Data processing method and device, electronic equipment and storage medium

Abstract

Embodiments of the present application provide a data processing method and device, electronic equipment and storage medium, and relate to the technical field of computer. The method comprises: obtaining a simulation model of a diseased organ and applying a preset voltage for a preset time length; determining the electric field intensity and the conductivity at each time and performing at least one iteration operation until the conductivity of the point position converges; and obtaining the conductivity of each point position. When determining the conductivity of the point position in the organ at each time, the maximum value in each electric field intensity at the historical time is used to calculate the conductivity, and the conductivity is used to calculate the electric field intensity of the point position at each time, so that the irreversibility of the conductivity of the human organ is considered in the process of determining the conductivity, and the calculation of the conductivity is more accurate, and the accuracy of the simulation process is improved.

Description

Technical Field

[0001] This application relates to the field of computer technology, and more specifically, to a data processing method, apparatus, electronic device, and storage medium. Background Technology

[0002] Irreversible electroporation tumor ablation, as a tumor ablation method, has the advantages of being minimally invasive, having little impact on blood flow, and having a large ablation range. Before it is formally applied to the human body, it is often necessary to evaluate its tumor ablation effect through simulation and then determine the specific ablation plan based on the simulation results.

[0003] Traditional simulation ablation schemes use the conductivity function under the H model (i.e., a model built based on the Heaviside step function). This model describes the actual conductivity change in an abrupt manner, using the Heaviside step function for mathematical description in the change region. However, this function is relatively regular and symmetrical, and does not take into account the actual change law of conductivity of human organs in the electric field during actual operation. It has a certain gap with experimental data, and the fitting results are too ideal, which leads to the inaccuracy of the simulation effect. Summary of the Invention

[0004] The purpose of this application is to at least solve one of the aforementioned technical defects. The technical solution provided by the embodiments of this application is as follows: In a first aspect, embodiments of this application provide a data processing method, including: Obtain a simulation model of the diseased organ, the initial conductivity of the diseased organ, and the breakdown conductivity of the organ when it is electrically broken down. A voltage is applied to the simulation model for a preset duration; wherein the voltage value at each moment within the preset duration changes with time. For each point on the simulation model, at each time moment, the maximum value of the first electric field intensity at each historical time moment is obtained. Based on the maximum value, the voltage value at the time moment, the initial conductivity, and the breakdown conductivity, the second electric field intensity and the second conductivity at the time moment are determined; where the maximum value at the initial time moment is zero. For each point in the simulation model, at each time step, perform at least one iteration operation on the second conductivity and second electric field strength of the point at time step until the conductivity of the point converges. For each point on the simulation model, at each time step, the second conductivity obtained from the last iteration at time step is taken as the first conductivity of the point at time step, and the second electric field intensity obtained from the last iteration is taken as the first electric field intensity at time step.

[0005] Secondly, embodiments of this application provide a data processing apparatus, including: The simulation model acquisition module is used to acquire the simulation model of the diseased organ, the initial conductivity of the diseased organ, and the breakdown conductivity of the organ when it is electrically broken down. The voltage addition module is used to apply a voltage to the simulation model for a preset duration; wherein the voltage value at each moment within the preset duration changes with time. The electric field data calculation module is used to obtain the maximum value of the first electric field intensity at each point on the simulation model at each time. Based on the maximum value, the voltage value at the time, the initial conductivity, and the breakdown conductivity, the second electric field intensity and the second conductivity at the time are determined. The maximum value at the initial time is zero. The electric field data iteration module is used to perform at least one iteration operation on the second conductivity and second electric field strength of each point on the simulation model at each time, until the conductivity of the point converges. The electric field data recording module is used to, for each point on the simulation model, at each time step, take the second conductivity obtained from the last iteration at time step as the first conductivity of the point at time step, and take the second electric field intensity obtained from the last iteration as the first electric field intensity at time step.

[0006] Thirdly, embodiments of this application provide an electronic device, including a memory, a processor, and a computer program stored in the memory; The processor executes a computer program to implement the method provided in the first aspect embodiment or any alternative embodiment of the first aspect.

[0007] Fourthly, embodiments of this application provide a computer-readable storage medium storing a computer program, which, when executed by a processor, implements the method provided in the first aspect embodiment or any optional embodiment of the first aspect.

[0008] The beneficial effects of the technical solutions provided in this application are: The solution provided in this application firstly involves constructing a simulation model of the diseased organ and obtaining its initial conductivity and breakdown conductivity to simulate the diseased organ, thereby achieving a simulation of the real diseased organ. Secondly, by applying voltage to the simulation model, each point in the diseased organ is subjected to electric shock. When calculating the first conductivity of each point at each moment, the maximum value of the first electric field strength in each historical moment before that moment is obtained. Then, the second conductivity at that moment is calculated using this maximum value. This process takes into account the irreversible conductivity of human organs in the process of determining conductivity, thereby making the conductivity calculation more accurate and improving the accuracy of the simulation process. Finally, by modifying the second conductivity, the second electric field intensity at that point at that moment is further calculated, and the second electric field intensity and the second conductivity are iterated multiple times until convergence, so as to obtain the first electric field intensity and the first conductivity at that moment, making the data more accurate and providing a solid data foundation for subsequent simulation analysis. Attached Figure Description

[0009] To more clearly illustrate the technical solutions in the embodiments of this application, the accompanying drawings used in the description of the embodiments of this application will be briefly introduced below.

[0010] Figure 1 A flowchart illustrating a data processing method provided in an embodiment of this application; Figure 2 This is a flowchart illustrating the overall process of a data processing method in one example of an embodiment of this application. Figure 3 This is a schematic diagram of the unit structure of a data processing method in one example of an embodiment of this application; Figure 4 A structural block diagram of a data processing apparatus provided in an embodiment of this application; Figure 5 This is a schematic diagram of the structure of an electronic device provided in an embodiment of this application. Detailed Implementation

[0011] The embodiments of this application are described below with reference to the accompanying drawings. It should be understood that the embodiments described below with reference to the accompanying drawings are exemplary descriptions for explaining the technical solutions of the embodiments of this application, and do not constitute a limitation on the technical solutions of the embodiments of this application.

[0012] Those skilled in the art will understand that, unless specifically stated otherwise, the singular forms “a,” “an,” “the,” and “the” used herein may also include the plural forms. It should be further understood that the terms “comprising” and “including” as used in embodiments of this application mean that the corresponding feature can be implemented as the presented feature, information, data, step, operation, element, and / or component, but do not exclude implementation as other features, information, data, step, operation, element, component, and / or combinations thereof supported by the art. It should be understood that when we say that an element is “connected” or “coupled” to another element, the one element can be directly connected or coupled to the other element, or it can mean that the one element and the other element establish a connection relationship through an intermediate element. Furthermore, “connected” or “coupled” as used herein can include wireless connection or wireless coupling. The term “and / or” as used herein indicates at least one of the items defined by the term; for example, “A and / or B” can be implemented as “A,” or as “B,” or as “A and B.”

