Creation method of tumor personalized treatment simulation model based on overlapped microwave ablation

Abstract

The invention discloses a method for creating a tumor personalized treatment simulation model based on overlapped microwave ablation in the technical field of biomedical engineering and computer simulation, and the method comprises the steps: constructing a three-dimensional geometric model containing a liver and a tumor based on medical image data of a patient; and establishing an overlapping microwave ablation finite element model coupling electromagnetic wave propagation and biological tissue heat transfer according to the three-dimensional geometric model. According to the method, the overlapping ablation process is dispersed into a plurality of continuous'ablation-cooling-re-ablation 'stages, the thermal field of the previous stage is inherited as the initial condition of the next stage, and the tissue characteristics changed due to temperature change are dynamically updated, so that accurate simulation of the overlapping thermal field cumulative effect is realized, and the accuracy of the thermal field cumulative effect is improved. Therefore, the prediction precision of the form of the final solidification area of overlapping ablation of the liver tumor is improved, and a doctor can clearly know the possible effect of ablation treatment according to the predicted visual solidification area and the quantitative evaluation index.

Description

Technical Field

[0001] This invention relates to the fields of biomedical engineering and computer simulation technology, specifically a method for creating a simulation model of personalized tumor treatment based on overlapping microwave ablation. Background Technology

[0002] Microwave ablation (MWA) is an important local treatment for liver cancer, offering advantages such as rapid heating, large ablation volume, and minimal impact from heat sink effects. As a minimally invasive tumor treatment technique, microwave ablation has been widely used clinically. For small tumors, a single ablation session can achieve good results. However, for large-volume tumors (typically defined as those with a maximum diameter >3 cm) or irregularly shaped tumors, a single ablation session is insufficient for complete coverage, easily leading to tumor residue or excessive damage to surrounding healthy tissue. Overlapping microwave ablation (OMWA), which creates a superimposed coagulation necrosis zone through multiple ablation sessions, represents a potential solution to these problems.

[0003] However, existing clinical practice lacks effective preoperative planning tools to predict the final effect of overlapping ablation. Existing simulation models are mostly for single ablation and often use simplified geometric models, failing to fully consider the temperature dependence of real patient anatomy and tissue parameters, as well as the thermal field coupling effect between multiple ablations. This results in a large deviation between the prediction results and clinical reality, which is not conducive to doctors' preoperative formulation of optimal ablation paths and parameters. Summary of the Invention

[0004] The purpose of this invention is to provide a method for creating a simulation model of personalized tumor treatment based on overlapping microwave ablation, in order to solve the problem that the existing simulation models mentioned above are mostly for single ablation and often use simplified geometric models, which fail to fully consider the temperature dependence of the actual patient's anatomical structure and tissue parameters, as well as the thermal field coupling effect between multiple ablations, resulting in a large deviation between the prediction results and the clinical reality.

[0005] To achieve the above objectives, the present invention provides the following technical solution: A method for creating a simulation model of personalized tumor treatment based on overlapping microwave ablation, comprising: Based on the patient's medical imaging data, a three-dimensional geometric model including the liver and tumor was constructed; An overlapping microwave ablation finite element model coupling electromagnetic wave propagation and biological tissue heat transfer is established based on a three-dimensional geometric model. The overlapping microwave ablation finite element model includes thermal parameters and electrical parameters, and the dynamic functional relationship between the thermal parameters, electrical parameters and temperature changes is defined. The overlapping microwave ablation finite element model is divided into multiple target regions, and the boundary conditions of the target regions are set. A three-dimensional coordinate system is established with the transmitting end of the microwave antenna as the origin by coupling and overlapping the microwave ablation finite element model of the microwave antenna. The initial temperature of the divided overlapping microwave ablation finite element model is set, and the overlapping ablation process is simulated and executed according to the dynamic function relationship and boundary conditions. The parameters of the microwave antenna are adjusted, and the overlapping ablation process is simulated and executed again to obtain personalized ablation data. Based on personalized ablation data, a predicted and visualized solidification zone is obtained, and a quantitative evaluation index is calculated.

[0006] As a further aspect of the present invention: based on the patient's medical imaging data, a personalized three-dimensional geometric model including the liver and tumor is constructed, comprising: Acquire the patient's medical imaging data, which includes a three-dimensional image of the liver; The liver 3D image is segmented at the volume pixel level and each segment is assigned a preset category label to obtain labeled voxel data; The labeled voxel data is preprocessed using three-dimensional morphology to obtain processed voxel data. Based on the isosurface extraction algorithm, the three-dimensional isosurface of the target structure is extracted from the processed voxel data, wherein the target structure includes liver tissue and tumor tissue; The three-dimensional isosurface is smoothed using a mesh smoothing algorithm, and then simplified using a mesh simplification algorithm to obtain a simplified three-dimensional isosurface. A three-dimensional mesh model is obtained by reconstructing a simplified three-dimensional isosurface. A three-dimensional geometric model containing the liver and tumor was constructed based on the three-dimensional mesh model.

[0007] As a further aspect of the present invention: the overlapping microwave ablation finite element model of coupled electromagnetic wave propagation and biological tissue heat transfer is established based on a three-dimensional geometric model. The overlapping microwave ablation finite element model includes thermal parameters and electrical parameters, and defines the dynamic functional relationship between the thermal and electrical parameters and temperature changes, including: The electrical parameters include electromagnetic energy deposition and tissue specific absorptivity, and the thermal parameters include transient heat transfer within the tissue. The calculation formula for the electromagnetic energy deposition is as follows: ; The formula for calculating the intra-tissue specific absorption rate is: ; The formula for calculating transient heat transfer within the tissue is:

[0008] In the above formula, For curl operator; Let be the relative permeability, where =1; E is the electric field strength, in V / m; For free space wavenumber; is the relative permittivity of vacuum; Electrical conductivity of biological tissues, expressed in S / m; It is the relative permittivity; Angular frequency, in rad / s; Tissue density, in kg / m³; SAR, specific absorptivity, in W / kg; t is the specific heat capacity of the liver, in J / (kg·℃); T is the temperature, in ℃; t is the time, in s; k is the thermal conductivity, in W / (m·℃); Blood flow temperature; The specific heat capacity of blood is expressed in J / (kg·℃). This represents blood perfusion rate, expressed in units of 1 / s. The heat generated by tissue metabolism is expressed in W / m³; the subscript "b" indicates a blood-related parameter. Define the dynamic functional relationship between thermal and electrical parameters and temperature changes.

