A bidirectional ablation control system and control method

Abstract

The application discloses a bidirectional ablation control system and a control method, and the system comprises: an ablation control system comprising a radio frequency generator for generating a radio frequency signal of a preset frequency required by radio frequency ablation; an ablation electrode array for emitting the radio frequency signal to a lesion to be ablated in a biological tissue; a low-temperature cooling device for realizing refrigeration and adjusting the temperature of the biological tissue close to the ablation electrode array region; a data acquisition unit for acquiring a target ablation depth and a target protection depth, and acquiring a cooling medium temperature and a tissue control point temperature; and a control unit for ablation of the lesion to be ablated according to the target ablation depth and the target protection depth. The temperature generated during ablation of the ablation electrode array is controlled by the low-temperature cooling device, so that the surface layer tissue close to the electrode can be protected and the deep layer lesion can be heated at the same time, and the thickness of the surface layer tissue to be protected and the thickness of the deep layer tissue to be heated can be adjusted by control parameters to realize individualized and accurate treatment effect.

Description

TECHNICAL FIELD

[0001] The embodiment of the present application relates to the field of biomedical engineering, in particular to a bidirectional ablation control system and a control method. BACKGROUND

[0002] Cardiovascular and malignant tumors are two major diseases threatening human health worldwide, and with the development of population aging, the incidence of these two diseases is increasing year by year. Traditional treatment methods, such as surgical operation (heart bypass, surgical resection of tumor), radiotherapy, chemotherapy and other methods, all have problems such as great harm to patients, obvious side effects, and long-term treatment effect needs to be improved.

[0003] In recent years, with the development of science and technology, medical imaging technologies such as nuclear magnetic resonance, CT, ultrasound, OCT and other imaging technologies have also made great progress, which has greatly promoted the development of related minimally invasive surgery treatment, among which the minimally invasive surgery for precise target treatment of lesions by thermal physics has received widespread attention.

[0004] Radiofrequency ablation uses a probe to apply a high-frequency current field to heat and treat lesion tissue. Compared with microwave, laser ablation and other technologies, radiofrequency ablation has the advantages of controllability and low cost, and is widely used in the treatment of tumors, atrial fibrillation, atherosclerosis and other diseases. Because the size and shape of lesions in different parts are different, and the protection of some key tissues is the key to ensure long-term treatment effect, such as the intima integrity in atherosclerosis. How to achieve complete ablation of lesions without damaging normal tissues and key organs such as the intima and adventitia of the blood vessel is a difficult point to ensure that no other complications occur and to ensure long-term good treatment effect. Therefore, it is necessary to study the control system for precise ablation to ensure that energy is precisely targeted to the lesion site and achieve long-term good treatment effect. SUMMARY

[0005] The embodiment of the present application provides a bidirectional ablation control system and a control method, and the main purpose is to overcome the shortcomings and deficiencies of the prior art, and to flexibly select the working electrode mode during ablation, and to control the directional output of radiofrequency energy and the heat exchange power of surface convection cooling at different lesion sites, to achieve conformal ablation of deep tissues while protecting surface tissues, and to improve treatment effect.

[0006] In a first aspect, the embodiment of the present application provides a bidirectional ablation control system, which comprises:

[0007] A radiofrequency generator for generating a radiofrequency signal of a preset frequency required for radiofrequency ablation;

[0008] An ablation electrode array for transmitting the radiofrequency signal to a lesion to be ablated in a biological tissue;

[0009] A cryogenic cooling device is used to realize refrigeration and adjust the temperature of biological tissue close to the ablation electrode array region;

[0010] A data acquisition unit is used to acquire a target ablation depth of the lesion to be ablated and a target protection depth between the surface tissue and the lesion to be ablated, and to acquire the cooling medium temperature and the tissue control point temperature of the cryogenic cooling device in real time during the ablation process;

[0011] A control unit is used to control the signal generation of the radio frequency generator, the working state of the ablation electrode array and the working state of the cryogenic cooling device, and to control the radio frequency generator and the ablation electrode array to ablate the lesion to be ablated according to the target ablation depth and the target protection depth.

