Simulation evaluation method based on focused ultrasound and electronic equipment

Abstract

The invention provides a simulation evaluation method based on focused ultrasound and electronic equipment, and relates to the technical field of computers. The method comprises the following steps: generating a three-dimensional part model and initial treatment parameters corresponding to a target part according to medical image data of the target part; based on the three-dimensional part model and the initial treatment parameters, transmitting a simulation ultrasonic pulse to a three-dimensional focus model corresponding to the target tissue in the three-dimensional part model; according to the method, the acoustic parameters and the thermal parameters of the preset sampling points in the three-dimensional part model are obtained, the evaluation item for the target tissue is calculated according to the acoustic parameters and the thermal parameters, and the evaluation result is generated according to the evaluation item, so that the three-dimensional part model can be constructed by considering the acoustic characteristics and the thermal characteristics corresponding to the target part, and the evaluation result is generated according to the three-dimensional part model. If the evaluation result indicates that the treatment effect corresponding to the simulation treatment operation is poor, the training medical staff can adjust the treatment scheme so as to optimize the treatment effect, summarize the treatment experience and improve the training effect.

Description

Technical Field

[0001] The present application relates to the field of computer technology, and in particular to a simulation evaluation method and electronic equipment based on focused ultrasound. Background Art

[0002] High-Intensity Focused Ultrasound (HIFU) is a non-invasive medical technology used primarily to treat specific types of tumors and other diseases. HIFU uses a high-energy, focused ultrasound beam to heat and destroy diseased tissue while minimizing the impact on surrounding healthy tissue. This technology can be used to treat deep tissue within the body and is widely used in various medical fields, particularly oncology.

[0003] In the prior art, when medical personnel are trained on the use of HIFU equipment based on virtual simulation technology, they can often only be trained on the basic operating procedures and usage methods of the HIFU equipment.

[0004] Therefore, the existing training methods are relatively simple, and the operation process of medical staff cannot be effectively evaluated during the training process, resulting in poor training results. Summary of the Invention

[0005] The purpose of this application is to address the deficiencies in the above-mentioned prior art and provide a simulation evaluation method and electronic equipment based on focused ultrasound, which can effectively evaluate the operation process of medical staff and improve the training effect.

[0006] To achieve the above objectives, the technical solutions adopted in the embodiments of the present application are as follows:

[0007] In a first aspect, the present invention provides a simulation evaluation method based on focused ultrasound, the method comprising:

[0008] generating a three-dimensional part model and initial treatment parameters corresponding to the target part based on medical imaging data of the target part, wherein the three-dimensional part model has acoustic and thermal properties corresponding to the target part, and the target part includes target tissue;

[0009] Based on the three-dimensional part model and the initial treatment parameters, emitting simulated ultrasound pulses to a three-dimensional lesion model corresponding to the target tissue in the three-dimensional part model, and acquiring acoustic parameters and thermal parameters of each preset sampling point in the three-dimensional part model;

[0010] According to the acoustic parameters and thermal parameters of each preset sampling point, evaluation items for the target tissue are calculated, and evaluation results are generated according to the evaluation items.

[0011] In an optional embodiment, the calculating of evaluation items for the target tissue based on the acoustic parameters and thermal parameters of each preset sampling point, and generating an evaluation result based on the evaluation items, includes: acquiring ultrasound image data of the target part based on medical image data of the target part;

[0012] Based on the ultrasound image data, initial attribute information of the target tissue is acquired, where the initial attribute information includes an initial volume and an initial blood flow signal area;

[0013] According to the acoustic parameters and thermal parameters of each preset sampling point and the initial attribute information of the target tissue, evaluation items for the target tissue are calculated, and evaluation results are generated according to the evaluation items.

[0014] In an optional embodiment, the evaluation items include the coverage level of the simulated focal area relative to the target tissue area, the damage level of the healthy tissue area in the target area, the ablation rate level of the target tissue, the blood flow signal evaluation results of the target tissue, and the evaluation results of the simulated ultrasonic pulse emission properties.

[0015] In an optional embodiment, based on the three-dimensional part model and the initial treatment parameters, emitting simulated ultrasound pulses to a three-dimensional lesion model corresponding to the target tissue in the three-dimensional part model, and acquiring acoustic parameters and thermal parameters of each preset sampling point in the three-dimensional part model, includes:

[0016] Construct a simulation treatment head model corresponding to the treatment head in the focused ultrasound device;

[0017] generating simulated ultrasonic pulses through the simulated treatment head model according to the initial treatment parameters;

[0018] Based on a preset ultrasound propagation model, emitting a simulated ultrasound pulse to a three-dimensional lesion model corresponding to the target tissue in the three-dimensional part model, and calculating acoustic parameters of each preset sampling point in the three-dimensional part model during the propagation of the simulated ultrasound pulse, wherein the acoustic parameters include sound pressure and / or sound intensity;

[0019] According to the acoustic parameters of each preset sampling point in the three-dimensional part model, thermal parameters of each preset sampling point are calculated by a preset thermal effect model, where the thermal parameters include thermal dose.

[0020] In an optional embodiment, the evaluation item includes: a coverage level of the simulation focus area relative to the target tissue area, and the calculation of the evaluation item for the target tissue based on the acoustic parameters and thermal parameters of each preset sampling point includes:

[0021] Determining a simulation focus area according to the acoustic parameters of each of the preset sampling points;

[0022] Acquiring a coverage parameter of the simulation focus area relative to the target tissue area, wherein the coverage parameter includes a first overlapping area or a first volume ratio;

[0023] The coverage level of the simulation focus area relative to the target tissue area is determined according to the coverage parameter.

[0024] In an optional embodiment, the evaluation item includes: the damage level of the healthy tissue area in the target part, and the evaluation item for the target tissue is calculated based on the acoustic parameters and thermal parameters of each preset sampling point, including:

[0025] Determine the simulation focus area based on the acoustic parameters of each preset sampling point;

[0026] Obtaining overlap parameters between the simulation focus area and the healthy tissue area;

[0027] Obtain thermal parameters of each preset sampling point in the healthy tissue area;

[0028] The damage level of the healthy tissue area in the target part is determined according to the coincidence parameter and the thermal parameters of each preset sampling point in the healthy tissue area.

[0029] In an optional embodiment, determining the damage level of the healthy tissue area in the target site based on the coincidence parameter and the thermal parameters of each preset sampling point in the healthy tissue area includes:

[0030] determining the sensitivity of healthy tissue in the overlapping area between the simulation focus area and the healthy tissue area according to the overlap parameter;

[0031] determining a first type of damage level of a healthy tissue area within the overlapped area according to the overlap parameter and the sensitivity of the healthy tissue within the overlapped area;

[0032] A second type of damage level of the healthy tissue area is determined according to the thermal parameters of each preset sampling point in the healthy tissue area.

[0033] In an optional embodiment, the simulated ultrasonic pulse is generated based on the ultrasonic emission angle and initial treatment parameters, and the initial treatment parameters include at least one of the following: the initial interval time between two adjacent consecutive simulated ultrasonic pulses, the initial interval time between two simulated ultrasonic pulses, the initial number of ultrasonic pulses emitted at each simulated treatment point, the initial duration of each simulated ultrasonic pulse, and the initial pulse intensity of each simulated ultrasonic pulse.

[0034] In an optional embodiment, the method further comprises:

[0035] If the evaluation result indicates that the ablation rate level of the target tissue and / or the damage level of the healthy tissue area in the target site do not meet the preset requirements, the initial treatment parameters are updated.

[0036] In a second aspect, the present invention provides a simulation evaluation device based on focused ultrasound, comprising:

[0037] a generation module for generating a three-dimensional part model and initial treatment parameters corresponding to the target part based on medical image data of the target part, wherein the three-dimensional part model has acoustic and thermal properties corresponding to the target part, and the target part includes target tissue;

[0038] an acquisition module, configured to transmit simulated ultrasound pulses to a three-dimensional lesion model corresponding to the target tissue in the three-dimensional part model based on the three-dimensional part model and the initial treatment parameters, and to acquire acoustic parameters and thermal parameters of each preset sampling point in the three-dimensional part model;

[0039] The calculation module is used to calculate the evaluation items for the target tissue according to the acoustic parameters and thermal parameters of each preset sampling point, and generate an evaluation result according to the evaluation items.

[0040] In a third aspect, the present invention provides an electronic device comprising: a processor, a storage medium and a bus, wherein the storage medium stores machine-readable instructions executable by the processor. When the electronic device is running, the processor and the storage medium communicate through the bus, and the processor executes the machine-readable instructions to perform the steps of the simulation evaluation method based on focused ultrasound as described in any of the aforementioned embodiments.

[0041] In a fourth aspect, the present invention provides a computer-readable storage medium having a computer program stored thereon, and when the computer program is executed by a processor, the steps of the simulation evaluation method based on focused ultrasound as described in any of the aforementioned embodiments are executed.