[0009] As a further aspect of the present invention: the definition of the dynamic functional relationship between thermal parameters and electrical parameters and temperature change includes: The dynamic functional relationship includes the specific heat capacity function and the relative permittivity function based on changes in water content. (T) Conductivity function (T), thermal conductivity function K; The specific heat capacity function based on changes in water content is:

[0010]

[0011] In the formula, and The specific heat capacities at 25 °C and 70 °C, respectively; This represents the temperature coefficient, with units of J / (kg). ); The latent heat constant is 2260 kJ / kg; W(T) is a function of water content.

[0012]

[0013]

[0014] In the formula The value is the thermal conductivity at 25 °C.

[0015] As a further aspect of the present invention: the step of dividing the overlapping microwave ablation finite element model into multiple target regions and setting boundary conditions for the target regions includes: An automatic mesh generation method was used to perform free tetrahedral mesh generation on the overlapping microwave ablation finite element model to obtain multiple target regions, including an outer surface region, a surface region, and an internal region. The surface region is set as an ideal electromagnetic scattering boundary, the outer surface region is set as an adiabatic boundary, and the inner region is set as the transient heat transfer description region within the tissue. A preset isotherm threshold is set, which is used to evaluate the necrosis range and characterize the size of the solidification region.

[0016] As a further aspect of the present invention: the step of coupling and overlapping the microwave ablation finite element model with the microwave antenna, and establishing a three-dimensional coordinate system based on the transmitting end of the microwave antenna as the origin, includes: Multiple microwave antennas with preset parameters are inserted into the overlapping microwave ablation finite element model. A corresponding number of ablation points are formed according to the number of tumors in the overlapping microwave ablation finite element model. The corresponding ablation points are then inserted into the microwave antennas in sequence to simulate the surgical steps of clinical overlapping ablation. A three-dimensional coordinate system is established with the transmitter of the microwave antenna as the origin, which provides a spatial positioning reference for the microwave antenna to be inserted into the overlapping microwave ablation finite element model.

[0017] As a further aspect of the present invention: the initial temperature is set for the divided overlapping microwave ablation finite element model, and the overlapping ablation process is simulated and executed according to the dynamic function relationship and boundary conditions. The parameters of the microwave antenna are adjusted, and the overlapping ablation process is simulated and executed again to obtain personalized ablation data, including: The overlapping ablation process consists of at least two consecutive ablation stages, with the initial temperature as the starting temperature. Each subsequent ablation stage uses the temperature at the end of the previous ablation stage as its initial temperature. The ablation phase includes an electromagnetic simulation phase, a transient thermal simulation phase, and a tissue state update phase. The electromagnetic simulation phase is used to calculate the electromagnetic energy deposition of the microwave antenna in the tissue at the current phase. The transient thermal simulation stage uses the current tissue temperature and electromagnetic energy deposition as inputs to calculate the final temperature; The tissue state update stage is based on the final temperature of the ablation stage and updates the thermal damage parameters of the tissue according to a preset isotherm threshold. The number of microwave antenna coupling and overlapping microwave ablation finite element models is adjusted according to the number of ablation points, and the corresponding continuous ablation stages are simulated according to the dynamic function relationship and boundary conditions to obtain the final thermal damage parameters. Adjust the parameters of the microwave antenna and simulate the overlapping ablation process again to obtain the corresponding final thermal damage parameters. Multiple final thermal damage parameters form personalized ablation data.

[0018] As a further aspect of the present invention: the adjustment of the microwave antenna parameters includes: The parameters of a microwave antenna include its position, power, angle, and time. After adjusting the parameters of the microwave antenna, the corresponding overlap ablation process is executed.

[0019] As a further aspect of the present invention: the step of obtaining the predicted visual coagulation zone based on personalized ablation data and calculating the quantitative evaluation index includes: The total visualized coagulation zone was obtained by simulation and prediction based on personalized ablation data, and the coagulation distribution inside the tumor, at the tumor margin, and in the surrounding healthy tissue was plotted. Quantitative evaluation indicators are calculated based on personalized ablation data.

[0020] As a further aspect of the present invention: the quantitative evaluation index includes at least one of ablation safety margin, healthy tissue damage volume, and healthy tissue damage ratio; The ablation safety margin is the distance beyond the tumor boundary of the ablation zone; The volume of healthy tissue damaged refers to the volume of healthy tissue contained within the ablation zone. The healthy tissue damage ratio, which is the ratio of the volume of healthy tissue damage to the total ablation volume, is used to quantify the relative degree of damage to healthy tissue during the ablation process.

[0021] Compared with the prior art, the beneficial effects of the present invention are: 1. In this invention, a three-dimensional geometric model is established using medical imaging data. After processing the three-dimensional geometric model, an overlapping microwave ablation finite element model coupling electromagnetic wave propagation and biological tissue heat transfer is established. The ablation process is realistically simulated based on the defined thermal and electrical parameters and their dynamic functional relationships. Simulation modeling of overlapping microwave ablation is carried out based on real anatomical structures, and boundary conditions for multiple target regions are set. For large-volume, irregularly shaped liver tumors, multi-point insertion of microwave antennas is used for simulation. The overlapping ablation process is discretized into multiple continuous "ablation-cooling-re-ablation" stages. By inheriting the thermal field of the previous stage as the initial condition of the next stage, and dynamically updating the tissue characteristics changed by temperature changes, the cumulative effect of overlapping thermal fields is accurately simulated. This improves the prediction accuracy of the final coagulation zone morphology of liver tumor overlapping ablation, thereby enabling the formulation of more precise and personalized treatment plans before actual surgical operations, improving the success rate and safety of surgery, and reducing unnecessary tissue damage and complications.

