automatically adjusting power provided by the first embodiment of the present application;

Figure 2 is a schematic module diagram of an automatic power adjustment system provided by the second embodiment and the third embodiment of the present application;

Figure 3 is a schematic module diagram of an example of an automatic power adjustment system provided by the third embodiment of the present application;

Figure 4 is a module schematic diagram of the sampling unit in Figures 2 and 3;

Figure 5 is a module schematic diagram of the current detection circuit in Figure 4;

Figure 6 is a circuit schematic diagram of the current detection circuit in Figure 4;

Figure 7 is a module schematic diagram of the voltage detection circuit in Figure 4;

Figure 8 is a circuit schematic diagram of the voltage detection circuit in Figure 4;

Figure 9 is a module schematic diagram of the neutral electrode detection circuit in Figure 4;

Figure 10 is a circuit schematic diagram of the neutral electrode detection circuit in Figure 4;

Figure 11 is a module schematic diagram of the temperature detection circuit in Figure 4;

Figure 12 is a circuit schematic diagram of the temperature detection circuit in Figure 4;

Figure 13 is a module schematic diagram of the relay control circuit in Figure 4;

Figure 14 shows the circuit diagram of the relay unit in bitmap 13;

Figure 15 is a circuit schematic diagram of the power output board in Figure 2;

Figure 16 is a schematic structural diagram of an ablation control device provided by this application.

Detailed ways

The following is a further detailed description through specific implementation methods:

In order to make the purpose, technical solutions and advantages of the embodiments of the present application clearer, each implementation mode of the present application will be described in detail below with reference to the accompanying drawings. However, those of ordinary skill in the art can understand that in each embodiment of the present application, many technical details are provided to enable readers to better understand the present application. However, even without these technical details and various changes and modifications based on the following embodiments, the technical solution claimed in this application can also be implemented.

Implementation method one:

The first embodiment of the present application provides a method for automatically adjusting power. The method is used to adjust the output power of an ablation control device. The ablation control device includes a plurality of electrodes. The method includes: obtaining ablation control during the ablation process. The real-time current value and the real-time voltage value of each electrode of the device; according to the real-time current value and the real-time voltage value, determine the real-time impedance of each electrode, and determine a designated electrode from each of the electrodes based on the real-time impedance; based on the real-time impedance Determine the target monopolar power of at least one of the electrodes based on the real-time impedance of the specified electrode and the set preset monopolar power; based on the real-time power of the at least one electrode and the target monopolar power, The input voltage of the ablation control device is adjusted to adjust the output power of the ablation control device.

During implementation, the ablation control equipment of this solution obtains the ablation start signal; starts the ablation according to the ablation start signal; obtains the real-time current value and real-time voltage value of each electrode during the ablation process; according to the real-time current value and real-time voltage value, determine the real-time impedance of each electrode; according to the real-time impedance of each electrode, determine a designated electrode from each electrode; based on the real-time impedance of the designated electrode and the set preset monopolar power, determine the The target monopolar power of at least one electrode in each electrode; adjusting the input voltage of the ablation control device according to the real-time power of the at least one electrode and the target monopolar power to adjust the output power of the ablation control device .

In this embodiment, each electrode of the ablation control device is connected in parallel and the real-time power is affected by impedance. Therefore, a designated electrode can be set according to the real-time impedance of each electrode. Based on the designated electrode, the target monopolar power to be adjusted to at least one electrode can be determined according to the preset monopolar power, that is, by adjusting the input voltage so that the real-time power of the at least one electrode is adjusted as close as possible to the target monopolar power, As a result, the output power can be adjusted more accurately.

The following is a detailed description of the implementation details of a method for automatically adjusting power in this embodiment. The following content is only for the convenience of understanding and is not necessary to implement this application. The specific process of this implementation is shown in Figure 1. This embodiment is applied to a system that automatically adjusts power.

Step 101: Obtain the real-time current value and real-time voltage value of each electrode of the ablation control device during the ablation process.

Specifically, there are two prerequisites for the implementation of step 101. First, the ablation control device directly performs step 101 after being powered on. Second, the ablation control device performs step 101 after acquiring the ablation start signal.

In some examples, before step 101, the method further includes: S100, obtaining an ablation start signal.

Specifically, the ablation start signal is sent under user control. Usually the user triggers by clicking, selecting, etc. through the control panel, thereby generating an ablation start signal. During specific implementation, the ablation start signal is usually received by the communication unit of the ablation control device, and the ablation start signal is usually transmitted in the form of two signals, LOW_MCU_RX and LOW_MCU_TX.

In some examples, step 101 includes: S1-1, obtain the real-time current value of each electrode during the ablation process; S1-2, obtain the real-time voltage value of each electrode during the ablation process.

Specifically, S1-1 obtains the real-time current value of each electrode during the ablation process, including: S1-1-1, which differentially amplifies the current signal to be detected to obtain an amplified current signal; S1-1-2, which performs half-processing on the amplified current signal. Wave rectification, rectifying the waveform of the positive half-axis to obtain the current rectified waveform; S1-1-3, performing DC filtering on the current rectified waveform to obtain an approximate DC signal; S1-1-4, converting the approximate DC signal For a signal with a waveform close to linear, perform RC filtering to obtain a stable current; S1-1-5, detect the current value of the stable current, and calculate the current current value of the current signal to be detected based on the preset coefficient. Wherein, the preset coefficient is associated with the differential amplification multiple, the half-wave rectification coefficient, the DC filter coefficient and the RC filter coefficient.

Differential amplification is used to amplify the current signal to be detected, and the detection accuracy of the current signal to be detected is improved while the detection accuracy remains unchanged. Through RC filtering, the output current is more stable and basically does not fluctuate, which prevents the detection results from deteriorating due to fluctuations.

Specifically, S1-2, obtains the real-time voltage value of each electrode during the ablation process, including: S1-2-1, attenuates the voltage signal to be detected to obtain an attenuated voltage signal; S1-2-2, attenuates the voltage signal Perform half-wave rectification and rectify the waveform of the positive half-axis to obtain a voltage rectified waveform; S1-2-3, perform DC filtering on the voltage rectified waveform to obtain an approximate DC voltage signal; S1-2-4, convert the approximate DC voltage signal The DC voltage signal is converted into a signal with a waveform close to linear, and RC filtering is performed to obtain a stable voltage; S1-2-5, detect the current value of the stable voltage, and calculate the current voltage of the voltage signal to be detected based on the preset coefficient value. Wherein, the preset coefficient is associated with the multiple of the attenuation, the coefficient of half-wave rectification, the DC filter coefficient and the RC filter coefficient.

The measured voltage value is attenuated through a resistor divider circuit because the measured voltage value is too large and requires a resistor divider method to attenuate the voltage signal to a state that is convenient for measurement. The waveform is modulated and filtered to make the voltage for detection more stable and basically non-fluctuating, thus preventing the detection results from deteriorating in accuracy due to fluctuations.

Step 102: Determine the real-time impedance of each electrode based on the real-time current value and the real-time voltage value, and determine a designated electrode from each of the electrodes based on the real-time impedance.

Specifically, based on the real-time current value I and real-time voltage value U of the same electrode, combined with the formula R=U/I, the real-time impedance R of the electrode is calculated. Then, based on the real-time impedance corresponding to these electrodes, one of the electrodes is selected as the designated electrode.

In one embodiment, determining a designated electrode from the electrodes based on the real-time impedance includes: determining the electrode with the smallest real-time impedance as the designated electrode. For example, the impedance of the designated electrode can be recorded as R _min .

In one embodiment, the real-time impedance corresponding to each electrode can reflect whether the electrode is in contact with the target object. The electrodes that are not in contact with the target object can be determined as invalid electrodes and removed when the designated electrode is determined. For example, before performing step S102 to determine a designated electrode from each of the electrodes based on the real-time impedance, the method will also screen the electrodes that participate in the calculation of the unipolar ablation power. The screening process is as follows: S2-1 , obtain the preset maximum impedance value and minimum impedance value; S2-2, when the current impedance corresponding to the electrode is greater than the maximum impedance value or less than the minimum impedance value, the electrode is not included in the monopolar ablation power. Calculation range.

