Radiofrequency ablation data processing method, device, system, equipment and storage medium

Abstract

The present invention provides a data processing method, device, system, equipment and storage medium for radiofrequency ablation. The data processing method includes: obtaining a three-dimensional anatomical model corresponding to a target object; constructing a medium distribution model of the cooling medium in the three-dimensional anatomical model based on the three-dimensional anatomical model and the description information of the cooling medium; constructing a temperature change model corresponding to the target object based on the constructed medium distribution model and the radiofrequency energy released by the acquired radiofrequency ablation device at a second position point in the three-dimensional anatomical model; combining the simulated cooling position points, the position points to be ablated and the temperature change model preset in the three-dimensional anatomical model, predicting the temperature change of the tissue in the target object during the radiofrequency ablation process.

Description

Technical Field

[0001] The present invention relates to the medical field, and in particular to a data processing method, device, system, electronic equipment and storage medium for radiofrequency ablation. Background Art

[0002] Radiofrequency ablation is an ablation technique achieved through high-frequency oscillation. Specifically, electrodes are inserted into the target tissue, current is connected, and high-frequency oscillations are used to generate heat energy.

[0003] In existing related technologies, during or before ablation surgery, only past experience and the results of preoperative ablation experiments can be used to provide a reference basis for radiofrequency ablation, and the actual state of the tissue in the target object during the radiofrequency ablation process cannot be depicted. Summary of the Invention

[0004] The present invention provides a data processing method, device, system, electronic device and storage medium for radiofrequency ablation, so as to solve the problem that the actual state of tissue in a target object during radiofrequency ablation cannot be depicted.

[0005] According to a first aspect of the present invention, a method for processing radiofrequency ablation data is provided, comprising:

[0006] obtaining a three-dimensional anatomical model corresponding to the target object;

[0007] Based on the three-dimensional anatomical model and the description information of the cooling medium, a medium distribution model of the cooling medium in the three-dimensional anatomical model is constructed, wherein the medium distribution model is used to simulate: after each first position point in the three-dimensional anatomical model is supplied with the cooling medium, the cooling medium concentration distribution corresponding to each position point in the three-dimensional anatomical model;

[0008] Based on the constructed medium distribution model and the acquired radiofrequency energy released by the radiofrequency ablation device at a second location within the three-dimensional anatomical model, a temperature change model corresponding to the target object is constructed, wherein the temperature change model is used to simulate: changes in temperature of tissue within the target object over time; the second location is associated with one or more first locations;

[0009] The temperature change of the tissue in the target object during the radiofrequency ablation process is predicted by combining the simulated cooling position points, the position points to be ablated, and the temperature change model preset in the three-dimensional anatomical model.

[0010] Optionally, constructing a medium distribution model of the cooling medium within the three-dimensional anatomical model based on the three-dimensional anatomical model and the description information of the cooling medium includes:

[0011] The description information of the three-dimensional anatomical model and the cooling medium is processed using a dual-porosity model to determine simulated medium flow rate information of the three-dimensional anatomical model; the simulated medium flow rate information is used to simulate: after the cooling medium is supplied to the first position point, the flow rate distribution of the cooling medium in the three-dimensional anatomical model;

[0012] The medium distribution model is determined based on the simulated medium flow rate information of the three-dimensional anatomical model.

[0013] Optionally, determining the medium distribution model based on the simulated medium flow rate information of the three-dimensional anatomical model includes:

[0014] A convection-diffusion equation of the target object is obtained, and the flow velocity information of the simulated medium is processed based on the convection-diffusion equation to determine the medium distribution model.

[0015] Optionally, constructing a temperature change model corresponding to the target object based on the constructed medium distribution model and the acquired radiofrequency energy released by the radiofrequency ablation device at a second position point within the three-dimensional anatomical model includes:

[0016] Calculating the absorption rate of the released radiofrequency energy at each position point on the three-dimensional anatomical model during the radiofrequency ablation process based on the cooling medium concentration distribution simulated by the medium distribution model and the simulated electric field strength generated by the radiofrequency energy within the three-dimensional anatomical model;

[0017] Based on the absorption rate, the temperature change model is constructed.

[0018] Optionally, based on the cooling medium concentration distribution simulated by the medium distribution model and the simulated electric field strength generated by the ablation energy within the three-dimensional anatomical model, calculating the absorption rate of the released radiofrequency energy at each position point of the three-dimensional anatomical model during the radiofrequency ablation process includes:

[0019] Calculating simulated electrical conductivity information of the three-dimensional anatomical model based on the cooling medium concentration distribution simulated by the medium distribution model; the simulated electrical conductivity information is used to simulate: the electrical conductivity of each position point in the three-dimensional anatomical model after the cooling medium is supplied to the first position point;

[0020] The absorption rate is calculated based on the simulated electrical conductivity information and the simulated electric field strength.

[0021] Optionally, constructing the temperature change model based on the absorption rate includes:

[0022] Acquiring a simulated blood flow condition of the target object, and determining a corresponding heat diffusion model based on the simulated blood flow condition and the second location point, wherein the heat diffusion model is used to model heat changes caused by the simulated blood flow condition at various locations within the target object during a process of performing radiofrequency ablation within the target object that matches the second location point;

[0023] The temperature change model is constructed based on the calculated absorption rate and the thermal diffusion model.

[0024] Optionally, the radiofrequency ablation data processing method further includes:

[0025] Acquiring an ablation effect simulation model; the ablation effect simulation model is used to simulate damage to tissue in the target object during radiofrequency ablation;

[0026] Based on the ablation effect simulation model and the radiofrequency ablation duration, a current ablation effect of the tissue in the target object is predicted, where the current ablation effect represents the damage to the tissue in the target object during the radiofrequency ablation process.

[0027] According to a second aspect of the present invention, there is provided a data processing device for radiofrequency ablation, comprising:

[0028] A model acquisition module, configured to acquire a three-dimensional anatomical model corresponding to a target object;

[0029] a medium distribution construction module, configured to construct a medium distribution model of the cooling medium within the three-dimensional anatomical model based on the three-dimensional anatomical model and the description information of the cooling medium, wherein the medium distribution model is configured to simulate: after each first position point within the three-dimensional anatomical model is supplied with the cooling medium, the cooling medium concentration distribution corresponding to each position point within the three-dimensional anatomical model;

[0030] a temperature model construction module, configured to construct a temperature change model corresponding to the target object based on the constructed medium distribution model and the acquired specified radiofrequency energy released by the radiofrequency ablation device at a second location point within the three-dimensional anatomical model, wherein the temperature change model is configured to simulate: changes in temperature of tissue within the target object over time; the second location point is associated with one or more first location points;

[0031] The prediction module is used to predict the temperature change of the tissue in the target object during the radiofrequency ablation process by combining the simulated cooling position points, the position points to be ablated and the temperature change model preset in the three-dimensional anatomical model.