[0042] The beneficial effects of this application are:

[0043] The focused ultrasound-based simulation evaluation method and electronic device provided in the embodiments of the present application include: generating a three-dimensional part model and initial treatment parameters corresponding to the target part based on medical imaging data of the target part, wherein the three-dimensional part model has acoustic and thermal characteristics corresponding to the target part, and the target part includes target tissue; based on the three-dimensional part model and the initial treatment parameters, emitting simulated ultrasound pulses to a three-dimensional lesion model corresponding to the target tissue in the three-dimensional part model, and obtaining acoustic parameters and thermal parameters of each preset sampling point in the three-dimensional part model; calculating evaluation items for the target tissue based on the acoustic parameters and thermal parameters of each preset sampling point, and generating evaluation results based on the evaluation items, thereby taking into account the acoustic and thermal characteristics corresponding to the target part, constructing a three-dimensional part model, and performing simulated treatment to generate evaluation results based on the evaluation items, thereby ensuring the accuracy of the treatment plan. If the evaluation result indicates that the treatment effect corresponding to this simulated treatment operation is poor, then the trained medical staff can adjust the treatment according to the evaluation result to optimize the treatment effect, summarize the treatment experience, and improve the training effect. BRIEF DESCRIPTION OF THE DRAWINGS

[0044] In order to more clearly illustrate the technical solutions of the embodiments of the present application, the following is a brief introduction to the drawings required for use in the embodiments. It should be understood that the following drawings only show certain embodiments of the present application and therefore should not be regarded as limiting the scope. For ordinary technicians in this field, other relevant drawings can be obtained based on these drawings without creative work.

[0045] Figure 1 A schematic flow chart of a focused ultrasound-based simulation evaluation method provided in an embodiment of the present application;

[0046] Figure 2 A schematic flow chart of another simulation evaluation method based on focused ultrasound provided in an embodiment of the present application;

[0047] Figure 3 A schematic flow chart of another simulation evaluation method based on focused ultrasound provided in an embodiment of the present application;

[0048] Figure 4 A partial schematic diagram of a three-dimensional part model provided in an embodiment of the present application;

[0049] Figure 5 A schematic flow chart of another simulation evaluation method based on focused ultrasound provided in an embodiment of the present application;

[0050] Figure 6 A schematic flow chart of another simulation evaluation method based on focused ultrasound provided in an embodiment of the present application;

[0051] Figure 7A schematic flow chart of another simulation evaluation method based on focused ultrasound provided in an embodiment of the present application;

[0052] Figure 8 A schematic diagram of the functional modules of a simulation evaluation device based on focused ultrasound provided in an embodiment of the present application;

[0053] Figure 9 A schematic diagram of the structure of an electronic device provided in an embodiment of the present application. DETAILED DESCRIPTION

[0054] To make the objectives, technical solutions, and advantages of the embodiments of the present application more clear, the technical solutions in the embodiments of the present application will be clearly and completely described below in conjunction with the accompanying drawings of the embodiments of the present application. Obviously, the described embodiments are only part of the embodiments of the present application, not all of the embodiments. Generally, the components of the embodiments of the present application described and shown in the drawings herein can be arranged and designed in various different configurations.

[0055] Therefore, the following detailed description of the embodiments of the present application provided in the accompanying drawings is not intended to limit the scope of the present application for protection, but merely represents selected embodiments of the present application. All other embodiments obtained by persons of ordinary skill in the art based on the embodiments in the present application without creative work are within the scope of protection of the present application.

[0056] It should be noted that similar reference numerals and letters denote similar items in the following drawings, and therefore, once an item is defined in one drawing, it does not need to be further defined or explained in subsequent drawings.

[0057] Existing virtual simulation-based training for medical personnel on the use of HIFU devices often only covers the basic operating procedures and usage methods. Consequently, these training methods are relatively simplistic, making it impossible to effectively evaluate the medical personnel's operational processes, resulting in poor training effectiveness.

[0058] In view of this, an embodiment of the present application provides a simulation evaluation method based on focused ultrasound. The application of this method can realize effective evaluation of the simulated treatment process, obtain evaluation results, and then train medical staff to adjust the treatment process according to the evaluation results, summarize treatment experience, and improve training effects.

[0059] Before introducing this application, the working principle of the focused ultrasound device is briefly explained:

[0060] High-Intensity Focused Ultrasound (HIFU) is a medical device that uses high-intensity focused ultrasound energy for non-invasive treatment. It focuses ultrasound energy on specific parts of the body to produce thermal or mechanical effects, thereby achieving treatment of the tissue to be treated.

[0061] The working principle of the focused ultrasound device is that the focused ultrasound device includes a treatment head, which includes a transducer. The transducer can convert electrical energy into ultrasonic energy. The converted ultrasonic energy can be concentrated to the lesion area to be treated through geometric focusing or electronic focusing to form a focus; at the focus, the ultrasonic energy can be absorbed by the tissue, generating thermal effect or mechanical effect, among which the thermal effect generated will cause the local temperature to rise, leading to protein denaturation and cell necrosis; the mechanical effect generated can further produce cavitation effect, which can further cause tissue damage.

[0062] Figure 1 A flowchart of a simulation evaluation method based on focused ultrasound is provided in an embodiment of the present application. The execution subject of the method can be a computer, server, processor or other electronic device that can perform virtual simulation. The method can be used to virtually simulate focused ultrasound equipment and evaluate the simulation results. Optionally, the method of the present application can be applied to training medical staff to improve the training effect, or it can be applied to simulation in actual medical scenarios (for example, simulation can be performed before surgery to determine the best treatment plan, or the treatment plan can be adjusted in real time through simulation during surgery). The specific application scenario is not limited here and may vary according to the actual application scenario. Figure 1 As shown, the method includes:

[0063] Step 101: Generate a three-dimensional part model and initial treatment parameters corresponding to the target part based on the medical image data of the target part.

[0064] The three-dimensional part model has acoustic and thermal properties corresponding to the target part, which includes target tissue. Optionally, the target part can be any part of the human or animal body, such as the liver, pancreas, bones, joints, thyroid gland, etc., without limitation. The target tissue in the target part can be target lesion tissue in the target part, i.e., abnormal tissue in the target part, or tissue in the target part that requires ultrasonic irradiation energy, such as in the field of cosmetic surgery.

[0065] The medical imaging data of the target site may include computed tomography (CT), magnetic resonance imaging (MRI), positron emission tomography (PET), etc., which are not limited here.

[0066] In some embodiments, based on the medical imaging data of the target part, a three-dimensional part model corresponding to the target part can be generated using three-dimensional reconstruction technology. Optionally, when generating the three-dimensional part model, the medical imaging data can be segmented based on the characteristics of different types of tissue (such as skin, fat, muscle, fascia, bone, tumor, etc.) to obtain medical imaging data corresponding to each layer of tissue; based on the medical imaging data corresponding to each layer of tissue, according to the acoustic properties and thermal properties of each layer of tissue, a tissue model corresponding to each tissue can be generated using three-dimensional reconstruction technology. It can be understood that at this time, each tissue model will have corresponding acoustic properties and thermal properties; further, a three-dimensional part model corresponding to the target part can be constructed based on each tissue model.

[0067] It should be noted that the acoustic properties of tissue may include but are not limited to: the propagation speed of ultrasound in the tissue (i.e., the speed of sound), density, attenuation coefficient, etc. It is understandable that different acoustic properties will cause ultrasound to be scattered, reflected, or attenuated to varying degrees during propagation in each layer of tissue; the thermal properties of tissue may include but are not limited to: absorption coefficient, specific heat capacity, thermal conductivity, etc. It is understandable that different thermal properties will cause ultrasound to generate different thermal energy during propagation in each layer of tissue.

[0068] Optionally, when performing the specific segmentation, it can be implemented based on segmentation algorithms such as threshold segmentation, region growing, DeepLabV3+, U-Net, nnU-net, V-net, SAM2, etc., which are not limited here.

[0069] Furthermore, it should be noted that the initial treatment parameters may represent the pulse parameters of the initial simulated ultrasound pulses generated during the simulation process. Optionally, the pulse parameters may include pulse intensity, pulse duration, the number of initial ultrasound pulses emitted at each simulated treatment point, etc., which are not limited herein. Alternatively, the initial treatment parameters may be determined based on medical imaging data of the target site and according to a preset algorithm, or may be determined by the simulation user based on simulation experience. These parameters are not limited herein and may vary depending on the actual application scenario.

[0070] Step 102: Based on the three-dimensional part model and the initial treatment parameters, simulated ultrasound pulses are transmitted to the three-dimensional lesion model corresponding to the target tissue in the three-dimensional part model, and acoustic parameters and thermal parameters of each preset sampling point in the three-dimensional part model are obtained.

[0071] Optionally, the 3D part model can be configured to correspond to a plurality of preset sampling points. Of course, this application does not limit the number of preset sampling points in the 3D part model, and the number can be flexibly set according to the actual application scenario such as the size of the 3D part model and the simulation accuracy.

[0072] Based on the above description, after obtaining the initial treatment parameters, a simulated ultrasonic pulse can be generated and transmitted to the three-dimensional lesion model corresponding to the target tissue in the three-dimensional part model to realize the simulation of the focused ultrasound working process. During the simulation process, the acoustic parameters and thermal parameters of each preset sampling point in the three-dimensional part model can be further obtained.

[0073] Optionally, the acoustic parameters of each preset sampling point may include sound pressure, sound intensity, etc., and the thermal parameters of each preset sampling point may include temperature, but are not limited thereto.

[0074] Step 103: Calculate evaluation items for the target tissue based on the acoustic parameters and thermal parameters of each preset sampling point, and generate evaluation results based on the evaluation items.

[0075] Based on the above description, after determining the acoustic and thermal parameters of each preset sampling point in the three-dimensional part model, the simulated treatment for the target tissue can be evaluated based on this, the evaluation items for the target tissue can be calculated, and the final evaluation results can be generated based on this.

[0076] In some embodiments, the evaluation items for the target tissue may include multiple dimensions, for example, they may include: the coverage level of the simulation focus area relative to the target tissue area, the damage level of the healthy tissue area in the target area, the ablation rate level of the target tissue, etc., which are not limited here and may vary according to the actual application scenario.

