Ablation system suitable for non-fully parenchymal tissue and control method therefor

Abstract

Disclosed in the present invention are an ablation system suitable for non-fully parenchymal tissue and a control method therefor. In the present invention, the control method for the ablation system suitable for non-fully parenchymal tissue comprises the following steps: controlling a freezing apparatus of the ablation system to be preliminarily turned on, such that a probe located at a target position implements a freezing function; controlling the freezing apparatus to operate, such that the target position is frozen and a freezing region is formed; and controlling the freezing apparatus to be turned off, such that the freezing region is reheated. The impedance of non-fully parenchymal tissue can be reduced, the heat conduction efficiency of radio frequency ablation can be improved, and the ablation region can meet the requirements.

Description

Ablation systems and control methods suitable for non-solid tissues

[0001] This patent application claims priority to the following Chinese patent application:

[0002] Submission Date: October 14, 2024; Application Number: 2024114348536; Invention Title: Ablation System and Control Method Suitable for Non-Full Substance Tissues;

[0003] The full text of the above application is incorporated herein by reference. Technical Field

[0004] This invention relates to the field of medical devices, and in particular to an ablation system and control method suitable for non-full-solid tissues. Background Technology

[0005] Radiofrequency ablation is a common method for physically destroying tissue activity. It uses radiofrequency energy to raise the temperature of the surrounding tissue. Previous experiments have shown that when the tissue temperature exceeds approximately 55°C, cells begin to undergo coagulative necrosis, leading to the formation of localized ablation lesions and thus eliminating harmful tissue. Radiofrequency energy delivery is most effective when applied to solid tissues; otherwise, it significantly reduces efficiency and introduces operational risks.

[0006] Taking non-solid tissues like the lungs as an example, the presence of air in the alveoli makes them less efficient at conducting heat than other tissues. When heated, air-containing tissues have difficulty quickly transferring heat away. Furthermore, lung tissue has a low solid content, so even a small amount of heat applied can cause rapid carbonization in the contact area, ultimately increasing the tissue's resistance. At this point, further heating of the target tissue is ineffective, thus limiting the size of the ablation zone. Summary of the Invention

[0007] The purpose of this invention is to provide an ablation system and control method suitable for non-full-substance tissues, which can reduce the impedance of non-full-substance tissues, improve the thermal conductivity of radiofrequency ablation, and ensure that the ablation area meets the requirements.

[0008] To address the aforementioned technical problems, embodiments of the present invention provide a control method suitable for ablation systems of non-full-substance tissues, comprising the following steps:

[0009] The freezing device of the control ablation system is initially activated, allowing the probe located at the target position to perform the freezing function;

[0010] Controlling the operation of the refrigeration unit freezes the target location, creating a frozen zone;

[0011] The refrigeration unit is shut down to allow the frozen area to warm up again.

[0012] Compared to existing technologies, the embodiments of this invention first control the freezing device to enable the probe to perform freezing functions, freezing the target location to form a frozen region. This allows the target object with non-substantial components to be transformed into a near-substantial object, thereby improving the ablation thermal conductivity. Then, the frozen region is reheated, reducing the initial impedance before heating and slowing down the rate of impedance increase during heating. This allows for a continuous input of subsequent ablation energy, greatly improving controllability. Furthermore, the ablation range precisely covers the aforementioned frozen region. Beyond the frozen region, the target object containing non-substantial components is encapsulated, making it difficult to extend beyond the frozen region. Therefore, by creating a solidified region to be ablated, the control of the thermal ablation range is facilitated.

[0013] In one embodiment, after the step control refrigeration device is turned off, the following steps are further included:

[0014] Obtain the impedance of the frozen area and determine whether the impedance has decreased to the target range;

[0015] If the impedance of the frozen area decreases to the target range, the step is to control the radio frequency heating device of the ablation system to work, so that the probe heats and ablates the frozen area after it has been reheated until the ablation range covers the frozen area.

[0016] In one embodiment, the impedance value of the target range is less than or equal to 100Ω.