The minimum impedance value and maximum impedance value set by the user are used to determine whether the electrode is in close contact; specifically, if the current impedance is greater than the minimum impedance value and less than the maximum impedance value, it is determined that the electrode corresponding to the current impedance is in good contact; if the electrode is in contact If the current impedance is greater than the maximum impedance value or less than the minimum impedance value, it is determined that the electrode corresponding to the current impedance is not in good contact.

Step 103: Determine the target monopolar power of at least one of the electrodes based on the real-time impedance of the designated electrode and the set preset monopolar power.

The preset monopolar power can be determined by the user based on experience, for example, it can be the maximum power that a single electrode can achieve.

Among them, the target unipolar power can be understood as the target power to be adjusted. For example, for a designated electrode, the current real-time power of the designated electrode is 1W, and it is determined that the target monopolar power of the designated electrode is 2W. Then 2W can be used as the target power to be adjusted to the designated electrode, that is, the real-time power of the designated electrode is adjusted. To get as close to 2W as possible.

In one embodiment, at least one electrode may include only designated electrodes. Based on this, the implementation of step 103 may include:

S3-1: Determine the target monopolar power of the specified electrode based on the set preset monopolar power.

In one embodiment, at least one electrode may include a specified electrode and other electrodes, for example, may include all electrodes in the ablation control device, or may include all other electrodes in the ablation control device except for electrodes that are not attached. Based on this, the implementation of step 103, in addition to the above S3-1, may also include:

S3-2, for each other electrode except the designated electrode, calculate the ratio R min /R of the real-time impedance R _min of the designated electrode and the real-time impedance of the other electrode (for example, denoted as R), and calculate the ratio R _min /R based on the The target monopolar power of the other electrodes is determined based on the ratio of the real-time impedance and the target monopolar power of the designated electrode.

The above steps S3-1 and S3-2 will be described in detail below.

During implementation, in S3-1, a preset monopolar power P' is first set, and based on the preset monopolar power P', the target monopolar power P ₀ of the specified electrode is set. For example, the preset monopolar power P' can be set to the target monopolar power P ₀ of the specified electrode; or, a power adjustment value can be determined in combination with the temperature adjustment mechanism, so that the preset monopolar power P' and The power is adjusted to ΔP to determine the target unipolar power P ₀ . It can be understood that since the specified electrode has the smallest resistance among all electrodes, the power of the specified electrode is the largest among all electrodes. Therefore, if the specified electrode is adjusted to the preset monopolar power, it can ensure that the power of all electrodes is the same. On the basis that the power does not exceed the preset unipolar power, the entire circuit can reach the maximum power as a whole and improve the ablation efficiency.

In one embodiment, the target monopolar power P ₀ of the designated electrode can also be determined based on the preset monopolar power P' and the temperature adjustment mechanism, which will be described in detail below and will not be described again here.

Optionally, the preset monopolar power value P' can be preset in the following ways: (1) The monopolar power value P' set by the user is determined based on the operator's experience. The site and ablation depth determine different ablation powers. (2) Combine the historical ablation site, ablation depth, and monopolar power values into a table; search the table to obtain the corresponding ablation depth based on the detected ablation site and ablation depth. (3) Combine historical ablation sites, ablation depths, and unipolar power values into a basic data set, and use a neural network model to train the basic data set to obtain multiple historical ablation sites, corresponding ablation depths, and unipolar power values that are associated with each other. model; according to the detected multiple ablation sites and the ablation depth corresponding to the ablation site, substitute them into the trained neural network model to obtain the corresponding preset monopolar power value P'. It should be noted that the above methods are only exemplary descriptions. In actual applications, they can also be determined by other methods, which are not limited in this embodiment.

In some examples, step S3-1 may also include: S3-1-1, obtaining the real-time temperature of the ablation object corresponding to the specified electrode during the ablation process; S3-1-2, according to the ablation object corresponding to the specified electrode The comparison result between the real-time temperature and the preset temperature threshold is used to determine the power adjustment value ΔP of the designated electrode. The power adjustment value ΔP is used to adjust the real-time temperature of the ablation object corresponding to the designated electrode; S3- 1-3. Based on the set preset monopolar power P' and the power adjustment value ΔP, determine the target monopolar power P ₀ of the designated electrode.

It can be understood that when the ablation control device ablates an ablation object through electrodes, it actually controls the temperature of the ablation object to perform the ablation. Therefore, effective ablation must control the temperature of the ablation object within an appropriate range.

In one embodiment, in S3-1-2, the temperature threshold may include a preset temperature range [a, b] and a preset protection temperature c, and the maximum value b of the preset temperature range is less than or equal to the preset temperature range [a, b]. Protection temperature c, that is, b≤c. Among them, the preset temperature range can be understood as a suitable range with better ablation effect, and the preset protection temperature can be understood as the highest temperature that prevents the ablation object from being damaged. For the convenience of description, here the real-time temperature of the ablation object corresponding to the specified electrode is denoted as x.

Specifically, S3-1-2, determine the power adjustment value of the designated electrode based on the comparison result between the real-time temperature of the ablation object corresponding to the designated electrode and the preset temperature threshold, including:

S3-1-2-1, when the real-time temperature x of the designated electrode corresponding to the ablation object is in the preset temperature range [a, b] (i.e., x∈[a, b]), adjust the power of the designated electrode The value ΔP is set to 0 to maintain the current output power P ₀ of the specified electrode;

S3-1-2-2, when the real-time temperature x of the ablation object corresponding to the designated electrode is greater than the preset protection temperature c (ie, x>c), set the power adjustment value ΔP of the designated electrode to less than 0, so as to Reduce the current output power P ₀ of the specified electrode;

It is understandable that if the real-time temperature of the ablation object is greater than the preset protection temperature, it may cause damage to the ablation object, so the temperature needs to be lowered immediately. In one example, the temperature can be lowered by reducing power.

S3-1-2-3: When the real-time temperature x of the designated electrode corresponding to the ablation object is less than the minimum value a of the preset temperature range [a, b] (that is, x < a), adjust the power of the designated electrode The value ΔP is set greater than 0 to increase the current output power of the specified electrode.

It can be understood that if the real-time temperature of the ablation object is less than the minimum value of the preset temperature range, the ablation effect may be poor due to the temperature being too low. Therefore, increasing the power can improve both the ablation effect and the ablation efficiency.

In some examples, the ablation control device further includes a perfusion pump, which is used to perfuse physiological saline into the ablation object corresponding to the designated electrode to reduce the current temperature of the corresponding ablation object. Therefore, by increasing the flow rate of the perfusion pump, the current temperature of the ablation object can be reduced; by decreasing the flow rate of the perfusion pump, the current temperature of the ablation object can be increased. Specifically, (1) when the real-time temperature x of the ablation object corresponding to the designated electrode is greater than the preset insulation temperature, that is, x>c, the flow rate v of the physiological saline injected by the perfusion pump can be increased first. When the pump flow is raised to the highest level and the real-time temperature x is still greater than c, the power adjustment value ΔP of the designated electrode is set to 0, thereby reducing the target monopolar power based on the preset monopolar power, thereby enabling ablation The real-time temperature of the object is below the protection temperature; optionally, the power adjustment value can be determined based on the current real-time power and the target unipolar power, for example, so that the power adjustment value is less than the difference between the real-time power and the preset unipolar power, so that the target The monopolar power is less than the real-time power, thereby quickly reducing the temperature of the target object by reducing the power; (2) the real-time temperature x of the ablation object corresponding to the designated electrode is greater than the maximum value b of the preset temperature range, and is less than or equal to When the preset protection temperature c is x∈(b, c], increase the flow rate v of the perfusion pump to inject physiological saline until the flow rate v reaches the maximum flow rate v _max ; optionally, when the perfusion pump When the flow reaches the highest level, the power adjustment value ΔP of the designated electrode can also be set to 0, thereby reducing the target monopolar power based on the preset monopolar power, so that the real-time temperature of the ablation object is within an appropriate range. ; (3) When the real-time temperature x of the designated electrode corresponding to the ablation object is in the preset temperature range [a, b], that is, x∈[a, b], set the power adjustment value ΔP of the designated electrode to 0, so that the preset monopolar power can be directly used as the target power P ₀ ; (4) When the real-time temperature x of the ablation object corresponding to the designated electrode is less than the minimum value a of the preset temperature range, that is, x < a, Adjusting the power adjustment value ΔP of the designated electrode to 0, thereby increasing the target monopolar power on the basis of the preset monopolar power, can not only improve the real-time temperature of the ablation object and improve the ablation effect, but also improve the ablation efficiency and shorten the time Ablation time; optionally, if the real-time temperature x of the ablation object is still less than the minimum value a after reaching the maximum monopolar power, the flow rate v of the physiological saline injected by the perfusion pump can be reduced until it is reduced to the minimum value v _min .