[0012] Preferably, the control unit is specifically used to control the cryogenic cooling device, the radio frequency generator and the ablation electrode array to ablate the lesion to be ablated according to the target ablation depth and the target protection depth.

[0013] Preferably, the data acquisition unit is also used to acquire the electrical conductivity and the thermal conductivity of the lesion to be ablated.

[0014] The control unit is also used to construct a theoretical calculation model according to the electrical conductivity, the thermal conductivity of the lesion to be ablated and the real-time control parameters; wherein the control parameters include the tissue control point temperature and the cooling medium temperature.

[0015] The control unit performs parameterized scanning on the control parameters, inputs the theoretical calculation model, obtains the ablation depth and the protection depth corresponding to each control parameter, and establishes the relationship between the ablation depth, the protection depth and the cooling medium temperature and the tissue control point temperature.

[0016] Preferably, the data acquisition unit acquires the electrical impedance between the electrodes of the ablation electrode array, and uses the four-electrode method or the two-electrode method to solve the electrical conductivity of the region where the lesion to be ablated is located.

[0017] Preferably, the data acquisition unit solves the thermal conductivity of the region where the lesion to be ablated is located according to the transient plane heat source method.

[0018] Preferably, the data acquisition unit can also acquire the cooling medium flow rate of the cooling medium in the cryogenic cooling device.

[0019] The control unit is also used to control the cryogenic cooling device to adjust the cooling medium temperature and the tissue control point temperature according to the cooling medium flow rate.

[0020] Preferably, the target ablation depth and the target protection depth of the lesion to be ablated are obtained by the data acquisition unit through optical coherence tomography (OCT) or ultrasound (US).

[0021] Preferably, the radio frequency generator comprises a radio frequency power amplifier module, a radio frequency voltage and current acquisition module, and the radio frequency control parameters are acquired during the ablation process while the radio frequency treatment signal is generated, and after being processed by a data acquisition unit, the radio frequency control parameters are transmitted to the control unit as the feedback control of the radio frequency energy output.

[0022] Preferably, the ablation electrode array is arranged in a regular array, and a temperature sensor is arranged at a corresponding position of the electrode array, so that the working state of each ablation electrode can be controlled individually or jointly during the ablation process, and the temperature can be monitored in real time, and the radio frequency energy can be accurately applied to the target area.

[0023] Preferably, the low-temperature cooling device comprises a refrigeration device, a speed-adjustable pump, a gas-liquid transportation pipeline and a flow sensor, the control unit comprises a control module of the refrigeration device and the speed-adjustable pump, the refrigeration device is controlled to cool the cooling medium to a cooling medium temperature, and the speed-adjustable pump is controlled to adjust the flow rate of the cooling medium in the gas-liquid transportation pipeline in real time, so as to adjust the temperature of the tissue control point in the region where the ablation electrode array is located; and the flow sensor is used to acquire the flow rate of the cooling medium during the cooling control process for feedback control.

[0024] In a second aspect, the embodiments of the present application also provide a bidirectional ablation control method, and the method comprises:

[0025] acquiring a target ablation depth of the lesion to be ablated and a target protection depth between the surface tissue and the lesion to be ablated;

[0026] ablation is performed on the lesion to be ablated according to the target ablation depth and the target protection depth.

[0027] Preferably, the ablation performed on the lesion to be ablated according to the target ablation depth and the target protection depth comprises:

[0028] Step 1: according to the target ablation depth and the target protection depth, and the relationship between the ablation depth, the protection depth, the cooling medium temperature and the tissue control point temperature, the cooling medium temperature and the tissue control point temperature corresponding to the target ablation depth and the target protection depth are obtained by an iterative calculation method;

[0029] Step 2: according to the cooling medium temperature and the tissue control point temperature corresponding to the target ablation depth and the target protection depth, the low-temperature cooling device, the radio frequency generator and the ablation electrode array are controlled to ablate the lesion to be ablated.