[0017] In one embodiment, after the step of controlling the freezing device to shut down and allowing the frozen area to reheat, the method further includes: controlling the freezing device to turn on again, so that there is a cold circulation inside the probe; wherein the temperature of the cold circulation is higher than the temperature at which the probe performs its freezing function when the freezing device is initially turned on.

[0018] In one embodiment, the step of controlling the operation of the radiofrequency heating device suitable for an ablation system for non-full-substance tissue specifically includes: controlling the radiofrequency heating device to start and stop multiple times.

[0019] In one embodiment, the radio frequency heating device is controlled to start and stop multiple times based on the obtained impedance value.

[0020] In one embodiment, the cold cycle temperature range is -10°C to 10°C.

[0021] In one embodiment, the step controls the operation of the freezing device to freeze the target location, the cooling rate of the probe is greater than 50°C / min, and the minimum temperature at which the probe performs the freezing function is less than or equal to -100°C.

[0022] In one embodiment, after the refrigeration device has been running for a preset period of time, a step is executed to control the refrigeration device to shut down.

[0023] The present invention also provides an ablation system suitable for non-full-substance tissues, the ablation system suitable for non-full-substance tissues being capable of executing any of the control methods described above, comprising: a cryostat, a probe, and a control module; the control module being electrically connected to the cryostat and controlling the start and stop of the cryostat; one end of the cryostat being connected to a cold source, and the other end being connected to the probe; the control module controlling the cryostat to input the low-temperature medium of the cold source to the probe for cooling the probe.

[0024] In one embodiment, the ablation system suitable for non-full-substance tissue further includes: a radio frequency heating device disposed in the probe head, wherein the control module is electrically connected to the radio frequency heating device and controls the start and stop of the radio frequency heating device.

[0025] The present invention also provides a control method for an ablation system suitable for non-full-solid tissues. The ablation system suitable for non-full-solid tissues includes: a radiofrequency heating device, a cryotherapy device, a probe, and a control module; the control module is electrically connected to the radiofrequency heating device and the cryotherapy device, and controls the start and stop of the radiofrequency heating device and the cryotherapy device.

[0026] The control method includes the following steps:

[0027] The cryotherapy device, which is suitable for ablation systems of non-full-solid tissues, is initially turned on, allowing the probe to perform its cryotherapy function;

[0028] The operation of the freezing device is controlled to freeze the target location where the probe is located, thus forming a frozen area;

[0029] Control the refrigeration unit to shut down;

[0030] When the impedance of the frozen area is detected to decrease to the target range, the radio frequency heating device is controlled to operate, so that the probe has radio frequency ablation function.

[0031] Embodiments of the present invention also provide a method for improving the heat transfer efficiency of non-full-grained tissues, comprising the following steps:

[0032] Control the probe located at the target position to perform the freezing function;

[0033] Freeze the target location for a preset time until it is frozen, thus forming a frozen area;

[0034] Turn off the probe's freezing function and allow the frozen area to reheat. Attached Figure Description

[0035] One or more embodiments are illustrated by way of example with reference numerals in the accompanying drawings. These illustrations do not constitute a limitation on the embodiments. Elements with the same reference numerals in the drawings are denoted as similar elements. Unless otherwise stated, the figures in the drawings are not to be limited by scale.

[0036] Figure 1 is a flowchart of a control method for an ablation system suitable for non-full-substance tissues according to an embodiment of the present invention;

[0037] Figure 2 is a control module diagram of an ablation system suitable for non-full-substance tissues according to an embodiment of the present invention. Detailed Implementation

[0038] To make the objectives, technical solutions, and advantages of the embodiments of the present invention clearer, the various embodiments of the present invention will be described in detail below with reference to the accompanying drawings. However, those skilled in the art will understand that many technical details have been presented in the various embodiments of the present invention to enable the reader to better understand this application. However, the technical solutions claimed in this application can be implemented even without these technical details and various changes and modifications based on the following embodiments.