[0077] Optionally, the evaluation result can indicate the quality of the treatment effect corresponding to the simulated treatment operation. It can be understood that if the evaluation result indicates that the treatment effect corresponding to the simulated treatment operation is poor, then optimization adjustments can be made next time to improve the treatment effect. For example, the treatment parameters can be adjusted. Of course, the specific adjustment method is not limited to this.

[0078] In some embodiments, the evaluation results can be presented in the form of a report that can include a rating scale (e.g., A to F) corresponding to each evaluation item, so that medical trainers can identify areas that require adjustment and optimization by previewing the lower-rated items in the evaluation results, thereby improving optimization efficiency. Of course, it should be noted that the evaluation results can also include improvement suggestions corresponding to each rating scale to help medical trainers quickly identify areas that require adjustment and optimization.

[0079] In summary, an embodiment of the present application provides a simulation evaluation method based on focused ultrasound, which includes: generating a three-dimensional part model and initial treatment parameters corresponding to the target part based on medical imaging data of the target part, wherein the three-dimensional part model has acoustic and thermal characteristics corresponding to the target part, and the target part includes target tissue; based on the three-dimensional part model and the initial treatment parameters, emitting simulated ultrasound pulses to a three-dimensional lesion model corresponding to the target tissue in the three-dimensional part model, and obtaining the acoustic parameters and thermal parameters of each preset sampling point in the three-dimensional part model; calculating evaluation items for the target tissue based on the acoustic parameters and thermal parameters of each preset sampling point, and generating evaluation results based on the evaluation items, thereby taking into account the acoustic and thermal characteristics corresponding to the target part, constructing a three-dimensional part model, and performing simulated treatment to generate evaluation results based on this, which can ensure the accuracy of the treatment plan. If the evaluation result indicates that the treatment effect corresponding to this simulated treatment operation is poor, then the trained medical staff can adjust the treatment according to the evaluation result to optimize the treatment effect, summarize the treatment experience, and improve the training effect.

[0080] Figure 2 A flow chart of another simulation evaluation method based on focused ultrasound provided in an embodiment of the present application. In an optional embodiment, as Figure 2 As shown above, the evaluation items for the target tissue are calculated based on the acoustic parameters and thermal parameters of each preset sampling point, and the evaluation results are generated based on the evaluation items, including:

[0081] Step 201: Acquire ultrasound image data of the target part according to the medical image data of the target part.

[0082] Optionally, during the specific acquisition, 3D volume data containing acoustic characteristics can be first generated based on the medical imaging data of the target area; then, based on the 3D volume data, an acoustic simulation algorithm (such as ray tracing, finite element method or wave equation solution, etc.) is used to simulate the propagation of ultrasound in the tissue; echo signals are generated according to the reflection, scattering and attenuation characteristics of ultrasound in the tissue; further, the echo signals can be synthesized into ultrasound image data using algorithms such as delay and sum.

[0083] Of course, it should be noted that, depending on the actual application scenario, the process of generating ultrasound image data is not limited to this.

[0084] Step 202: Acquire initial attribute information of the target tissue based on the ultrasound image data.

[0085] Optionally, the initial attribute information includes an initial volume and an initial blood flow signal area.

[0086] Among them, the initial attribute information of the target tissue can represent the characteristic parameters of the target tissue before treatment, for example, it can include the volume of the target tissue before treatment (i.e., the initial volume) and the blood flow signal area before treatment (i.e., the initial blood flow signal area), but is not limited to this.

[0087] Depending on the actual application scenario, other characteristic parameters may also be included, for example, the area and temperature of the target tissue before treatment, etc., which are not limited here and may vary depending on the actual application scenario.

[0088] Optionally, when obtaining the initial properties of the target tissue based on the ultrasound image data, it can be calculated by combining segmentation technology, three-dimensional reconstruction technology, etc.

[0089] For example, the calculation of the target tissue volume before treatment can be used as an example. Alternatively, the target tissue region can be segmented and determined based on ultrasound image data using manual, semi-automatic, or fully automatic segmentation techniques. Ultrasound slices of the target tissue region at different angles can be registered using 3D reconstruction techniques, and a 3D surface model of the target tissue region can be generated using a surface reconstruction algorithm. Subsequently, the target tissue volume before treatment can be calculated using a pixel / voxel approach. Of course, it should be noted that the specific calculation method is not limited to this.

[0090] Step 203 : Calculate evaluation items for the target tissue according to the acoustic parameters and thermal parameters of each preset sampling point and the initial attribute information of the target tissue, and generate evaluation results according to the evaluation items.

[0091] Optionally, during the specific evaluation, the target attribute information of the target tissue can be estimated based on the acoustic parameters and thermal parameters of each preset sampling point. The target attribute information can be compared with the initial attribute information to calculate the evaluation items for the target tissue, and generate the evaluation results based on the evaluation items.

[0092] The target attribute information of the target tissue may represent characteristic parameters of the target tissue after treatment, for example, the volume of the target tissue before treatment (ie, the target volume) and the blood flow signal area after treatment (ie, the target blood flow signal area).

[0093] By applying the embodiments of the present application, it is possible to calculate the evaluation items for the target tissue based on the attribute information of the target tissue before and after simulated treatment, and obtain more accurate evaluation results. In other words, it is possible to provide real-time feedback based on the performance of trained medical staff. Through an adaptive learning feedback mechanism, it helps to quickly improve the operator's treatment skills.

[0094] In an optional embodiment, the evaluation items include the coverage level of the simulated focal area relative to the target tissue area, the damage level of the healthy tissue area in the target area, the ablation rate level of the target tissue, the blood flow signal evaluation results of the target tissue, and the evaluation results of the simulated ultrasonic pulse emission properties.

[0095] Optionally, each evaluation item may correspond to a corresponding evaluation level, which may include 6 levels, but is not limited thereto and may be flexibly set according to actual application scenarios.

[0096] Among them, the coverage level of the simulated focus area relative to the target tissue area can be used to evaluate whether the simulated focus area can accurately cover the target tissue area, that is, whether precise treatment can be achieved.

[0097] The damage level of the healthy tissue area in the target area can be used to evaluate the impact on the healthy tissue in the target area other than the target tissue during treatment, and avoid unnecessary transmission of ultrasound pulses to the surrounding healthy tissue, which will cause higher temperature of the healthy tissue and cause potential damage.

[0098] The ablation rate level of the target tissue can be used to evaluate the reduction in target tissue volume before and after treatment, as well as the ablation effect.

[0099] In some embodiments, the ablation rate level of the target tissue can be determined based on the ablation rate of the target tissue and preset ablation rate level classification criteria. The ablation rate of the target tissue can be calculated using the following formula: ablation rate of target tissue = (volume of target tissue before treatment - volume of target tissue after treatment) / volume of target tissue before treatment × 100%.

[0100] Optionally, the preset ablation rate classification conditions can be set as follows: where the ablation rate of the target tissue is W, if W ≥ 90%, it means that after treatment, the ablation effect is excellent, the volume of the target tissue is significantly reduced, and it is almost completely ablated, and the corresponding ablation rate grade is A; if 70% < W ≤ 89%, it means that after treatment, the ablation effect is good, the volume of the target tissue is significantly reduced, and most areas are ablated, and the corresponding ablation rate grade is B; if 50% < W ≤ 69%, it means that after treatment, the ablation effect is moderate, the volume of the target tissue is partially reduced, and the ablation range is ≤ 50%. The ablation rate is relatively limited, and the corresponding ablation rate grade is C; if 30% < W ≤ 49%, it means that after treatment, the ablation effect is general, the volume of the target tissue is slightly reduced, and the ablation range is limited, and the corresponding ablation rate grade is D; if 10% < W ≤ 29%, it means that after treatment, the ablation effect is poor, the volume of the target tissue is not significantly reduced, and the ablation range is small, and the corresponding ablation rate grade is E; if W ≤ 10%, it means that after treatment, the ablation effect is ineffective, the volume of the target tissue is almost unchanged, the ablation range is extremely small or the treatment goal is not achieved, and the corresponding ablation rate grade is F.

[0101] Of course, it should be noted that the preset ablation rate classification conditions are not limited to this and can be flexibly set according to the actual application scenario. In addition, it should be noted that the ablation rate grades from low to high are: A, B, C, D, E, F, among which the higher the ablation rate grade, the worse the ablation effect.

[0102] The blood flow signal evaluation results of the target tissue can evaluate the changes in blood flow signals inside and around the target tissue before and after treatment.

[0103] In some embodiments, the blood flow signal assessment result of the target tissue can be determined based on the blood flow signal area change rate of the target tissue region and a preset change rate classification condition. The blood flow signal area change rate of the target tissue region can be calculated using the following formula: blood flow signal area change rate of the target tissue region = (blood flow signal area of the target tissue region before treatment - blood flow signal area of the target tissue region after treatment) / blood flow signal area of the target tissue region before treatment × 100%.