[0013] To make the objectives, technical solutions, and advantages of this application clearer, the embodiments of this application will be described in further detail below with reference to the accompanying drawings.

[0014] The technical solutions of this application and their effects are described below through several exemplary embodiments. It should be noted that the following embodiments can be referenced, borrowed from, or combined with each other. Identical terms, similar features, and similar implementation steps in different embodiments will not be repeated.

[0015] Figure 1 This application provides a flowchart illustrating a data processing method. The execution subject of this method can be a terminal (e.g., a computer, mobile phone, etc.) or an intelligent agent, such as... Figure 1 As shown, the method may include: Step S101: Obtain the simulation model of the diseased organ, the initial conductivity of the diseased organ, and the breakdown conductivity of the organ when it is electrically broken down.

[0016] In the embodiments of this application, the diseased organ can refer to a human organ suffering from a tumor. The simulation model of the diseased organ can be a three-dimensional geometric model with the exact same shape as the diseased organ, drawn based on the CT scan results of the patient. In this simulation model, the normal tissue portion and the tumor tissue portion of the diseased organ can be labeled in different ways (such as different colors). The initial conductivity can be the conductivity of the diseased organ without receiving any electric field stimulation. The breakdown conductivity can be the conductivity when the organ breaks down after receiving an electric field of a certain intensity. Optionally, both the initial conductivity and the breakdown conductivity can be obtained in advance by inspection or reference.

[0017] Specifically, in order to achieve a simulated ablation process of the diseased organ, it is first necessary to obtain a simulation model of the diseased organ. In order to ensure that the simulation ablation effect is more accurate, it is necessary to ensure that the constructed simulation model is completely consistent with the actual diseased organ of the patient. Therefore, a CT scan of the patient's diseased organ can be performed first, and then a simulation model with the exact same shape as the diseased organ can be constructed based on the CT scan results. At the same time, the initial conductivity and breakdown conductivity of the diseased organ can be obtained. The method of obtaining the conductivity can be to directly check the relevant conductivity of others in the historical records (because the initial conductivity and breakdown conductivity of most people are almost the same), or it can be to sample and measure the diseased organ of the patient.

[0018] Step S102: Apply a voltage for a preset duration to the simulation model; wherein the voltage value at each moment within the preset duration changes with time.

[0019] Specifically, the preset duration in this embodiment can be set by setting the simulation start time and simulation end time respectively. The simulation of dynamic voltage (i.e., voltage value changing over time) can be achieved by inputting a preset voltage-time correlation function. The method of applying voltage to the simulation model can be to construct a needle body model including multiple electrode needles, then add the needle body model to the simulation model, so as to set a certain number of electrode needles at multiple positions in the simulation model, and then apply voltage to the multiple electrode needles.

[0020] Step S103: For each point on the simulation model, at each time moment, obtain the maximum value of the first electric field intensity at each historical time moment. Based on the maximum value, the voltage value at the time moment, the initial conductivity, and the breakdown conductivity, determine the second electric field intensity and the second conductivity at the time moment; wherein, the maximum value at the initial time moment is zero.

[0021] Because the conductivity of human organs and tissues follows the objective law of irreversibility during irreversible electroporation ablation, when calculating the second conductivity at each point at the current moment, it is necessary to obtain the maximum value of the first electric field intensity at each historical moment, and then use this maximum value, the initial conductivity, and the breakdown conductivity to calculate the second conductivity at the current moment. Then, the second electric field intensity at the current moment is calculated using the second conductivity and the voltage value at the current moment.

[0022] It should be noted that in actual operation, the irreversibility of the conductivity of human organs will also be reflected in the conductivity. In other words, during the ablation simulation, the dynamic conductivity of the human body is also irreversible.

[0023] Step S104: For each point on the simulation model, at each time step, perform at least one iteration operation on the second conductivity and second electric field strength of the point at that time, until the conductivity of the point converges. In the embodiments of this application, the simulation model can first be divided into several multi-scale grids, and then the grid vertices can be selected as the calculation points of the simulation model. The first electric field strength can be the electric field strength of each point at each time step that is finally recorded. The second electric field strength can be the electric field strength of each point at each time step that is calculated before the final recording. The first conductivity can be the conductivity of each point at each time step that is finally recorded. The second conductivity can also be the conductivity of each point at each time step that is calculated before the final recording.

[0024] Specifically, since the principle of irreversible electroporation ablation involves applying a high-intensity electric field pulse to tumor tissue to perforate the cell membranes of tumor cells until the membrane pores become irreversible, thereby inducing apoptosis, and the condition for destroying tissue at a certain point in the diseased organ is that the electric field strength at that point exceeds a preset threshold, the ablation range of electromagnetic ablation can only be determined after determining the electric field strength at each point. Therefore, in this embodiment, the first electric field strength at each point at each moment is calculated and recorded. During the calculation of the first electric field strength, since the calculated second electric field strength may have deviations each time, multiple iterative calculations are required until the final calculated conductivity converges, at which point the calculation of the second electric field strength can be considered to have reached a relatively accurate level.

[0025] Step S105: For each point on the simulation model, at each time step, the second conductivity obtained from the last iteration at time step is taken as the first conductivity of the point at time step, and the second electric field intensity obtained from the last iteration is taken as the first electric field intensity at time step.

[0026] Specifically, after iterating the second conductivity to convergence through the above process, the iterated second conductivity and second electric field intensity can be recorded as the first conductivity and first electric field intensity at the current moment, respectively.

[0027] Optionally, in this embodiment of the application, the first electric field strength can be recorded using a pre-set distributed ordinary differential equation, the specific equation of which is as follows:

[0028] Wherein, the quality coefficient e a =0, damping or mass coefficient is d a =1, the source term f=k on the right-hand side of the equation up flc2hs(Em,epsE) (Em), where E is the second electric field strength, m is a memory variable introduced (used to record the first electric field strength), and k up The parameter is a user-defined parameter that represents the time it takes for m to approach E. flc2hs(Em, epsE) is a gating term that controls m to increase monotonically without regressing. epsE is a user-defined parameter that represents half of the transition region.

[0029] The solution provided in this application firstly involves constructing a simulation model of the diseased organ and obtaining its initial conductivity and breakdown conductivity to simulate the diseased organ, thereby achieving a simulation of the real diseased organ. Secondly, by applying voltage to the simulation model, each point in the diseased organ is subjected to electric shock. When calculating the first conductivity of each point at each moment, the maximum value of the first electric field strength in each historical moment before that moment is obtained. Then, the second conductivity at that moment is calculated using this maximum value. This process takes into account the irreversible conductivity of human organs in the process of determining conductivity, thereby making the conductivity calculation more accurate and improving the accuracy of the simulation process. Finally, by modifying the second conductivity, the second electric field intensity at that point at that moment is further calculated, and the second electric field intensity and the second conductivity are iterated multiple times until convergence, so as to obtain the first electric field intensity and the first conductivity at that moment, making the data more accurate and providing a solid data foundation for subsequent simulation analysis.