[0039] In the following description, certain specific details are set forth for the purpose of illustrating various disclosed embodiments in order to provide a thorough understanding of the various disclosed embodiments. However, those skilled in the art will recognize that embodiments may be practiced without one or more of these specific details. In other instances, well-known apparatuses, structures, and techniques associated with this application may not have been shown or described in detail to avoid unnecessarily obscuring the description of the embodiments.

[0040] Unless the context requires otherwise, throughout the specification and claims, the word “comprising” and its variations, such as “including” and “having”, shall be understood to have an open, inclusive meaning, that is, to be interpreted as “including, but not limited to”.

[0041] The embodiments of the present invention will be described in detail below with reference to the accompanying drawings to provide a clearer understanding of the purpose, features, and advantages of the present invention. It should be understood that the embodiments shown in the drawings are not intended to limit the scope of the present invention, but are merely illustrative of the essential spirit of the technical solution of the present invention.

[0042] Throughout this specification, references to "an embodiment" or "an embodiment" indicate that a particular feature, structure, or characteristic described in connection with the embodiment is included in at least one embodiment. Therefore, the appearance of "in an embodiment" or "an embodiment" in various places throughout the specification does not necessarily refer to the same embodiment. Furthermore, a particular feature, structure, or characteristic may be combined in any manner in one or more embodiments.

[0043] The singular forms “a” and “the” used in this specification and the appended claims include plural references unless otherwise expressly stated herein. It should be noted that the term “or” is generally used to mean “and / or” unless otherwise expressly stated herein.

[0044] In the following description, in order to clearly demonstrate the structure and working method of the present invention, a number of directional terms will be used. However, terms such as "front", "back", "left", "right", "outside", "inside", "outward", "inward", "up", and "down" should be understood as convenient terms and not as limiting terms.

[0045] Embodiments of the present invention are described below with reference to the accompanying drawings.

[0046] The first embodiment of this invention relates to a control method for an ablation system suitable for non-solid tissues. This control method is used for targets with non-solid components, such as tumor ablation experiments on dissected animal lungs, where the lung is a non-solid tissue. Radiofrequency ablation is a common method for physically destroying tissue activity by transferring radiofrequency energy, causing an increase in the temperature of the surrounding tissue. Previous experiments have shown that when the tissue temperature exceeds approximately 55°C, cells begin to undergo coagulative necrosis, leading to the formation of local ablation lesions and achieving the goal of eliminating harmful tissue. For radiofrequency energy transfer, the transfer effect is better when applied to solid tissues; otherwise, efficiency is greatly reduced and operational risks are introduced. For example, when applied to the lungs, the presence of air in the alveoli results in lower thermal conductivity than other tissues. Air-containing tissues have difficulty quickly conducting heat away after being heated, and the lung tissue has a low solid component; even a small amount of heat applied will cause rapid carbonization of the contact area, ultimately increasing the tissue impedance in that area. At this point, further heating of the target tissue is ineffective, thus limiting the size of the ablation area. Measurements show that this area is difficult to exceed 2 cm in size. The above problems can be overcome by the ablation system control method suitable for non-full-substance tissues in this embodiment, which allows for continuous input of radiofrequency ablation energy, improves the energy output efficiency of radiofrequency ablation, and enables the ablation area to meet the requirements, rather than being limited to 2cm.

[0047] Specifically, the ablation system suitable for non-full-substance tissue includes: a display module, a radio frequency heating device, a cryotherapy device, a probe, and a control module. The control module is electrically connected to the display module, the radio frequency heating device, and the cryotherapy device, and controls the start and stop of the radio frequency heating device and the cryotherapy device. The control module controls the radio frequency transmitter of the radio frequency heating device to provide radio frequency current to the probe, thereby heating the probe. The control module controls the cryotherapy device to input liquid nitrogen from the liquid nitrogen storage tank to the probe for cooling. The display module displays the probe temperature, operating time, impedance of the probe area, cryotherapy area, and probe temperature. In this embodiment, the ablation system suitable for non-full-substance tissue is a multimodal ablation system with a cryotherapy device and a radio frequency heating device. However, in other embodiments, the ablation system may be a combination of an ablation device with a cryotherapy device or an ablation device with a radio frequency heating device.