[0032] According to a third aspect of the present invention, a radiofrequency ablation system is provided, comprising a radiofrequency ablation device, a data processing device, and a display device, wherein the data processing device is used to execute the data processing method involved in the first aspect and its optional scheme, and the display device is used to display the temperature change predicted by the data processing method.

[0033] According to a fourth aspect of the present invention, there is provided an electronic device comprising a processor and a memory,

[0034] The memory is used to store code;

[0035] The processor is used to execute the code in the memory to implement the method involved in the first aspect and its optional solutions.

[0036] According to a fifth aspect of the present invention, there is provided a storage medium having a computer program stored thereon, which, when executed by a processor, implements the method involved in the first aspect and its optional solutions.

[0037] The radiofrequency ablation data processing method, apparatus, system, electronic device, and storage medium provided by the present invention incorporate a temperature variation model specific to the target object. This temperature variation model can then be used to predict changes in the temperature of the target object's tissue over time. The changes predicted by the temperature variation model can be used to depict the actual temperature of the target object's tissue during radiofrequency ablation, providing a sufficient and effective basis for executing radiofrequency ablation.

[0038] At the same time, the present invention constructs a temperature change model based on the concentration distribution of the cooling medium in the three-dimensional anatomical model and the release of radiofrequency energy brought by the radiofrequency ablation equipment. Therefore, the corresponding temperature change model can accurately predict the amount of radiofrequency energy absorbed by each position of the target object along with the input of the cooling medium, thereby accurately predicting the temperature changes of each position point in the three-dimensional anatomical model corresponding to the target object, which can guide the subsequent radiofrequency ablation operation, is conducive to the formulation of targeted ablation treatment strategies, and can provide accurate and effective reference for the radiofrequency ablation process, which can not only optimize the effect of the radiofrequency ablation operation, but also improve the safety and reliability of the radiofrequency operation, so that when the lesion site is killed (for example, completely killed), the possibility of damaging healthy tissue in the target object can be minimized. BRIEF DESCRIPTION OF THE DRAWINGS

[0039] In order to more clearly illustrate the embodiments of the present invention or the technical solutions in the prior art, the following briefly introduces the drawings required for use in the embodiments or the description of the prior art. Obviously, the drawings described below are only some embodiments of the present invention. For ordinary technicians in this field, other drawings can be obtained based on these drawings without paying any creative work.

[0040] Figure 1 is a schematic diagram of the structure of a radiofrequency ablation system in an exemplary embodiment of the present invention;

[0041] Figure 2 is a flow chart of a data processing method for radiofrequency ablation in an exemplary embodiment of the present invention;

[0042] Figure 3 is a schematic diagram of a process for determining a medium distribution model in an exemplary embodiment of the present invention;

[0043] Figure 4 is a schematic diagram of a process for constructing a temperature change model in an exemplary embodiment of the present invention;

[0044] Figure 5 is a schematic diagram of a process for constructing a temperature change model based on absorption rate in an exemplary embodiment of the present invention;

[0045] Figure 6 is a schematic diagram of a process for predicting the current ablation effect in an exemplary embodiment of the present invention;

[0046] Figure 7 is a schematic diagram of a process for adjusting a temperature change model in an exemplary embodiment of the present invention;

[0047] Figure 8 is a schematic diagram of a program module of a data processing device for radiofrequency ablation in an exemplary embodiment of the present invention;

[0048] Figure 9 is a schematic diagram of program modules of a data processing device for radiofrequency ablation in another exemplary embodiment of the present invention;

[0049] Figure 10 FIG. 1 is a schematic diagram of the structure of an electronic device in an exemplary embodiment of the present invention. DETAILED DESCRIPTION

[0050] The following will clearly and completely describe the technical solutions in the embodiments of the present invention in conjunction with the accompanying drawings. Obviously, the described embodiments are only part of the embodiments of the present invention, not all of the embodiments. Based on the embodiments of the present invention, all other embodiments obtained by ordinary technicians in this field without making creative efforts are within the scope of protection of the present invention.

[0051] The terms "first", "second", "third", "fourth", etc. (if any) in the description and claims of the present invention and the above-mentioned drawings are used to distinguish similar objects and are not necessarily used to describe a specific order or sequence. It should be understood that the numbers used in this way are interchangeable where appropriate, so that the embodiments of the invention described herein can be implemented in orders other than those illustrated or described herein. In addition, the terms "including" and "having" and any variations thereof are intended to cover non-exclusive inclusions. For example, a process, method, system, product or apparatus that includes a series of steps or units is not necessarily limited to those steps or units clearly listed, but may include other steps or units that are not clearly listed or inherent to these processes, methods, products or apparatus.

[0052] The following specific embodiments are used to describe the technical solution of the present invention in detail. The following specific embodiments can be combined with each other, and the same or similar concepts or processes may not be described in detail in some embodiments.

[0053] Please refer to Figure 1 An embodiment of the present invention provides a radiofrequency ablation system, including a radiofrequency ablation device 101 , a data processing device 102 and a display device 103 .

[0054] The radiofrequency ablation device 101 may include, for example, an ablation electrode and an ablation circuit. The ablation circuit is electrically connected to the ablation electrode and may generate a high-frequency current. The high-frequency current acts on the tissue to be ablated via the ablation electrode.

[0055] When using the radiofrequency ablation device 101, radiofrequency ablation targets and kills cancer cells. An ablation electrode is inserted into the target tissue, and an electric current is applied. High-frequency oscillation generates heat energy, and when heated to 60-100°C, the tissue undergoes thermal coagulative necrosis. When using the radiofrequency ablation device 101 to ablate the target tissue, there are currently issues with excessive impedance in the target tissue, resulting in carbonization and scorching of the tissue, and adhesion of tissue near the probe. These issues can result in incomplete ablation and premature termination of the ablation procedure. Injecting a cooling medium (e.g., saline) can effectively address these issues.

[0056] The data processing device 102 is used to execute the data processing method of the embodiment of the present invention. The data processing device 102 can be any device with data processing capabilities, such as a computer, a tablet computer, a server, a terminal, etc.

[0057] The display device 103 is used to display the temperature changes predicted by the data processing method, and can be a two-dimensional display device or a three-dimensional display device. The temperature changes specifically refer to the temperature changes of the tissue within the target object during the radiofrequency ablation process, for example, including the temperature changes at one or more locations within the target object over time during the radiofrequency ablation process.