[0030] Based on the above embodiments, as an optional embodiment, the second electric field strength and the second conductivity at a given time are determined based on the maximum value, the voltage value at that time, the initial conductivity, and the breakdown conductivity. Specifically, this includes: The second conductivity at a given time is determined based on the breakdown conductivity, initial conductivity, and maximum conductivity. Based on the second conductivity, the voltage value at time, and the preset boundary set, the second electric field strength at time is determined. The boundary condition set includes the range of values ​​for current, potential, and structural electrical insulation.

[0031] Specifically, in this embodiment, the second conductivity is calculated using the Gompertz model (G model for short). The tissue conductivity function of this model can characterize the dynamic change of conductivity of the tumor tissue region in the diseased organ with the electric field strength. The specific formula is as follows:

[0032] Where σ(M) is the dynamic conductivity (i.e., the second conductivity) with the introduction of the variable M. σ0 is the initial conductivity; σ max The maximum electrical conductivity (i.e., breakdown conductivity) that the diseased organ tissue can achieve after electroporation is denoted as M. A and B are the coefficients of the displacement and growth rate of the S-curve, respectively (i.e., constant terms, which can be set according to requirements). M is the maximum value of the first electric field intensity at each historical moment.

[0033] Because cellular conductivity parameters have irreversible characteristics—that is, tissue conductivity only increases with increasing electric field and remains at its maximum value achievable during electric field changes—traditional ablation simulations do not consider the irreversible nature of tissue conductivity during treatment and only use… Assigning a value to tissue conductivity can lead to a decrease in conductivity as the electric field decreases with the pulse voltage, which contradicts actual physical effects. Over multiple pulses, the accumulated error can cause inaccuracies at the boundary of the final effective ablation area, reducing the accuracy of simulation results. Therefore, the solution provided in this application introduces a variable M to record the maximum value of the first electric field intensity at each historical point. This maximum value can be used to calculate conductivity, effectively reducing the errors caused by the aforementioned reasons.

[0034] For the calculation of the second electric field strength, since the potential gradient and conductivity are inversely proportional within organs and tissues, the relationship between the potential gradient and conductivity can be expressed by the following Laplace equation: ▽(σ▽φ)=0 Where ▽ is the difference operator, σ is the second conductivity of the point at the current time, the second conductivity and the second electric field strength affect each other, φ represents the electric potential, and the electric potential can be determined according to the voltage value applied at the corresponding time.

[0035] The above formula indicates that the divergence of the current density is zero under passive steady-state conditions. Furthermore, it is necessary to first obtain the potential distribution by solving the Laplace equation based on a pre-defined boundary set, and then calculate the potential difference φ between the point and the electrode needle.

[0036] The second electric field strength can be calculated using the following formula: E=-▽φ Where E is the magnitude of the second electric field strength.

[0037] Based on the above embodiments, as an optional embodiment, for each point on the simulation model, at each time step, at least one iteration operation is performed on the second conductivity and second electric field strength of the point at time step, specifically including: For each iteration, the third conductivity of the point at the given time is determined based on the initial conductivity, the breakdown conductivity, and the third electric field strength of the point in the previous iteration; wherein the third electric field strength of the first iteration is the second electric field strength. Based on the third conductivity and the boundary set, the third electric field intensity at the point at time t is determined; Arrange the third conductivity and the second conductivity in the order of the iteration rounds to obtain the conductivity sequence; A convergence analysis is performed on the conductivity sequence. If the conductivity sequence converges, the conductivity at the determined point has converged; if the conductivity sequence does not converge, the conductivity at the determined point has not converged.

[0038] In the embodiments of this application, after the second electric field strength and the second conductivity are initially calculated, in order to further verify whether the second electric field strength and the second conductivity calculated in this instance are accurate, it is necessary to recalculate iteratively based on the second electric field strength and the second conductivity calculated in this instance. Specifically, firstly, the second electric field strength calculated in this instance is substituted into the tissue conductivity function formula mentioned above (taking the second electric field strength as M in the formula) to calculate the third conductivity for the first iteration. Then, the third conductivity and the boundary set are substituted into the Laplace equation mentioned above (taking the third conductivity as σ in the equation) and the electric field strength calculation formula to calculate the third electric field strength for the first iteration.

[0039] Then, the second iteration begins. The second iteration first substitutes the third electric field strength from the previous iteration into the tissue conductivity function formula mentioned above (taking the third electric field strength as M in the formula) to calculate the third conductivity of this iteration. Then, the third conductivity and the boundary set are substituted into the Laplace equation mentioned above (taking the third conductivity as σ in the equation) and the electric field strength calculation formula to calculate the third electric field strength of this iteration.

[0040] Starting from the second iteration, after each iteration's calculation is completed, the conductivity values ​​are arranged in the order of calculation (first is the second conductivity value obtained from the first iteration, second is the third conductivity value obtained from the first iteration, then the third conductivity value obtained from the second iteration, and so on) to obtain the conductivity sequence for that point at that moment. A convergence analysis is then performed on this conductivity sequence. If the conductivity sequence is determined to be convergent, it can be considered that the calculation error of the conductivity is within an acceptable range, and the iteration process stops. If the conductivity sequence is determined to be non-convergent, it can be considered that the calculation error of the conductivity is still too large, and a new iteration process begins.

[0041] Optionally, the convergence judgment method used in the embodiments of this application may be the Cauchy convergence criterion, the four arithmetic rules, the Stoltz theorem, etc. The embodiments of this application do not limit the specific convergence judgment method used.

[0042] Based on the above embodiments, as an optional embodiment, the method further includes: For each point on the simulation model, at each time step, the electromagnetic heat at that point is determined based on the first conductivity and the first electric field strength at that time step, and the temperature at that point is determined based on the electromagnetic heat.

[0043] In embodiments of this application, electromagnetic heat can be the heat generated at various points in the simulated diseased organ due to the application of voltage to the simulation model.

[0044] Specifically, methods that can damage the tissue of diseased organs include not only electrical breakdown but also methods that destroy cell structures through high temperatures. Therefore, in determining the final simulation effect, this application's embodiments must consider not only the ablation range formed by electrical breakdown itself but also the ablation range formed by the temperature rise caused by electromagnetic radiation, leading to cell structure destruction. To determine this ablation range caused by high temperatures, it is necessary to first calculate the electromagnetic heat generated at each point. The specific calculation method for the electromagnetic heat generated at each point at each time can be determined according to Ohm's heat formula: Q=σE 2 Where Q represents electromagnetic heat, σ represents the first conductivity of the point at that time, and E represents the first electric field strength of the point at that time.