[0022] 2. In this invention, the constructed overlapping microwave ablation finite element model can couple microwave antennas with different parameters and numbers. The number, position, power, time, and angle of the microwave antennas can be flexibly adjusted according to the specific tumor morphology, location, and tissue characteristics of different patients. Different overlapping ablation processes can be simulated for the same liver tumor model, thereby optimizing the most suitable combination of microwave ablation parameters for the patient and achieving truly personalized treatment. The personalized parameter optimization process not only considers the morphology and location of the tumor, but also fully considers the uniqueness of the patient's liver tissue, such as thermal conductivity and blood perfusion rate, thereby ensuring that the ablation process is both effective and safe. Attached Figure Description

[0023] Figure 1 This is a schematic diagram of the method flow of the present invention; Figure 2 This is a schematic diagram of the segmentation results of a clinical patient's liver CT image according to the present invention; Figure 3 This is a schematic diagram of the segmentation, reconstruction, and mesh generation of the liver three-dimensional simulation model of the present invention; Figure 4 This is a schematic diagram of the 54 °C isotherm threshold solidification zone of the present invention; Figure 5 This is a schematic diagram of the three-dimensional solidification zone formed under different ablation strategies of the present invention; Figure 6 The diagram shows the temperature distribution results under different ablation strategies of this invention. Figure 7 This is a schematic diagram comparing the three-dimensional coagulation zones of overlapping and single-needle microwave ablation in clinical patients according to the present invention. Figure 8 This is a schematic diagram of the two-dimensional coagulation zone and temperature distribution under different ablation strategies in clinical patients according to the present invention. Figure 9 This is a comparison of CT images for preoperative patient localization, intraoperative ablation, and postoperative evaluation in accordance with the present invention. Detailed Implementation

[0024] The technical solutions of the embodiments of the present invention will be clearly and completely described below with reference to the accompanying drawings. Obviously, the described embodiments are only some embodiments of the present invention, and not all embodiments. Based on the embodiments of the present invention, all other embodiments obtained by those skilled in the art without creative effort are within the scope of protection of the present invention.

[0025] Example: Please see Figures 1-4 In this embodiment of the invention, a method for creating a simulation model of personalized tumor treatment based on overlapping microwave ablation includes: S1: Based on the patient's medical imaging data, construct a three-dimensional geometric model including the liver and tumor; S2: Based on the three-dimensional geometric model, establish an overlapping microwave ablation finite element model that couples electromagnetic wave propagation with heat transfer in biological tissue. The overlapping microwave ablation finite element model includes thermal parameters and electrical parameters, and defines the dynamic functional relationship between thermal parameters, electrical parameters and temperature changes. S3: Divide the overlapping microwave ablation finite element model into multiple target regions and set the boundary conditions for the target regions; S4: Couple and overlap the microwave antenna with the microwave ablation finite element model, and establish a three-dimensional coordinate system with the transmitting end of the microwave antenna as the origin; S5: Set the initial temperature of the divided overlapping microwave ablation finite element model, and simulate the overlapping ablation process according to the dynamic function relationship and boundary conditions. Adjust the parameters of the microwave antenna, simulate the overlapping ablation process again, and obtain personalized ablation data. S6: Based on personalized ablation data, a predicted and visualized solidification zone is obtained, and a quantitative evaluation index is calculated.

[0026] Specifically, this method establishes a three-dimensional geometric model using medical imaging data. After processing the three-dimensional geometric model, an overlapping microwave ablation finite element model coupling electromagnetic wave propagation and biological tissue heat transfer is established. Based on defined thermal and electrical parameters and their dynamic functional relationships, the ablation process is realistically simulated. Simulation modeling of overlapping microwave ablation is carried out based on real anatomical structures, and boundary conditions for multiple target regions are set. Multi-point insertion of microwave antennas is used to simulate large-volume, irregularly shaped liver tumors. The overlapping ablation process is discretized into multiple continuous "ablation-cooling-re-ablation" stages. Using the thermal field from the previous stage as the initial condition for the next stage, and dynamically updating the tissue characteristics that change due to temperature variations, the system achieves accurate simulation of the cumulative effect of overlapping thermal fields. This improves the accuracy of predicting the final coagulation zone morphology of overlapping ablation of liver tumors. Based on the predicted visualized coagulation zone and quantitative evaluation indicators, doctors can clearly understand the potential effects of ablation treatment, including information such as the size, shape, and location of the coagulation zone. This allows for the development of more precise and personalized treatment plans before actual surgical procedures, improving the success rate and safety of the surgery, and reducing unnecessary tissue damage and complications. Furthermore, the overlapping microwave ablation finite element model constructed using this method can couple microwave antennas with different parameters and numbers. This allows for flexible adjustment of parameters such as the number, position, power, time, and angle of the microwave antennas based on the specific tumor morphology, location, and tissue characteristics of different patients. Different overlapping ablation processes can be simulated for the same liver tumor model, thereby optimizing the most suitable microwave ablation parameter combination for the patient. This achieves truly personalized treatment. The personalized parameter optimization process not only considers the morphology and location of the tumor but also fully takes into account the unique characteristics of the patient's liver tissue, such as thermal conductivity and blood perfusion rate, ensuring that the ablation process is both effective and safe. Through this refined simulation and optimization, doctors can anticipate the possible treatment effects before surgery, proactively avoid potential risks, and provide patients with more precise and reliable treatment plans. In addition, with the help of visualized coagulation zones and quantitative evaluation indicators, doctors can more intuitively and accurately understand the ablation effect, providing a reliable basis for subsequent treatment decisions. Compared to traditional single-ablation models, this method can be applied to ablation of larger tumors, providing more precise guidance for tumor ablation in real-world patients. It makes tumor ablation safer and more precise in terms of ablation range. When ablation large areas of tumors, it can protect healthy tissue as much as possible while ensuring that tumor tissue is fully ablated, effectively reducing the risk of recurrence.

[0027] Preferably, based on the patient's medical imaging data, a personalized three-dimensional geometric model including the liver and tumor is constructed, including: Acquire the patient's medical imaging data, which includes three-dimensional images of the liver; The liver 3D image is segmented at the volume pixel level and each segment is assigned a preset category label to obtain labeled voxel data; Processed voxel data is obtained by preprocessing labeled voxel data based on three-dimensional morphology. Based on the isosurface extraction algorithm, three-dimensional isosurfaces of target structures are extracted from the processed voxel data, where the target structures include liver tissue and tumor tissue; The three-dimensional isosurface is smoothed using a mesh smoothing algorithm, and then simplified using a mesh simplification algorithm to obtain a simplified three-dimensional isosurface. A three-dimensional mesh model is obtained by reconstructing a simplified three-dimensional isosurface. A three-dimensional geometric model containing the liver and tumor was constructed based on the three-dimensional mesh model.