[0058] The displayed content can be the temperature data itself, or the temperature can be displayed using colors, lines, etc. In one example, on the display device 103, an image of the temperature field can be used to reflect the distribution of temperature in space and time; in another example, a virtual model (such as a virtual anatomical model of the target object) can be displayed on the display device 103, and then the temperature and temperature changes at each location can be reflected by filling in the virtual model with color. In another example, the temperature change curve of each location can be used to reflect the temperature change at that location. In another example, two-dimensional or three-dimensional temperature chart data can be used to reflect the temperature change at each location over time.

[0059] Please refer to Figure 2 , an embodiment of the present invention provides a method for processing radiofrequency ablation data, comprising:

[0060] S201: Acquire a three-dimensional anatomical model corresponding to the target object;

[0061] The target object herein can be understood as any object to be ablated by radiofrequency ablation, for example, a physiological part of the human body to be ablated by radiofrequency ablation, such as the lungs including the trachea, or other physiological parts such as the liver, intestines, and urinary tract;

[0062] For ease of explanation, in the following embodiments, the target object is taken as lung tissue as an example.

[0063] The three-dimensional anatomical model can be understood as any virtual model that can represent the three-dimensional anatomical structure of the target object.

[0064] In a specific example, the three-dimensional anatomical model may include virtual biological tissues such as a virtual lesion point (for simulating a lesion point), a virtual lung (for simulating a lung), and a virtual blood vessel (for simulating a blood vessel, for example, simulating at least one blood vessel-related parameter including the position, size, and other blood vessel characteristics of the blood vessel). Furthermore, the blood flow in the virtual blood vessel of the three-dimensional anatomical model may be configured with corresponding blood flow-related parameters.

[0065] In some examples, the three-dimensional anatomical model can be reconstructed based on medical images of the target object (e.g., CT data);

[0066] For example, based on the patient's CT data, lung biological tissue containing cancer foci can be reconstructed, i.e., three-dimensional reconstructed data can be obtained, which can be in a data format such as STL. Then, the three-dimensional reconstructed data in a data format such as STL can be input into simulation pre-processing software (such as Geomagic software / hypermash software). Through processing by the simulation pre-processing software Geomagic, an optimized three-dimensional anatomical model surface (such as a NURBS surface) can be obtained. The optimized three-dimensional anatomical model surface (such as a NURBS surface) is then imported into Hypermesh software for two-dimensional and three-dimensional mesh division to obtain a processed mesh model. Furthermore, the processed mesh model can be imported into finite element simulation (Finite Element Analysis) software to construct biological tissue structures containing cancer foci, lungs, and intravascular blood flow according to the anatomical morphology of the target object, and use this as a three-dimensional anatomical model. The three-dimensional anatomical model obtained by processing with the aforementioned simulation processing software can be more consistent with the biological characteristics of the target object.

[0067] The finite element simulation software may include Comsol, Abaqus, Ansys, etc.;

[0068] For example, mesh convergence analysis can be performed in finite element simulation software to verify that the 3D lung anatomical model processed by the finite element simulation software better matches the actual lung tissue. This can also make the subsequent medium distribution model and temperature change model constructed based on the 3D anatomical model more consistent with the actual tissue conditions.

[0069] S202: Constructing a medium distribution model of the cooling medium within the three-dimensional anatomical model based on the three-dimensional anatomical model and the description information of the cooling medium;

[0070] The cooling medium can be understood as a gas or liquid medium. During the process of performing a radiofrequency ablation operation on the target object, by infusing the cooling medium into the target object, the cavities between the tissues in the target object can be effectively filled, so that the current generated by the radiofrequency ablation operation forms a loop, and the temperature of the tissues in the target object is appropriately reduced, effectively avoiding carbonization, scorching or tissue adhesion of the tissues in the target object, thereby preventing the radiofrequency ablation operation from being terminated prematurely and ensuring the treatment effect of the radiofrequency ablation operation. For example, the cooling medium can be physiological saline, etc.

[0071] Correspondingly, any information that can describe the cooling medium can be used as an optional scheme for the description information of the cooling medium. Furthermore, the description information can be any information related to the effect produced by the cooling medium after acting on the human body. For example, the description information may include the permeability of the cooling medium in the target object or the dynamic viscosity of the cooling medium.

[0072] The medium distribution model is used to simulate: after each first position point in the three-dimensional anatomical model is supplied with a cooling medium, the cooling medium concentration distribution corresponding to each position point in the three-dimensional anatomical model; wherein the first position point can be any position in the three-dimensional anatomical model;

[0073] Each position point in the three-dimensional anatomical model can be determined manually or automatically. When each position point is determined automatically, for example, a position point can be determined at a certain interval in the virtual lung of the three-dimensional anatomical model, and then each position point can be evenly distributed in the virtual lung.

[0074] S203: constructing a temperature change model corresponding to the target object based on the constructed medium distribution model and the acquired radiofrequency energy released by the radiofrequency ablation device at a second position point within the three-dimensional anatomical model;

[0075] The second position point may be manually selected in the acquired three-dimensional anatomical model, or may be automatically determined in the three-dimensional anatomical model by a data processing device based on acquired corresponding position data. The second position point may be any position in the three-dimensional anatomical model.

[0076] The temperature change model is used to simulate: the temperature change of the tissue in the target object over time, that is, when a cooling medium is supplied at a first position point in the three-dimensional anatomical model and radiofrequency energy is released at a second position point, the temperature change of each position point in the target object during radiofrequency ablation can be determined based on the temperature change model; the second position point is associated with one or more first position points, and this association can be reflected as follows: if the ablation electrode of the radiofrequency ablation device is inserted into the second position point and a radiofrequency ablation operation is performed at the second position point, then by providing a cooling medium at any first position point, the impedance of the target tissue at and around the second position point can be reduced, effectively preventing carbonization or scorching of the target tissue, and effectively avoiding premature termination of the radiofrequency ablation operation. Therefore, the number of first position points that meet the above requirements can be one or more, wherein the first position point is located around the second position point, or the first position point and the second position point overlap, etc.;

[0077] S204: Predicting temperature changes of tissues in the target object during the radiofrequency ablation process by combining the simulated cooling locations, the locations to be ablated, and the temperature change model preset in the three-dimensional anatomical model;

[0078] The location point to be ablated can be any location point or multiple location points within the target object, and the simulated cooling location point can be any location point or multiple location points within the target object that are associated with the location point to be ablated. This specification does not limit this. The correlation between the simulated cooling location point and the location point to be ablated is consistent with the correlation between the first location point and the second location point, and will not be repeated here.