[0045] After obtaining the electromagnetic heat at each point at a certain moment, the temperature at that point at that moment can be further calculated. The specific calculation formula is as follows: ρC p T / t = (k T) + ρ b C p , b ω b ( T a T )+ Q m + Q in, ρ This indicates the tissue density of the diseased organ. C p This indicates the specific heat capacity of the diseased organ or tissue. k This indicates the thermal conductivity of the diseased organ or tissue. ρ b This indicates the patient's blood density. C p , b This indicates the specific heat capacity of the patient's blood. ω b This indicates the blood perfusion rate (usually expressed as "1 / s"). T a This indicates the temperature of arterial blood (usually 37°C). TThat is, the temperature of the point to be solved at that moment. Q m "Bioheat source" usually refers to metabolic heat. "Q" represents other heat sources, which in this embodiment refers to electromagnetic heat.

[0046] Based on the above embodiments, as an optional embodiment, the method further includes the step of determining the electroporation damage region of the simulation model: Obtain the maximum value of the first electric field intensity at each point within a preset time period; The closed surface formed by the points where the maximum value of the first electric field intensity is equal to the first preset threshold is taken as the electroporation damage area.

[0047] In the embodiments of this application, the first preset threshold is used to characterize the electric field strength when the diseased organ tissue is electrically broken down.

[0048] It is understandable that if the organ tissue at a given point does not break down under the maximum electric field strength when the first electric field strength reaches its maximum value, then the organ tissue at that point will naturally not break down at other times either. Therefore, it is only necessary to use this maximum value to determine whether the organ tissue at that point has broken down. Optionally, since the distribution data of the first electric field strength at all times can be obtained after the simulation, the first electric field strength corresponding to different times can also be selected according to the actual voltage changes. For example, the first electric field strength corresponding to the maximum voltage in the last pulse train can be used for judgment.

[0049] Then, connecting the points where the maximum first electric field strength equals the first preset threshold yields a closed surface (also called an equipotential surface). Since the points inside the closed surface are closer to the electrode needle than the points involved in the connection, the maximum first electric field strength at these points inside the closed surface will naturally be higher than the first preset threshold. Therefore, these points inside the closed surface will also be electrically broken down. Thus, the interior of this closed surface constitutes the ablation region (i.e., the electroporation damage region) formed by electrical breakdown.

[0050] Based on the above embodiments, as an optional embodiment, the method further includes the step of determining the thermal damage region of the simulation model: For each point, based on the temperature of the point at each time moment, a function is constructed to show the temperature change of the point over a preset time period. For each point, the degree of thermal loss at the point is evaluated based on a function to obtain the probability of thermal damage at the point; The closed surface formed by each point whose thermal damage probability is equal to the second preset threshold is taken as the thermal damage region.

[0051] In embodiments of this application, the thermal damage probability is used to characterize the probability that the site will be damaged due to a temperature increase caused by electromagnetic heat.

[0052] Specifically, as mentioned above, in addition to considering the ablation region formed by electrical breakdown, this embodiment also needs to consider the ablation region formed by temperature rise. This ablation region can be determined by calculating the thermal damage probability P, which characterizes the destruction of tissue cell structure at each point. Generally, when the thermal damage probability P exceeds 99% (i.e., the second preset threshold), it can be determined that the tissue cell structure at that point has been destroyed. Therefore, the points with a thermal damage probability of 99% can be connected to form a new closed surface. Similar to the electrical breakdown principle described above, the points inside the closed surface are closer to the electrode needle, so the probability of tissue cell structure destruction at these points will naturally be greater than 99%. Through this method, the ablation region (i.e., the thermal damage region) formed by high temperature can be determined.

[0053] Regarding the probability of thermal damage at each point, this embodiment of the application can use the Arrhenius first-order kinetic model for evaluation and calculation. The specific evaluation and calculation function can be the dimensionless thermal damage function of the tissue.

[0054] Where Ω(t) represents the degree of thermal damage, T(t) is a function of the temperature at the site changing with time, and E a R is the activation energy, and R is the gas constant.

[0055] After obtaining Ω(t), it is further quantified into the thermal damage probability P: P=1-exp(Ω(t)) Based on the above embodiments, as an optional embodiment, the method further includes: The area covered by the combined electroporation and thermal damage areas is used as the final ablation area of ​​the simulation model; If the boundary of the final ablation area coincides with the boundary of the tumor area in the simulation model, it is determined that the final ablation area does not completely cover the tumor tissue. If the boundary of the final ablation area does not coincide with the boundary of the tumor area in the simulation model, then the final ablation area is determined to completely cover the tumor tissue.

[0056] Specifically, traditional treatment effects are only roughly judged based on the relationship between the cloud map and the tumor envelope. This method is difficult to apply to complex tumor shapes and is prone to misjudgment. Therefore, the solution provided in this application, after determining the electroporation area and the thermal damage area, determines the area covered by both areas as the final ablation area of ​​the simulation model, since the organs and tissues corresponding to each point in these two areas have been destroyed.

[0057] After determining the final ablation area, it is necessary to further verify whether the final ablation area in this simulation can completely cover the tumor tissue of the diseased organ. A specific method for determining this is to check whether the boundary of the final ablation area and the boundary of the tumor tissue overlap (the model boundary data and ablation range data from each cross-section can be exported and processed to check for intersections). Understandably, if the two boundaries do not intersect, it means that the tumor tissue is completely within the final ablation area, indicating that the final ablation area completely covers the tumor tissue, and this can be used as the final ablation scheme. Conversely, if the ablation area does not completely cover the tumor tissue, it indicates that the final ablation area did not completely cover the tumor tissue. In this case, the extreme value of the distance between the two boundaries can be calculated (for example, on a certain cut surface of a closed surface, by traversing each point on the tissue boundary, calculating the distance between each point and the final ablation range boundary, recording the minimum value of the distance calculation results on the tissue boundary and integrating it into a new set A, and using the minimum and maximum values ​​in set A as data support for judging the ablation treatment effect on this cut surface) to provide more detailed and intuitive data support for the ablation treatment results. Based on the incompletely covered part, the relevant parameters of each electrode needle (such as coordinate position, number, etc.) and the applied voltage can be adjusted to formulate a new simulation scheme to re-simulate the ablation effect.

[0058] By processing the simulation results, numerical results of the multi-section ablation range and tumor range under the current treatment plan can be given, which can greatly improve the accuracy of the treatment effect assessment.

[0059] The following is combined with Figure 2 The process of organizing the data processing method provided in the embodiments of this application will be described, such as... Figure 2 As shown, the data processing method provided in this application embodiment can be divided into the following steps: Step S1: Identify the organ that has developed the disease and construct an organ simulation model of that organ in the Comsol simulation software.