[0104] Optionally, the preset change rate level division conditions can be set as follows: where the blood flow signal area change rate of the target tissue region is recorded as Z. If, after treatment, there is no blood flow signal inside and around the target tissue region, it indicates complete ablation, and the corresponding blood flow signal evaluation level is A; Z>90%, it means that after treatment, there are very few blood flow signals inside and around the target tissue region, indicating that most areas are ablated, and the corresponding blood flow signal evaluation level is B; if 50%<Z≤90%, it means that after treatment, the blood flow signals inside and around the target tissue region are significantly reduced, indicating that part of the area is ablated, and the corresponding blood flow signal evaluation level is B. The corresponding blood flow signal evaluation level is C; if 10%<Z≤50%, it means that after treatment, the blood flow signals inside and around the target tissue area are slightly reduced, indicating that the ablation range is limited, and the corresponding blood flow signal evaluation level is D; if Z≤10%, it means that after treatment, the blood flow signals inside and around the target tissue area have no obvious changes, indicating that the ablation effect is poor, and the corresponding blood flow signal evaluation level is E; In addition, it should be noted that if the blood flow signals inside and around the target tissue area increase after treatment, it may indicate that the treatment is ineffective or the lesion is progressing, and the corresponding blood flow signal evaluation level is F.

[0105] Of course, it should be noted that the setting of the preset change rate classification conditions is not limited to this and can be flexibly set according to the actual application scenario. In addition, it should be noted that the blood flow signal evaluation levels are from low to high: A, B, C, D, E, F, among which the higher the blood flow signal evaluation level, the worse the ablation effect.

[0106] The evaluation results of the simulated ultrasonic pulse emission properties can be used to indicate whether the ultrasonic emission angle of the simulated ultrasonic pulse is appropriate. Optionally, the setting of the ultrasonic emission angle can refer to the following principles: the simulated focal area can overlap with the target tissue and avoid healthy tissue as much as possible.

[0107] Figure 3 A flow chart of another simulation evaluation method based on focused ultrasound provided in an embodiment of the present application. In an optional embodiment, as Figure 3 As shown, based on the three-dimensional part model and the initial treatment parameters, the above-mentioned method transmits a simulated ultrasonic pulse to the three-dimensional lesion model corresponding to the target tissue in the three-dimensional part model, and obtains the acoustic parameters and thermal parameters of each preset sampling point in the three-dimensional part model, including:

[0108] Step 301: Construct a simulation treatment head model corresponding to the treatment head in the focused ultrasound device.

[0109] Among them, in order to realize the generation and emission of simulated ultrasonic pulses, a corresponding simulated treatment head model can be constructed based on a three-dimensional environment according to the property parameters of the treatment head in the actual focused ultrasound device (for example, the radius of curvature, the outer opening diameter and inner opening diameter of the transducer in the treatment head, etc.).

[0110] Step 302: Generate simulated ultrasonic pulses using a simulated treatment head model according to the initial treatment parameters.

[0111] Specifically, during the generation, initial treatment parameters may be set through a treatment parameter setting interface based on a virtual environment, and based on the set initial treatment parameters, simulated ultrasonic pulses may be generated through a simulated treatment head model.

[0112] Referring to the above description, the initial treatment parameters can characterize the pulse parameters of the initial simulated ultrasonic pulses generated during the simulation process, such as: pulse intensity, pulse duration, the number of initial ultrasonic pulses emitted at each simulated treatment point, etc.; then, during the simulation, the simulated treatment head model can be used to generate simulated ultrasonic pulses that meet the initial treatment parameters (for example, with a certain pulse intensity and a certain pulse duration).

[0113] Step 303: Based on the preset ultrasound propagation model, simulated ultrasound pulses are transmitted to the three-dimensional lesion model corresponding to the target tissue in the three-dimensional part model, and acoustic parameters of each preset sampling point in the three-dimensional part model during the propagation of the simulated ultrasound pulses are calculated.

[0114] Acoustic parameters include sound pressure and / or sound intensity. Optionally, the preset ultrasound propagation model can be constructed based on a wave equation model, a ray tracing model, an angular spectrum method, a finite element method, or the like. Its operating principle is to simulate the propagation of an ultrasound pulse in a three-dimensional part model using physical equations and numerical methods, thereby obtaining the acoustic parameters of each preset sampling point in the three-dimensional part model. Based on this, the sound field distribution and focal distribution can be further determined.

[0115] It should be noted that during the simulation process, the simulated ultrasonic pulses generated by the simulated treatment head model can be emitted to the three-dimensional lesion model, so that the ultrasonic energy generated by the simulated ultrasonic pulses can be concentrated to the three-dimensional lesion model through geometric focusing or electronic focusing to form a simulated focus area. Furthermore, relevant evaluation items can be calculated based on this in the future.

[0116] Figure 4 This is a partial schematic diagram of a three-dimensional part model provided in an embodiment of the present application. Figure 4 As shown, the three-dimensional part model includes: a first area model P1 corresponding to skin tissue, a second area model P2 corresponding to fat tissue, a third area model P3 corresponding to muscle tissue, a fourth area model P4 corresponding to bone tissue, and a fifth area model P5 corresponding to lesion tissue.

[0117] When emitting a simulated ultrasonic pulse to the three-dimensional lesion model corresponding to the target tissue (P5) in the three-dimensional part model based on the preset ultrasonic propagation model, it should be noted that when the ultrasonic pulse reaches a discontinuity or boundary, the sound wave will be refracted, some energy passes through the boundary to form a transmission wave, and the rest is reflected; and when the sound wave propagates in two different tissues, due to the difference in acoustic impedance between different tissues, the sound wave will be refracted and reflected at the critical surfaces of different tissues, causing the focus to shift and not be at the ideal focal position (for example, the geometric focus of the transducer in the simulated treatment head model). Therefore, by establishing a three-dimensional part model with acoustic and thermal characteristics and presetting the ultrasonic propagation model, the propagation process of the ultrasonic pulse in complex tissues can be simulated, the focus shift can be simulated, and the actual focus position can be simulated. Reference Figure 4 As shown, in some scenarios, the simulated focus area P6 can be obtained through simulation. Currently, it should be noted that the display position of the simulated focus area P6 is not limited to this.

[0118] It should be noted that, in some embodiments, different tissues may correspond to different acoustic properties (e.g., sound velocity, density, attenuation coefficient, etc.) and thermal properties (e.g., absorption coefficient, specific heat capacity, thermal conductivity, etc.). Table 1 shows the acoustic and thermal properties of some types of tissues.

[0119] Table 1

[0120]

[0121]

[0122] Optionally, the acoustic parameters of each preset sampling point in the three-dimensional part model may include sound pressure. Optionally, based on the sound pressure, the sound field may be further calculated. When calculating the sound field corresponding to the target tissue in the three-dimensional part model during the simulated ultrasonic pulse propagation process based on the preset ultrasonic propagation model, it may be calculated based on the Rayleigh-Sommerfeld diffraction integral model. For details, see the following calculation formula:

[0123]

[0124] Where ψ(r) represents the acoustic field corresponding to the target tissue in the three-dimensional part model, r_j represents the distance from the point source position on the transducer to the preset sampling point j in the three-dimensional part model, and k represents the wave number of the simulated ultrasonic pulse. λ represents the wavelength of the simulated ultrasonic pulse, ω represents the angular frequency of the simulated ultrasonic pulse, c represents the speed of the simulated ultrasonic pulse propagating in the tissue, s represents the area of the transducer in the simulated treatment head model, ds represents the unit area of each point source on the transducer that emits the simulated ultrasonic pulse, v s represents the normal particle velocity at the transducer.

[0125] Furthermore, when calculating the sound pressure, it can be further calculated based on the sound field calculated above, specifically referring to the following formula:

[0126]

[0127] Where p(r)_j represents the sound pressure at the preset sampling point j in the three-dimensional part model, ρ_j represents the density of the tissue at the preset sampling point j in the three-dimensional part model, represents the derivative of the acoustic field ψ(r) corresponding to the target tissue.

[0128] Based on the above, it should also be noted that the sound pressure in complex tissues can be calculated based on the above sound pressure calculation formula using the finite difference time domain method, pseudospectral method, hybrid angular spectrum method, or methods based on the k-Wave toolbox.

[0129] Referring to the above description, it can be understood that by calculating the sound field corresponding to the target tissue in the three-dimensional part model, the position of the simulation focus area in the three-dimensional part model, the sound pressure distribution of the simulation focus area, the size of the sound pressure of each preset sampling point, etc. can be determined. Among them, according to the sound pressure distribution of the simulation focus area, the sidelobe situation can be observed, that is, whether there is excessive energy in other areas except the simulation focus area, and the safety of the treatment can be predicted; and by obtaining the sound pressure of each preset sampling point, the thermal parameters of each preset sampling point can be better calculated in the future.

[0130] Step 304 : Calculate thermal parameters of each preset sampling point in the three-dimensional part model using a preset thermal effect model according to the acoustic parameters of each preset sampling point. The thermal parameters include thermal dose.

[0131] The thermal effect model describes the temperature changes caused by tissue absorption of ultrasonic energy to predict the range of heat diffusion and the extent of thermal damage. The biological heat conduction equation is used to calculate the temperature changes at each preset sampling point in the three-dimensional model. Numerical methods (such as the finite element method) can be used to determine the temperature distribution across the entire tissue region.

[0132] Optionally, during the specific calculation, the sound intensity of each preset sampling point can be calculated based on the sound pressure of each preset sampling point; the heat deposition rate of each preset sampling point can be calculated based on the sound intensity of each preset sampling point; the real-time temperature of each preset sampling point can be calculated based on the heat deposition rate of each preset sampling point; and the thermal dose of each preset sampling point can be calculated based on the real-time temperature of each preset sampling point.

[0133] It should be noted that thermal dose is used to quantify the biological effects of hyperthermia by converting heat exposure at different temperatures and times into equivalent minutes at 43°C. The thermal dose value (CEM43) is usually used to determine whether the irreversible damage threshold has been reached in order to assess the cumulative effect of thermal damage.