[0030] Preferably, the method further comprises:

[0031] acquiring the electrical conductivity and the thermal conductivity of the lesion to be ablated;

[0032] construct a theoretical calculation model according to the electrical conductivity, the thermal conductivity of the lesion to be ablated and real-time control parameters; wherein the control parameters include a tissue control point temperature and a cooling medium temperature;

[0033] The control parameters are subjected to parameterized scanning, input into the theoretical calculation model, and the ablation depth and the protection depth corresponding to each control parameter are obtained, and the relationship between the ablation depth, the protection depth and the cooling medium temperature and the tissue control point temperature is established.

[0034] In a third aspect, the embodiments of the present application also provide a computing device, comprising:

[0035] a memory for storing program instructions;

[0036] a processor for calling the program instructions stored in the memory and executing the above-mentioned bidirectional ablation control method according to the obtained program.

[0037] In a fourth aspect, the embodiments of the present application also provide a computer-readable nonvolatile storage medium comprising computer-readable instructions, which, when read and executed by a computer, cause the computer to execute the above-mentioned bidirectional ablation control method.

[0038] The bidirectional ablation control system in the embodiments of the present application comprises a radio frequency generator for generating a radio frequency signal of a preset frequency required for radio frequency ablation; an ablation electrode array for emitting the radio frequency signal to a lesion site to be ablated in a biological tissue; a low-temperature cooling device for realizing refrigeration and adjusting the temperature of the biological tissue close to the ablation electrode array region; a data acquisition unit for acquiring a target ablation depth of the lesion to be ablated and a target protection depth between the surface tissue and the lesion to be ablated; and acquiring in real time the cooling medium temperature of the low-temperature cooling device and the tissue control point temperature of the surface tissue where the ablation electrode array is located during the ablation process; a control unit for controlling the signal generation of the radio frequency generator, the working state of the ablation electrode array and the working state of the low-temperature cooling device, and controlling the radio frequency generator and the ablation electrode array to ablate the lesion to be ablated according to the target ablation depth and the target protection depth. The temperature generated by the ablation electrode array during ablation is controlled by the low-temperature cooling device to avoid the temperature of the surface tissue being too high to damage the healthy tissue, so as to realize complete ablation of the lesion and no damage to the normal tissue such as the intima and the adventitia of the blood vessel and the key organs, thereby ensuring that no other complications are generated and the long-term good treatment effect is guaranteed. BRIEF DESCRIPTION OF DRAWINGS

[0039] In order to more clearly illustrate the technical solutions in the embodiments of the present application, the drawings needed to be used in the embodiments will be briefly introduced. Obviously, the drawings described below only represent some of the embodiments of the present application, and all other drawings obtained by those of ordinary skill in the art without creative effort based on these drawings also belong to the protection scope of the present application.

[0040] Figure 1 is a structural schematic diagram of a bidirectional ablation control system provided by an embodiment of the present application;

[0041] Figure 2 is a schematic diagram of an electrode array provided by an embodiment of the present application;

[0042] Figure 3 is a schematic diagram of an ablation electrode array located on the surface of a catheter provided by an embodiment of the present application;

[0043] Figure 4 is a schematic diagram of a radio frequency catheter electrode heating body model provided by an embodiment of the present application;

[0044] Figure 5 is a schematic diagram of an ablation experiment provided by an embodiment of the present application;

[0045] Figure 6 is a precise temperature control curve diagram of an example provided by an embodiment of the present application;

[0046] Figure 7 is a model verification diagram of an example provided by an embodiment of the present application;

[0047] Among them, 1-radio frequency generator; 2-ablation electrode array; 3-low temperature cooling device; 4-data acquisition unit; 5-control unit; 11-radio frequency power amplifier module; 12-radio frequency voltage and current acquisition module; 13-refrigeration device; 14-adjustable speed pump; 15-flow sensor; 16-gas-liquid transportation pipeline; 17-main control module; 18-radio frequency control module; 19-refrigeration device and adjustable speed pump control module; 20-data storage module; 21-wire. DETAILED DESCRIPTION

[0048] In order to make the purpose, technical solutions and advantages of the present application more clear, the present application will be further described in detail below with the drawings. Obviously, the described embodiments only represent some of the embodiments of the present application, and not all the embodiments. Based on the embodiments in the present application, all other embodiments obtained by those of ordinary skill in the art without creative effort also belong to the protection scope of the present application.