[0060] Step S2: Obtain the initial conductivity of the organ when no voltage is applied (this initial conductivity can be obtained directly from the data of most patients) and the breakdown conductivity when it is electrically broken down, and add dynamic voltage (i.e., voltage changes with time, and this change can be represented by a function that changes with time) to the organ simulation model. Step S3: Next, the conductivity and electric field strength at each point on the organ simulation model at each time step are determined: For each moment, through Determine the first conductivity at each point at this moment (M is the first electric field intensity recorded at each point at the previous moment, σ max The breakdown conductivity of the organ is represented by σ0, where σ0 represents the initial conductivity of the organ before an applied voltage is applied; then the first conductivity is substituted into ( (σ φ)=0, E=- φ) to determine the first electric field intensity at each point at that moment (where φ refers to the electric potential, which can be determined by the gradient value of the voltage at that moment); Step S3.1: In the above process, the determination of the first conductivity and the first electric field strength at each point at each time moment will be obtained through multiple iterations. Specifically, in the first iteration, the maximum value of the first electric field strength at each historical time moment is used as the introduced variable M (if it is the initial time moment, the first electric field strength is defaulted to 0) and substituted into the input. The second conductivity at the current moment is determined, and then this second conductivity is substituted into ( (σ φ)=0, E=- φ) to determine the second electric field intensity at that point; starting from the second iteration, in each iteration, the second electric field intensity obtained in the previous iteration is first substituted into φ. The new second conductivity is determined in the middle, and then the new second conductivity is substituted into ( (σ φ)=0, E=- φ) to determine the new second electric field strength; Step S3.2: After each iteration, determine whether the second conductivity values ​​obtained from all iterations converge numerically. If they converge, stop the iteration process and take the second conductivity value obtained in the last iteration as the first conductivity value at that point at that moment.

[0061] Step S3.3: After determining the second conductivity and the second electric field strength in the last iteration, record the second conductivity and the second electric field strength obtained in the last iteration as the first conductivity and the first electric field strength at that point at that time, respectively.

[0062] Step S4 involves evaluating the tissue thermal damage transformation process caused by temperature increases during tissue electroporation ablation using an Arrhenius first-order kinetic model. Specifically, this is achieved through... As a dimensionless thermal damage function of the organization.

[0063] Step S5: Considering the electromagnetic thermal effect brought about by electromagnetic-thermal multi-physics coupling, first determine the electromagnetic heat Q generated at each point at each time based on the first conductivity and the first electric field strength at each point at each time, and then determine the temperature at each point at each time by combining the various properties of the organ.

[0064] Step S6: Determine the final ablation region for this simulation. The final ablation region consists of two parts: electroporation damage and thermal damage. The determination of electroporation damage is based on whether the first electric field strength exceeds the preset electric field strength threshold (i.e., the first preset threshold). Use the equipotential surface function to connect points in the tissue whose potential is equal to the preset value. The volume enclosed by the closed surface formed by the connection is the first ablation region caused by electroporation in this simulation. The determination of thermal damage is based on the following: the cell death probability P is the probability of thermal damage to normal tissue cells in the organ, P=1-exp(Ω(t)). When the thermal damage probability value P at a certain point is greater than 0.99, it can be regarded as irreversible thermal damage. Similarly, draw the equipotential surface in the tissue where P equals 0.99. The volume enclosed by this closed surface is the second ablation region caused by thermal damage. Take the union of the two ablation regions as the final ablation region for accurate analysis of the effectiveness of the ablation.

[0065] Multiple cross-sections are selected to compare the final ablation area with the tumor tissue in the organ. The model boundary data and ablation area data of each cross-section are exported and processed again to check for intersections. If there are intersections, it means that the ablation has not completely covered the area, and the relevant parameters of each electrode needle need to be further adjusted. If there are no intersections on all selected cross-sections, it means that the ablation has completely covered the area, and this can be used as the final ablation plan, thus achieving a precise judgment on the tumor treatment effect.

[0066] like Figure 3 As shown, the data processing method provided in this application embodiment can also be implemented by multiple configurable independent units, specifically including: I. Geometric Model Setting Unit: This unit imports the diseased organ and its geometric simulation model. Based on the number of electrode needles, needle spacing, and spatial arrangement of the ablation product used, a three-dimensional geometric simulation model of irreversible electroporation ablation of the tumor is established in the simulation software based on the geometric information.

[0067] II. Mathematics Module Setting Unit: This unit is used for calculating the conductivity at various spatial locations within the computational domain in time-domain analysis. By setting the domain-distributed ordinary differential equation and adjusting the values ​​of multiple parameters in the custom formula, it ensures a high degree of fit between the calculated variable m and the actual electric field value. This guarantees the accuracy of the calculation results while realizing the irreversible characteristic of material properties that permanently change after biological tissue reaches a certain threshold, as described in the dynamic conductivity theory.

[0068] III. Multiphysics Coupled Simulation Setting Unit: This unit is used to determine the tissue material parameters and boundary conditions of the three-dimensional geometric simulation model. Based on the tissue material parameters and boundary conditions, a multiphysics tumor ablation simulation model is constructed. The effective ablation range distribution data of the diseased organ tissue during irreversible electroporation tumor ablation surgery is determined through simulation of the simulation model.

[0069] IV. Ablation Protocol Effectiveness Judgment and Adjustment Unit: This unit is used to judge the effectiveness of ablation treatment. By exporting and reprocessing data from multiple sections within the computational domain, it obtains the intersection of the tumor boundary and the ablation treatment boundary on each section, as well as the extreme value of the distance between the two boundaries. The effectiveness of the ablation treatment protocol is judged through intuitive numerical results. If the boundary of the ablation treatment does not meet expectations, the parameter settings in the preset treatment protocol can be adjusted accordingly and recalculated until the comparison result of the selected ablation treatment effect and the treatment target meets expectations. The adjusted ablation treatment protocol is then determined as the final ablation treatment protocol.

[0070] Unit 1 is characterized in that the parameters used for setting the geometric simulation model can optionally include: diseased organ, diseased organ simulation model, electrode needle size, needle insertion angle, needle insertion depth, needle body spacing, and needle body spatial arrangement.

[0071] The second unit is characterized by setting up a distributed ordinary differential equation for the computational domain and introducing a variable m to record the historical maximum electric field intensity at each point at each time.

[0072] Unit 3 is characterized in that, 1. The determination of the tissue material parameters of the three-dimensional geometric simulation model in the multi-physics coupling modeling unit includes: setting the tissue type of the tumor region and target region in the diseased organ tissue, as well as the material type of the conductive part and insulating part of the electrode needle, and setting the conductivity, relative permittivity, thermal conductivity, constant pressure heat capacity, and density of each tissue type and material.

[0073] 2. The boundary conditions in the multiphysics coupling modeling unit include electrode needle potential boundaries, current boundaries, tissue electrical insulation boundaries, temperature boundaries, and thermal damage boundaries. The electrode needle potential boundary is used to determine the electrode potential on the surface of the electrode needle; the tissue electrical insulation boundary is used to determine the insulation state of the outer boundary of the diseased organ tissue; the current boundary is used to determine the potential inside the target tissue; the temperature boundary is used to determine the temperature of the outer boundary of the tissue under the coupling of electro-thermal-biological multi-physical fields; and the thermal damage boundary is used to determine the thermal damage state inside the diseased organ tissue under the coupling of electro-thermal-biological multi-physical fields.