In one embodiment, the power adjustment value ΔP may be a preset fixed value, for example, when ΔP<0 is determined, ΔP=-1; when ΔP>0 is determined, ΔP=1, etc. Alternatively, the power adjustment value ΔP is determined based on the preset corresponding relationship between the temperature difference and the power adjustment value. For example, when x∈(b,c], the power adjustment value can be determined based on the difference between x and b. Generally, Ground, the difference is positively correlated with the absolute value of the power adjustment value. For other situations, similar corresponding relationships are also preset, which will not be described again here.

Specifically, S3-1-3, based on the set preset monopolar power P' and the power adjustment value ΔP, determining the target monopolar power P ₀ of the designated electrode includes: according to the preset value set by the user. Assume that the monopolar power value P' and the adjustment amount ΔP generated by the temperature adjustment mechanism are added together to obtain the monopolar ablation power P ₀ ; wherein, the preset monopolar power P' is preset by the user based on the ablation site and ablation depth. , the ablation temperature will change in real time during the ablation process, and the temperature adjustment mechanism can control the ablation temperature to be within an appropriate range.

In S3-2, the ratio k of the real-time impedance of the designated electrode to the real-time impedance of the other electrodes = the real-time impedance Rmin of the designated electrode/the real-time impedance R of other electrodes. Based on the ratio of the real-time impedances and the target monopolar power of the designated electrode, the target monopolar power of the other electrodes is determined. For example, the ratio of target monopolar power between other electrodes and a given electrode can be inversely proportional to the ratio of real-time impedance. Specifically: according to the inverse relationship Calculate the target unipolar power P _x that needs to be output by each electrode; _among them, _R ₀ represents the target monopolar power of the specified electrode, and P _x represents the target monopolar power of the current electrode (that is, the electrode with an impedance value of R _x ). If there are n electrodes in the electrodes in normal working condition in addition to the designated electrode, the target monopolar power of each electrode can be recorded as P ₁ ~ P _n , where the value range of x is [1, n] , the value of n is a positive integer.

In this step, each electrode is connected in parallel and the real-time power is affected by the impedance R, and the smaller the impedance R, the greater the real-time power P of the electrode. It can be known that in each channel, the electrode with the smallest impedance R, the real-time power P of this electrode is the maximum power value in each channel. Therefore, the electrode with the smallest impedance is set as the designated electrode, and the target monopolar power to be adjusted to the designated electrode can be determined based on the preset monopolar power. That is, the real-time power of the designated electrode is subsequently adjusted to be as close as possible to the preset monopolar power. power. At the same time, the target monopolar power of other electrodes is determined based on the target monopolar power of the specified electrode. It can also be used to adjust the power subsequently: it not only ensures that each electrode does not exceed the preset monopolar power, but also enables real-time power adjustment of each electrode. In order to be as large as possible to achieve the maximum output power value of the entire circuit and improve ablation efficiency. In addition, the calculation of the monopolar ablation power takes into account that the temperature of each electrode changes in real time with the degree of ablation. Based on the temperature changes, a temperature adjustment mechanism is set so that the monopolar ablation power fully takes into account the temperature factor. Among them, in the temperature adjustment mechanism, based on the set monopolar ablation power, the temperature during the ablation process can always be below the protection temperature.

Step 104: Adjust the input voltage of the ablation control device based on the real-time power of the at least one electrode and the target monopolar power to adjust the output power of the ablation control device.

Specifically, the implementation of step 104 includes: S4-1, determine the sum of the target monopolar powers of all electrodes in the at least one electrode as the target total power; S4-2, based on the power of all electrodes in the at least one electrode The difference between the sum of real-time powers and the target total power is used to adjust the input voltage of the ablation control device.

Wherein, at least one electrode may include only the specified electrode; or may include both the specified electrode and other electrodes.

In one embodiment, at least one electrode only includes the designated electrode, then the real-time power, which is the "sum of real-time power" described in step 104, can be calculated first based on the real-time voltage value and current value of the designated electrode; then, The target unipolar power of the designated electrode can be used as the "target total power" in step 104, so that the input voltage can be adjusted according to the real-time power of the designated electrode and the target unipolar power.

It can be understood that in this embodiment, the input voltage is fed back through the power of a single electrode (ie, the designated electrode), and the calculation is relatively simple and fast. On the basis of ensuring accuracy, the calculation efficiency is also improved.

In one embodiment, at least one electrode includes a designated electrode and other electrodes. Then the real-time power of each electrode can be calculated separately based on the real-time voltage value and current value of each electrode, and then the "sum of real-time power" can be determined by adding them up. ; Then, the target monopolar power corresponding to each electrode can be added to obtain the "target total power" Therefore, the input voltage can be adjusted according to the real-time power sum and the target total power.

Among them, other electrodes may include electrodes that are effectively in contact, and whether they are in effective contact can be determined by the impedance of the electrodes. When the current impedance is less than or equal to the maximum impedance value, and greater than or equal to the minimum impedance value; the maximum impedance value and the minimum impedance value are both set by the user; when "the current impedance is less than or equal to the maximum impedance value, and greater than or equal to The electrodes within the range of "equal to the minimum impedance value" are considered to be in good contact and are included in the power calculation range; the electrodes in other cases are not in contact or are in poor contact and are not included in the power calculation range.

It can be understood that compared with direct control through unipolar output power and unipolar target power, this embodiment uses the total power of the entire circuit to feedback control the output voltage, which has higher reliability; at the same time, since each circuit in the circuit The resistance of the electrodes changes in real time, and the designated electrode with the smallest resistance will also change (for example, the original designated electrode is electrode 1 and is changed to electrode 2). Therefore, feedback through the total power of the entire circuit can reduce instantaneous voltage fluctuations. , which is more conducive to stable output.

Specifically, S4-2, adjust the input voltage of the ablation control device based on the current difference between the sum of the real-time power of all electrodes in the at least one electrode and the target total power, including:

S4-2-1. Based on the last acquired real-time power of all electrodes in the at least one electrode, determine the sum of historical real-time power, and determine the difference between the sum of historical real-time power and the target total power. Historical difference; in the preset correspondence table between the power difference range and the voltage change (DAC voltage change), find the current power difference range and the corresponding voltage change to which the current difference ΔP belongs, and The historical power difference range to which the historical difference belongs; wherein the correspondence table includes the associated power difference range and voltage change (DAC voltage change).

Among them, in S4-2, the preset corresponding relationship table between the power difference range and the voltage change amount is the relationship between the power difference range, the power change range and the DAC change amount summarized after many experiments, and Summarize the correlations between multiple sets of data. The comparison table can be multiple mappings in one-to-one correspondence, or it can be a database formed by sorting historical data, or it can be a model between the summarized power difference range and the DAC variation.