[0049] Figure 1 A bidirectional ablation control system provided by an embodiment of the present application. As shown in Figure 1As shown, the system can include:

[0050] A radio frequency generator for generating a radio frequency signal of a preset frequency required for radio frequency ablation.

[0051] An ablation electrode array for transmitting the radio frequency signal into a lesion to be ablated in biological tissue.

[0052] A cryogenic cooling device for realizing refrigeration and adjusting the temperature of biological tissue close to the area of the ablation electrode array.

[0053] A data acquisition unit for acquiring a target ablation depth of the lesion to be ablated and a target protection depth between surface tissue and the lesion to be ablated, and acquiring in real time the temperature of a cooling medium of the cryogenic cooling device and the temperature of a tissue control point during ablation.

[0054] A control unit for controlling the signal generation of the radio frequency generator, the working state of the ablation electrode array, and the working state of the cryogenic cooling device, and controlling the radio frequency generator and the ablation electrode array to ablate the lesion to be ablated according to the target ablation depth and the target protection depth.

[0055] The control unit is specifically configured to control the cryogenic cooling device, the radio frequency generator, and the ablation electrode array to ablate the lesion to be ablated according to the target ablation depth and the target protection depth, and the relationship between the ablation depth, the protection depth, and the temperature of the cooling medium and the temperature of the tissue control point.

[0056] In addition, in order to establish the relationship between the ablation depth, the protection depth, and the temperature of the cooling medium and the temperature of the tissue control point, the data acquisition unit can also be configured to acquire the electrical conductivity and the thermal conductivity of the lesion to be ablated; the control unit is further configured to construct a theoretical calculation model according to the electrical conductivity and the thermal conductivity of the lesion to be ablated and real-time control parameters; the control parameters can include the temperature of the tissue control point and the temperature of the cooling medium; the control unit performs parameterized scanning on the control parameters, inputs the theoretical calculation model, obtains the ablation depth and the protection depth corresponding to each control parameter, and establishes the relationship between the ablation depth, the protection depth, and the temperature of the cooling medium and the temperature of the tissue control point.

[0057] In the specific implementation process, the data acquisition unit can acquire the electrical conductivity σ and the thermal conductivity λ of the lesion to be ablated, and the control unit can construct a finite element calculation model according to the electrical quasi-static equation and the three-dimensional heat conduction equation to obtain the ablation depth A and the protection depth P under the current control parameters; wherein V is the radio frequency voltage, σ is the electrical conductivity (S / m) of the lesion to be ablated, ρ is the density (kg / m 3), c is the specific heat capacity (J / (kg*K)) of the lesion to be ablated, k is the thermal conductivity (W / (m*K)) of the lesion to be ablated, T is the tissue temperature (℃) of the lesion to be ablated, and τ is the treatment time (s) of the lesion to be ablated. The control parameters can include, but are not limited to, the tissue control point temperature T target , the cooling medium temperature T f , and the cooling medium flow rate V f . It should be noted that the thermal conductivity λ and the thermal conductivity k are two representations of the same concept.

[0058] Then, the control unit parameterizes the control parameters, including the tissue control point temperature T target , the cooling medium temperature T f , and the cooling medium flow rate V f , obtains the ablation depth A and the protection depth P under the corresponding conditions, and further analyzes the relationship between the ablation depth A, the protection depth P, and the treatment parameters (T target , T f , V f ) to obtain f(T target , T f , V f , A, P).