[0074] 3. Setting the conductivity of tissue types in the tumor region of the diseased organ includes: characterizing the dynamic change of the conductivity of the tumor region with the electric field intensity using the tissue conductivity function of the Gompertz model.

[0075] 4. Methods for determining the boundary of internal thermal damage include: The thermal damage transformation process of tissue induced by temperature rise during electroporation ablation was evaluated using an Arrhenius first-order kinetic model. A dimensionless thermal damage function was used, and the calculation results were compared with a set threshold to determine the degree of thermal damage.

[0076] Unit 4 is characterized by performing multi-sectional analysis on the spatial location of the tumor based on the ablation treatment results of irreversible electroporation under multi-physics coupling, which has been simulated and calculated. Using the coordinates of each point on the tumor tissue boundary and the coordinates of each point on the electrical injury threshold contour line in the two-dimensional plane of each section as a basis, the above data is exported and processed in a secondary manner to determine the intersection of the maximum ablation boundary and the tumor tissue boundary in each section under the current ablation treatment plan. If there is an intersection, it means that the ablation area does not completely cover the tumor area and the treatment plan needs to be adjusted. If there is no intersection, the extreme value of the distance between the two boundaries is calculated to provide more detailed and intuitive data support for the treatment results.

[0077] Figure 4 A structural block diagram of a data processing apparatus provided in an embodiment of this application is shown below. Figure 4 As shown, the data processing device 400 may include: a simulation model acquisition module 401, a voltage addition module 402, an electric field data calculation module 403, an electric field data iteration module 404, and an electric field data recording module 405, wherein, The simulation model acquisition module 401 is used to acquire the simulation model of the diseased organ, the initial conductivity of the diseased organ, and the breakdown conductivity of the organ when it is electrically broken down. The voltage application module 402 is used to apply a voltage to the simulation model for a preset duration; wherein the voltage value at each moment within the preset duration changes with time; The electric field data calculation module 403 is used to obtain the maximum value of the first electric field intensity at each point on the simulation model at each time. Based on the maximum value, the voltage value at the time, the initial conductivity, and the breakdown conductivity, the second electric field intensity and the second conductivity at the time are determined. The maximum value at the initial time is zero. The electric field data iteration module 404 is used to perform at least one iteration operation on the second conductivity and second electric field strength of the point at each time step for each point on the simulation model, until the conductivity of the point converges. The electric field data recording module 405 is used to, for each point on the simulation model, at each time moment, take the second conductivity obtained from the last iteration at time moment as the first conductivity of the point at time moment, and take the second electric field intensity obtained from the last iteration as the first electric field intensity at time moment.

[0078] First, by constructing a simulation model of the diseased organ and obtaining its initial conductivity and breakdown conductivity, the simulation of the diseased organ is realized, thus achieving a simulation of the real diseased organ. Secondly, by applying voltage to the simulation model, each point in the diseased organ is subjected to electric shock. When calculating the first conductivity of each point at each moment, the maximum value of the first electric field strength in each historical moment before that moment is obtained. Then, the second conductivity at that moment is calculated using this maximum value. This process takes into account the irreversible conductivity of human organs in the process of determining conductivity, thereby making the conductivity calculation more accurate and improving the accuracy of the simulation process. Finally, by modifying the second conductivity, the second electric field intensity at that point at that moment is further calculated, and the second electric field intensity and the second conductivity are iterated multiple times until convergence, so as to obtain the first electric field intensity and the first conductivity at that moment, making the data more accurate and providing a solid data foundation for subsequent simulation analysis.

[0079] Based on the above embodiments, as an optional embodiment, the electric field data calculation module is specifically used for: The second conductivity at time t is determined based on the breakdown conductivity, initial conductivity, and the first electric field strength at the point at the previous time step. Based on the second conductivity and a preset boundary set, the intensity of the second electric field at a given time is determined. The boundary condition set includes the range of values ​​for current, potential, and structural electrical insulation.

[0080] Based on the above embodiments, as an optional embodiment, the electric field data iteration module is specifically used for: For each iteration, the third conductivity of the point at the given time is determined based on the initial conductivity, the breakdown conductivity, and the third electric field strength of the point in the previous iteration; wherein the third electric field strength of the first iteration is the second electric field strength. Based on the third conductivity and the boundary set, the third electric field intensity at the point at time t is determined; Arrange the third conductivity and the second conductivity in the order of the iteration rounds to obtain the conductivity sequence; A convergence analysis is performed on the conductivity sequence. If the conductivity sequence converges, the conductivity at the determined point has converged; if the conductivity sequence does not converge, the conductivity at the determined point has not converged.

[0081] Based on the above embodiments, as an optional embodiment, the device further includes a temperature determination module, specifically used for: For each point on the simulation model, at each time step, the electromagnetic heat at that point is determined based on the first conductivity and the first electric field strength at that time step, and the temperature at that point is determined based on the electromagnetic heat.

[0082] Based on the above embodiments, as an optional embodiment, the device further includes an electroporation loss region determination module, specifically used for: Obtain the maximum value of the first electric field intensity at each point within a preset time period; The closed surface formed by the points where the maximum value of the first electric field intensity is equal to the first preset threshold is taken as the electroporation damage area.

[0083] Based on the above embodiments, as an optional embodiment, the device further includes an electrical damage area determination module, specifically used for: For each point, based on the temperature of the point at each time moment, a function is constructed to show the temperature change of the point over a preset time period. For each point, the degree of thermal loss at the point is evaluated based on a function to obtain the probability of thermal damage at the point; The closed surface formed by each point whose thermal damage probability is equal to the second preset threshold is taken as the thermal damage region.

[0084] Based on the above embodiments, as an optional embodiment, the device further includes an ablation area determination module, specifically used for: The area covered by the combined electroporation and thermal damage areas is used as the final ablation area of ​​the simulation model; If the boundary of the final ablation area coincides with the boundary of the tumor area in the simulation model, it is determined that the final ablation area does not completely cover the tumor tissue. If the boundary of the final ablation area does not coincide with the boundary of the tumor area in the simulation model, then the final ablation area is determined to completely cover the tumor tissue.

[0085] The following is for reference. Figure 5 It illustrates an electronic device suitable for implementing embodiments of this application (e.g., performing...). Figure 1 The diagram shows the structure of the terminal device or server 500 of the method shown. The electronic devices in the embodiments of this application may include, but are not limited to, mobile terminals such as mobile phones, laptops, digital broadcast receivers, PDAs (personal digital assistants), PADs (tablet computers), PMPs (portable multimedia players), vehicle terminals (e.g., vehicle navigation terminals), wearable devices, and fixed terminals such as digital TVs and desktop computers. Figure 5 The electronic device shown is merely an example and should not impose any limitation on the functionality and scope of use of the embodiments of this application.