[0079] For example, assuming that according to the surgical plan, a radiofrequency ablation device is required to perform a radiofrequency ablation surgery on position point 1 in the target object, then the temperature change of the tissue in the target object during the radiofrequency ablation process can be predicted by combining the position point 1, the position point 2 adapted to the position point 1 and cooled (i.e., the simulated cooling position point), and the temperature change model. Then, the relevant operator can adjust the surgical plan or execute the surgical plan based on the obtained temperature change.

[0080] In the above scheme, a temperature change model is introduced for the target object; this temperature change model can then be used to predict the temperature changes of the target object's tissue over time. The changes predicted by the temperature change model can be used to depict the actual temperature of the target object's tissue during radiofrequency ablation, providing a sufficient and effective basis for performing radiofrequency ablation.

[0081] At the same time, the present invention constructs a temperature change model based on the concentration distribution of the cooling medium in the three-dimensional anatomical model and the release of radiofrequency energy brought by the radiofrequency ablation equipment. Therefore, the corresponding temperature change model can accurately predict the amount of radiofrequency energy absorbed by each position of the target object along with the input of the cooling medium, thereby accurately predicting the temperature changes of each position point in the three-dimensional anatomical model corresponding to the target object, which can guide the subsequent radiofrequency ablation operation, is conducive to the formulation of targeted ablation treatment strategies, and can provide accurate and effective reference for the radiofrequency ablation process, which can not only optimize the effect of the radiofrequency ablation operation, but also improve the safety and reliability of the radiofrequency operation, so that when the lesion site is killed (for example, completely killed), the possibility of damaging healthy tissue in the target object can be minimized.

[0082] Based on the solution of the present invention, accurate and effective guidance and suggestions can be provided for the surgical planning of radiofrequency ablation. In actual application, it can be applied to the entire clinical workflow from planning to evaluation. Based on the temperature change model, different ablation treatment strategies can be formulated for different patients to meet the needs of personalized treatment. It can significantly improve the effect of radiofrequency ablation surgery and effectively avoid the occurrence of non-lethal situations in the corresponding lesion site due to the inability to accurately ablate during the ablation surgery.

[0083] In addition, by adding the simulation of the infusion of cooling medium (such as saline) (embodied in the medium distribution model), it can help to effectively improve the conductivity and reduce the impedance. When applied to radiofrequency ablation surgery on the lungs, it can fill the lung cavity to form a current loop, avoid the carbonization and scorching of tissues, and adhesion of tissues near the probe, thereby preventing the radiofrequency ablation surgery from being terminated prematurely.

[0084] In one implementation, please refer to Figure 3 , based on the three-dimensional anatomical model and the description information of the cooling medium, constructing a medium distribution model of the cooling medium in the three-dimensional anatomical model, including:

[0085] S301: Processing the description information of the three-dimensional anatomical model and the cooling medium using a dual-porosity model to determine the simulated medium flow rate information of the three-dimensional anatomical model;

[0086] S302: Determine the medium distribution model based on the simulated medium flow rate information of the three-dimensional anatomical model.

[0087] The dual-porosity model can also be understood as a dual-porosity medium model. Through this model, the transmission process of the cooling medium (such as saline) injected into the tissue of the target object can be described, and the pressure distribution within the three-dimensional anatomical model corresponding to the target object during this transmission process can be obtained.

[0088] The dual-porosity model includes equations for the pressure distribution within tissues, assuming that the interstitial tissue (the lung interstitium excluding the bronchi and blood vessels surrounding the first RF ablation site) and the vascular system are incompressible porous media overlapping the same space. Then:

[0089] Assuming that the cooling medium is injected into the target object's tissue during the transmission process, the pressure distribution equation (1) within the three-dimensional anatomical model corresponding to the target object can be, for example:

[0090]

[0091] in:

[0092] p i Characterizes the pressure within the interstitial tissue of the target object;

[0093] K i Characterizing the penetration rate of a cooling medium (e.g., saline) into the interstitial tissue of the target subject;

[0094] p v characterizing the vascular pressure of the target subject;

[0095] K vCharacterizing the penetration rate of a cooling medium (e.g., saline) into the vascular system of a target subject;

[0096] μ characterizes the dynamic viscosity of the cooling medium (e.g., saline);

[0097] W i and W v represent the volume fractions of the porous regions in the interstitial tissue and vascular system of the target object respectively; and W i +W v = 1, ensuring that mass conservation between the interstitium and the vascular system is satisfied due to the difference in spatial volume fraction;

[0098] Θ v The transfer of a cooling medium (e.g., saline) between the vasculature and interstitial tissue of a target subject due to a pressure differential is described;

[0099] Θ L Describes the loss of cooling media (e.g., saline) from the interstitial tissue of a target subject to the lymphatic vessels due to pressure differential;

[0100] In one example, according to the Kedem–Katchalsky theory, equation (2) can be obtained:

[0101]

[0102] in:

[0103] L p Characterizing the permeability coefficient of the vascular system of the target subject;

[0104] S / V represents the ratio of the vascular surface area to the tissue volume of the target object;

[0105] σ t Characterizes the penetration reflectance coefficient;

[0106] π v and π i characterizing the osmotic pressure of the vascular system and interstitium of the target subject, respectively;

[0107] L pL Characterizes the permeability coefficient of the lymphatic vessels of the target object,

[0108] characterizing the ratio of lymphatic vessel surface area to tissue volume of the target subject;

[0109] p L Characterizes the lymphatic pressure of the target subject;

[0110] The "max" operator simulates the presence of valves in the target subject's lymphatic vessels, thereby preventing the cooling medium (eg, saline) from flowing back into the interstitium.

[0111] In one example, Darcy's equation can be used to obtain U i and U v The equation expression (3):

[0112]

[0113] Combining the above equations (1), (2), and (3), the flow velocity distribution of the cooling medium in the target object can be obtained, and the simulated medium flow velocity information of the three-dimensional anatomical model corresponding to the target object can be determined. The simulated medium flow velocity information is used to simulate: after the first position point is supplied with cooling medium, the flow velocity distribution of the cooling medium in the three-dimensional anatomical model.

[0114] in:

[0115] U i , i.e., the flow rate of the cooling medium (e.g., saline) in the interstitial space of the target object: which may reflect the mapping relationship between each position point in the tissue interstitium surrounding the cooling medium (e.g., saline) release position point (i.e., the first position point) and the corresponding saline flow rate;

[0116] U v , i.e., the flow rate of the cooling medium (e.g., saline) in the blood vessels of the target object: it can reflect the mapping relationship between each position point in the blood vessel around the cooling medium (e.g., saline) release position point (i.e., the first position point) and the corresponding saline flow rate.