[0059] In specific applications, the target ablation depth A t and the target protection depth P t of the lesion to be ablated are input, and the optimal treatment parameters (T target , T f , V f ) are obtained by using the interpolation iteration f(T target0 , T f0 , V f0 ), which are used as the control parameters in the control unit to ablate the lesion to be ablated.

[0060] Wherein, the linear interpolation iteration method is as follows:

[0061] Step 1: According to the objective function min{||A t -A k ||+(A t / P t )*||P t -P k ||}, traverse the f(T target , T f , V f , A, P) relationship table to obtain the results A0, P0 closest to the ablation target, and the iteration count k=0.

[0062] Step 2: Repeat:

[0063] If At > A k and P t < P k , then k = k + 1, T fk = T fk + 1 / 8 k , T targetk = T targetk - 1 / 8 k , V fk = V fk - 1 / 8 k ;

[0064] If A t < A k and P t > P k , then k = k + 1, T fk = T fk - 1 / 8 k , T targetk = T targetk + 1 / 8 k , V fk = V fk + 1 / 8 k ;

[0065] Otherwise, output T fk , T targetk , V fk ;

[0066] If {||A t - A k || + (A t / P t )*||P t - P k ||} < 0.001 or k > m, terminate iteration, output T fk , T targetk , V fk . Where A k , P k , T fk , T targetk , V fk are the results of the kth interpolation of A, P, T f , T target , V f , and m is the termination iteration number.

[0067] It should be noted that the conductivity σ is collected by the data acquisition unit, and the electrical impedance between the electrodes of the ablation electrode array is collected. The conductivity σ of the region where the lesion to be ablated is located is solved by using a four-electrode method or a two-electrode method. In the implementation process, the ablation system can turn on the ablation electrodes of the corresponding region, apply a small signal radio frequency, use the electrical impedance between the electrodes, and solve the conductivity σ of the corresponding region by using a four-electrode method.

[0068] The thermal conductivity λ is also collected by the data acquisition unit, and the thermal conductivity λ of the region where the lesion to be ablated is located is mainly solved according to the transient plane heat source method. Specifically, the ablation system can use a plane probe made of thermal resistance material, apply a small constant power, record the temperature and probe response time, and solve the thermal conductivity λ of the corresponding region according to the transient plane heat source method.

[0069] The target ablation depth and the target protection depth of the lesion to be ablated can be obtained by the data acquisition unit through optical coherence tomography OCT or ultrasound US. The target ablation depth and the target protection depth of the lesion to be ablated can also be obtained by input or pre-stored parameters obtained by other imaging methods. The embodiments of the present application are not limited to the above-mentioned optical coherence tomography OCT or ultrasound US or manual input (or reading storage in the computer) other imaging methods, and other technologies that can achieve the same technical effect can also be used.

[0070] Specifically, the ablation electrode array adopts a regular array arrangement, and temperature sensors are arranged at corresponding positions of the electrode array. The working state of each ablation electrode can be controlled during the ablation process, and the temperature can be monitored in real time, so that the radio frequency energy can be accurately applied to the target region.

[0071] Figure 1 The ablation electrode array in the present application is arranged in a flexible electrode array by a plurality of small electrodes in order, the structure is as shown in Figure 2 The thermocouple is arranged at the corresponding position of the electrode array for real-time temperature monitoring and accurate transmission of radio frequency signals to the target region. The flexible electrode array can be adhered to the catheter, as shown in Figure 3 The flexible electrode array can also be adhered to the surface of the tissue to be treated, such as heating the deep layer of tissue through the skin surface.

[0072] Each electrode has three working states, which are positive, negative and not connected, and the working state of each electrode can be controlled independently or jointly. The control of the working state of each electrode is based on the actual lesion length L and width W information, and the electrodes at the corresponding positions are selected as working electrodes. In combination with the main control unit, different sizes of radio frequency energy can be applied to the corresponding lesion site according to the size of the lesion, so that multiple lesion sites can be treated at one time.