[0086] The electronic device includes a memory and a processor. The memory stores a program for executing the methods described in the various method embodiments above. The processor is configured to execute the program stored in the memory. The processor may be referred to as processing device 501 as described below. The memory may include at least one of read-only memory (ROM) 502, random access memory (RAM) 503, and storage device 508 as described below, as follows: like Figure 5 As shown, the electronic device 500 may include a processing unit (e.g., a central processing unit, a graphics processing unit, etc.) 501, which can perform various appropriate actions and processes according to a program stored in a read-only memory (ROM) 502 or a program loaded from a storage device 508 into a random access memory (RAM) 503. The RAM 503 also stores various programs and data required for the operation of the electronic device 500. The processing unit 501, ROM 502, and RAM 503 are interconnected via a bus 504. An input / output (I / O) interface 505 is also connected to the bus 504.

[0087] Typically, the following devices can be connected to I / O interface 505: input devices 506 including, for example, touchscreens, touchpads, keyboards, mice, cameras, microphones, accelerometers, gyroscopes, etc.; output devices 507 including, for example, liquid crystal displays (LCDs), speakers, vibrators, etc.; storage devices 508 including, for example, magnetic tapes, hard disks, etc.; and communication devices 509. Communication device 509 allows electronic device 500 to communicate wirelessly or wiredly with other devices to exchange data. Although Figure 5Electronic devices with various devices are shown, but it should be understood that it is not required to implement or have all of the devices shown. More or fewer devices may be implemented or have alternatively.

[0088] Specifically, according to embodiments of this application, the processes described above with reference to the flowcharts can be implemented as computer software programs. For example, embodiments of this application include a computer program product comprising a computer program carried on a non-transitory computer-readable medium, the computer program containing program code for performing the methods shown in the flowcharts. In such embodiments, the computer program can be downloaded and installed from a network via communication device 509, or installed from storage device 508, or installed from ROM 502. When the computer program is executed by processing device 501, it performs the functions defined in the methods of embodiments of this application.

[0089] It should be noted that the computer-readable storage medium described above in this application can be a computer-readable signal medium, a computer-readable storage medium, or any combination of the two. A computer-readable storage medium can be, for example,—but not limited to—an electrical, magnetic, optical, electromagnetic, infrared, or semiconductor system, apparatus, or device, or any combination thereof. More specific examples of a computer-readable storage medium may include, but are not limited to: an electrical connection having one or more wires, a portable computer disk, a hard disk, random access memory (RAM), read-only memory (ROM), erasable programmable read-only memory (EPROM or flash memory), optical fiber, portable compact disk read-only memory (CD-ROM), optical storage device, magnetic storage device, or any suitable combination thereof. In this application, a computer-readable storage medium can be any tangible medium containing or storing a program that can be used by or in conjunction with an instruction execution system, apparatus, or device. In this application, a computer-readable signal medium can include a data signal propagated in baseband or as part of a carrier wave, carrying computer-readable program code. Such propagated data signals can take various forms, including but not limited to electromagnetic signals, optical signals, or any suitable combination thereof. A computer-readable signal medium can be any computer-readable medium other than a computer-readable storage medium, which can send, propagate, or transmit a program for use by or in connection with an instruction execution system, apparatus, or device. The program code contained on the computer-readable medium can be transmitted using any suitable medium, including but not limited to: wires, optical fibers, RF (radio frequency), etc., or any suitable combination thereof.

[0090] In some implementations, clients and servers can communicate using any currently known or future-developed network protocol such as HTTP (Hypertext Transfer Protocol) and can interconnect with digital data communication (e.g., communication networks) of any form or medium. Examples of communication networks include local area networks (“LANs”), wide area networks (“WANs”), the Internet (e.g., the Internet of Things), and peer-to-peer networks (e.g., ad hoc peer-to-peer networks), as well as any currently known or future-developed networks.

[0091] The aforementioned computer-readable medium may be included in the aforementioned electronic device; or it may exist independently and not assembled into the electronic device.

[0092] The aforementioned computer-readable medium carries one or more programs, which, when executed by the electronic device, cause the electronic device to: The simulation model of the diseased organ, its initial conductivity, and its breakdown conductivity when electrically broken down are obtained. A voltage of a preset duration is applied to the simulation model, wherein the voltage value at each moment within the preset duration changes with time. For each point on the simulation model, at each moment, based on the first electric field strength, initial conductivity, and breakdown conductivity of the point at the previous moment, the second electric field strength and second conductivity at that moment are determined. The first electric field strength at the previous moment corresponding to the initial moment is zero. For each point on the simulation model, at each moment, at least one iteration operation is performed on the second conductivity and second electric field strength of the point at that moment until the conductivity of the point converges. For each point on the simulation model, at each moment, the second conductivity obtained from the last iteration at that moment is taken as the first conductivity of the point at that moment, and the second electric field strength obtained from the last iteration is compared with the first electric field strength at the previous moment, and the larger electric field strength is taken as the first electric field strength of the point at that moment.

[0093] Computer program code for performing the operations of this application can be written in one or more programming languages ​​or a combination thereof, including but not limited to object-oriented programming languages ​​such as Java, Smalltalk, and C++, as well as conventional procedural programming languages ​​such as the "C" language or similar programming languages. The program code can be executed entirely on the user's computer, partially on the user's computer, as a standalone software package, partially on the user's computer and partially on a remote computer, or entirely on a remote computer or server. In cases involving remote computers, the remote computer can be connected to the user's computer via any type of network—including a local area network (LAN) or a wide area network (WAN)—or can be connected to an external computer (e.g., via the Internet using an Internet service provider).

[0094] The flowcharts and block diagrams in the accompanying drawings illustrate the architecture, functionality, and operation of possible implementations of systems, methods, and computer program products according to various embodiments of this application. In this regard, each block in a flowchart or block diagram may represent a module, segment, or portion of code containing one or more executable instructions for implementing a specified logical function. It should also be noted that in some alternative implementations, the functions indicated in the blocks may occur in a different order than those indicated in the drawings. For example, two consecutively indicated blocks may actually be executed substantially in parallel, and they may sometimes be executed in reverse order, depending on the functions involved. It should also be noted that each block in the block diagrams and / or flowcharts, and combinations of blocks in the block diagrams and / or flowcharts, can be implemented using a dedicated hardware-based system that performs the specified function or operation, or using a combination of dedicated hardware and computer instructions.

[0095] The modules or units described in the embodiments of this application can be implemented in software or hardware. The names of modules or units do not necessarily limit the specific unit; for example, a first constraint acquisition module can also be described as a "module for acquiring the first constraint".