[0117] The specific example of step S302 may include:

[0118] The convection-diffusion equation of the target object is obtained, and the simulated medium flow rate information obtained in step S301 is used as input to the convection-diffusion equation. The medium distribution model is determined by solving the convection-diffusion equation.

[0119] The convection-diffusion equation can be understood as a convection-diffusion equation constructed based on the double-pore model. This convection-diffusion equation can describe the transport process of solutes in the interstitium and blood vessels. Specifically, it can include the following equation expressions (4) and (5):

[0120]

[0121]

[0122] Equation (4) is the convection-diffusion equation for interstitial tissue, and equation (5) is the convection-diffusion equation for blood vessels, where:

[0123] ci and c v The interstitial and intravascular cooling medium (e.g., saline) concentrations of the target subject are characterized separately;

[0124] D i and D v The diffusion coefficients of the interstitial and intravascular cooling media (e.g., saline) in the target subject are characterized respectively;

[0125] U i and U v The interstitial and intravascular cooling medium (e.g., saline) flow rates of the target subject are characterized respectively;

[0126] In addition, F s Describes the fluid transport between the interstitial and vascular systems of the target subject, while F l The solute transport between the interstitium and lymphatic vessels of the target object is described as shown in the following equation (6):

[0127]

[0128] F L =Θ L c i

[0129] where Θ v 、Θ L The equations for pressure distribution in tissues can be used to understand σ f Indicates the resistance reflection coefficient of the cooling medium.

[0130] By combining the above equations (4), (5), and (6) and solving them, the concentration distribution of the cooling medium in the target object can be obtained.

[0131] In the above scheme, by simulating the medium flow rate, the accuracy of the medium distribution model (i.e., the accuracy of the cooling medium concentration distribution) can be guaranteed, and the flow of the cooling medium in the target object can be accurately reflected. On this basis, the accuracy and effectiveness of the temperature change model finally constructed can be effectively guaranteed.

[0132] In one implementation, please refer to Figure 4 , based on the constructed medium distribution model and the acquired radiofrequency energy released by the radiofrequency ablation device at the second position point within the three-dimensional anatomical model, constructing a temperature change model corresponding to the target object, including:

[0133] S401: Calculating the absorption rate of the released radiofrequency energy at each position point on the three-dimensional anatomical model during the radiofrequency ablation process based on the cooling medium concentration distribution simulated by the medium distribution model and the simulated electric field strength generated by the radiofrequency energy within the three-dimensional anatomical model;

[0134] S402: Constructing the temperature change model based on the absorption rate.

[0135] Some examples of step S401 may include:

[0136] Based on the cooling medium concentration distribution simulated by the medium distribution model, the simulated electrical conductivity information of the three-dimensional anatomical model is calculated, and based on the simulated electrical conductivity information and the simulated electric field strength, the absorption rate is calculated.

[0137] The simulated electrical conductivity information is used to simulate: the electrical conductivity of each position point in the three-dimensional anatomical model after the cooling medium is supplied to the first position point, that is, the ability to conduct current;

[0138] In a specific example, the operating frequency of the RF ablation probe is relatively high, such as 350-550 kHz. At a relatively high operating frequency, the wavelength of the electromagnetic energy is several orders of magnitude larger than the size of the ablation electrode. Therefore, the RF ablation device can generate an electric field during the RF ablation operation at the second location within the target object. The electric field can be expressed as the following equation (7) using the Laplace equation:

[0139]

[0140] in:

[0141] is the gradient operator;

[0142] c represents the concentration of cooling medium in the interstitial space of the target object (i.e. Figure 3 The specific example of c in the embodiment shown is i );

[0143] σ(c, T) represents the electrical conductivity related to the cooling medium concentration and temperature; it can be understood as the electrical conductivity simulated by the simulated electrical conductivity information; σ(c, T) can be calculated according to a preset calculation formula, or σ(c, T) can be obtained by querying an existing database according to the corresponding cooling medium concentration and temperature information. This specification is not limited to this.

[0144] φ characterizes the electric potential within the target object.

[0145] Then, the electric field intensity and current density generated in the tissue of the target object can be expressed as the following equation (8):

[0146] J=σ(c,T)E

[0147] Here, E can be used to represent the electric field strength corresponding to each position point within the target object.

[0148] The absorption rate Q of the radiofrequency energy released by the radiofrequency ablation device in the tissue of the target object hs It is defined as the product of current density J and electric field strength E, which can be expressed by the following equation (9):

[0149] Q hs =JE=σ(c, T)·E 2

[0150] Q hs It can be used to characterize the absorption rate of radiofrequency ablation energy acquired at each position point of the target object during radiofrequency ablation operation accompanied by infusion of a cooling medium (such as saline), that is, the absorption rate.

[0151] In the above scheme, the simulated electric field strength is fully considered, which can reflect the conductivity of the ablation process and then reflect the energy transfer brought by conductivity. On this basis, based on the simulated electric field strength and the concentration distribution of the cooling medium, the absorption rate of radio frequency energy at each position point in the target object can be accurately and effectively calculated, which is conducive to the subsequent accurate prediction of the temperature distribution of each position point in the target object.

[0152] In one implementation, please refer to Figure 5 , based on the absorption rate, constructing the temperature change model, including:

[0153] S501: Acquire a simulated blood flow condition of the target object, and determine a corresponding heat diffusion model based on the simulated blood flow condition and the second position point;

[0154] S502: Constructing the temperature change model based on the calculated absorption rate and the thermal diffusion model.

[0155] The heat diffusion model is used to model: during the process of performing radiofrequency ablation at the second position point in the target object, heat changes caused by the simulated blood flow situation at various positions in the target object.

[0156] In a specific example, the heat diffusion caused by blood flow in the tissue can be simulated based on the obtained simulated blood flow conditions and blood rheology to form a heat diffusion model. For example, based on the simulated blood flow conditions, a heat diffusion model caused by blood flow can be established for any of the aforementioned position information:

[0157] The simulated blood flow condition can be expressed by solving the following equation (10):

[0158] in:

[0159] t represents time;

[0160] v represents the blood flow rate in the target object;

[0161] ρ represents the fluid density of the blood in the target object;

[0162] p represents the pressure of the blood in the target object;

[0163] ε represents the porosity;

[0164] μ represents the dynamic viscosity of the blood in the target subject;

[0165] F represents the porous force in the blood within the target object;

[0166] Then, the above equation (10) and the biological heat equation (such as the Pennes model and the Wulff-Klinger (WK) model) can be combined to simulate the part of the heat that may be carried away by the blood flow and obtain the corresponding heat diffusion model.