[0028] Specifically, three-dimensional images of the patient's liver were acquired. These images encompassed both normal morphology and complex pathological features such as vascular structures. During modeling, based on voxel-level segmentation masks, three-dimensional morphological preprocessing was performed first, followed by the Marching Cubes algorithm to extract isosurfaces under physical voxel spacing constraints. Taubin smoothing was combined to reduce jagged artifacts, while QEM mesh simplification was employed to reduce computational complexity. Finally, a mesh model of the liver and tumor was reconstructed and stored in STL format for subsequent simulation and visualization. Based on the three-dimensional mesh model, a three-dimensional geometric model containing the liver and tumor was constructed. When constructing this three-dimensional geometric model, the morphological characteristics, positional relationships, and proximity to surrounding tissues of the liver and tumor were fully considered to ensure that the constructed three-dimensional geometric model could realistically and accurately reflect the actual condition of the liver and tumor, providing a reliable foundation for subsequent simulation analysis. Furthermore, the contour surface extraction algorithm employs the Marching Cubes algorithm. This algorithm iterates through each voxel in the volume data, determining the topological structure of the contour surfaces within the voxel based on the relationship between the scalar values ​​at the voxel vertices and the given contour surfaces, thereby generating a set of triangular facets that approximate the contour surfaces. In the reconstruction of the liver and tumor mesh models, the Marching Cubes algorithm can accurately extract the contour surfaces of the liver and tumor surfaces under physical voxel spacing constraints, providing a foundation for subsequent smoothing and mesh simplification operations, thus ensuring that the reconstructed mesh model accurately reflects the morphological characteristics of the liver and tumor. The mesh smoothing algorithm employed is the Taubin smoothing algorithm. The Taubin smoothing algorithm, through alternating contraction and expansion operations, effectively removes surface noise and irregularities while maintaining the overall shape of the model, resulting in a smoother and more natural mesh surface for the liver and tumor models. This smoothing process not only enhances the model's visualization but also provides more accurate geometric input for subsequent simulation calculations such as finite element analysis, contributing to improved accuracy and reliability of the simulation results.

[0029] Preferably, an overlapping microwave ablation finite element model coupling electromagnetic wave propagation and biological tissue heat transfer is established based on a three-dimensional geometric model. The overlapping microwave ablation finite element model includes thermal and electrical parameters, and defines the dynamic functional relationship between these parameters and temperature changes, including: Electrical parameters include electromagnetic energy deposition and tissue specific absorptivity, while thermal parameters include transient heat transfer within the tissue. The formula for calculating electromagnetic energy deposition is: ; The formula for calculating the intra-tissue specific absorption rate is: ; The formula for calculating transient heat transfer within an organization is:

[0030] In the above formula, For curl operator; Let be the relative permeability, where =1; E is the electric field strength, in V / m; For free space wavenumber; is the relative permittivity of vacuum; Electrical conductivity of biological tissues, expressed in S / m; It is the relative permittivity; Angular frequency, in rad / s; Tissue density, in kg / m³; SAR, specific absorptivity, in W / kg; t is the specific heat capacity of the liver, in J / (kg·℃); T is the temperature, in ℃; t is the time, in s; k is the thermal conductivity, in W / (m·℃); Blood flow temperature; The specific heat capacity of blood is expressed in J / (kg·℃). This represents blood perfusion rate, expressed in units of 1 / s. This represents the heat generated by tissue metabolism, expressed in W / m³. The subscript "b" indicates relevant blood parameters, including blood flow temperature, blood specific heat capacity, and blood perfusion rate. Blood flow temperature is the actual temperature of blood within the body, significantly influencing tissue heat exchange. Blood specific heat capacity reflects the blood's ability to absorb or release heat and is a key parameter for calculating energy changes during heat exchange. Blood perfusion rate represents the amount of blood flowing through the tissue per unit time, determining the rate of heat exchange between blood and tissue, and directly impacting temperature distribution and therapeutic efficacy during tumor ablation.

[0031] Define the dynamic functional relationship between thermal and electrical parameters and temperature changes.

[0032] Preferably, the dynamic functional relationship between thermal and electrical parameters and temperature change is defined, including: Dynamic functional relationships include specific heat capacity function and relative permittivity function based on changes in water content. (T) Conductivity function (T), thermal conductivity function K; The specific heat capacity function based on changes in water content is:

[0033]

[0034] In the formula, and The specific heat capacities at 25 °C and 70 °C, respectively; This represents the temperature coefficient, with units of J / (kg). ); The latent heat constant is 2260 kJ / kg; W(T) is a function of water content.

[0035]

[0036]

[0037] In the formula The value is the thermal conductivity at 25 °C.

[0038] Specifically, by defining dynamic functional relationships between thermal and electrical parameters and temperature changes, the actual ablation process can be realistically simulated. These dynamic functional relationships fully consider the changes in the thermal and electrical properties of the liver and tumor at different temperatures, providing accurate parameter basis for the simulation model. For example, the relative permittivity function ε(T) can accurately reflect the material's response characteristics to electromagnetic fields at different temperatures, and the conductivity function σ(T) can reflect the change in the material's conductivity with temperature. By incorporating these dynamic functional relationships into the simulation model, the model can better fit various physical phenomena in the actual ablation process, thereby providing more reliable and accurate simulation results for personalized tumor treatment.

[0039] Preferably, the overlapping microwave ablation finite element model is divided into multiple target regions, and boundary conditions for the target regions are set, including: An automatic mesh generation method was used to perform free tetrahedral mesh generation on the overlapping microwave ablation finite element model to obtain multiple target regions, including outer surface region, surface region and internal region. The surface region is set as an ideal electromagnetic scattering boundary, the outer surface region is set as an adiabatic boundary, and the inner region is set as the transient heat transfer description region within the tissue. Set a preset isotherm threshold to evaluate the necrosis range and characterize the size of the solidification area.

[0040] Specifically, after setting the boundary conditions, material properties are assigned to each target region. Based on the actual thermal and electrical properties of the liver and tumor, corresponding parameters such as relative permittivity and conductivity are assigned to the outer surface region, surface region, and internal region, respectively, to ensure that the model can accurately simulate the physical properties of different regions and more realistically reflect the temperature changes and thermal damage in the tissue during the actual ablation process.

[0041] Preferably, the microwave antenna is coupled and overlapped with a microwave ablation finite element model, and a three-dimensional coordinate system is established based on the transmitting end of the microwave antenna as the origin, including: Multiple microwave antennas with preset parameters are inserted into the overlapping microwave ablation finite element model. A corresponding number of ablation points are formed according to the number of tumors in the overlapping microwave ablation finite element model. The corresponding ablation points are then inserted into the microwave antennas in sequence to simulate the surgical steps of clinical overlapping ablation. A three-dimensional coordinate system is established with the transmitter of the microwave antenna as the origin, which provides a spatial positioning reference for the microwave antenna to be inserted into the overlapping microwave ablation finite element model.

[0042] Specifically, by establishing a three-dimensional coordinate system with the transmitting end of the microwave antenna as the origin, the position and orientation of each microwave antenna in the model can be accurately determined, ensuring that the layout of the ablation points is highly consistent with the layout in actual clinical surgery. At the same time, the insertion depth and angle of the microwave antenna can be flexibly adjusted according to the size, shape and location of different tumors to achieve precise ablation of the tumor. In addition, this three-dimensional coordinate system also provides a reliable spatial reference framework for subsequent analysis and research on physical fields such as temperature field and electromagnetic field during the ablation process.