[0096] The functions described above in this document can be performed at least in part by one or more hardware logic components. For example, exemplary types of hardware logic components that can be used, without limitation, include: field-programmable gate arrays (FPGAs), application-specific integrated circuits (ASICs), application-specific standard products (ASSPs), system-on-a-chip (SoCs), complex programmable logic devices (CPLDs), and so on.

[0097] In the context of this application, a machine-readable medium can be a tangible medium that may contain or store a program for use by or in conjunction with an instruction execution system, apparatus, or device. A machine-readable medium can be a machine-readable signal medium or a machine-readable storage medium. Machine-readable media can be, but is not limited to, electronic, magnetic, optical, electromagnetic, infrared, or semiconductor systems, apparatus, or devices, or any suitable combination of the foregoing. More specific examples of machine-readable storage media include electrical connections based on one or more wires, portable computer disks, hard disks, random access memory (RAM), read-only memory (ROM), erasable programmable read-only memory (EPROM or flash memory), optical fibers, portable compact disk read-only memory (CD-ROM), optical storage devices, magnetic storage devices, or any suitable combination of the foregoing.

[0098] It should be understood that although the steps in the flowcharts of the accompanying figures are shown sequentially as indicated by the arrows, these steps are not necessarily executed in the order indicated by the arrows. Unless explicitly stated herein, there is no strict order restriction on the execution of these steps, and they can be executed in other orders. Moreover, at least some steps in the flowcharts of the accompanying figures may include multiple sub-steps or multiple stages. These sub-steps or stages are not necessarily completed at the same time, but can be executed at different times, and their execution order is not necessarily sequential, but can be performed alternately or in turn with other steps or at least some of the sub-steps or stages of other steps.

[0099] The above description is only a partial embodiment of the present invention. It should be noted that for those skilled in the art, several improvements and modifications can be made without departing from the principle of the present invention, and these improvements and modifications should also be considered within the scope of protection of the present invention.

Claims

1. A data processing method, characterized in that, include: Obtain a simulation model of the diseased organ, the initial conductivity of the diseased organ, and the breakdown conductivity of the organ when it is electrically broken down; A voltage of a preset duration is applied to the simulation model; wherein the voltage value at each moment within the preset duration changes with time. For each point on the simulation model, at each time moment, the maximum value of the first electric field intensity at each historical time moment is obtained. Based on the maximum value, the voltage value at the time moment, the initial conductivity, and the breakdown conductivity, the second electric field intensity and the second conductivity at the time moment are determined; wherein, the maximum value at the initial time moment is zero. For each point on the simulation model, at each time step, at least one iteration operation is performed on the second conductivity and second electric field strength of the point at that time step until the conductivity of the point converges. For each point on the simulation model, at each time step, the second conductivity obtained from the last iteration at that time is taken as the first conductivity of that point at that time, and the second electric field strength obtained from the last iteration is taken as the first electric field strength at that time.

2. The method according to claim 1, characterized in that, Determining the second electric field strength and second conductivity at the specified time based on the maximum value, the voltage value at the specified time, the initial conductivity, and the breakdown conductivity includes: The second conductivity of the point at the given time is determined based on the breakdown conductivity, the initial conductivity, and the maximum value. Based on the second conductivity, the voltage value at the time, and a preset boundary set, the second electric field strength at the time is determined, wherein the boundary condition set includes the range of values ​​for current, potential, and tissue electrical insulation.

3. The method according to claim 2, characterized in that, For each point on the simulation model, at each time moment, at least one iteration operation is performed on the second conductivity and second electric field strength of the point at that time, including: For each iteration, the third conductivity of the point at the given time is determined based on the initial conductivity, the breakdown conductivity, and the third electric field strength of the point in the previous iteration; wherein the third electric field strength of the first iteration is the second electric field strength. Based on the third conductivity and the boundary set, the third electric field strength at the point at the time is determined; The third conductivity and the second conductivity are arranged in the order of the iteration rounds to obtain the conductivity sequence; A convergence analysis is performed on the conductivity sequence. If the conductivity sequence converges, the conductivity at the point is determined to have converged; if the conductivity sequence does not converge, the conductivity at the point is determined to have not converged.

4. The method according to claim 1, characterized in that, The method further includes: For each point on the simulation model, at each time moment, the electromagnetic heat of the point at that time moment is determined based on the first conductivity and the first electric field strength at that time moment, and the temperature of the point at that time moment is determined based on the electromagnetic heat.

5. The method according to claim 4, characterized in that, The method further includes the step of determining the electroporation damage region of the simulation model: Obtain the maximum value of the first electric field intensity at each point within the preset time period; The closed surface formed by the points where the maximum value of the first electric field intensity is equal to the first preset threshold is taken as the electroporation damage area.

6. The method according to claim 5, characterized in that, The method further includes the step of determining the thermal damage region of the simulation model: For each point, based on the temperature of the point at each time moment, a function is constructed to show the temperature change of the point over time within the preset duration. For each point, the degree of thermal damage at the point is evaluated based on the function to obtain the probability of thermal damage at the point; The closed surface formed by each point whose thermal damage probability is equal to the second preset threshold is taken as the thermal damage region.

7. The method according to claim 6, characterized in that, The method further includes: The area covered by the combined electroporation region and the thermal damage region is taken as the final ablation region of the simulation model; If the boundary of the final ablation area coincides with the boundary of the tumor area in the simulation model, it is determined that the final ablation area does not completely cover the tumor tissue. If the boundary of the final ablation region does not coincide with the boundary of the tumor region in the simulation model, then the final ablation region is determined to completely cover the tumor tissue.

8. A data processing apparatus, characterized in that, include: The simulation model acquisition module is used to acquire the simulation model of the diseased organ, the initial conductivity of the diseased organ, and the breakdown conductivity of the organ when it is electrically broken down. A voltage application module is used to apply a voltage to the simulation model for a preset duration; wherein the voltage value at each moment within the preset duration changes with time. The electric field data calculation module is used to obtain the maximum value of the first electric field intensity at each historical moment for each point on the simulation model at each moment, and determine the second electric field intensity and the second conductivity at the moment based on the maximum value, the voltage value at the moment, the initial conductivity and the breakdown conductivity; wherein the maximum value at the initial moment is zero; The electric field data iteration module is used to perform at least one iteration operation on the second conductivity and second electric field strength of each point on the simulation model at each time, until the conductivity of the point converges. The electric field data recording module is used to, for each point on the simulation model, at each time moment, take the second conductivity obtained from the last iteration at that time moment as the first conductivity of that point at that time moment, and take the second electric field intensity obtained from the last iteration as the first electric field intensity at that time moment.

9. An electronic device comprising a memory, a processor, and a computer program stored in the memory, characterized in that, The processor executes the computer program to implement the method of any one of claims 1-7.

10. A computer-readable storage medium having a computer program stored thereon, characterized in that, When the computer program is executed by a processor, it implements the method of any one of claims 1-7.

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