[0048] The cryogenic device includes a gas-liquid separator and a valve block. The inlet of the gas-liquid separator is connected to a liquid nitrogen storage tank for liquid nitrogen input. The liquid outlet of the gas-liquid separator is connected to the valve block, through which liquid nitrogen is input to the probe for probe cooling. The exhaust port of the gas-liquid separator is connected to an exhaust solenoid valve. The valve block is equipped with a first temperature sensor and a pressure sensor to measure the temperature and pressure values ​​of the liquid nitrogen flowing through the valve block. The probe outlet is connected to a loop solenoid valve, through which waste liquid is input to a waste liquid treatment device. The outlet of the exhaust solenoid valve is also connected to the waste liquid treatment device, which treats the input waste liquid into room temperature gas before discharging it into the air. The probe can be a rigid puncture needle, inserted directly into the target tissue area from the outside, or a flexible probe, i.e., a flexible smooth needle, which can be pushed along the cavity to the target tissue area. The probe includes a working section for freezing and heating, an insulating section for thermal and electrical insulation of normal tissue, and a connection section for temperature signal, radio frequency signal, and liquid nitrogen transmission. During freezing, liquid nitrogen flows into the working section's cavity through the inlet pipe, undergoes phase change heat, and then flows out of the probe through the return gas channel. During heating, the probe receives radio frequency current through the radio frequency signal line. The probe shaft, except for the working section, is wrapped with an electrical insulation layer to ensure that radio frequency energy is output only from the working section. The working section includes a temperature sensor for real-time temperature feedback during the elimination of harmful tissue.

[0049] A control method suitable for ablation systems of non-solid tissues includes the following steps:

[0050] Step 110: Control the cryo-device of the ablation system suitable for non-full-solid tissue to be initially turned on, so that the probe located at the target position can perform the cryo-feeding function;

[0051] Step 120: Control the operation of the freezing device to freeze the target location and form a frozen area;

[0052] Step 130: Control the freezing device to shut down, allowing the frozen area to rewarm. Specifically, during the rewarming process, the frozen area gradually thaws, tissue bleeding and fluid discharge occur, forming a condensed state, and the impedance decreases. At this time, the size and state of the frozen area can be displayed through the display module suitable for ablation systems of non-full-solid tissues.

[0053] Step 140: Control the radio frequency heating device suitable for the ablation system of non-full solid tissue to work, so that the probe heats and ablates the frozen area after rewarming until the ablation range covers the frozen area.

[0054] By first controlling the freezing device to enable the probe to freeze, the target location is frozen to form a frozen zone, thereby transforming the target object with non-material components into a near-material object, thus improving the ablation thermal conductivity. Then, the frozen zone is reheated, reducing the initial impedance before heating and slowing down the rate of impedance increase during heating. This allows for continuous input of ablation energy, greatly improving controllability. Furthermore, the ablation range precisely covers the aforementioned frozen zone; beyond this zone, the target object containing non-material components further obstructs the ablation process, making it difficult to extend beyond the frozen zone. This creates a solidified area to be ablated, facilitating control of the thermal ablation range.

[0055] Furthermore, in step 120, the cooling rate of the probe is greater than 50℃ / min, and the minimum temperature at which the probe performs its freezing function is less than or equal to -100℃. Optionally, the minimum temperature at which the probe performs its freezing function can be -110℃, -115℃, or -120℃, etc.

[0056] Furthermore, when the refrigeration unit operates in the freezing zone for a preset duration, step 120 is executed to control the refrigeration unit to shut down. In step 120, the preset operating time for the refrigeration unit can be 5-10 minutes; in step 130, the shutdown time for the refrigeration unit can be 1-2 minutes.

[0057] Additionally, after step 130 controls the freezing device to shut down and before step 140 controls the radiofrequency heating device suitable for the ablation system of non-full-solid tissues to operate, the impedance of the freezing area is acquired, and it is determined whether the impedance has decreased to the target range.

[0058] If the impedance of the frozen area decreases to the target range, then step 140 is executed to control the radiofrequency heating device suitable for the ablation system of non-full-substance tissues.