[0043] Preferably, the initial temperature is set for the divided overlapping microwave ablation finite element model, and the overlapping ablation process is simulated and executed according to the dynamic function relationship and boundary conditions. The parameters of the microwave antenna are adjusted, and the overlapping ablation process is simulated and executed again to obtain personalized ablation data, including: Starting from the initial temperature, the overlapping ablation process consists of at least two consecutive ablation stages, wherein the temperature at the end of the previous ablation stage is used as the initial temperature for each subsequent ablation stage. The ablation phase includes an electromagnetic simulation phase, a transient thermal simulation phase, and a tissue state update phase. The electromagnetic simulation phase is used to calculate the electromagnetic energy deposition of the microwave antenna in the tissue at the current stage. The transient thermal simulation stage uses the current tissue temperature and electromagnetic energy deposition as inputs to calculate the final temperature; The tissue state update phase is based on the final temperature of the ablation phase and updates the thermal damage parameters of the tissue according to a preset isotherm threshold. The number of microwave antenna coupling and overlapping microwave ablation finite element models is adjusted according to the number of ablation points, and the corresponding continuous ablation stages are simulated according to the dynamic function relationship and boundary conditions to obtain the final thermal damage parameters. Adjust the parameters of the microwave antenna and simulate the overlapping ablation process again to obtain the corresponding final thermal damage parameters. Multiple final thermal damage parameters form personalized ablation data.

[0044] Specifically, after obtaining personalized ablation data, this data can be used to construct a simulation model for personalized tumor treatment. This model can accurately simulate the effect of overlapping microwave ablation in tumor treatment under different parameter settings, providing a strong basis for doctors to formulate personalized treatment plans.

[0045] Preferably, adjusting the parameters of the microwave antenna includes: The parameters of a microwave antenna include its position, power, angle, and time. After adjusting the parameters of the microwave antenna, the corresponding overlap ablation process is executed.

[0046] Specifically, when adjusting the microwave antenna parameters, the antenna at different locations needs to be precisely positioned according to the shape, size, and location of the tumor to ensure that the antenna can cover the key areas of the tumor. Through multiple simulation attempts, the optimal simulated treatment plan is obtained. This plan comprehensively considers the characteristics of the tumor, various parameters of the microwave antenna, and dynamic changes during the ablation process, which can achieve effective ablation of the tumor to the greatest extent while minimizing damage to surrounding normal tissues.

[0047] Preferably, the predicted visual coagulation zone is obtained based on personalized ablation data, and quantitative evaluation indicators are calculated, including: The total visualized coagulation zone was obtained by simulation and prediction based on personalized ablation data, and the coagulation distribution inside the tumor, at the tumor margin, and in the surrounding healthy tissue was plotted. Quantitative evaluation indicators are calculated based on personalized ablation data.

[0048] Preferably, the quantitative evaluation indicators include at least one of the following: ablation safety margin, healthy tissue damage volume, and healthy tissue damage ratio; The safe margin for ablation is the distance the ablation zone extends beyond the tumor boundary. The volume of healthy tissue damaged is the volume of healthy tissue contained within the ablation zone. The healthy tissue damage ratio, which is the ratio of the volume of healthy tissue damaged to the total ablation volume, is used to quantify the relative degree of damage to healthy tissue during the ablation process.

[0049] Specifically, by monitoring the ablation safety margin, doctors can ensure that the tumor is fully ablated, reducing the risk of recurrence; while the analysis of the volume of damage to healthy tissue and the ratio of damage to healthy tissue allows doctors to understand the extent of damage to normal tissue in a timely manner and take appropriate measures to protect the patient's health.

[0050] Example 1: The software used in this embodiment is all open source and widely used medical image processing and analysis software, which will not be described in detail here.

[0051] Three representative liver models were selected from the LiTS2017 (Liver Tumor Segmentation Challenge 2017) dataset, covering pathological features such as normal morphology and complex vascular structures.

[0052] Simultaneously, tumor cases of different sizes, locations, and numbers (single and multiple tumors) were selected to verify the adaptability of the overlapping microwave ablation strategy in diverse clinical scenarios. Liver and tumor characteristics are shown in Table 1. During modeling, based on voxel-level segmentation masks, three-dimensional morphological preprocessing was performed first, followed by the MarchingCubes algorithm to extract isosurfaces under physical voxel spacing constraints. Taubin smoothing was combined to reduce jagged artifacts, and QEM mesh simplification was employed to reduce computational complexity. Finally, a mesh model of the liver and tumor was reconstructed and stored in STL format for subsequent simulation and visualization.

[0053] Table 1

[0054] Note: In the table, 50, 88, and 90 represent patients numbered 50, 88, and 90 from the LiTS2017 dataset, respectively.

[0055] The clinical data in this embodiment comes from enhanced CT scans of two liver tumor patients at a certain hospital (Table 2). The physician first used 3DSlicer software to perform CT image segmentation as follows: Figure 2 As shown, where, Figure 2 (A)- Figure 2 In the middle (C), the segmentation and reconstruction results, COMSOL solid simulation model, and mesh generation results of patients number 50, 88, and 90 in the LiTS2017 dataset are respectively represented. Then, the STL model of the liver and tumor is generated by the surface reconstruction algorithm.

[0056] Table 2

[0057] Import the STL file into COMSOL Multiphysics software (v6.0, COMSOL Inc., Stockholm, Sweden) to create a 3D simulation model, such as... Figure 2 and Figure 3 As shown in Table 3, the microwave antenna required for the simulation consists of an inner conductor, a dielectric, and a slotted outer conductor. A three-dimensional coordinate system is established with the antenna transmitter as the origin.

[0058] Table 3

[0059] An overlapping microwave ablation finite element model is established based on a three-dimensional geometric model, which couples electromagnetic wave propagation with heat transfer in biological tissue. The overlapping microwave ablation finite element model includes thermal parameters and electrical parameters, and defines the dynamic functional relationship between the thermal parameters, electrical parameters and temperature changes.