[0134] Optionally, in some embodiments, if CEM43 ≥ 240 min, it usually leads to complete tissue necrosis (such as tumor ablation, but irreversible damage to healthy tissue); if 60 min ≤ CEM43 < 240 min, it will cause partial cell damage, which may trigger inflammation or repair response; if CEM43 < 60 min, it is generally safe for tissues without obvious irreversible damage.

[0135] In some embodiments, the specific calculation may be performed using the following formula:

[0136] Q_j=2α_j×I_j

[0137] Wherein, Q_j represents the heat deposition rate at the preset sampling point j in the three-dimensional part model, α_j represents the acoustic absorption coefficient of the tissue at the preset sampling point j, and I_j represents the sound intensity at the preset sampling point j, which can be calculated based on the sound pressure p(r)_j at the preset sampling point j.

[0138] Based on the heat deposition rate at the preset sampling point j, the real-time temperature of the preset sampling point j can be further calculated. The specific calculation can be found in the following formula:

[0139]

[0140] Where W(t)_j represents the temperature of the preset sampling point j at time t, k_j represents the thermal conductivity at the preset sampling point j, ω_j b Represents the blood perfusion rate at the preset sampling point j, ρ_j b Represents the density at the preset sampling point j, C_j b represents the blood specific heat capacity at the preset sampling point j, t_j represents the temperature of the tissue at the preset sampling point j, T_j art represents the blood arterial temperature at the preset sampling point j, and Q_j represents the heat deposition rate at the preset sampling point j. In addition, it should be noted that is the heat conduction term, which is used to describe the heat diffusion.

[0141] Furthermore, the thermal dose at the preset sampling point j can be calculated by referring to the following formula:

[0142]

[0143] Wherein, CEM43_j represents the thermal dose at the preset sampling point j at time t, W(t)_j represents the temperature of the preset sampling point j at time t (unit, °C), Δt represents the duration of the temperature W(t)_j at the preset sampling point j, and R represents the temperature sensitivity coefficient, which is used to reflect the multiplying effect of each 1°C increase in temperature on the thermal damage rate. When T ≥ 43°C, R = 0.5, and when T < 43°C, R = 0.25.

[0144] For example, if a preset sampling point j is kept at 60°C for 5 seconds, then referring to the above formula, the thermal dose at the 5th second can be calculated as This value is greater than 240 min, and therefore usually results in complete tissue necrosis (eg, leading to tumor ablation, but causing irreversible damage to healthy tissue).

[0145] Alternatively, if a preset sampling point j is kept at 45°C for 30 minutes, then referring to the above formula, the thermal dose at the 30th minute can be calculated as 120 min (CEM43 = 0.5 (43-45) ×30=0.5 -2 × 30 = 120 min), which is less than 240 min. Therefore, if treatment is needed, the treatment time needs to be extended.

[0146] Figure 5 A flow chart of another simulation evaluation method based on focused ultrasound provided in an embodiment of the present application. In an optional embodiment, the evaluation items include: the coverage level of the simulation focus area relative to the target tissue area. Figure 5 As shown above, the evaluation items for the target tissue are calculated based on the acoustic parameters and thermal parameters of each preset sampling point, including:

[0147] Step 501: Determine a simulation focus area according to the acoustic parameters of each preset sampling point.

[0148] The simulation focus area is the spatial position where the sound pressure or sound intensity is the largest in the sound field. Therefore, the simulation focus area can be determined based on the sound pressure or sound intensity of each preset sampling point.

[0149] Of course, the present application does not limit the size of the simulation focus area, and it may correspond to areas or volumes of different sizes in different scenarios.

[0150] Step 502: Obtain coverage parameters of the simulation focus area relative to the target tissue area, where the coverage parameters include a first overlapping area or a first volume ratio.

[0151] The coverage parameter can be any value between 0 and 100%, and is not limited here. It is understood that a higher coverage parameter indicates higher treatment accuracy, less damage to healthy tissue, and better treatment effect.

[0152] It can be understood that in different application scenarios, the target tissue area can be a surface or have a certain volume. Therefore, the simulation focus area can be a surface or have a certain volume. Then, according to the actual application scenario, when calculating the coverage parameter between the two, it can be determined by the first overlapping area of the simulation focus area relative to the target tissue area, or it can be determined by the first volume ratio. There is no limitation here, and it can be flexibly selected according to the actual application scenario.

[0153] Step 503: Determine the coverage level of the simulation focus area relative to the target tissue area based on the coverage parameter.

[0154] Optionally, the coverage parameter and the coverage level have a certain mapping relationship. In some embodiments, the coverage level can be determined by referring to the following preset level mapping relationship. In some embodiments, the preset level mapping relationship can be:

[0155] Among them, the coverage parameter is M. If M ≥ 90%, the coverage level is A, indicating that the simulated focus area completely covers the target tissue area and the treatment effect is ideal; if 80% < M ≤ 90%, it means that the coverage of the simulated focus area is good, with a slight deviation, but still within an acceptable range, and the coverage level is B; if 70% < M ≤ 80%, it means that the simulated focus area has a certain deviation, and some target tissue areas are not fully covered and need to be adjusted, and the coverage level is C; if 60% < M ≤ 70%, it means that the simulation focus area has a large deviation, the treatment effect is limited, and a large adjustment is required, and the coverage level is D; if 0% < M ≤ 60%, it means that the simulation focus area almost does not cover the target tissue area, the treatment effect is significantly reduced, and the treatment parameters need to be readjusted, and the coverage level is E; if M = 0, it means that the simulation focus area does not cover the target tissue area at all, the treatment fails, and the treatment plan needs to be redesigned, and the coverage level is F.

[0156] Of course, it should be noted that the settings of the preset level mapping relationships are not limited to this and may vary depending on the actual application scenario. In addition, it should be noted that the coverage levels are from low to high: A, B, C, D, E, F, among which the higher the coverage level, the greater the deviation of the simulation focus area and the worse the treatment effect.

[0157] Figure 6 A flow chart of another simulation evaluation method based on focused ultrasound provided in an embodiment of the present application. In an optional embodiment, as Figure 6 As shown, in the above optional embodiment, the evaluation items include: the damage level of the healthy tissue area in the target part, and the above evaluation items for the target tissue are calculated based on the acoustic parameters and thermal parameters of each preset sampling point, including:

[0158] Step 601: Determine a simulation focus area based on the acoustic parameters of each preset sampling point.

[0159] Here, referring to the above description, the simulation focus area can be determined according to the sound pressure or sound intensity of each preset sampling point, that is, the area corresponding to the maximum sound pressure or sound intensity is determined as the simulation focus area.

[0160] Step 602: Obtain the overlap parameters between the simulation focus area and the healthy tissue area.

[0161] The healthy tissue region is the region other than the target tissue in the target site. Alternatively, the target tissue region in the target site can be determined based on the characteristics of the lesion using algorithms such as machine learning and deep learning.

[0162] Optionally, the overlap parameter may be used to indicate the size of the overlap area between the simulated focal area and the healthy tissue area. Optionally, the overlap parameter may include overlap area, overlap volume, overlap position, etc., which are not limited here and can be flexibly set according to actual application scenarios.

[0163] It is understandable that during the treatment process, when the simulated focus area completely overlaps with the target tissue, complete ablation of the target tissue can be achieved, and the damage to the healthy tissue area is relatively small, and the treatment effect is better; but in the actual treatment process, due to the influence of the simulated ultrasonic pulse emission angle, treatment parameters and the acoustic characteristics of the target part, the simulated focus area and the healthy tissue area may partially overlap. In this scenario, it is necessary to calculate the overlap parameters of the simulated focus area and the healthy tissue area, so that the damage to the healthy tissue area caused by the offset of the simulated focus area can be determined later.

[0164] Step 603: Acquire thermal parameters of each preset sampling point in the healthy tissue area.

[0165] Step 604: Determine the damage level of the healthy tissue area in the target site based on the coincidence parameter and the thermal parameters of each preset sampling point in the healthy tissue area.

[0166] Optionally, the damage level of healthy tissue areas within the target site can be assessed using two dimensions: a first dimension, based on the overlap parameters between the simulated focal area and the healthy tissue area, yielding a Category I damage level for the healthy tissue area; and a second dimension, based on the heat accumulation generated in the healthy tissue area during treatment, yielding a Category II damage level for the healthy tissue area. The introduction of the first dimension avoids the inaccurate assessment results often associated with a single assessment dimension based solely on heat accumulation, thereby improving both the accuracy and safety of the assessment.

[0167] Based on the above description, it can be understood that if it is necessary to evaluate the damage level of the healthy tissue area in the first dimension, the aforementioned method can be referred to to obtain the coincidence parameters; and if it is necessary to evaluate the damage level of the healthy tissue area in the target part in the second dimension, the thermal parameters of each preset sampling point in the healthy tissue area can be obtained based on the thermal parameters of each preset sampling point in the three-dimensional part model, and determined accordingly. The specific determination method can be referred to the following specific embodiment.

[0168] Figure 7 A flow chart of another simulation evaluation method based on focused ultrasound provided in an embodiment of the present application. In an optional embodiment, as Figure 7 As shown, the above-mentioned determination of the damage level of the healthy tissue area in the target part based on the coincidence parameter and the thermal parameters of each preset sampling point in the healthy tissue area includes:

[0169] Step 701: Determine the sensitivity of healthy tissue in the overlapping area between the simulation focus area and the healthy tissue area according to the overlap parameter.

[0170] The overlapping area between the simulation focus area and the healthy tissue area can be determined according to the above-mentioned overlapping parameters, for example, according to the overlapping coordinates indicated by the overlapping parameters, which is not limited here.