[0059] Furthermore, the impedance value of the target range is less than or equal to 100Ω. That is, in step 130, the freezing device is turned off, allowing the frozen area to thaw and bleed during the rewarming process, reducing the impedance to less than or equal to 100Ω. At this time, the probe temperature rises above 0°C.

[0060] Additionally, after controlling the freezing device to shut down in step 130 to allow the frozen area to rewarm, the process further includes: controlling the freezing device to restart, enabling cold circulation within the probe; wherein the cold circulation temperature is higher than the temperature at which the probe performs its freezing function when the freezing device is initially turned on. Controlling the restart of the freezing device can be done before or simultaneously with controlling the RF heating device to turn on, or immediately after the heating device is turned on. The probe operates on the rewarmed frozen area, which can stably reach temperatures above 60°C, with a maximum temperature exceeding 120°C.

[0061] Furthermore, step 140, controlling the operation of the radiofrequency heating device suitable for the ablation system of non-full-substance tissue, specifically includes: controlling the radiofrequency heating device to start and stop multiple times. That is, first, the radiofrequency heating device is turned on, allowing the probe to heat and ablate the rewarmed frozen area. When the impedance first decreases and then increases, and an upward trend occurs, the radiofrequency power output is immediately stopped (for about a few seconds). The impedance decreases again, and then the radiofrequency power is output again. After the impedance rises, the radiofrequency is stopped again. That is, the start and stop of the radiofrequency heating device is repeated in a pulse form until the ablation range covers the frozen area. In step 140, the radiofrequency heating device can be controlled to operate in a pulse form for 5-15 minutes.

[0062] The steps of the various methods described above are only for clarity. In practice, 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, but without changing the core design of the algorithm and process, are also within the scope of protection of this patent.

[0063] The second embodiment of the present invention relates to a control method for an ablation system suitable for non-full-substance tissues, used to improve the heating efficiency of non-full-substance tissues, specifically including the following steps.

[0064] Step 110: Control the cryo-device of the ablation system suitable for non-full-solid tissue to be initially turned on, so that the probe located at the target position can perform the cryo-feeding function;

[0065] Step 120: Control the operation of the freezing device to freeze the target location and form a frozen area;

[0066] Step 130: Control the refrigeration unit to shut down, allowing the frozen area to warm up again.

[0067] Steps 110-130 above are as described in the first embodiment and will not be repeated hereafter.

[0068] It is not difficult to see that this embodiment is a system implementation corresponding to the first embodiment, and this embodiment can be implemented in conjunction with the first embodiment. The relevant technical details mentioned in the first embodiment are still valid in this embodiment, and will not be repeated here to reduce repetition. Accordingly, the relevant technical details mentioned in this embodiment can also be applied to the first embodiment.

[0069] A third embodiment of the present invention relates to an ablation system suitable for non-full-tumor tissues. The ablation system for non-full-tumor tissues includes: a radiofrequency heating device, a cryotherapy device, a probe, and a control module. The control module is electrically connected to the cryotherapy device and controls its start and stop. One end of the cryotherapy device is connected to a cold source, and the other end is connected to the probe; the cold source can be a liquid nitrogen storage tank. The control module controls the cryotherapy device to input liquid nitrogen from the liquid nitrogen storage tank into the probe for probe cooling.

[0070] The ablation system may also include a display module electrically connected to the control module, which displays the probe temperature, operating time, impedance of the probe area, freezing zone, and probe temperature.

[0071] Furthermore, the ablation system suitable for non-full-substance tissues also includes: a radio frequency heating device disposed in the probe head, wherein the control module is electrically connected to the radio frequency heating device and controls the start and stop of the radio frequency heating device.