[0060] Electromagnetic energy deposition was calculated using the Helmholtz harmonic equation (1), and the specific absorptivity (SAR) within the tissue was calculated using formula (2). Transient heat transfer within the tissue was solved using the Pennes classical biological heat transfer equation (3). The relevant equations are as follows: (1) (2) (3) In the formula, relative permeability ( =1); E is the electric field strength (V / m); For free space wavenumber; is the relative permittivity of vacuum; The relative permittivity of biological tissue; The electrical conductivity of biological tissue (s / m); Tissue density (kg / m³); SAR is specific absorption rate (W / kg); t is the specific heat capacity of the liver (J / (kg·℃)); T is the temperature (℃); t is the time (s); k is the thermal conductivity (W / (m·℃)). Blood specific heat capacity (J / (kg·℃)); Blood perfusion volume (kg / (m³·s)); This refers to the heat generated by tissue metabolism (W / m³). The subscript "b" indicates a relevant blood parameter.

[0061] During the MWA process, the thermal and electrical parameters of liver tissue change with increasing temperature. To describe the true changes in these parameters, this study used temperature-dependent electrical parameters, a specific heat capacity function based on changes in water content, and a linearly changing thermal conductivity function.

[0062] The specific heat capacity function based on changes in water content is: (4) (5) In the formula, and The specific heat capacities at 25 °C and 70 °C, respectively; Temperature coefficient (J / (kg)) )); is the latent heat constant (set to 2260 kJ / kg); W(T) is a function of water content.

[0063] Relative permittivity The expressions for electrical conductivity s (s / m) and thermal conductivity K (W / (m·℃)) are: (6) (7) (8) In the formula The value is the thermal conductivity at 25 °C.

[0064] The initial model temperature was set to 24 °C. An automatic mesh generation method was used to create a free tetrahedral mesh. Ideal electromagnetic scattering boundary conditions were applied to the surface, with an adiabatic boundary on the outer surface of the liver. The heat conduction process of the internal tissues was described by the Pennes biological heat transfer equation. The extent of tumor necrosis was assessed based on the 54 °C isotherm threshold to characterize the size of the coagulation zone (see...). Figure 4 ).

[0065] To ensure consistent measurement standards, this study implemented different ablation strategies by adjusting the treatment time and needle insertion angle under the same ablation power conditions. The execution of each strategy strictly adhered to the hard constraints of surgical navigation while also considering the optimization objectives of soft constraints. The ablation strategies for different cases are shown in Table 4, with an ablation power of 50W. In the table, "First Ablation, Second Ablation, Third Ablation, Fourth Ablation" represent the ablation time; surgical planning represents the time spent simulating clinical surgical path planning. Under the same case conditions, the total time for achieving conformal tumor coverage using the single-needle ablation strategy was 340 s, 7200 s, 4060 s, 240 s, and 360 s, respectively.

[0066] Table 4

[0067] Note: * indicates that this ablation or surgical procedure was not planned in this case.

[0068] This study calculated and visualized the volume and morphology of the final coagulation zone, and plotted the coagulation distribution within the tumor, at the tumor margin, and in the surrounding healthy tissue. To evaluate the ablation effect, the following metrics were defined: Ablation Margin (AM), the distance the ablation zone extends beyond the tumor boundary; Healthy Tissue Damage Volume (HTDV), the volume of healthy tissue contained within the ablation zone; and Healthy Tissue Damage Ratio (HTDR), the ratio of healthy tissue damage volume to the total ablation volume (HTDR = HTDV / AV), used to quantify the relative degree of damage to healthy tissue during ablation. Finally, the overlapping microwave ablation strategy was compared with a single-segment ablation strategy that also achieved conformal ablation to assess the effectiveness and safety of different approaches. All simulation parameters and strategies were set under the guidance of clinicians.

[0069] Comparison of results between overlapping ablation and single-needle ablation: Figure 5 The image shows a comparison of the effects of single-needle and overlapping microwave ablation in three patients. The left column represents the three-dimensional coagulation zone formed by the overlapping microwave ablation strategy, and the right column represents the three-dimensional coagulation zone formed by the single-needle microwave ablation strategy in the same cases. Patient 50 ( Figure 5 (A) The liver volume of the patient was small, and the tumor morphology was relatively regular. Parallel needle insertion with double-target overlapping ablation achieved complete conformal coverage, while single-needle single-point ablation with the same power and ablation time failed to completely cover the tumor. If a single-needle single-point strategy is used to achieve complete ablation, the treatment time needs to be extended. Patient 88 ( Figure 5 (B) The tumor was large and irregularly shaped, located near the hepatic aorta, making ablation difficult. A multi-target overlap strategy was employed, resulting in four ablation procedures: the first two were performed using a single needle with multiple overlapping points (pulling back and deflecting to the left); the latter two were also performed using a single needle with pullback and deflection to the right. This approach effectively expanded the coagulation area without increasing power. Patient 90 ( Figure 5 (C) represents multiple, irregular, large tumors, which underwent three overlapping ablation procedures. The ablation path was replanned via CT after the first ablation, and the subsequent two ablations achieved multi-target ablation through single-needle retraction and angle adjustment. Results showed that overlapping microwave ablation can achieve larger and more uniform coagulation zones in a shorter time, effectively improving tumor coverage while reducing thermal damage to surrounding healthy tissues.

[0070] Figure 6 The final temperature distribution results (cross-sectional view and vertical cross-sectional view) of three patients under different ablation strategies are shown, where the 54 °C isotherm represents the final thermal ablation coagulation zone. Figure 6(A) shows the ablation effect in patient 1. Compared with single-needle single-point ablation, the coagulation zone formed by overlapping microwave ablation is slightly smaller in volume, but better conforms to the morphology of the tumor, achieving conformal coverage of the lesion with minimal damage to healthy tissue. Figure 6 (B) shows the effect of multiple overlapping ablation procedures in patient 2. As can be seen from the figure, in this case, the coagulation zone was concentrated and the temperature distribution was uniform, with heat more focused on the tumor area, avoiding excessive heat diffusion. Patient 3 ( Figure 6 (C) The two needle insertions were placed at similar horizontal levels, resulting in a final coagulation zone that covered key areas of the tumor while effectively protecting surrounding normal liver tissue. Overall, overlapping microwave ablation demonstrated good thermal control and conformity in various patients, providing strong support for the precision treatment of complex tumors. Figure 6 (A)~ Figure 6 (C) represents the two-dimensional coagulation zones formed in patients 50, 88, and 90 of the LiTS2017 dataset when the overlapping microwave ablation strategy and the single-needle ablation strategy were implemented, respectively. The colored vertical bars represent the temperature distribution, and 54 indicates that we set the tumor to complete necrosis in the coagulation zone at 54℃. The isotherms of different colors (54 ℃) represent the range of the coagulation zone reaching 54 ℃ under different ablation cycles.