[0167] In a specific example, in addition to solving the thermal diffusion model through mathematical models and formula equations, a pre-trained neural network of machine learning can also be used to output the thermal diffusion model, and this specification does not limit this.

[0168] In the specific example of step S502, the diffusion heat (the diffusion heat can represent the heat carried away by the blood flow), Q hs As well as biological heat equations (such as the Pennes model and the Wulff-Klinger (WK) model, etc.), the corresponding temperature change model is calculated, so that the ablation heat ultimately obtained at each position point in the target object and the temperature distribution in the target object during the radiofrequency ablation process of the radiofrequency ablation device on the target object can be simulated, and the corresponding temperature cloud map can be output.

[0169] In one example, the thermal bioequation can be the Pennis bioheat equation PBE, and the corresponding equation expression (11) is as follows:

[0170]

[0171] in:

[0172] ρ represents the density of tissue within the target object (e.g., including the lungs);

[0173] c represents the specific heat capacity of tissue in the target object (e.g., including the lungs);

[0174] T represents the temperature at any point; it can be understood as the temperature at any point at time t;

[0175] represents the temperature-dependent thermal conductivity;

[0176] ρ b Indicates the blood density in the target object;

[0177] c b represents the specific heat capacity of the blood in the target subject;

[0178] T b The reference temperature of the blood in the target subject; usually set at 37°C.

[0179] w b is the blood perfusion rate within the target object, taking into account the heat exchange between blood and lymphatic vessels;

[0180] q m and q r It is metabolic heat, which is related to the actual ablation heat calculated based on the diffusion heat and the ablation energy.

[0181] In the above embodiments, the heat diffusion caused by blood flow and the influence of the input cooling medium on the absorption rate of radiofrequency ablation energy are fully considered, so that the constructed temperature change model can accurately reflect the influence of the target object's blood flow on heat and temperature, thereby ensuring the accuracy of the temperature change model.

[0182] In the above embodiment, the expression of the electric potential can be determined by combining equations (7)-(9) and equation (11), so that the corresponding electric potential distribution diagram can be output to provide a reference for the operator.

[0183] In other embodiments, the above-mentioned thermal diffusion model may be ignored, that is, the heat diffusion caused by blood flow may be ignored, and a corresponding temperature change model may be constructed directly based on the absorption rate and the bioheat equation. This can facilitate the rapid construction of the temperature change model and improve the calculation rate, but it will reduce the accuracy of the temperature change model. This specification does not limit this.

[0184] In one implementation, please refer to Figure 6 , the radiofrequency ablation data processing method further includes:

[0185] S601: Acquire an ablation effect simulation model;

[0186] S602: Predicting a current ablation effect of tissue in the target object based on the ablation effect simulation model and the radiofrequency ablation duration;

[0187] The ablation effect simulation model is used to simulate the damage to the tissue in the target object during the radiofrequency ablation process. It can be any information that can describe the damage. Correspondingly, the current ablation effect represents the damage to the tissue in the target object during the radiofrequency ablation process.

[0188] The damage conditions may include, for example, at least one of the following during the ablation process: the number of dead cells, the proportion of dead cells, the number of active cells, the proportion of active cells, the number of cells in an intermediate state (cells that are not completely inactivated), the proportion of cells in an intermediate state, etc.

[0189] In one solution, the processing logic of the ablation effect simulation model can be understood by referring to the following formula:

[0190]

[0191] in:

[0192] A stands for Active, which means active cells;

[0193] D stands for Death, which means dead cells;

[0194] V represents the intermediate state, that is, cells in the intermediate state (cells that are not completely inactivated)

[0195] Furthermore, during radiofrequency ablation, active cells are damaged at a cell damage rate (kf), while cells in an intermediate state may be repaired at a cell repair rate (kb). Over time, cell damage continues, and active cells may transition to an intermediate state. Further damage may cause them to transform from intermediate state cells into dead cells.

[0196] By pre-calibrating kf and kb above, the relationship between the damage situation (e.g., the percentage and number of dead cells, the percentage and number of cells in an intermediate state, and the percentage and number of active cells) and the duration of radiofrequency ablation can be obtained. This relationship can be understood as an ablation effect simulation model. In other examples, the relationship between the damage situation (e.g., the percentage and number of dead cells, the percentage and number of cells in an intermediate state, and the percentage and number of active cells) and the duration of radiofrequency ablation can also be directly defined manually or automatically.

[0197] As can be seen, the ablation effect simulation model can record the relationship between damage status and RF ablation duration. For example, RF ablation duration S1 can correspond to 01% active cells, P1% intermediate cells, and Q1% dead cells, while RF ablation duration S2 can correspond to 02% active cells, P2% intermediate cells, and Q2% dead cells. O1, O2, P1, P2, Q1, and Q2 are arbitrary values ​​within the range of [0, 100]. Furthermore, assuming that O1 is 99, P1 is 1, and Q1 is 0 in the initial state of the ablation effect simulation model, the current ablation effect of the target tissue can be simulated based on this initial state ablation simulation model.

[0198] The predicted current ablation effect can be displayed externally through a display device. For example, the number and proportion of active cells, dead cells, and cells in an intermediate state can be displayed in a graphical manner. For another example, different display units can represent active cells, dead cells, and cells in an intermediate state, and then at least one of the color, number, and size of each display unit can be used to characterize the damage situation (such as the proportion and number of dead cells, the proportion and number of cells in an intermediate state, and the proportion and number of active cells). For another example, on a display device, green can be used to represent active cells, red can be used to represent dead cells, and yellow can be used to represent cells in an intermediate state.

[0199] In the above scheme, by introducing the ablation effect simulation model and predicting the current ablation effect, a reliable and effective basis can be provided for the execution of radiofrequency ablation surgery. On the one hand, during the execution of radiofrequency ablation surgery, the relevant operator can determine the progress or stage of the current radiofrequency ablation surgery based on the ablation effect simulation model, which is conducive to guiding the relevant operator to accurately adjust or continue the radiofrequency ablation surgery; on the other hand, the accuracy of the temperature change model obtained above can be further verified by the ablation simulation model, that is, the ablation simulation model and the temperature change model can constrain each other. Then, even if any of the models in the ablation simulation model and the temperature change model deviates, the relevant operator can discover it in time, avoid misoperation, and significantly improve the reliability and safety of radiofrequency ablation surgery.

[0200] In one implementation, please refer to Figure 7 , the radiofrequency ablation data processing method further includes:

[0201] S701: Acquire any actual radiofrequency ablation position point and any actual cooling position point in the actual ablation set;

[0202] S702: Obtaining a predicted radiofrequency ablation result according to any actual radiofrequency ablation position point and any actual cooling position point;

[0203] S703: Adjusting the personalized physiological parameters of the temperature change model based on the difference information between the actual radiofrequency ablation position point, the actual radiofrequency ablation result corresponding to the actual cooling position point, and the predicted radiofrequency ablation result.