In one embodiment, after each sampling of the current value and voltage value, the real-time power of all electrodes in the at least one electrode can be calculated, and then the difference between the real-time power and the target total power can be calculated, And record it, for example, it can be recorded in the historical difference table; or you can only record the last calculated difference; or you can only record the difference range corresponding to the last or multiple historical differences, for example, record the difference The sequence number corresponding to the range, etc.

Optionally, when recording historical differences or historical difference ranges, you can initialize the difference range before recording for the first time, and return the values of the difference range to be calculated and judged by the software to the original unadjusted state first, to prevent the previous Test data has an impact on operations.

In one embodiment, for the real-time power obtained by the first sampling, the voltage change corresponding to the difference can be directly searched in the preset correspondence table between the power difference range and the voltage change, and then directly based on the voltage change Adjust the amount.

In one embodiment, for the real-time power obtained by sampling other than for the first time, after calculating the current difference, the last calculated historical difference can be searched; and then the current power difference to which the current difference belongs can be searched in the correspondence table. value range, and the historical power difference range to which the historical difference value belongs, and compare them.

S4-2-2. If the current power difference range is different from the historical power difference range, adjust the input voltage of the ablation control device according to the corresponding voltage change, that is, change the set DAC amount, updated from the last DAC change amount to the current DAC change amount corresponding to the power change range obtained in S4-2-1.

Among them, the set DAC variation can be used to adjust the input voltage and thereby adjust the output power.

S4-2-3, if the current power difference range is the same as the historical power difference range, obtain the currently set voltage change amount, and reduce the currently set voltage change amount, and adjust the voltage according to the reduced voltage The amount of change adjusts the input voltage of the ablation control device so that the output power can be adjusted.

Further, in S4-2-3, obtain the currently set voltage change amount and reduce the currently set voltage change amount, including: the voltage change amount (DAC change amount) is reduced according to the preset fixed reduction value, which is about to set The DAC change amount is updated to: the original DAC change amount - fixed reduction value; where the fixed reduction value is the preset value.

When adjusting the input voltage, the updated DAC value can be obtained by adding the set DAC change amount to the currently set DAC value. The current DAC value is fed back to the relevant modules in the power circuit, and the output is output through these relevant modules. voltage, thereby adjusting the output power value.

It can be understood that in this step, the DAC change amount used to adjust the input voltage does not remain constant, but the DAC change amount continues to decrease, approaching the preset threshold in a curve, which can reduce the fluctuation of the output voltage. , reduce the impact on output power.

In addition, after the implementation of step 101, this method may also include the following content:

Step 105: Limit the energy generated by the electrodes per unit time according to the real-time current value and voltage value of each electrode.

Specifically, the implementation of step 105 includes: S5-1, based on the real-time current value and voltage value of each electrode, combined with the series and parallel connection method, calculate the energy accumulated by each electrode per unit time; S5-2, Accumulate the real-time energy generated by each channel in each unit time to obtain the total energy generated by the electrodes of this channel; S5-3, compare the total energy generated by each channel in accumulation with the preset energy value; S5 -4, when the total energy generated by accumulation is equal to the preset energy value, the output power is adjusted to 0.

The preset total energy is preset by the user, and may be the ablation energy required to achieve the ablation effect. That is to say, when the total energy accumulated by the electrodes of this circuit reaches the preset total energy, it can be considered that the ablation target of this electrode has achieved the ablation effect, and the ablation of this electrode can be stopped.

In one embodiment, when the total energy output by any electrode of the electrode reaches a preset energy value, it can be determined that the ablation object of the electrode of the electrode has achieved an ablation effect. Therefore, the electrode can be controlled by turning off the relay corresponding to the electrode. Turn off and stop energy operation to avoid electrode burnout and unnecessary damage to the ablation object.

Wherein, the relay corresponds to the electrode one-to-one, and the relay is used to control the opening and closing of the corresponding electrode. Multiple electrodes have one-to-one corresponding control relays. The control relays are used to control the on and off of each electrode to achieve independent control of the ablation time of each electrode. By individually controlling the ablation time of each electrode, the energy output of each electrode is achieved. consistent.

Step 106: Based on the real-time current value and voltage value of each electrode, determine whether all the electrodes in the two paths led out by the negative connecting plate are properly attached.

Specifically, the implementation of step 106 includes: S6-1, compare the current value of one contact path of the negative plate with the current value of the other contact path of the negative plate; S6-2, compare the current value of one contact path of the negative plate equal to double the current value of the negative plate contact. When the current value of the other channel reaches the current value, an alarm will be issued.

When the current on one side is twice that of the other side, it can be judged that the side with the smaller current value is not in good contact, and an alarm will be issued directly to remind the user that the position of the negative plate needs to be adjusted. For example: When the current difference between two paths reaches 1 times, that is, I ₁ = 2I ₂ , the path with the smaller current, that is, I ₂ , is judged to be in an unconnected state. When this happens, the software will issue an alarm. Signal prompts to manually adjust the position of the negative plate.

Step 107: Detect the temperature of each electrode, and when it reaches the upper temperature limit, turn off the relay corresponding to the electrode.

Specifically, the implementation of step 107 includes: S7-1, detect the current temperature of each electrode when each electrode is undergoing the ablation process; S7-2, compare the current temperature with the preset temperature upper limit; when the current temperature is greater than or When it is equal to the upper temperature limit, the control relay is turned off. Wherein, the relay corresponds to the electrode one-to-one, and the relay is used to control the opening and closing of the corresponding electrode. Multiple electrodes have one-to-one corresponding control relays. The control relays are used to control the on and off of each electrode to achieve independent control of the ablation time of each electrode. By individually controlling the ablation time of each electrode, the energy output of each electrode is achieved. consistent. It is realized that once the temperature of a certain electrode exceeds the set temperature upper limit, the corresponding relay is controlled to turn off, and subsequent ablation operations are no longer performed to avoid malfunctions.

The steps of the various methods above are divided just for the purpose of clear description. During implementation, they can be combined into one step or some steps can be split into multiple steps. As long as they include the same logical relationship, they are all within the scope of protection of this patent. ; Adding insignificant modifications or introducing insignificant designs to the algorithm or process without changing the core design of the algorithm and process are within the scope of protection of this patent.

Implementation method two:

The second embodiment of the present application provides an ablation system, as shown in Figure 2, including a power output board 22 and an ablation control device 23; the ablation control device 23 includes a central processing unit 232, a sampling unit 233 and a plurality of electrode, where,

The sampling unit 233 is used to detect the real-time current value and real-time voltage value of each electrode and send them to the central processing unit;

The central processing unit 232 is configured to: determine the real-time impedance of each electrode based on the real-time current value and the real-time voltage value sent by the sampling unit 233, and determine a designated electrode from each of the electrodes based on the real-time impedance; And, based on the real-time impedance of the designated electrode and the set preset monopolar power, determine the target electrode monopolar power of at least one electrode in each electrode; and, based on the real-time power of the at least one electrode, and The target monopolar power determines the control voltage signal that the ablation control device needs to send, and sends the control voltage signal to the power output board 22;

The power output board 22 is used to determine the target voltage according to the control voltage signal sent by the central processing unit, and adjust the output power of the electrode according to the control voltage signal.

It can be understood that the control voltage signal that the ablation control device needs to send can be understood as a control voltage signal used to indicate the target voltage.

In the above embodiment, each electrode of the ablation control device is connected in parallel and the real-time power is affected by impedance, so that a designated electrode can be set according to the real-time impedance of each electrode. Based on the designated electrode, the target monopolar power to be adjusted to at least one electrode can be determined according to the preset monopolar power, that is, by adjusting the input voltage so that the real-time power of the at least one electrode is adjusted as close as possible to the target monopolar power, As a result, the output power can be adjusted more accurately.

In one embodiment, the sampling unit is also configured to detect the real-time temperature of the ablation object connected to the designated electrode, and send the real-time temperature to the central processing unit.