[0073] The radio frequency generator can include a radio frequency power amplifier module, a radio frequency voltage and current acquisition module, in the ablation process, radio frequency treatment signals are generated while radio frequency control parameters are acquired, after being processed by a data acquisition unit, the radio frequency control parameters are transmitted to a control unit as feedback control of radio frequency energy output.

[0074] The low-temperature cooling device includes a refrigeration device, a variable speed pump, a gas-liquid transportation pipeline, and a flow sensor.

[0075] The refrigeration temperature of the refrigeration device in the low-temperature cooling device can be set and adjusted by the control unit. f The control range of the cooling medium temperature T

[0076] Specifically, the flow rate of the cooling medium in the gas-liquid transportation pipeline can be adjusted by the control unit according to the flow signal Q = SV f , S is the cross-sectional area of the pipeline (m 2 ), Q is the volume flow rate (m 3 / s), and the feedback control can adjust the flow rate V f of the variable speed pump to achieve the adjustment of the flow rate V f of the pipeline.

[0077] Specifically, for minimally invasive transvascular or percutaneous puncture treatment, the cooling medium pipeline needs to consider the recycling of the cooling medium or the biological safety of the cooling medium entering the human body.

[0078] The control unit includes a main control module, a radio frequency control module, and a data storage module. The main control module controls the radio frequency control module, the refrigeration device, the variable speed pump, the ablation electrode array, the data acquisition unit, and the data storage module. The temperature control algorithm built in the radio frequency control module can achieve rapid and accurate control of the target area temperature, achieving the purpose of precise treatment. The data storage module can record the parameters during the treatment process in real time for subsequent data analysis and evaluation.

[0079] Specifically, the control method of the radio frequency control module includes temperature control, radio frequency power control, radio frequency voltage control, radio frequency current control, and radio frequency output energy control.

[0080] The tissue control point temperature T in the control parameters above target The cooling medium temperature T f The cooling medium flow rate V f The above-mentioned control parameters can be monitored by temperature sensors (such as thermocouples, platinum resistance), temperature sensors, and flow sensors, and the control unit can perform real-time feedback control according to the collected signals.

[0081] In this test example, the conformal ablation system and its control method are tested.

[0082] During the test, the flexible electrode array is adhered to the catheter, and two working electrodes are selected as the positive and negative electrodes. The temperature control mode is selected, and the middle point of the two electrodes is selected as the temperature control point. The temperature near the electrode is measured and monitored by a thermocouple. In order to ensure that the thermocouple temperature measurement is not disturbed by the radio frequency signal, there is a layer of polyimide film with a thickness of 0.05mm between the thermocouple and the flexible electrode, as shown in Figure 4 .

[0083] The catheter with the flexible electrode array and the thermocouple adhered to it is inserted into a 10cm*3cm*3cm size body membrane or tissue, as shown in Figure 5 , the depth information A t =1.02mm and the size P t =0.055mm of the given lesion to be ablated are tested and verified by a finite element simulation model. The precise temperature control curve during the experiment is as shown in Figure 6 , and the finite element simulation model verification result is as shown in Figure 7 .

[0084] The bidirectional ablation control system provided by the embodiments of the present application has at least the following advantages and effects compared with the prior art:

[0085] The three-dimensional conformal ablation problem in the current biological tissue radio frequency ablation surgery is mainly for the surgical planning, designing the conformal ablation electrode probe to realize the ablation of a larger range of tumors, and the problem that the treatment scene of protecting the surface layer tissue and heating the deep tissue is not applicable. An ablation system is provided, which can realize the treatment effect of protecting the surface layer tissue and heating the deep tissue through the cooperative control of the radio frequency body heating power and the surface convective heat transfer cooling power. And according to the characteristics of the lesion to be ablated, that is, the depth to be protected and the depth to be ablated, the radio frequency output energy, the cooling medium temperature and the flow rate are controlled to adjust the radio frequency body heating power and the surface convective heat transfer cooling power respectively, so that the surface layer protection of different thicknesses and the heating and ablation of different degrees of deep tissue are realized. The design of the electrode array can flexibly select the working state of the working electrode, which is conducive to obtaining different ablation shapes on the plane or curved surface. The combination of surface convective heat transfer and radio frequency heating can realize the protection of normal tissue from damage during the ablation process while realizing the targeted and precise ablation, and is especially suitable for the precise conformal treatment of a class of problems that need to protect the endothelial layer and heat the deep plaque, such as in the ablation of atherosclerotic plaques.