[0071] Table 5 lists the long and short axis dimensions of the final ablation coagulation zone for patients 50, 88, and 90. The results show that both the long and short axes of the coagulation zone from single-needle ablation are larger than those from overlapping microwave ablation. This difference is more pronounced for larger or irregularly shaped tumors, indicating that overlapping microwave ablation effectively reduces excessive thermal diffusion while achieving conformal coverage.

[0072] Table 5. Morphological characteristics of the solidification zone of LiTS2017 (in millimeters)

[0073] Validation of clinical data To verify the clinical applicability of the multi-target simulation model based on COMSOL software, this study selected two cases of liver tumors with complete preoperative, intraoperative, and postoperative CT scans from a hospital to evaluate the reliability of the proposed method in predicting actual ablation parameters (ablation time and power).

[0074] Comparison of results between overlapping ablation and single-needle ablation Figure 7 Patient 1 was shown. Figure 7 (A) and patient 2 ( Figure 7(B) Comparison of coagulation zones under single-needle ablation and overlapping microwave ablation strategies. Patient 1 had a small liver volume and a single, regular lesion that was narrow anteriorly and wide posteriorly. This patient underwent a single-needle multi-point ablation strategy, with a shorter first ablation time and a longer second ablation time. The results showed that both strategies achieved complete tumor coverage, while the resulting coagulation zone was slightly smaller than that produced by the single-needle ablation strategy. Patient 2 had a normal-sized liver with multiple, irregularly shaped tumors. This case was treated using both multi-target overlapping ablation and single-needle ablation strategies. The results indicated that for tumors with complex morphology, single-needle ablation caused significantly greater thermal damage to surrounding healthy tissue than overlapping microwave ablation. Figure 7 (A) and Figure 7 (B) represents the size of the three-dimensional coagulation zone (represented by the 54°C isotherm) of the overlapping microwave ablation and single needle ablation in patients 1 and 2, respectively.

[0075] Figure 8 The final two-dimensional coagulation zones formed in patients 1 and 2 using single-needle and overlapping microwave ablation strategies are shown. For patient 1, the coagulation zone formed by overlapping microwave ablation showed a slightly irregular morphology, but its area was smaller than that formed by single-needle ablation. For patient 2, the coagulation zone formed by single-needle ablation was significantly larger than that formed by overlapping ablation. These results further validate that overlapping microwave ablation can effectively reduce thermal damage to surrounding healthy tissues while achieving conformal tumor coverage.

[0076] Table 6 lists the measured long and short axis data of the final ablation and coagulation zones for Patient 1 and Patient 2. It can be seen that single-needle ablation outperforms overlapping ablation in both metrics, and the difference is more significant in irregularly shaped tumors.

[0077] Table 6. Size of the two-dimensional coagulation zone in clinical data (in millimeters)

[0078] CT image analysis In clinical surgery, CT scans play a crucial role in determining the ablation needle insertion point and enabling surgical navigation. To verify the applicability of the proposed simulation method in clinical practice, this study analyzed two patients with complete preoperative, intraoperative, and postoperative CT scan data (see [link to study]. Figure 9 By comparing the coagulation range predicted by the simulation with the actual postoperative imaging results, a high degree of consistency was found between the two in terms of ablation range, morphology, and edge distribution. Overall, the difference between the simulation results and the postoperative follow-up CT images was small, verifying the reliability and clinical reference value of the COMSOL-based multi-target simulation method in predicting actual ablation effects.

[0079] Evaluation indicators Table 7 lists the main data evaluation indicators for overlapping microwave ablation and single-needle ablation in different cases, including ablation volume (AV), long and short axes of the safety margin, healthy tissue damage volume (HTDV), and healthy tissue damage ratio (HTDR). The table shows that, under the same power conditions, overlapping microwave ablation achieves a more uniform coagulation range, more precise control of the safety margin, and significantly lower healthy tissue damage volume and ratio compared to single-needle ablation. These results further validate that overlapping microwave ablation can effectively reduce thermal damage to surrounding healthy tissue while achieving conformal tumor coverage.

[0080] Table 7 Data Evaluation Indicators (in mm)

[0081] The above description is only a preferred embodiment of the present invention, but the scope of protection of the present invention is not limited thereto. Any equivalent substitutions or modifications made by those skilled in the art within the scope of the technology disclosed in the present invention, based on the technical solution and inventive concept of the present invention, should be covered within the scope of protection of the present invention.

Claims

1. A method for creating a simulation model of personalized tumor treatment based on overlapping microwave ablation, characterized in that, include: Based on the patient's medical imaging data, a three-dimensional geometric model including the liver and tumor was constructed; An overlapping microwave ablation finite element model coupling electromagnetic wave propagation and biological tissue heat transfer is established based on a three-dimensional geometric model. The overlapping microwave ablation finite element model includes thermal parameters and electrical parameters, and the dynamic functional relationship between the thermal parameters, electrical parameters and temperature changes is defined. The overlapping microwave ablation finite element model is divided into multiple target regions, and the boundary conditions of the target regions are set. A three-dimensional coordinate system is established with the transmitting end of the microwave antenna as the origin by coupling and overlapping the microwave ablation finite element model of the microwave antenna. The initial temperature of the divided overlapping microwave ablation finite element model is set, and the overlapping ablation process is simulated and executed according to the dynamic function relationship and boundary conditions. The parameters of the microwave antenna are adjusted, and the overlapping ablation process is simulated and executed again to obtain personalized ablation data. Based on personalized ablation data, a predicted and visualized solidification zone is obtained, and a quantitative evaluation index is calculated.

2. The method for creating a simulation model of personalized tumor treatment based on overlapping microwave ablation according to claim 1, characterized in that, Based on the patient's medical imaging data, a personalized 3D geometric model including the liver and tumor is constructed, including: Acquire the patient's medical imaging data, which includes a three-dimensional image of the liver; The liver 3D image is segmented at the volume pixel level and each segment is assigned a preset category label to obtain labeled voxel data; The labeled voxel data is preprocessed using three-dimensional morphology to obtain processed voxel data. Based on the isosurface extraction algorithm, the three-dimensional isosurface of the target structure is extracted from the processed voxel data, wherein the target structure includes liver tissue and tumor tissue; The three-dimensional isosurface is smoothed using a mesh smoothing algorithm, and then simplified using a mesh simplification algorithm to obtain a simplified three-dimensional isosurface. A three-dimensional mesh model is obtained by reconstructing a simplified three-dimensional isosurface. A three-dimensional geometric model containing the liver and tumor was constructed based on the three-dimensional mesh model.