Based on this, the central processing unit is also configured to: determine the power adjustment value of the designated electrode based on the comparison result between the real-time temperature of the ablation object connected to the designated electrode and the preset temperature threshold; and, based on the set preset temperature threshold Assume that the monopolar power and the power adjustment value are used to determine the target monopolar power of the designated electrode; wherein the power adjustment value is used to adjust the real-time temperature of the ablation object connected to the designated electrode.

When calculating the monopolar ablation power and maximum output power, the effect of temperature on the overall impedance is fully taken into account. The adjustment amount corresponding to the temperature adjustment mechanism represents the amount of influence on impedance due to temperature changes (the change in current value/voltage value ). The adjustment amount corresponding to the temperature adjustment mechanism is used as one of the calculation factors for calculating the unipolar ablation power and the maximum output power, so that the calculation of the unipolar ablation power and the maximum output power is more accurate, and the adjustment of the output power is more accurate.

In one embodiment, the ablation control device further includes a relay control unit; the relay control unit is connected to the plurality of electrodes and is used to control the on/off of each electrode. For example, the relay control unit may include multiple relay control sub-units, each sub-unit corresponding to each electrode one-to-one, so that each sub-unit controls the on/off of the corresponding electrode.

In one embodiment, the central processing unit is also used to: calculate the real-time energy generated by each channel in unit time based on the real-time current value and real-time voltage value of each electrode; and calculate the real-time energy generated by each channel in each unit time. The real-time energy is accumulated to obtain the total energy generated by the electrode of this circuit; if the total energy is equal to the preset energy value, the relay unit is controlled to disconnect the electrode of this circuit to reduce the output of the circuit where the electrode of this circuit is located. Power is adjusted to 0.

Optionally, the power output board can be connected to the relay control unit, so that the power output board can be connected to the electrode through the relay control unit and output power to the electrode. Therefore, when the relay control unit is turned on, the power output board can output power to the electrode; when the relay control unit is turned off, the power output board cannot output power to the electrode, and the output power of the electrode is 0.

It is not difficult to find that this embodiment is a system embodiment corresponding to the first embodiment, and this embodiment can be implemented in cooperation with the first embodiment. The relevant technical details mentioned in the first embodiment are still valid in this embodiment, and will not be described again in order to reduce duplication. Correspondingly, the relevant technical details mentioned in this embodiment can also be applied to the first embodiment.

Implementation method three:

Based on the second embodiment, this embodiment further provides a system for automatically adjusting power, as shown in FIG. 2 , including a power output board 22 and an ablation control device 23 . The central processing unit 232 in the ablation control device 23 starts the ablation mode to enter the ablation process according to the ablation start signal. The ablation start signal may include one or more of a preset single-level ablation power value, a maximum impedance value, and a minimum impedance value.

The ablation control device 23 includes a central processing unit 232 and a sampling unit 233. The sampling unit 233 is used to collect the real-time current value and real-time voltage value of each electrode during the ablation process, and send them to the central processing unit 232.

The central processing unit 232 is also configured to determine the real-time impedance of each electrode based on the real-time current value and real-time voltage value sent by the sampling unit 233, and determine a designated electrode from each of the electrodes based on the real-time impedance; And, based on the real-time impedance of the designated electrode and the set preset monopolar power, determine the target monopolar power of at least one electrode in each electrode; and, based on the real-time power of the at least one electrode, and the Determine the control voltage signal that the ablation control device needs to send according to the target monopolar power, and send the control voltage signal to the power output board 22;

The power output board 22 is used to determine the target voltage according to the control voltage signal sent by the central processing unit 232, and adjust the output power of the electrode according to the control voltage signal.

In some examples, as shown in FIG. 3 , the system for automatically adjusting power further includes a control board 21 , and the ablation control device further includes a communication unit 231 . The control board 21 is used to send an ablation start signal to the communication unit 231 of the ablation control device 23; the ablation start signal may include one or more of a preset single-stage ablation power value, a maximum impedance value, and a minimum impedance value. . The communication unit 231 of the ablation control device 23 is used to receive the ablation start signal sent by the control board 21 and send it to the central processing unit 232, so that the central processing unit 232 starts the ablation mode and enters the ablation process according to the ablation start signal.

The ablation control device 23 is remotely controlled through the control panel 21, and the ablation start signal is input directly or indirectly. The ablation start signal received by the central processing unit 232 may originate from input from the control panel 21 , may be generated by itself, or may be generated after receiving user instructions through other means, etc. This embodiment is not limited.

In one embodiment, the ablation control device further includes a relay control unit connected to the plurality of electrodes and used to control on/off of each electrode.

In some examples, the relay control unit may belong to the sampling unit, for example, it may be a relay control circuit in the sampling unit. The following is introduced using Figure 4 as an example. As shown in FIG. 4 , the sampling unit 233 includes one or more of a current detection circuit 2331 , a voltage detection circuit 2332 , a relay control circuit 2333 , a neutral electrode detection circuit 2334 and a temperature detection circuit 2335 . The circuits in the sampling unit 233 (parts numbered 2331-2335 in Figure 4) are introduced below:

The current detection circuit 2331, the output end of the current detection circuit 2331 is connected to the input end of the central processing unit 232, is used to detect the current of each electrode, and convert the AC signal sampled by each electrode using the sampling resistor into a DC level and send it to central processing unit 232;

The voltage detection circuit 2332, the output end of the voltage detection circuit 2332 is connected to the input end of the central processing unit 232, is used to detect the voltage of the radio frequency output, and changes the radio frequency output voltage into an AC signal with a smaller amplitude through the attenuation circuit and utilizes The voltage sampling circuit converts it into a DC level and sends it to the central processing unit 232;

The neutral electrode detection circuit 2334, the output end of the neutral electrode detection circuit 2334 is connected to the input end of the central processing unit 232, is used to monitor in real time whether the neutral electrode and the human body contact point are in good contact, and the voltage detected by the transformer is The current signal passing through the human body flows back to the output end, and is converted into a DC level after sampling processing and sent to the central processing unit 232;

The temperature detection circuit 2335, the output end of the temperature detection circuit 2335 is connected to the input end of the central processing unit 232, is used to read the temperature generated by the electrode placed in the human body and send it to the central processing unit 232;

The relay control circuit 2333 is used to control the on-off of the relay according to the current and voltage of each electrode; the relay corresponds to the electrode one-to-one, and the relay is used to control the on-off of the corresponding electrode;

It can be understood that the circuits 2331-2335 in Figure 4 can be applied to each of the above embodiments, and are not limited to the third embodiment.

Based on each circuit in the above-mentioned sampling unit, the central processing unit 232 is used to adjust the current value output by the current detection circuit 2331 and the voltage value output by the voltage detection circuit 2332 in combination with the unipolar power value and the temperature adjustment mechanism. The amount and preset impedance are used to calculate the monopolar ablation power and maximum output power. The output terminal of the central processing unit 232 is connected to the input terminal of the power output board 22 .

In this application, the output end of the current detection circuit 2331 and the output end of the voltage detection circuit 2332 of the ablation control device 23 are both connected to the central processing unit 232. The connection method can be through a lead connection, or through Bluetooth, wifi, etc., the module can be changed first. It is then sent to the central processing unit 232 for digital-to-analog conversion, and then controls the power output board 22 .

When this application calculates the unipolar ablation power and maximum output power, on the one hand, the impact of temperature on the overall impedance is fully considered. The adjustment amount corresponding to the temperature adjustment mechanism represents the amount of influence on the impedance due to temperature changes (current value/ The change in voltage value), on the other hand, takes into account the possible damage to the target object when the temperature is too high. Therefore, the method of this application not only ensures the ablation efficiency by setting the preset temperature range and protection temperature, but also keeps the temperature during the ablation process below the protection temperature to avoid damage to the target object.