[0204] The actual ablation set includes a mapping relationship between each actual radiofrequency ablation position point, an actual cooling position point, and a corresponding actual radiofrequency ablation result; wherein the actual radiofrequency ablation position point refers to a position in the target object where the corresponding radiofrequency ablation operation has actually been performed, and the actual cooling position point refers to a position in the target object where the cooling medium is actually supplied.

[0205] The actual ablation result represents: the temperature changes at various positions of the target object actually obtained when the radiofrequency ablation operation is performed at the actual radiofrequency ablation position points corresponding to the actual radiofrequency ablation positions in the target object and the actual cooling positions are supplied with cooling medium; for example, it may include a corresponding thermal map, a table formed by temperature data, etc. The actual ablation result may be detected by a temperature detection component provided in the radiofrequency ablation device, or may be detected or calculated by other methods.

[0206] The predicted radiofrequency ablation result is predicted by the temperature change model; further, in an example, the implementation process of step S702 can be similar to Figure 2 In another example, the process of step S204 shown in FIG. Figure 2 The process of step S204 shown predicts the temperature change as the predicted location point ablation result, and then the predicted radiofrequency ablation result is retrieved in step S702.

[0207] The personalized physiological parameters of the temperature change model include at least one of the following:

[0208] thermal conductivity of tissue within the target object;

[0209] tissue density of tissue within the target object;

[0210] tissue heat capacity of tissue within the target object;

[0211] The blood density in the target object

[0212] the specific heat capacity of the blood in the target subject;

[0213] blood perfusion rate in the target object;

[0214] vascular pressure of the target subject;

[0215] the permeability coefficient of the vascular system of the target subject;

[0216] a ratio of vascular surface area to tissue volume of the target subject;

[0217] permeability coefficient of the lymphatic vessels of the target subject;

[0218] osmotic pressure of the vasculature and interstitium of the target subject;

[0219] the ratio of lymphatic vessel surface area to tissue volume of the target subject;

[0220] The lymphatic vessel pressure of the target subject.

[0221] The processing of steps S701 to S703 may occur after any actual ablation, or before or after any prediction of temperature changes in the tissue of the target object during radiofrequency ablation.

[0222] In the above scheme, the above personalized physiological parameters can reflect the characteristics of the physiological structure of the target object. By adjusting the above personalized physiological parameters, the temperature change model can be adjusted so that its prediction results can be more accurately adapted to the target object, thereby accurately reflecting the actual changes that occur when the target object is ablated.

[0223] Please refer to Figure 8 The embodiment of the present invention further provides a radiofrequency ablation data processing device 800, comprising:

[0224] A model acquisition module 801 is used to acquire a three-dimensional anatomical model corresponding to a target object;

[0225] A medium distribution construction module 802 is configured to construct a medium distribution model of the cooling medium within the three-dimensional anatomical model based on the three-dimensional anatomical model and the description information of the cooling medium, wherein the medium distribution model is configured to simulate: after each first position point within the three-dimensional anatomical model is supplied with the cooling medium, the cooling medium concentration distribution corresponding to each position point within the three-dimensional anatomical model;

[0226] The temperature model construction module 803 is configured to construct a temperature change model corresponding to the target object based on the constructed medium distribution model and the acquired specified radiofrequency energy released by the radiofrequency ablation device at a second location point within the three-dimensional anatomical model, wherein the temperature change model is configured to simulate: changes in temperature of tissue within the target object over time; the second location point is associated with one or more first location points;

[0227] The prediction module 804 is configured to predict the temperature change of the tissue in the target object during the radiofrequency ablation process by combining the simulated cooling positions, the positions to be ablated, and the temperature change model preset in the three-dimensional anatomical model.

[0228] Optionally, the medium distribution construction module 802 is specifically configured to:

[0229] The description information of the three-dimensional anatomical model and the cooling medium is processed using a dual-porosity model to determine simulated medium flow rate information of the three-dimensional anatomical model; the simulated medium flow rate information is used to simulate: after the cooling medium is supplied to the first position point, the flow rate distribution of the cooling medium in the three-dimensional anatomical model;

[0230] The medium distribution model is determined based on the simulated medium flow rate information of the three-dimensional anatomical model.

[0231] Optionally, the medium distribution construction module 802 is specifically configured to:

[0232] A convection-diffusion equation of the target object is obtained, and the flow velocity information of the simulated medium is processed based on the convection-diffusion equation to determine the medium distribution model.

[0233] Optionally, the temperature model building module 803 is specifically configured to:

[0234] Calculating the absorption rate of the released radiofrequency energy at each position point on the three-dimensional anatomical model during the radiofrequency ablation process based on the cooling medium concentration distribution simulated by the medium distribution model and the simulated electric field strength generated by the radiofrequency energy within the three-dimensional anatomical model;

[0235] Based on the absorption rate, the temperature change model is constructed.

[0236] Optionally, the temperature model building module 803 is specifically configured to:

[0237] Calculating simulated electrical conductivity information of the three-dimensional anatomical model based on the cooling medium concentration distribution simulated by the medium distribution model; the simulated electrical conductivity information is used to simulate: the electrical conductivity of each position point in the three-dimensional anatomical model after the cooling medium is supplied to the first position point;

[0238] The absorption rate is calculated based on the simulated electrical conductivity information and the simulated electric field strength.

[0239] Optionally, the temperature model building module 803 is specifically configured to:

[0240] Acquiring a simulated blood flow condition of the target object, and determining a corresponding heat diffusion model based on the simulated blood flow condition and the second location point, wherein the heat diffusion model is used to model heat changes caused by the simulated blood flow condition at various locations within the target object during a process of performing radiofrequency ablation within the target object that matches the second location point;

[0241] The temperature change model is constructed based on the calculated absorption rate and the thermal diffusion model.

[0242] Figure 9 The data processing device 900 for radiofrequency ablation in the embodiment shown can refer to Figure 8 The data processing device 800 for radiofrequency ablation in the illustrated embodiment is understood, and repeated details will not be described again here.

[0243] Optional, please refer to Figure 9 The radiofrequency ablation data processing device 900 further includes:

[0244] The effect simulation module 901 is used to obtain an ablation effect simulation model; the ablation effect simulation model is used to simulate the damage of the tissue in the target object during the radiofrequency ablation process;

[0245] The ablation effect prediction module 902 is used to predict the current ablation effect of the tissue in the target object based on the ablation effect simulation model and the radiofrequency ablation duration. The current ablation effect represents the damage of the tissue in the target object during the radiofrequency ablation process.