[0086] It should be noted that the embodiments of the present application are not limited to the ablation of tumor tissue lesions, but can also be applied to other ablation fields, such as subcutaneous fat ablation, surface skin tissue protection and deep fat tissue heating.

[0087] Based on the same technical concept, the embodiments of the present application also provide a bidirectional ablation control method, and the specific steps are as follows:

[0088] Step 1, collecting the target ablation depth of the lesion to be ablated and the target protection depth between the surface layer tissue and the lesion to be ablated.

[0089] Step 2, ablation is performed on the lesion to be ablated according to the target ablation depth and the target protection depth.

[0090] Specifically, first, according to the target ablation depth and the target protection depth, and the relationship between the ablation depth, the protection depth, the cooling medium temperature and the tissue control point temperature, the cooling medium temperature and the tissue control point temperature corresponding to the target ablation depth and the target protection depth are obtained through an iterative calculation method; and then according to the cooling medium temperature and the tissue control point temperature corresponding to the target ablation depth and the target protection depth, the low-temperature cooling device, the radio frequency generator and the ablation electrode array are controlled to ablate the lesion to be ablated.

[0091] Specifically, in establishing the relationship between the ablation depth, the protection depth, the cooling medium temperature and the tissue control point temperature, the conductivity and the thermal conductivity of the lesion to be ablated are mainly obtained through signal acquisition processing calculation or direct input; a theoretical calculation model is constructed according to the conductivity, the thermal conductivity of the lesion to be ablated and real-time control parameters; wherein the control parameters include the tissue control point temperature and the cooling medium temperature; the control parameters are parameterized scanned, input into the theoretical calculation model, and the ablation depth and the protection depth corresponding to each control parameter are obtained, and the relationship between the ablation depth, the protection depth, the cooling medium temperature and the tissue control point temperature is established.

[0092] It should be noted that the ablation control method has been described in detail in the above-mentioned bidirectional ablation control system, and will not be described again.

[0093] Based on the same technical concept, the embodiment of the present application also provides a computing device, comprising:

[0094] a memory for storing program instructions;

[0095] a processor for calling the program instructions stored in the memory, and executing the above-mentioned bidirectional ablation control method according to the obtained program.

[0096] Based on the same technical concept, the embodiment of the present application also provides a computer readable non-volatile storage medium, comprising computer readable instructions, when the computer reads and executes the computer readable instructions, the computer executes the above-mentioned bidirectional ablation control method.

[0097] The present application is described with reference to flowcharts and / or block diagrams of the method, device (system) and computer program product according to the embodiment of the present application. It should be understood that each flow and / or block in the flowchart and / or block diagram, and the combination of the flows and / or blocks in the flowchart and / or block diagram can be realized by computer program instructions. These computer program instructions can be provided to the processor of a general-purpose computer, a special-purpose computer, an embedded processor or other programmable data processing device to produce a machine, so that the instructions executed by the processor of the computer or other programmable data processing device produce a device that realizes the functions specified in the flowchart and / or block diagram. Figure 1 one flow or multiple flows and / or blocks Figure 1 an apparatus that realizes the functions specified in one block or multiple blocks.

[0098] These computer program instructions can also be stored in a computer readable memory capable of guiding the computer or other programmable data processing device to work in a specific way, so that the instructions stored in the computer readable memory produce a product including instruction apparatus, which realizes the functions specified in the flowchart and / or block diagram. Figure 1 one flow or multiple flows and / or blocks Figure 1the function specified in one or more blocks.