3. The method for creating a simulation model of personalized tumor treatment based on overlapping microwave ablation according to claim 2, characterized in that, The aforementioned method establishes an overlapping microwave ablation finite element model based on a three-dimensional geometric model, coupling electromagnetic wave propagation and biological tissue heat transfer. This overlapping microwave ablation finite element model includes thermal and electrical parameters, and defines the dynamic functional relationship between these parameters and temperature changes, including: The electrical parameters include electromagnetic energy deposition and tissue specific absorptivity, and the thermal parameters include transient heat transfer within the tissue. The calculation formula for the electromagnetic energy deposition is as follows: ； The formula for calculating the intra-tissue specific absorption rate is: ； The formula for calculating transient heat transfer within the tissue is: In the above formula, For curl operator; Let be the relative permeability, where =1; E is the electric field strength, in V / m; For free space wavenumber; is the relative permittivity of vacuum; Electrical conductivity of biological tissues, expressed in S / m; It is the relative permittivity; Angular frequency, in rad / s; Tissue density, in kg / m³; SAR, specific absorptivity, in W / kg; t is the specific heat capacity of the liver, in J / (kg·℃); T is the temperature, in ℃; t is the time, in s; k is the thermal conductivity, in W / (m·℃); Blood flow temperature; The specific heat capacity of blood is expressed in J / (kg·℃). This represents blood perfusion rate, expressed in units of 1 / s. The heat generated by tissue metabolism is expressed in W / m³; the subscript "b" indicates relevant blood parameters. Define the dynamic functional relationship between thermal and electrical parameters and temperature changes.

4. The method for creating a simulation model of personalized tumor treatment based on overlapping microwave ablation according to claim 3, characterized in that, The defined dynamic functional relationship between thermal and electrical parameters and temperature change includes: The dynamic functional relationship includes the specific heat capacity function and the relative permittivity function based on changes in water content. conductivity function Thermal conductivity function K; The specific heat capacity function based on changes in water content is: In the formula, and The specific heat capacities at 25 °C and 70 °C, respectively; This represents the temperature coefficient, with units of J / (kg). ); The latent heat constant is 2260 kJ / kg; W(T) is a function of water content. In the formula The value is the thermal conductivity at 25 °C.

5. The method for creating a simulation model of personalized tumor treatment based on overlapping microwave ablation according to claim 4, characterized in that, The process of dividing the overlapping microwave ablation finite element model into multiple target regions and setting boundary conditions for the target regions includes: An automatic mesh generation method was used to perform free tetrahedral mesh generation on the overlapping microwave ablation finite element model to obtain multiple target regions, including an outer surface region, a surface region, and an internal region. The surface region is set as an ideal electromagnetic scattering boundary, the outer surface region is set as an adiabatic boundary, and the inner region is set as the transient heat transfer description region within the tissue. A preset isotherm threshold is set, which is used to evaluate the necrosis range and characterize the size of the solidification region.

6. The method for creating a simulation model of personalized tumor treatment based on overlapping microwave ablation according to claim 5, characterized in that, The process of coupling and overlapping microwave ablation finite element models with microwave antennas, establishing a three-dimensional coordinate system with the transmitting end of the microwave antenna as the origin, includes: Multiple microwave antennas with preset parameters are inserted into the overlapping microwave ablation finite element model. A corresponding number of ablation points are formed according to the number of tumors in the overlapping microwave ablation finite element model. The corresponding ablation points are then inserted into the microwave antennas in sequence to simulate the surgical steps of clinical overlapping ablation. A three-dimensional coordinate system is established with the transmitter of the microwave antenna as the origin, which provides a spatial positioning reference for the microwave antenna to be inserted into the overlapping microwave ablation finite element model.

7. The method for creating a simulation model of personalized tumor treatment based on overlapping microwave ablation according to claim 6, characterized in that, The process involves setting an initial temperature for the divided overlapping microwave ablation finite element model, simulating the overlapping ablation process based on dynamic functional relationships and boundary conditions, adjusting the microwave antenna parameters, and simulating the overlapping ablation process again to obtain personalized ablation data, including: The overlapping ablation process consists of at least two consecutive ablation stages, with the initial temperature as the starting temperature. Each subsequent ablation stage uses the temperature at the end of the previous ablation stage as its initial temperature. The ablation phase includes an electromagnetic simulation phase, a transient thermal simulation phase, and a tissue state update phase. The electromagnetic simulation phase is used to calculate the electromagnetic energy deposition of the microwave antenna in the tissue at the current phase. The transient thermal simulation stage uses the current tissue temperature and electromagnetic energy deposition as inputs to calculate the final temperature; The tissue state update stage is based on the final temperature of the ablation stage and updates the thermal damage parameters of the tissue according to a preset isotherm threshold. The number of microwave antenna coupling and overlapping microwave ablation finite element models is adjusted according to the number of ablation points, and the corresponding continuous ablation stages are simulated according to the dynamic function relationship and boundary conditions to obtain the final thermal damage parameters. Adjust the parameters of the microwave antenna and simulate the overlapping ablation process again to obtain the corresponding final thermal damage parameters. Multiple final thermal damage parameters form personalized ablation data.

8. The method for creating a simulation model of personalized tumor treatment based on overlapping microwave ablation according to claim 7, characterized in that, The adjustment of microwave antenna parameters includes: The parameters of a microwave antenna include its position, power, angle, and time. After adjusting the parameters of the microwave antenna, the corresponding overlap ablation process is executed.

9. The method for creating a simulation model of personalized tumor treatment based on overlapping microwave ablation according to claim 8, characterized in that, The process of obtaining a predicted, visualized solidification zone based on personalized ablation data and calculating quantitative evaluation indicators includes: The total visualized coagulation zone was obtained by simulation and prediction based on personalized ablation data, and the coagulation distribution inside the tumor, at the tumor margin, and in the surrounding healthy tissue was plotted. Quantitative evaluation indicators are calculated based on personalized ablation data.

10. The method for creating a simulation model of personalized tumor treatment based on overlapping microwave ablation according to claim 9, characterized in that: The quantitative evaluation indicators include at least one of ablation safety margin, healthy tissue damage volume, and healthy tissue damage ratio. The ablation safety margin is the distance beyond the tumor boundary of the ablation zone; The volume of healthy tissue damaged refers to the volume of healthy tissue contained within the ablation zone. The healthy tissue damage ratio, which is the ratio of the volume of healthy tissue damage to the total ablation volume, is used to quantify the relative degree of damage to healthy tissue during the ablation process.

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