In some examples, as shown in Figure 5, the current detection circuit 2331 includes:

The current sampling circuit 23310 includes a sampling resistor. The signal output by the power board is applied to the sampling resistor. A voltage signal can be formed on the sampling resistor 23310, and this signal is input to the subsequent stage circuit (the subsequent differential amplifier circuit 23311);

The first-level operational amplifier amplifier circuit 23311 has an input end connected to the current sampling circuit of each electrode, used to amplify the voltage signal collected by the sampling resistor and output the amplified amplified voltage signal;

The input end of the second-level operational amplifier rectifier circuit 23312 is connected to the output end of the first-level operational amplifier amplifier circuit, and is used for half-wave rectification of the amplified voltage signal, filtering out the negative half-axis signal and retaining the positive half-axis signal. The signal outputs the positive half-axis waveform signal; the positive half-axis waveform signal is a sinusoidal signal with only the positive half-axis;

DC filter circuit 23313, the input end is connected to the output end of the two-stage operational amplifier rectifier circuit, used to filter the positive half-axis waveform signal output by the rectifier circuit, thereby obtaining a waveform that approximates a DC signal;

Follower 23314, the input end is connected to the output end of the DC filter circuit, is used to isolate the waveform of the approximate DC signal before and after, ensuring that the subsequent stage will not receive interference from the previous abnormal signal, and obtain a voltage that is relatively stable. DC signal, that is, a signal with a waveform close to linear;

RC filter circuit 23315, the input end is connected to the output end of the follower 23314, is used to further filter the signal with a waveform close to linear to obtain a linear DC signal with stable voltage, and send it to the central processing unit, so that the central processing unit The unit determines the current value based on this linear DC signal.

In specific implementation, the circuit structure of the current detection circuit 2331 can be as shown in Figure 6, which will not be described again here. Because the current value measured by the sampling resistor is too small, a first-level operational amplifier amplifier circuit 23311 is required to amplify the current signal, and then through a second-level operational amplifier rectifier circuit 23312, it is rectified into a positive half-axis waveform, and the waveform is DC filtered. Circuit 23313 obtains an approximate DC, which passes through the follower 23314 and obtains a nearly linear waveform, which then passes through an RC filter circuit 23315 in order to perform better filtering and output the detected current value that is more stable and basically non-fluctuating. Finally, Achieve the purpose of precise current detection.

Further, the preset coefficient in the stable current detection circuit 23316 is related to the resistance of the sampling resistor in the current sampling circuit 23310, the amplification factor in the differential amplifier circuit 23311, the half-wave rectification coefficient in the rectifier circuit 23312, and the DC filter circuit. The DC filter coefficients in 23313 are related to the RC filter coefficients in RC filter circuit 23315.

In this example, differential amplification is used to amplify the current signal to be detected, and the detection accuracy of the current signal to be detected is improved while the detection accuracy remains unchanged. Through RC filtering, the output current is more stable and basically does not fluctuate, which prevents the detection results from deteriorating due to fluctuations.

In some examples, as shown in Figure 7, the voltage detection circuit 2332 includes:

Voltage attenuation circuit 23321, the input end is connected to the voltage to be detected of each electrode, which is used to attenuate the voltage signal to be detected. Applying the radio frequency output signal to the attenuation circuit will obtain a voltage that is attenuated according to a certain proportion, and then send this voltage To the subsequent circuit, that is, to output an attenuated attenuated voltage signal, where the attenuation multiple of the voltage attenuation circuit is set by the user;

The input end of the two-level operational amplifier rectifier circuit 23322 is connected to the output end of the voltage attenuation circuit 23321, which is used to perform half-wave rectification on the attenuated voltage signal, filter out the negative half-axis signal, and retain the positive half-axis signal. , rectified into the waveform of the positive half axis and sent to the DC filter circuit 23323; the waveform of the positive half axis is a sinusoidal signal with only the positive half axis;

The input end of the DC filter circuit 23323 is connected to the output end of the two-level operational amplifier rectifier circuit 23322, and is used to filter the positive half-axis waveform output by the rectifier circuit 23322 into a waveform that approximates a DC signal, thereby obtaining an approximate DC signal;

The input end of the follower 23324 is connected to the output end of the DC filter circuit 23323, and is used to isolate the waveform of the approximate DC signal from the front and back to ensure that the subsequent stage will not receive interference from the previous abnormal signal and obtain a voltage comparison Stabilize the DC signal, that is, convert it into a signal with a waveform close to linear;

RC filter circuit 23325, the input end is connected to the output end of the follower 23324, used to filter the signal with a waveform close to linear, and further obtain a linear DC signal with stable voltage, used to indicate the device output voltage, and It is input to the central processing unit 232 for processing; the central processing unit 232 detects the voltage value according to the stable linear DC signal, and calculates the voltage value of the detected voltage signal at each electrode according to the preset coefficient.

When this example is implemented, the measured voltage value is attenuated through a resistor divider circuit. This is because the measured voltage value is too large and requires a resistor divider method to attenuate the voltage signal to a state that is convenient for measurement. The waveform is modulated and filtered to make the voltage for detection more stable and basically non-fluctuating, thus preventing the detection results from deteriorating in accuracy due to fluctuations.

In detail, the circuit structure of the voltage detection circuit 2332 can be shown in FIG. 8 . Among them, the voltage attenuation circuit (resistor voltage dividing circuit) 23321 can be shown as module 7 in Figure 8, the DC filter circuit 23323 can be shown as module 22, the follower can be shown as module 23, and the RC filter can be shown as module 24 shown, the specific structure will not be described again here.

Further, the preset coefficient of the voltage detection circuit is associated with the attenuation multiple of the voltage attenuation circuit, the half-wave rectification of the rectifier circuit, the DC filter coefficient of the DC filter circuit, and the RC filter coefficient of the RC filter circuit.

In some embodiments, the power output board 22 adjusts the voltage through a set of power supply devices. The input terminal is connected to a 220V AC power and is converted into a 300-400V DC voltage through a rectifier circuit. The DA module converts the digital quantity into an analog quantity and then feeds back the voltage. Go to the SC pin in the DC-DC device, and control the DC-DC device to output 0-48V DC, connect the energy storage inductor, and output the voltage. The output voltage is connected to the power amplifier circuit.

In some examples, the neutral electrode detection circuit 2334, as shown in Figure 9, includes:

Transformer 23341 is used to sense the current on the negative plate path. The current signal flowing through the human body passes through the neutral electrode and flows back to the output end. This current passes through the inductor coil and generates an induced current. The induced current passes through After sampling the resistor, a voltage indicating the induced current can be output to the next stage based on the sampling resistor;

The first-level operational amplifier amplifier circuit 23342 uses the operational amplifier to amplify the voltage output by the transformer 23341 to indicate the induced current, and sends it to the rectifier circuit 23343;

The input end of the second-level operational amplifier rectifier circuit 23343 is connected to the output end of the first-level operational amplifier amplifier circuit 23342. It rectifies the amplified current signal, filters out the negative half-axis signal, and retains the positive half-axis signal. The rectification is The waveform of the positive half axis is sent to the DC filter circuit 23344; the waveform of the positive half axis is a sinusoidal signal with only the positive half axis;

The input end of the DC filter circuit 23344 is connected to the output end of the rectifier circuit 23343, and is used to filter the positive half-axis waveform output by the rectifier circuit 23343 into a waveform that approximates a DC signal, thereby obtaining an approximate DC signal;

The input end of the follower 23345 is connected to the output end of the DC filter circuit 23344, and is used to isolate the waveform of the approximate DC signal from the front and back to ensure that the subsequent stage will not receive interference from the previous abnormal signal and obtain a voltage comparison Stabilize the DC signal, that is, convert it into a signal with a waveform close to linear;

The input end of the RC filter circuit 23346 is connected to the output end of the follower 23345, and is used to filter the signal with a waveform close to linear, and further obtain a linear DC signal with stable voltage, that is, a stable voltage, and input it to the central The processing unit 232 processes. The central processing unit 232 detects the current value according to the stable current, and calculates the current value of the induced current generated by the transformer according to the preset coefficient.