[0072] The refrigeration unit includes a gas-liquid separator and a valve block. The inlet of the gas-liquid separator is connected to a liquid nitrogen storage tank for liquid nitrogen input. The liquid outlet of the gas-liquid separator is connected to the valve block, through which liquid nitrogen is input to the probe for probe cooling. The exhaust port of the gas-liquid separator is connected to an exhaust solenoid valve. The valve block is equipped with a first temperature sensor and a pressure sensor to measure the temperature and pressure values ​​of the liquid nitrogen flowing through the valve block. The outlet of the probe is connected to a loop solenoid valve, through which waste liquid is input to a waste liquid treatment device. The outlet of the exhaust solenoid valve is also connected to the waste liquid treatment device, which treats the input waste liquid into room temperature gas before discharging it into the air. The probe includes a working section for freezing and heating, an insulating section for thermal and electrical insulation of normal tissue, and a connection section for temperature signal, radio frequency signal, and liquid nitrogen transmission. During freezing, liquid nitrogen flows into the cavity of the working section through the inlet pipe, undergoes phase change heat transfer, and then flows out of the probe through the return gas channel. During heating, the probe receives radio frequency current via a radio frequency signal line. The probe shaft, except for the working section, is wrapped with an electrical insulation layer to ensure that radio frequency energy is output only from the working section. The working section includes a temperature sensor to provide real-time temperature feedback during the elimination of harmful tissue.

[0073] It is not difficult to see that this embodiment is a system implementation corresponding to the first embodiment, and this embodiment can be implemented in conjunction with the first embodiment. The relevant technical details mentioned in the first embodiment are still valid in this embodiment, and will not be repeated here to reduce repetition. Accordingly, the relevant technical details mentioned in this embodiment can also be applied to the first embodiment.

[0074] The fourth embodiment of the present invention relates to a control method for an ablation system suitable for non-solid tissues, for a specific non-solid component target. The ablation system suitable for non-solid tissues includes: a radio frequency heating device, a freezing device, a probe, and a control module; the control module is electrically connected to the radio frequency heating device and the freezing device, and controls the start and stop of the radio frequency heating device and the freezing device.

[0075] The control method includes the following steps:

[0076] The cryotherapy device, which is suitable for ablation systems of non-full-solid tissues, is initially turned on, allowing the probe to perform its cryotherapy function;

[0077] Control the freezing device to operate until the target location of the probe is frozen, forming a frozen area;

[0078] Control the refrigeration unit to shut down;

[0079] When the impedance of the frozen area is detected to decrease to the target range, the radio frequency heating device is controlled to operate, so that the probe has radio frequency ablation function.

[0080] Another embodiment of the present invention provides a method for improving the heat transfer efficiency of non-full-grain tissues, comprising the following steps:

[0081] Control the probe located at the target position to perform the freezing function;

[0082] Freeze the target location for a preset time until it is frozen, thus forming a frozen area;

[0083] Turn off the probe's freezing function and allow the frozen area to rewarm. Specifically, to improve the heating efficiency of non-parenchymal tissue, the probe can be placed at the target location first, then the freezing device can be turned on to freeze the target location. After freezing for a certain period of time, the freezing device can be turned off, and the probe will no longer cool. At this time, the frozen area will rewarm, and the tissue will bleed and expel fluid. At this point, the impedance will decrease to the point where it can be heated for ablation. The specific system used can be the ablation system suitable for non-parenchymal tissue described in the third embodiment, which will not be detailed here. The control method can also refer to the control method of the ablation system suitable for non-parenchymal tissue.

[0084] The preferred embodiments of the present invention have been described in detail above, but it should be understood that, if necessary, aspects of the embodiments can be modified to utilize aspects, features, and concepts from various patents, applications, and publications to provide other embodiments.

[0085] In light of the detailed description above, these and other changes can be made to the embodiments. Generally, the terminology used in the claims should not be considered limited to the specific embodiments disclosed in the specification and claims, but should be understood to include all possible embodiments together with the full scope of equivalents enjoyed by these claims.

[0086] Those skilled in the art will understand that the above embodiments are specific examples of implementing the present invention, and in practical applications, various changes in form and detail may be made without departing from the spirit and scope of the present invention.