[0171] In some embodiments, the sensitivity of healthy tissue in the overlapping area can be determined based on the category of healthy tissue in the overlapping area. For example, tissues such as skin, fat, fascia, and muscle can be set as sensitive tissues, and other categories of tissue (such as bones) can be set as non-sensitive tissues.

[0172] Step 702: Determine the first type of damage level of the healthy tissue area in the overlapped area according to the overlap parameter and the sensitivity of the healthy tissue in the overlapped area.

[0173] The first-class damage level of the healthy tissue region within the overlapped area can represent the potential damage caused by the simulated focal region to the healthy tissue region. Optionally, during the specific determination, the overlap parameters of the simulated focal region and the healthy tissue region can be used to assess whether the treatment focus is too close to or enters the healthy tissue region. If so, further evaluation can be conducted in conjunction with tissue sensitivity to obtain a more detailed assessment result.

[0174] Optionally, the first injury grade of the healthy tissue area within the overlapping area may be determined by referring to the following grading standards:

[0175] In some embodiments, the overlap parameter includes the overlap volume N. If N=0, it means that the simulation focus area is completely concentrated in the target tissue area and has no effect on the sensitive tissue. The treatment is very safe, and the corresponding first-class damage level is A. If N1<N≤N2, and the healthy tissue in the overlap area is sensitive tissue, it means that the simulation focus area slightly exceeds the target tissue area, but the effect on the sensitive tissue is negligible and completely within the acceptable range. The corresponding first-class damage level is B. If N2<N≤N3, and the healthy tissue in the overlap area is sensitive tissue, it means that the simulation focus area exceeds the target tissue area and has a slight effect on the sensitive tissue. Further attention should be paid to the precise control of the focus. The corresponding first-class damage level is C. If N3<N If N4<N≤N5 and the healthy tissue in the overlapping area is sensitive tissue, it means that the simulation focus area deviates greatly and exceeds the target tissue area by a large margin. There is a certain risk of damage to the sensitive tissue, and the treatment plan needs to be adjusted. The corresponding first-class damage level is D. If N4<N≤N5 and the healthy tissue in the overlapping area is sensitive tissue, it means that the simulation focus area deviates too much and has a significant impact on the sensitive tissue. The treatment plan needs to be adjusted significantly. The corresponding first-class damage level is E. If N5<N≤N6 and the healthy tissue in the overlapping area is sensitive tissue, it means that the simulation focus area deviates completely and exceeds the target tissue area, causing serious damage to the healthy tissue. The treatment needs to be stopped immediately and the treatment plan needs to be re-evaluated. The corresponding first-class damage level is F.

[0176] Among them, N1<N2<N3<N4<N5. Of course, this application does not limit the values of N1, N2, N3, N4, and N5. In some embodiments, their values can be determined according to the size of the target tissue area. Of course, the specific setting method is not limited to this.

[0177] In addition, it should be noted that the first category injury levels from low to high are: A, B, C, D, E, F, among which the higher the first category injury level, the more serious the injury.

[0178] Based on the above description, it can be seen that by obtaining the first-class damage level of the healthy tissue area in the overlapping area, it is possible to evaluate whether the coverage area of the simulation focus area is reasonable and whether it exceeds the target tissue area, thereby avoiding unnecessary energy transfer to the surrounding healthy tissue and causing potential damage. Subsequently, by reasonably controlling parameters such as the positioning of the treatment focus, treatment time and focal area, it is possible to ensure that the healthy tissue is minimized and improve the overall treatment effect.

[0179] Step 703: Determine the second type of damage level of the healthy tissue area based on the thermal parameters of each preset sampling point in the healthy tissue area.

[0180] Among them, referring to the above-mentioned treatment principles, it can be seen that reasonable heat accumulation is helpful for the treatment of the target tissue area, but excessive heat accumulation may cause damage to healthy tissue. For example, according to medical research, the safe thermal dose threshold of healthy tissue is usually above 42°C. If the temperature exceeds this threshold and lasts for too long, it may cause tissue necrosis.

[0181] Therefore, the embodiment of the present application also introduces a second type of damage level for the healthy tissue area, which can characterize whether the heat generated during the treatment process is properly accumulated in the target tissue area while avoiding excessive thermal damage to the surrounding healthy tissue.

[0182] Optionally, for a healthy tissue area, when performing a specific evaluation, the thermal parameters of each preset sampling point in the healthy tissue area may be obtained first; and the second category damage level of the healthy tissue area may be determined based on the thermal parameters of each preset sampling point and preset evaluation conditions.

[0183] In some embodiments, the preset evaluation conditions may be set as follows:

[0184] Among them, the thermal parameters of the preset sampling point include: thermal dose S, then if S < S1, it means that the thermal accumulation of the preset sampling point is within the safe range, which can effectively treat the lesion area without damaging healthy tissue, and the corresponding second-category injury level is A; if S1 < S ≤ S2, it means that the thermal accumulation of the preset sampling point is slightly high, but does not exceed the safety threshold, and the risk of damage to healthy tissue is small, and the corresponding second-category injury level is B; if S2 < S ≤ S3, it means that the thermal accumulation of the preset sampling point is slightly high, and the healthy tissue corresponding to the preset sampling point will be at risk of certain thermal damage, and the corresponding second-category injury level is etc. The second category injury level is C; if S3<S≤S4, it means that the heat accumulation at the preset sampling point is too much, which may cause damage to the healthy tissue corresponding to the preset sampling point, and the treatment plan needs to be adjusted. The corresponding second category injury level is D; if S4<S≤S5, it means that the heat accumulation at the preset sampling point is seriously exceeded, the healthy tissue corresponding to the preset sampling point has been obviously damaged, the treatment is not appropriate, and the treatment plan needs to be redesigned. The corresponding second category injury level is E; if S5<S≤S6, it means that the heat accumulation at the preset sampling point is extremely high, causing irreversible damage to healthy tissue and treatment failure. The corresponding second category injury level is F.

[0185] Among them, S1<S2<S3<S4<S5. Of course, this application does not limit the values of S1, S2, S3, S4, and S5. In some embodiments, their values can be determined based on the safe thermal dose threshold of healthy tissue. Of course, the specific setting method is not limited to this.

[0186] In addition, it should be noted that the second category injury levels from low to high are: A, B, C, D, E, F, among which the higher the first category injury level, the more serious the injury.

[0187] By applying the embodiment of the present application, by introducing the second type of damage level, it is possible to evaluate the heat accumulation during the treatment process, analyze the propagation and distribution of heat energy in different tissues, avoid damage to healthy tissues, and then optimize the treatment effect through subsequent adjustments.

[0188] Based on the above embodiments, it can be seen that the simulation evaluation method based on focused ultrasound provided in the present application has the following technical effects: it can provide accurate feedback on treatment operations, wherein, through real-time data tracking and multi-dimensional evaluation, it can help operators identify problems in operation, adjust treatment plans in time, and improve the accuracy and safety of treatment; it can provide optimization suggestions based on the evaluation results, wherein, through multi-faceted evaluation, it can provide operators with targeted improvement suggestions and optimize treatment plans; it improves training effects, and trained medical staff can understand their own operating levels and make targeted improvements based on the evaluation reports fed back by the system, thereby accelerating the learning process and improving their operating skills; it improves treatment safety, wherein, by accurately evaluating the damage level of healthy tissue areas, it avoids overtreatment or damage to healthy tissue, and ensures safety during the treatment process.

[0189] In an optional embodiment, the simulated ultrasonic pulses are emitted according to the ultrasonic emission angle and initial treatment parameters, and the initial treatment parameters include at least one of the following: the initial interval time between two adjacent consecutive simulated ultrasonic pulses, the initial interval time between two simulated ultrasonic pulses, the initial number of ultrasonic pulses emitted at each simulated treatment point, the initial duration of each simulated ultrasonic pulse, and the initial pulse intensity of each simulated ultrasonic pulse.

[0190] Among them, the ultrasound emission angle, that is, the treatment posture, can optionally be based on the medical imaging data of the target part, combined with medical imaging preprocessing technology, sound beam path planning technology, etc., to find the optimal emission angle and focal position that avoids bones / gas. Of course, the specific determination method is not limited to this.

[0191] In some embodiments, the surface of the treatment area can be set perpendicular to the acoustic axis of the transducer to ensure that the sound beam of the simulated ultrasonic pulse enters the target tissue without deflection; or, in some embodiments, an inclined incidence can be set to avoid light and dark tissues such as nerves and blood vessels. Of course, the present application does not limit the inclination angle here, and it can be flexibly set according to the actual application scenario.

[0192] The initial interval between two consecutive simulated ultrasound pulses is the time interval between two consecutive pulses. For example, a short interval (50-200ms) is suitable for rapid treatment or tissues insensitive to thermal effects; a medium interval (201-500ms) is suitable for most treatment scenarios; and a long interval (501-1000ms) is suitable for high-energy treatment or heat-sensitive areas.

[0193] The initial interval between two simulated ultrasound pulses, also known as the initial cooldown time, is used to prevent tissue overheating and skin damage. For example, a short cooldown time (1-5 seconds) is suitable for low-energy treatments or tissues insensitive to thermal effects; a medium cooldown time (6-12 seconds) is suitable for most treatment scenarios, balancing treatment effectiveness and safety; and a long cooldown time (13-20 seconds) is suitable for high-energy treatments or heat-sensitive areas.