Further, the ratio of the preset coefficient of the neutral electrode detection circuit to the mutual inductor sampling, the amplification factor in the differential amplification circuit, the half-wave rectification coefficient in the rectifier circuit, the DC filter coefficient and RC filtering in the DC filter circuit associated with the RC filter coefficients in the circuit.

This application detects the mutual inductance current of the circuit where the transformer is located and calculates the current on the negative plate path, thereby facilitating the detection of the current value of the negative plate. Transformers are mutually inductive devices. The transformer has four legs, two of which are connected in series with the current path of the negative plate, and the negative plate current will pass through the transformer. The current on the path is too large and it is inconvenient to detect. The other two legs of the transformer are connected to the circuit to detect the negative plate current. As shown in Figure 10, the neutral electrode detection circuit can include a transformer TAK10-050 and a sampling resistor R152; the first-level operational amplifier method circuit can include an operational amplifier chip U38, and the positive input end of the operational amplifier chip is connected to Sampling resistor R152 to obtain the voltage signal indicating the induced current; the DC filter circuit may include resistor R156, filter capacitor C147 and Zener diode D41; the follower may include chip U40; the RC filter circuit may include Zener diode D40 and resistor R157 and filter capacitor C148. As for the connection relationship between various circuits and other circuit components, reference can be made to the embodiment shown in FIG. 10 and will not be described again here.

In some examples, temperature detection circuit 2335, as shown in Figures 11 and 12, includes:

Temperature sensor 23351, used to convert the detected temperature into a current signal through the miniature temperature sensor probe inside the conduit, and send it to the temperature sensor filter circuit 23352;

The temperature sensor filter circuit 23352 is used to filter the current signal sent by the temperature sensor 23351, obtain the filtered current signal, and send it to the temperature detection chip 23355;

The cold end compensation temperature sensor 23353 is used to read the cold end temperature using the cold end compensation temperature sensor 23353 and send it to the cold end compensation sensor filter circuit 23354; the junction of the constantan wire and the copper wire is called the cold end;

The cold end compensation sensor filter circuit 23354 is used to filter the cold end temperature signal sent by the cold end compensation temperature sensor 23353 and send it to the temperature detection chip 23355;

The temperature detection chip 23355 is used to combine the filtered current signal sent by the temperature sensor filter circuit 23352 with the filtered cold end temperature signal sent by the cold end compensation sensor filter circuit 23354 to calculate the actual temperature and display it in the form of a register. Sent to central processing unit 232.

Further, the collection accuracy of the temperature acquisition circuit 2335 is associated with the temperature sensor 23351, temperature sensor filter circuit 23352, temperature detection chip 23355, cold end compensation temperature sensor 23353, and cold end compensation sensor filter circuit 53354.

Further, as shown in Figure 13, the central processing unit also includes a memory 23331, a processor 23332, a comparator 23333, and a controller 23334. Optionally, the controller is connected to relay unit 23335;

The memory 23331 is used to store the preset energy value E input by the user;

The processor 23332 is used to receive the current of each electrode sent by the current detection circuit 2331 and the voltage of the total electrode 2332 sent by the voltage detection circuit, and calculate the unit time in combination with the series and parallel connection mode of the sampling unit 233 The energy value En generated by accumulation inside;

Comparator 23333, used to compare the energy value En accumulated in the unit time sent by the processor 23332 and the preset energy value E in the storage device. The energy value En accumulated in the unit time When the value is equal to the preset energy value E, an equality signal is output;

The controller 23334 is used to control the circuit where the relay unit 23335 is located to be disconnected according to the equality signal; wherein the relay unit 23335 corresponds to the electrodes one-to-one, and the relay unit 23335 is used to control the opening and closing of the corresponding electrode.

During implementation, the user sets the temperature upper limit. When the temperature value monitored by the temperature sensor exceeds the set temperature upper limit, the relay will be directly controlled to turn off, and subsequent ablation will no longer be performed, thus protecting the equipment.

The relay unit 23335 is used to use multiple high-power relays in parallel to divide the power provided by the power strip into multiple power outputs. In specific implementation, when there are multiple electrodes that need to detect current, multiple one-to-one relays are set up to control the current detection circuit of the corresponding electrode on a one-to-one basis.

As shown in Figure 14, the relay unit includes: relay resistors R1, relay resistors R2, relay resistors R4, relay resistors R5, and photoelectric relay U1. The transistor Q1 is an NPN type transistor, and the base of the transistor Q1 is connected to the second end of the relay resistor R1; the collector of the transistor Q1 is connected to the LEDK end of the photoelectric relay U1; the transmitter of the transistor Q1 The pole is grounded; the first end of the relay resistor R1 is connected to the control module (for example, it can be the central control unit in Figure 13); the second end of the relay resistor R1 is connected to the first end of the relay resistor R5; The second end of the relay resistor R5 is connected to the emitter of the triode. The first end of the relay resistor R2 is connected to a high-level voltage source AVCC of 12V, and the second end of the relay resistor R2 is connected to the LEDA end of the photoelectric relay U1. The first end of the relay resistor R3 is connected to the OUT1 end of the photoelectric relay U1, and the second end of the relay resistor R3 is connected to the voltage-controlled radio frequency source 1. The first end of the relay resistor R4 is connected to the OUT2 end of the photoelectric relay U1, and the second end of the relay resistor R4 is connected to the ablation electrode.

In some examples, the power output board is shown in Figure 15 and includes an AC-DC transformer circuit and a DA control module.

The AC-DC transformer circuit is composed of a rectifier part circuit and a DC transformer part circuit; the rectifier part circuit is used to connect to the 220VAC mains power, convert the 220VAC mains power from alternating current to DC voltage through the rectifier bridge, and input to the DC transformer part circuit; the DC transformer part circuit is used to convert the large DC voltage output by the rectifier part circuit into the DC voltage required by the equipment. The DC voltage output by the DC transformer circuit is controlled by the SC pin of the module.

The DA control module includes a DA chip and an operational amplifier chip; the DA chip is communicatively connected to the central processing unit 232 of the ablation control device 23, and is used to receive the target voltage (in the form of a digital signal) sent by the central processing unit 232, Convert this digital signal into a voltage signal to control the voltage on the SC pin, thereby controlling the output voltage; the input end of the follower circuit composed of an operational amplifier is connected to the output end of the DA control chip, and then the follower outputs the DA control chip The signal is sent to the SC pin, and the follower isolates the two voltages before and after.

It is not difficult to find that both the present implementation mode and the second implementation mode are system embodiments corresponding to the first implementation mode, and both the present implementation mode and the second implementation mode can be implemented in cooperation with the first implementation mode. The relevant technical details mentioned in the first embodiment are still valid in this embodiment, and will not be described again in order to reduce duplication. Correspondingly, the relevant technical details mentioned in this embodiment can also be applied to the first embodiment.

This application also provides an ablation control device 16, which includes a memory 161, at least one processor 162, and at least one communication bus 163.

In some embodiments, a computer program is stored in the memory 161 , and when the computer program is executed by the at least one processor 32 , all or part of the steps in the method for adjusting power are implemented. The memory 161 includes read-only memory, programmable read-only memory, erasable programmable read-only memory, one-time programmable read-only memory, electronically erasable rewritable read-only memory, read-only optical disk or other optical disk memory, magnetic disk memory, tape storage, or any other computer-readable medium that can be used to carry or store data.

In some embodiments, when the at least one processor 32 executes the computer program stored in the memory, all or part of the steps of the method for adjusting power described in the embodiments of this application are implemented.

In some embodiments, the at least one communication bus 33 is configured to implement connection communication between the memory 161 and the at least one processor 32 and the like.

This application also provides a computer-readable storage medium. A computer program is stored on the computer-readable storage medium. When the computer program is executed by a processor, all or part of the steps in a method for adjusting power are implemented.