[0099] These computer program instructions can also be loaded into computer or other programmable data processing devices, so that a series of operations steps are performed on the computer or other programmable data processing devices to generate computer-implemented processes, thus the instructions executed on the computer or other programmable data processing devices provide processes for implementing the flows Figure 1 one or more flows and / or blocks Figure 1 the function specified in one or more blocks.

[0100] Although preferred embodiments of the application have been described herein, changes and modifications can be suggested to one skilled in the art, and it is intended that the application encompass such changes and modifications as fall within the scope of the appended claims.

[0101] Obviously, numerous modifications and variations of the present application are possible in light of the above teachings. It is therefore to be understood that within the scope of the appended claims and their equivalents, the application can be practiced otherwise than as specifically described.

Claims

1. A bidirectional ablation control system, characterized in that, The system comprises: a radio frequency generator for generating a radio frequency signal of a preset frequency required for radio frequency ablation; an ablation electrode array for transmitting the radio frequency signal into a lesion to be ablated in a biological tissue; a low-temperature cooling device for realizing refrigeration and adjusting the temperature of the biological tissue in the region close to the ablation electrode array; a data acquisition unit for acquiring a target ablation depth and a target protection depth between a surface tissue and the lesion to be ablated, and acquiring the temperature of a cooling medium of the low-temperature cooling device and the temperature of a tissue control point in real time during the ablation process; a control unit for controlling the signal generation of the radio frequency generator, the working state of the ablation electrode array and the working state of the low-temperature cooling device, and controlling the radio frequency generator and the ablation electrode array to ablate the lesion to be ablated according to the target ablation depth and the target protection depth; wherein the control unit obtains the temperature of the cooling medium and the temperature of the tissue control point corresponding to the target ablation depth and the target protection depth by calculation according to the target ablation depth and the target protection depth, and the relationship between the ablation depth, the protection depth, the temperature of the cooling medium and the temperature of the tissue control point, and controls the low-temperature cooling device, the radio frequency generator and the ablation electrode array to ablate the lesion to be ablated according to the temperature of the cooling medium and the temperature of the tissue control point corresponding to the target ablation depth and the target protection depth. The ablation electrode array is arranged in a regular array, and temperature sensors are arranged at corresponding positions of the electrode array. The working state of each ablation electrode can be controlled, the temperature can be monitored in real time, and the radio frequency energy can be accurately applied to the target region during the ablation process. The working state of each electrode is controlled according to the actual lesion length and width information, and the electrodes at the corresponding positions are selected as working electrodes. Different sizes of radio frequency energy are applied to the corresponding lesion parts according to the lesion size, so that multiple lesion parts can be treated at one time.

2. The system of claim 1, wherein, The data acquisition unit can also acquire the flow rate of the cooling medium in the low-temperature cooling device. The control unit is also used for controlling the low-temperature cooling device to adjust the temperature of the cooling medium and the temperature of the tissue control point according to the flow rate of the cooling medium.

3. The system of claim 1, wherein, The target ablation depth and the target protection depth of the lesion to be ablated are obtained by the data acquisition unit through optical coherence tomography (OCT) or ultrasonic (US).

4. The system of claim 1, wherein, The radio frequency generator comprises a radio frequency power amplifier module and a radio frequency voltage and current acquisition module. Radio frequency treatment signals are generated while the control parameters of the radio frequency are acquired during the ablation process. After being processed by the data acquisition unit, the control parameters are transmitted to the control unit as feedback control of the radio frequency energy output.

5. The system of any one of claims 1 to 4, wherein, The low-temperature cooling device comprises a refrigeration device, a speed-adjustable pump, a gas-liquid transportation pipeline and a flow sensor. The control unit comprises a control module of the refrigeration device and the speed-adjustable pump. The refrigeration device is controlled to cool the cooling medium to the temperature of the cooling medium, and the speed-adjustable pump is controlled to adjust the flow rate of the cooling medium in the gas-liquid transportation pipeline in real time, so as to adjust the temperature of the tissue control point in the region where the ablation electrode array is located. The flow sensor acquires the flow of the cooling medium in the cooling control process in real time for feedback control.

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