Claims

1. A control method for an ablation system suitable for non-full-substance tissues, characterized in that, Includes the following steps: The freezing device of the control ablation system is initially activated, allowing the probe located at the target position to perform the freezing function; Controlling the operation of the refrigeration unit freezes the target location, creating a frozen zone; The refrigeration unit is shut down to allow the frozen area to warm up again.

2. The control method for an ablation system suitable for non-full-substance tissues according to claim 1, characterized in that, After the refrigeration unit is shut down, the following steps are also included: Obtain the impedance of the frozen area and determine whether the impedance has decreased to the target range; If the impedance of the frozen area decreases to the target range, the step is to control the radio frequency heating device of the ablation system to work, so that the probe heats and ablates the frozen area after it has been reheated until the ablation range covers the frozen area.

3. The control method for an ablation system suitable for non-full-substance tissues according to claim 2, characterized in that, The impedance value of the target range is less than or equal to 100Ω.

4. The control method for an ablation system suitable for non-full-substance tissues according to claim 2, characterized in that, After the step of controlling the freezing device to shut down and allowing the frozen area to reheat, the method further includes: controlling the freezing device to turn on again, so that there is a cold circulation inside the probe; wherein the temperature of the cold circulation is higher than the temperature at which the probe performs its freezing function when the freezing device is initially turned on.

5. The control method for an ablation system suitable for non-full-substance tissues according to claim 4, characterized in that, The steps for controlling the operation of the radiofrequency heating device suitable for ablation systems of non-full-substance tissues specifically include: controlling the radiofrequency heating device to start and stop multiple times.

6. The control method for an ablation system suitable for non-full-substance tissues according to claim 5, characterized in that, The radio frequency heating device is controlled to start and stop multiple times based on the obtained impedance value.

7. The control method for an ablation system suitable for non-full-substance tissues according to claim 4, characterized in that, The cooling cycle temperature range is -10°C to 10°C.

8. The control method for an ablation system suitable for non-full-substance tissues according to claim 1, characterized in that, The steps control the operation of the freezing device to freeze the target location. The cooling rate of the probe is greater than 50℃ / min, and the minimum temperature at which the probe performs the freezing function is less than or equal to -100℃.

9. The control method for an ablation system suitable for non-full-substance tissues according to claim 1, characterized in that, After the refrigeration unit has been running for a preset time in the freezing zone, the following steps are executed to shut down the refrigeration unit.

10. An ablation system suitable for non-full-solid tissues, characterized in that, The ablation system suitable for non-full-substance tissues can perform the control method as described in any one of claims 1-9, comprising: a cryostat, a probe, and a control module; the control module is electrically connected to the cryostat and controls the start and stop of the cryostat; one end of the cryostat is connected to a cold source, and the other end is connected to the probe; the control module controls the cryostat to input the low-temperature medium of the cold source to the probe for cooling.

11. The ablation system suitable for non-full-solid tissues according to claim 10, characterized in that, Also includes: A radio frequency heating device is installed inside the probe head. The control module is electrically connected to the radio frequency heating device and controls the start and stop of the radio frequency heating device.

12. A control method for an ablation system suitable for non-full-substance tissues, characterized in that, The ablation system suitable for non-full-substance tissues includes: a radiofrequency heating device, a cryotherapy device, a probe, and a control module; the control module is electrically connected to the radiofrequency heating device and the cryotherapy device, and controls the start and stop of the radiofrequency heating device and the cryotherapy device; The control method includes the following steps: The cryotherapy device, which is suitable for ablation systems of non-full-solid tissues, is initially turned on, allowing the probe to perform its cryotherapy function; The operation of the freezing device is controlled to freeze the target location where the probe is located, thus forming a frozen area; Control the refrigeration unit to shut down; When the impedance of the frozen area is detected to decrease to the target range, the radio frequency heating device is controlled to operate, so that the probe has radio frequency ablation function.

13. A method for improving the heat transfer efficiency of non-solid tissues, characterized in that, Includes the following steps: Control the probe located at the target position to perform the freezing function; Freeze the target location for a preset time until it is frozen, thus forming a frozen area; Turn off the probe's freezing function and allow the frozen area to reheat.

Images