The above are only embodiments of the present application. Common knowledge such as the specific structures and characteristics of the solutions are not described in detail here. Those of ordinary skill in the art are aware of all common knowledge in the technical field to which the invention belongs before the filing date or priority date. Technical knowledge, being able to know all the existing technologies in the field, and having the ability to apply conventional experimental methods before that date. Persons of ordinary skill in the field can, under the inspiration given by this application, combine their own abilities to perfect and implement this plan, Some typical well-known structures or well-known methods should not be an obstacle for those of ordinary skill in the art to implement the present application. It should be pointed out that for those skilled in the art, several modifications and improvements can be made without departing from the structure of the present application. These should also be regarded as the protection scope of the present application and will not affect the implementation of the present application. effectiveness and patented practicality. The scope of protection claimed in this application shall be based on the content of the claims, and the specific implementation modes and other records in the description may be used to interpret the content of the claims.

Claims

A method of adjusting power, wherein the method is used to adjust the output power of an ablation control device, the ablation control device including a plurality of electrodes; the method includes:

Obtain the real-time current value and real-time voltage value of each electrode of the ablation control device during the ablation process;

Determine the real-time impedance of each electrode according to the real-time current value and the real-time voltage value, and determine a designated electrode from each of the electrodes based on the real-time impedance;

Determine the target monopolar power of at least one of the electrodes based on the real-time impedance of the designated electrode and the set preset monopolar power;

Based on the real-time power of the at least one electrode and the target monopolar power, the input voltage of the ablation control device is adjusted to adjust the output power of the ablation control device.
The method of adjusting power according to claim 1, wherein determining a designated electrode from the electrodes based on the real-time impedance includes:

The electrode with the smallest real-time impedance is determined as the designated electrode.
The method of adjusting power according to claim 1, wherein the target monopolar power of at least one of the electrodes is determined based on the real-time impedance of the designated electrode and the set preset monopolar power, include:

Based on the set preset monopolar power, the target monopolar power of the designated electrode is determined.
The method of adjusting power according to claim 3, wherein the target monopolar power of at least one of the electrodes is determined based on the real-time impedance of the designated electrode and the set preset monopolar power, Also includes:

For each other electrode except the designated electrode, calculate the ratio of the real-time impedance of the designated electrode to the real-time impedance of the other electrode, and based on the ratio of the real-time impedance and the target monopolar power of the designated electrode , determine the target monopolar power for that other electrode.
The method of adjusting power according to claim 4, wherein determining the target monopolar power of the designated electrode based on the set preset monopolar power includes:

Obtain the real-time temperature of the ablation object corresponding to the specified electrode during the ablation process;

Determine the power adjustment value of the designated electrode according to the comparison result between the real-time temperature of the ablation object corresponding to the designated electrode and the preset temperature threshold; the power adjustment value is used to adjust the ablation corresponding to the designated electrode The real-time temperature of the object;

Based on the set preset monopolar power and the power adjustment value, the target monopolar power of the designated electrode is determined.
The method of adjusting power according to claim 5, wherein the temperature threshold includes a preset temperature range and a preset protection temperature, and the maximum value of the preset temperature range is less than or equal to the preset protection temperature;

The target monopolar power is the sum of the preset monopolar power and the power adjustment value;

Determining the power adjustment value of the designated electrode according to the comparison result between the real-time temperature of the ablation object corresponding to the designated electrode and the preset temperature threshold, including:

When the real-time temperature of the designated electrode corresponding to the ablation object is within the preset temperature range, set the power adjustment value of the designated electrode to 0 so that the target monopolar power is equal to the preset monopolar power;

When the real-time temperature of the ablation object corresponding to the designated electrode is greater than the preset protection temperature, the power adjustment value of the designated electrode is set to less than 0, so that the target monopolar power is less than the preset monopolar power;

When the real-time temperature of the ablation object corresponding to the designated electrode is less than the minimum value of the preset temperature range, the power adjustment value of the designated electrode is set to be greater than 0, so that the target monopolar power is greater than the preset monopolar power. power.
The method of adjusting power according to claim 1, wherein the adjusting the input voltage of the ablation control device based on the real-time power of the at least one electrode and the target monopolar power includes:

Determine the sum of the target monopolar powers of all electrodes in the at least one electrode as the target total power;

The input voltage of the ablation control device is adjusted based on the difference between the sum of real-time power of all electrodes in the at least one electrode and the target total power.
The method of adjusting power according to claim 7, wherein the ablation control device is adjusted based on a current difference between the sum of real-time powers of all electrodes in the at least one electrode and the target total power. input voltage, including:

Based on the last acquired real-time power of all electrodes in the at least one electrode, determine the sum of historical real-time power, and determine the historical difference between the sum of historical real-time power and the target total power;

In the preset correspondence table between the power difference range and the voltage change, find the current power difference range and the corresponding voltage change to which the current difference belongs, as well as the historical power difference to which the historical difference belongs. scope;

If the current difference range is different from the historical power difference range, adjust the input voltage of the ablation control device according to the corresponding voltage change;

If the current difference range is the same as the historical power difference range, obtain the currently set voltage change amount, reduce the currently set voltage change amount, and adjust the ablation control according to the reduced voltage change amount. The input voltage of the device.
The method of adjusting power according to claim 1, wherein the method further includes:

According to the real-time current value and real-time voltage value of each electrode, the real-time energy generated by each channel within unit time is calculated;

Accumulate the real-time energy generated by each channel in each unit time to obtain the total energy generated by the electrodes of this channel;

If the total energy is equal to the preset energy value, the output power of the circuit where the electrode is located is adjusted to 0.
An ablation system, which: includes a power output board and an ablation control device; the ablation control device includes a central processing unit, a sampling unit and a plurality of electrodes, wherein,

The electrode is connected to one or more ablation objects and is used to ablate the connected ablation objects;

The sampling unit is used to detect the real-time current value and real-time voltage value of each electrode and send them to the central processing unit;

The central processing unit is configured to: determine the real-time impedance of each electrode based on the real-time current value and real-time voltage value sent by the sampling unit, and determine a designated electrode from each of the electrodes based on the real-time impedance; and, Determine the target electrode monopolar power of at least one of the electrodes based on the real-time impedance of the designated electrode and the set preset monopolar power; and, based on the real-time power of the at least one electrode, and the Target monopolar power, determine the control voltage signal that the ablation control device needs to send, and send the control voltage signal to the power output board;

The power output board is used to determine the target voltage according to the control voltage signal sent by the central processing unit, and adjust the output power of the electrode according to the control voltage signal.
The system according to claim 10, wherein the sampling unit is also used to detect the real-time temperature of the ablation object connected to the designated electrode, and send the real-time temperature to the central processing unit;

The central processing unit is also configured to: determine the power adjustment value of the designated electrode based on the comparison result between the real-time temperature of the ablation object connected to the designated electrode and a preset temperature threshold; and, based on the Set the preset unipolar power and the power adjustment value, Determine the target monopolar power of the designated electrode; wherein the power adjustment value is used to adjust the real-time temperature of the ablation object connected to the designated electrode.
The system according to claim 10, wherein the ablation control device further includes a relay control unit; the relay control unit is connected to the plurality of electrodes and is used to control the on/off of each electrode;

The central processing unit is also used to: calculate the real-time energy generated by each channel in unit time based on the real-time current value and real-time voltage value of each electrode; and calculate the real-time energy generated by each channel in each unit time. The energy is accumulated to obtain the total energy generated by the electrode of this circuit; if the total energy is equal to the preset energy value, the relay unit is controlled to disconnect the electrode of this circuit to adjust the output power of the circuit where the electrode of this circuit is located. is 0.
An ablation control device, which includes a memory, a processor, and a computer program stored on the memory and executable on the processor. When the processor executes the computer program, the computer program according to claims 1-9 is implemented. The method of adjusting power according to any one of the above.
A computer-readable storage medium having a computer program stored thereon, wherein when the computer program is executed by a processor, the method for adjusting power according to any one of claims 1-9 is implemented.