[0194] The number of initial ultrasound pulses emitted at each simulated treatment point, also known as the initial pulse count (ranges from 1 to 50). For example, a pulse count of 1-10 is suitable for superficial tissue or low-energy treatments; a pulse count of 11-30 is suitable for most treatment scenarios; and a pulse count of 31-50 is suitable for deep tissue or treatments requiring high energy deposition.

[0195] The initial duration of each simulated ultrasound pulse, also known as the duration of each simulated ultrasound pulse, is determined by the duration of the pulse. For example, a short duration (50-300ms) is suitable for superficial tissue or treatments requiring high precision; a medium duration (301-800ms) is suitable for most treatment scenarios; and a long duration (801-1500ms) is suitable for deep tissue or treatments requiring high energy deposition. However, excessively long durations may increase the risk of tissue damage and should be adjusted in conjunction with the cooling time.

[0196] The initial pulse intensity of each simulated ultrasound pulse, also known as the initial treatment level, increases with the higher the level. For example, low levels (levels 1-3) are suitable for superficial tissue or energy-sensitive areas (such as near nerves); medium levels (levels 4-6) are suitable for most treatment scenarios, such as tumor ablation and pain management; and high levels (levels 7-8) are suitable for deep tissue or situations requiring high-energy therapy. Choosing the appropriate level depends on the depth and type of target tissue and the intended treatment.

[0197] Based on the aforementioned initial treatment parameters, it is understood that a simulated ultrasound pulse with specific properties can be emitted based on a specific ultrasound emission angle to cause damage to the target tissue and achieve a therapeutic effect. Of course, it should be noted that the categories of initial treatment parameters are not limited to these and may also include other categories depending on the actual application scenario.

[0198] In an optional embodiment, the above method further includes:

[0199] If the evaluation result indicates that the ablation rate level of the target tissue and / or the damage level of the healthy tissue area in the target site do not meet the preset requirements, the initial treatment parameters are updated.

[0200] In some embodiments, the evaluation items may include: the damage level of the healthy tissue area in the target site and / or the ablation rate level of the target tissue. In this scenario, the initial treatment parameters can be updated based on whether the ablation rate level and / or the damage level meet the preset requirements.

[0201] For example, the initial treatment parameters include: the initial duration of each simulated ultrasonic pulse. It can be understood that the duration assessment is mainly to ensure that the duration of the treatment process can achieve the therapeutic effect without causing overtreatment or damage to the tissue. Among them, too long a duration may lead to excessive heat accumulation, while too short a duration may not achieve the expected therapeutic effect.

[0202] Optionally, if it is determined based on the ablation rate level and / or the damage level that this simulated treatment can effectively treat the lesion without damaging healthy tissue, then it means that the initial duration setting is in line with expectations, and the corresponding evaluation level is A; if it is determined based on the ablation rate level and / or the damage level that the treatment time of this simulated treatment is slightly longer, but does not affect the treatment effect and safety, then the corresponding evaluation level is B; if it is determined based on the ablation rate level and / or the damage level that the treatment time of this simulated treatment is somewhat too long, which may cause certain damage to healthy tissue, then the corresponding evaluation level is C; if it is determined based on the ablation rate level and / or the damage level that the treatment time of this simulated treatment is too long, and there is an obvious risk of healthy tissue damage, then the corresponding evaluation level is D; if it is determined based on the ablation rate level and / or the damage level that the treatment time of this simulated treatment is too short, the treatment effect does not meet expectations, and the lesion cannot be effectively treated, then the corresponding evaluation level is E; if it is determined based on the ablation rate level and / or the damage level that the treatment time of this simulated treatment is too short, the lesion cannot be effectively treated, and the treatment fails, then the corresponding evaluation level is F.

[0203] Based on the above description, when the evaluation levels are C, D, E and F, the duration in the initial treatment parameters can be adjusted. By adjusting the ablation rate level of the target tissue and / or the damage level of the healthy tissue area in the target area to meet the preset requirements, the treatment effect can be optimized, and it is also convenient for training medical staff to summarize treatment experience and improve training effects.

[0204] In summary, it can be seen that the present application provides a simulation evaluation method based on focused ultrasound, wherein trained medical staff can perform simulated treatment operations through a virtual simulation evaluation system, and during the simulated treatment process, each operation step can be tracked in real time (for example, simulation focus area adjustment, treatment parameter setting, ultrasound emission angle setting, etc.), and evaluation items for the target tissue can be calculated, and evaluation results can be generated based on the evaluation items. The evaluation results can further guide the trained medical staff to adjust the simulated treatment plan (for example, adjust the ultrasound emission angle to achieve the purpose of adjusting the propagation path of the ultrasound, adjust the treatment parameters so that the ultrasound energy can be efficiently transmitted and focused on the target area), optimize the treatment effect, summarize the treatment experience, and improve the training effect.

[0205] Figure 8 This is a functional module diagram of a simulation evaluation device based on focused ultrasound provided in an embodiment of the present application. The basic principle and technical effects of the device are the same as those of the corresponding method embodiment described above. For the sake of brief description, the parts not mentioned in this embodiment can be referred to the corresponding contents in the method embodiment. Figure 8 As shown, the simulation evaluation device 100 includes:

[0206] A generating module 110 is configured to generate a three-dimensional part model and initial treatment parameters corresponding to the target part based on medical imaging data of the target part, wherein the three-dimensional part model has acoustic and thermal properties corresponding to the target part, and the target part includes target tissue;

[0207] an acquisition module 120 for transmitting simulated ultrasound pulses to a three-dimensional lesion model corresponding to the target tissue in the three-dimensional part model based on the three-dimensional part model and the initial treatment parameters, and acquiring acoustic parameters and thermal parameters of each preset sampling point in the three-dimensional part model;

[0208] The calculation module 130 is configured to calculate evaluation items for the target tissue according to the acoustic parameters and thermal parameters of each preset sampling point, and generate an evaluation result according to the evaluation items.

[0209] In an optional embodiment, the calculation module 130 is specifically configured to obtain ultrasound image data of the target part based on the medical image data of the target part;

[0210] Based on the ultrasound image data, initial attribute information of the target tissue is acquired, where the initial attribute information includes an initial volume and an initial blood flow signal area;

[0211] According to the acoustic parameters and thermal parameters of each preset sampling point and the initial attribute information of the target tissue, evaluation items for the target tissue are calculated, and evaluation results are generated according to the evaluation items.

[0212] In an optional embodiment, the evaluation items include the coverage level of the simulated focal area relative to the target tissue area, the damage level of the healthy tissue area in the target area, the ablation rate level of the target tissue, the blood flow signal evaluation results of the target tissue, and the evaluation results of the simulated ultrasonic pulse emission properties.

[0213] In an optional embodiment, the acquisition module 120 is specifically used to construct a simulation treatment head model corresponding to the treatment head in the focused ultrasound device;

[0214] generating simulated ultrasonic pulses through the simulated treatment head model according to the initial treatment parameters;

[0215] Based on a preset ultrasound propagation model, emitting a simulated ultrasound pulse to a three-dimensional lesion model corresponding to the target tissue in the three-dimensional part model, and calculating acoustic parameters of each preset sampling point in the three-dimensional part model during the propagation of the simulated ultrasound pulse, wherein the acoustic parameters include sound pressure and / or sound intensity;

[0216] According to the acoustic parameters of each preset sampling point in the three-dimensional part model, thermal parameters of each preset sampling point are calculated by a preset thermal effect model, where the thermal parameters include thermal dose.

[0217] In an optional embodiment, the evaluation items include: a coverage level of the simulation focus area relative to the target tissue area, and the calculation module 130 is specifically configured to determine the simulation focus area based on the acoustic parameters of each of the preset sampling points;

[0218] Acquiring a coverage parameter of the simulation focus area relative to the target tissue area, wherein the coverage parameter includes a first overlapping area or a first volume ratio;

[0219] The coverage level of the simulation focus area relative to the target tissue area is determined according to the coverage parameter.

[0220] In an optional embodiment, the evaluation items include: damage level of healthy tissue area in the target part, and the calculation module 130 is specifically used to determine the simulation focus area according to the acoustic parameters of each preset sampling point;

[0221] Obtaining overlap parameters between the simulation focus area and the healthy tissue area;

[0222] Obtain thermal parameters of each preset sampling point in the healthy tissue area;

[0223] The damage level of the healthy tissue area in the target part is determined according to the coincidence parameter and the thermal parameters of each preset sampling point in the healthy tissue area.

[0224] In an optional embodiment, the calculation module 130 is specifically configured to determine the sensitivity of the healthy tissue in the overlapping area between the simulation focus area and the healthy tissue area according to the overlap parameter;

[0225] determining a first type of damage level of a healthy tissue area within the overlapped area according to the overlap parameter and the sensitivity of the healthy tissue within the overlapped area;

[0226] A second type of damage level of the healthy tissue area is determined according to the thermal parameters of each preset sampling point in the healthy tissue area.

[0227] In an optional embodiment, the simulated ultrasonic pulse is generated based on the ultrasonic emission angle and initial treatment parameters, and the initial treatment parameters include at least one of the following: the initial interval time between two adjacent consecutive simulated ultrasonic pulses, the initial interval time between two simulated ultrasonic pulses, the initial number of ultrasonic pulses emitted at each simulated treatment point, the initial duration of each simulated ultrasonic pulse, and the initial pulse intensity of each simulated ultrasonic pulse.

[0228] In an optional embodiment, the calculation module 130 is further configured to update the initial treatment parameters if the evaluation result indicates that the ablation rate level of the target tissue and / or the damage level of the healthy tissue area in the target site do not meet preset requirements.