[0246] Please refer to Figure 10 , provides an electronic device 1000, including:

[0247] Processor 1001; and

[0248] Memory 1002, used to store executable instructions of the processor;

[0249] The processor 1001 is configured to execute the above-mentioned method by executing the executable instructions.

[0250] The processor 1001 can communicate with the memory 1002 via a bus 1003 .

[0251] An embodiment of the present invention further provides a computer-readable storage medium having a computer program stored thereon, which implements the above-mentioned method when executed by a processor.

[0252] Those skilled in the art will appreciate that all or part of the steps in the above-described method embodiments can be implemented using hardware associated with program instructions. The aforementioned program can be stored in a computer-readable storage medium. When executed, the program performs the steps of the above-described method embodiments. The aforementioned storage medium includes various media capable of storing program code, such as ROM, RAM, magnetic disks, or optical disks.

[0253] Finally, it should be noted that the above embodiments are only used to illustrate the technical solutions of the present invention, rather than to limit it. Although the present invention has been described in detail with reference to the above embodiments, those skilled in the art should understand that they can still modify the technical solutions described in the above embodiments, or replace some or all of the technical features therein with equivalents. However, these modifications or replacements do not cause the essence of the corresponding technical solutions to deviate from the scope of the technical solutions of the embodiments of the present invention.

Claims

1. A data processing device for radiofrequency ablation, characterized in that: include: A model acquisition module, configured to acquire a three-dimensional anatomical model corresponding to a target object; a medium distribution construction module, configured to construct a medium distribution model of the cooling medium within the three-dimensional anatomical model based on the three-dimensional anatomical model and the description information of the cooling medium, wherein the medium distribution model is configured to simulate: after each first position point within the three-dimensional anatomical model is supplied with the cooling medium, the cooling medium concentration distribution corresponding to each position point within the three-dimensional anatomical model; a temperature model construction module for constructing a temperature change model corresponding to the target object based on the constructed medium distribution model and the acquired radiofrequency energy released by the radiofrequency ablation device at a second location point within the three-dimensional anatomical model, wherein the temperature change model is used to simulate: changes in the temperature of tissue within the target object over time; the second location point is associated with one or more first location points; wherein the association is reflected in: if the ablation electrode of the radiofrequency ablation device is inserted into the second location point and a radiofrequency ablation operation is performed at the second location point, then by providing a cooling medium at any first location point, the impedance of the target tissue at and around the second location point can be reduced; The prediction module is used to predict the temperature change of the tissue in the target object during the radiofrequency ablation process by combining the simulated cooling position points, the position points to be ablated and the temperature change model preset in the three-dimensional anatomical model.

2. The radiofrequency ablation data processing device according to claim 1, characterized in that: Constructing a medium distribution model of the cooling medium within the three-dimensional anatomical model based on the three-dimensional anatomical model and the description information of the cooling medium includes: The description information of the three-dimensional anatomical model and the cooling medium is processed using a dual-porosity model to determine simulated medium flow rate information of the three-dimensional anatomical model; the simulated medium flow rate information is used to simulate: after the cooling medium is supplied to the first position point, the flow rate distribution of the cooling medium in the three-dimensional anatomical model; The medium distribution model is determined based on the simulated medium flow rate information of the three-dimensional anatomical model.

3. The radiofrequency ablation data processing device according to claim 2, characterized in that: Determining the medium distribution model based on the simulated medium flow rate information of the three-dimensional anatomical model includes: A convection-diffusion equation of the target object is obtained, and the flow velocity information of the simulated medium is processed based on the convection-diffusion equation to determine the medium distribution model.

4. The radiofrequency ablation data processing device according to claim 1, characterized in that: Based on the constructed medium distribution model and the acquired radiofrequency energy released by the radiofrequency ablation device at the second position point within the three-dimensional anatomical model, a temperature change model corresponding to the target object is constructed, including: Calculating the absorption rate of the released radiofrequency energy at each position point on the three-dimensional anatomical model during the radiofrequency ablation process based on the cooling medium concentration distribution simulated by the medium distribution model and the simulated electric field strength generated by the radiofrequency energy within the three-dimensional anatomical model; Based on the absorption rate, the temperature change model is constructed.

5. The radiofrequency ablation data processing device according to claim 4, characterized in that: Calculating the absorption rate of the released radiofrequency energy at each position point on the three-dimensional anatomical model during radiofrequency ablation based on the cooling medium concentration distribution simulated by the medium distribution model and the simulated electric field strength generated by the radiofrequency energy within the three-dimensional anatomical model, including: Calculating simulated electrical conductivity information of the three-dimensional anatomical model based on the cooling medium concentration distribution simulated by the medium distribution model; the simulated electrical conductivity information is used to simulate: the electrical conductivity of each position point in the three-dimensional anatomical model after the cooling medium is supplied to the first position point; The absorption rate is calculated based on the simulated electrical conductivity information and the simulated electric field strength.

6. The radiofrequency ablation data processing device according to claim 4, characterized in that: Based on the absorption rate, constructing the temperature change model includes: Acquiring a simulated blood flow condition of the target object, and determining a corresponding heat diffusion model based on the simulated blood flow condition and the second location point, wherein the heat diffusion model is used to simulate heat changes at various locations within the target object caused by the simulated blood flow condition during a process of performing radiofrequency ablation within the target object that matches the second location point; The temperature change model is constructed based on the calculated absorption rate and the thermal diffusion model.

7. The radiofrequency ablation data processing device according to claim 1, characterized in that: Also includes: An effect simulation module is used to obtain an ablation effect simulation model; the ablation effect simulation model is used to simulate the damage of tissue in the target object during the radiofrequency ablation process; The ablation effect prediction module is used to predict the current ablation effect of the tissue in the target object based on the ablation effect simulation model and the radiofrequency ablation duration, wherein the current ablation effect represents the damage of the tissue in the target object during the radiofrequency ablation process.

8. A radiofrequency ablation system, characterized in that: It comprises a radiofrequency ablation device, a data processing device, and a display device, wherein the data processing device is used to perform the functions of the data processing device according to any one of claims 1 to 7, and the display device is used to display the temperature change predicted by the data processing device.

9. An electronic device, characterized in that: Including processor and memory, The memory is used to store code; The processor is configured to execute the code in the memory to implement the functions of the data processing device according to any one of claims 1 to 7.

10. A storage medium storing a computer program, wherein when the program is executed by a processor, the function of the data processing device according to any one of claims 1 to 7 is realized.

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