[0229] The above-mentioned device is used to execute the method provided in the above-mentioned embodiment. Its implementation principle and technical effect are similar and will not be repeated here.

[0230] The above modules can be one or more integrated circuits configured to implement the above methods, such as one or more application-specific integrated circuits (ASICs), one or more microprocessors, or one or more field programmable gate arrays (FPGAs). For another example, when a module is implemented by scheduling program code through a processing element, the processing element can be a general-purpose processor, such as a central processing unit (CPU) or other processor that can call program code. For another example, these modules can be integrated together and implemented in the form of a system-on-a-chip (SOC).

[0231] Figure 9 This is a schematic diagram of the structure of an electronic device provided in an embodiment of the present application. The electronic device can be integrated into the above-mentioned simulation evaluation device. Figure 9As shown, the electronic device may include: a processor 210, a storage medium 220, and a bus 230. The storage medium 220 stores machine-readable instructions executable by the processor 210. When the electronic device is running, the processor 210 and the storage medium 220 communicate via the bus 230, and the processor 210 executes the machine-readable instructions to perform the steps of the above-mentioned method embodiment. The specific implementation methods and technical effects are similar and will not be repeated here.

[0232] Optionally, the present application further provides a storage medium storing a computer program, which, when executed by a processor, executes the steps of the above method embodiment. The specific implementation and technical effects are similar and will not be described in detail here.

[0233] In the several embodiments provided in this application, it should be understood that the disclosed devices and methods can be implemented in other ways. For example, the device embodiments described above are merely schematic. For example, the division of units is only a logical function division. In actual implementation, there may be other division methods, such as multiple units or components can be combined or integrated into another system, or some features can be ignored or not executed. Another point is that the mutual coupling or direct coupling or communication connection shown or discussed can be through some interfaces, indirect coupling or communication connection of devices or units, which can be electrical, mechanical or other forms.

[0234] Units described as separate components may or may not be physically separate, and components shown as units may or may not be physical units, that is, they may be located in one place or distributed across multiple network units. Some or all of these units may be selected to achieve the purpose of this embodiment according to actual needs.

[0235] In addition, the functional units in the various embodiments of the present application may be integrated into a single processing unit, or each unit may exist physically separately, or two or more units may be integrated into a single unit. The aforementioned integrated units may be implemented in the form of hardware or in the form of hardware plus software functional units.

[0236] The above-mentioned integrated unit implemented in the form of a software functional unit can be stored in a computer-readable storage medium. The above-mentioned software functional unit is stored in a storage medium and includes a number of instructions for causing a computer device (which can be a personal computer, server, or network device, etc.) or a processor (English: processor) to perform some steps of the methods of each embodiment of the present application. The aforementioned storage medium includes: a USB flash drive, a mobile hard disk, a read-only memory (English: Read-Only Memory, abbreviated: ROM), a random access memory (English: Random Access Memory, abbreviated: RAM), a magnetic disk or an optical disk, and other media that can store program code.

[0237] It should be noted that, in this document, relational terms such as "first" and "second" are used only to distinguish one entity or operation from another entity or operation, and do not necessarily require or imply any actual relationship or order between these entities or operations. Moreover, the terms "comprises," "comprising," or any other variations thereof are intended to cover non-exclusive inclusion, so that a process, method, article, or device that includes a series of elements includes not only those elements, but also other elements not explicitly listed, or elements inherent to such process, method, article, or device. In the absence of further limitations, an element defined by the phrase "comprising a ..." does not exclude the presence of other identical elements in the process, method, article, or device that includes the element.

[0238] The above are only preferred embodiments of the present application and are not intended to limit the present application. For those skilled in the art, the present application may have various changes and variations. Any modifications, equivalent substitutions, improvements, etc. made within the spirit and principles of the present application should be included in the scope of protection of the present application. It should be noted that similar numbers and letters represent similar items in the following figures. Therefore, once an item is defined in one figure, it does not need to be further defined and explained in subsequent figures. The above are only preferred embodiments of the present application and are not intended to limit the present application. For those skilled in the art, the present application may have various changes and variations. Any modifications, equivalent substitutions, improvements, etc. made within the spirit and principles of the present application should be included in the scope of protection of the present application.

Claims

1. A simulation evaluation method based on focused ultrasound, characterized in that: The method comprises: generating a three-dimensional part model and initial treatment parameters corresponding to the target part based on medical imaging data of the target part, wherein the three-dimensional part model has acoustic and thermal properties corresponding to the target part, and the target part includes target tissue; Based on the three-dimensional part model and the initial treatment parameters, emitting simulated ultrasound pulses to a three-dimensional lesion model corresponding to the target tissue in the three-dimensional part model, and acquiring acoustic parameters and thermal parameters of each preset sampling point in the three-dimensional part model; According to the acoustic parameters and thermal parameters of each preset sampling point, evaluation items for the target tissue are calculated, and evaluation results are generated according to the evaluation items.

2. The method according to claim 1, characterized in that Calculating evaluation items for the target tissue according to the acoustic parameters and thermal parameters of each preset sampling point, and generating evaluation results according to the evaluation items, includes: Acquiring ultrasound image data of the target part according to the medical image data of the target part; Based on the ultrasound image data, initial attribute information of the target tissue is acquired, where the initial attribute information includes an initial volume and an initial blood flow signal area; According to the acoustic parameters and thermal parameters of each preset sampling point and the initial attribute information of the target tissue, evaluation items for the target tissue are calculated, and evaluation results are generated according to the evaluation items.

3. The method according to claim 2, characterized in that The evaluation items include the coverage level of the simulated focus area relative to the target tissue area, the damage level of the healthy tissue area in the target part, the ablation rate level of the target tissue, the blood flow signal evaluation results of the target tissue, and the evaluation results of the simulated ultrasound pulse emission properties.

4. The method according to claim 1, wherein The step of transmitting a simulated ultrasonic pulse to a three-dimensional lesion model corresponding to the target tissue in the three-dimensional part model based on the three-dimensional part model and the initial treatment parameters, and acquiring acoustic parameters and thermal parameters of each preset sampling point in the three-dimensional part model, includes: Construct a simulation treatment head model corresponding to the treatment head in the focused ultrasound device; generating simulated ultrasonic pulses through the simulated treatment head model according to the initial treatment parameters; Based on a preset ultrasound propagation model, emitting a simulated ultrasound pulse to a three-dimensional lesion model corresponding to the target tissue in the three-dimensional part model, and calculating acoustic parameters of each preset sampling point in the three-dimensional part model during the propagation of the simulated ultrasound pulse, wherein the acoustic parameters include sound pressure and / or sound intensity; According to the acoustic parameters of each preset sampling point in the three-dimensional part model, thermal parameters of each preset sampling point are calculated by a preset thermal effect model, where the thermal parameters include thermal dose.

5. The method according to claim 3, characterized in that The evaluation items include: the coverage level of the simulation focus area relative to the target tissue area, and the evaluation items for the target tissue are calculated based on the acoustic parameters and thermal parameters of each preset sampling point, including: Determining a simulation focus area according to the acoustic parameters of each of the preset sampling points; Acquiring a coverage parameter of the simulation focus area relative to the target tissue area, wherein the coverage parameter includes a first overlapping area or a first volume ratio; The coverage level of the simulation focus area relative to the target tissue area is determined according to the coverage parameter.

6. The method according to claim 1, characterized in that The evaluation items include: the damage level of the healthy tissue area in the target part, and the evaluation items for the target tissue are calculated based on the acoustic parameters and thermal parameters of each preset sampling point, including: Determine the simulation focus area based on the acoustic parameters of each preset sampling point; Obtaining overlap parameters between the simulation focus area and the healthy tissue area; Obtain thermal parameters of each preset sampling point in the healthy tissue area; The damage level of the healthy tissue area in the target part is determined according to the coincidence parameter and the thermal parameters of each preset sampling point in the healthy tissue area.

7. The method according to claim 6, characterized in that Determining the damage level of the healthy tissue area in the target part according to the coincidence parameter and the thermal parameters of each preset sampling point in the healthy tissue area includes: determining the sensitivity of healthy tissue in the overlapping area between the simulation focus area and the healthy tissue area according to the overlap parameter; determining a first type of damage level of a healthy tissue area within the overlapped area according to the overlap parameter and the sensitivity of the healthy tissue within the overlapped area; A second type of damage level of the healthy tissue area is determined according to the thermal parameters of each preset sampling point in the healthy tissue area.

8. The method according to any one of claims 1 to 7, characterized in that The simulated ultrasonic pulse is generated according to the ultrasonic emission angle and initial treatment parameters, and the initial treatment parameters include at least one of the following: the initial interval time between two adjacent continuous simulated ultrasonic pulses, the initial interval time between two simulated ultrasonic pulses, the number of initial ultrasonic pulses emitted at each simulated treatment point, the initial duration of each simulated ultrasonic pulse, and the initial pulse intensity of each simulated ultrasonic pulse.

9. The method according to claim 8, characterized in that The method further comprises: If the evaluation result indicates that the ablation rate level of the target tissue and / or the damage level of the healthy tissue area in the target site do not meet the preset requirements, the initial treatment parameters are updated.

10. An electronic device, characterized in that: include: A processor, a storage medium and a bus, wherein the storage medium stores machine-readable instructions executable by the processor. When the electronic device is running, the processor and the storage medium communicate via the bus, and the processor executes the machine-readable instructions to perform the steps of the simulation evaluation method based on focused ultrasound as described in any one of claims 1 to 9.

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