An individual precise transcranial magnetic stimulation system and optimization method

Abstract

The present invention discloses an individual precise transcranial magnetic stimulation system and optimization method, belonging to the technical field of medical auxiliary equipment. The system includes a main control module, an individual head model optimization module, a magnetic field excitation module, a stimulation coil, a magnetic shielding headgear, a parameter monitoring module, a power module, a communication module and an interaction module. The system does not need to change the conventional magnetic stimulation coil design, but integrates magnetic shielding materials with different conductivity, magnetic permeability, structure and thickness into an easy-to-wear headgear, and at the same time combines individual magnetic resonance data to establish a magnetic stimulation simulation headgear. According to the organizational structure and characteristics of the head model of different individuals, the optimization algorithm is used to select the magnetic shielding headgear with appropriate parameters to achieve the preset focusing and induced electric field strength in the target area, and finally achieve individual precise transcranial magnetic stimulation. The present invention effectively improves the focusing of transcranial magnetic stimulation and enhances the convenience and safety of clinical use.

Description

Technical Field

[0001] The present invention relates to the technical field of medical auxiliary equipment, and in particular to an individual precise transcranial magnetic stimulation system and an optimization method. Background Art

[0002] Transcranial Magnetic Stimulation (TMS) is a promising non-invasive brain regulation technology that mainly generates a pulsed magnetic field through a coil, which in turn induces an electric field in the brain to regulate neural activity. This technology has been widely used in the treatment of various neuropsychiatric diseases and has also shown significant potential in enhancing the cognitive function of healthy individuals.

[0003] Improving the targeting and focusing of TMS has always been a challenge. The electric field distribution generated by TMS in the brain is closely related to its regulatory effect. At present, the most commonly used TMS coil is the "8"-shaped coil. Although this coil can effectively activate the cerebral cortex, its focusing is relatively poor. Therefore, many studies have proposed schemes to optimize TMS coils to enhance their focusing, including multi-coil combinations, modifications of coil winding patterns (such as U-shaped and butterfly coils), etc. At the same time, the introduction of nanomagnetic particles has also been studied to improve the targeting accuracy of magnetic stimulation.

[0004] In addition to optimizing the coil geometry, the researchers systematically studied rectangular window shields made of highly conductive materials through finite element simulation to improve the focusing of the "8"-shaped coil. These studies found that window size affects focusing and stimulation intensity, and that a certain trade-off is required between focusing and stimulation intensity. These studies used simulations of human and mouse head models to demonstrate the effects of these window shields, but further research is needed for full verification. Other studies have also combined a high permeability core with a specially designed coil to induce an electric field that slowly decays with depth, thereby improving focusing and field strength.

[0005] In addition, simulation modeling based on individual tissue structure is also used to optimize coil placement to achieve relevant intervention optimization. This method models the individual's brain anatomical structure in detail and simulates the impact of different coil placement positions on the electric field distribution, thereby finding the best coil placement plan to achieve the best treatment effect.

[0006] But overall, the current traditional transcranial magnetic stimulation system mainly optimizes intervention targeting by optimizing the TMS coil design, but this requires modification of the coil or complex clinical operations, which limits the widespread application of these methods. It is also difficult to consider the impact of individual tissue structure and dielectric differences, making it difficult to achieve individual precise transcranial magnetic stimulation.

[0007] Therefore, it is necessary to develop an individual precise and targeted transcranial magnetic stimulation system to overcome the above shortcomings. Summary of the invention

[0008] The present invention overcomes the shortcomings of the prior art and provides an individual precise transcranial magnetic stimulation system and optimization method to optimize the distribution of the induced electric field and improve the focus of the stimulation. The system does not need to change the conventional magnetic stimulation coil design, but integrates magnetic shielding materials with different conductivity, magnetic permeability, structure and thickness into an easy-to-wear headgear. The magnetic shielding headgear can weaken the magnetic field strength induced by TMS, thereby enhancing its focus. At the same time, a magnetic stimulation simulation head model (also referred to as a head model) is established in combination with individual magnetic resonance data. According to the tissue structure and tissue structure characteristics of the head model of different individuals, the result optimization algorithm selects the shielding headgear with appropriate parameters to achieve the preset focus and induced electric field strength in the target area, and finally achieve individual precise transcranial magnetic stimulation.

[0009] In order to achieve the above object, the technical solution adopted by the present invention is:

[0010] In a first aspect, the present invention provides a method for optimizing an individual head model of an individual transcranial magnetic stimulation system with high precision, comprising:

[0011] S1. Based on the imaging data of the individual to be treated with transcranial magnetic stimulation, an individual head model is constructed through brain tissue segmentation and three-dimensional reconstruction;

[0012] S2. Select a magnetic shielding headgear from the optional headgear set as the current simulation headgear, and form a magnetic shielding headgear model with the same structure and thickness as the current simulation headgear by expanding the scalp layer in the individual head model outward according to its thickness and opening method; then put the magnetic shielding headgear model on the individual head model, and place the virtualized transcranial magnetic stimulation coil model on the magnetic shielding headgear model at a specified angle, so as to form a finite element simulation model consisting of the individual head model, the magnetic shielding headgear model and the transcranial magnetic stimulation coil model;

[0013] S3. Perform finite element meshing on the finite element simulation model and assign dielectric parameters to the mesh nodes, wherein the mesh nodes in the individual head model need to be assigned magnetic permeability and electrical conductivity corresponding to the brain tissue type according to the brain tissue in which they are located, and the mesh nodes in the magnetic shielding headgear model and the transcranial magnetic stimulation coil model need to be assigned magnetic permeability and electrical conductivity matching the current simulation headgear material;

[0014] S4, according to the target excitation parameters of the transcranial magnetic stimulation coil and the target magnetic stimulation target area pre-marked on the individual head model, the finite element simulation model after the parameter assignment is completed is performed to obtain the spatial electric field distribution induced by the current simulation headgear in the target magnetic stimulation target area;

[0015] S5, for each magnetic shielding headgear in the optional headgear set, respectively simulate according to S2 to S4 to obtain the spatial electric field distribution induced in the target magnetic stimulation target area;

[0016] S6. Based on the spatial electric field distribution corresponding to each magnetic shielding headgear in the optional headgear set, target optimization is performed in combination with a pre-set optimization target to determine the optimal magnetic shielding headgear suitable for the individual to be treated with transcranial magnetic stimulation.

[0017] As a preferred embodiment of the first aspect, the imaging data is magnetic resonance imaging data or CT data.

[0018] As a preferred embodiment of the first aspect, the optimization target needs to consider both the electric field strength and focusing of transcranial magnetic stimulation in the target magnetic stimulation area.

[0019] As a preferred embodiment of the first aspect, the optional headgear set is a set including all optional prefabricated standard magnetic shielding headgear, and different prefabricated standard magnetic shielding headgear in the set have different magnetic permeability, electrical conductivity, thickness and opening methods;

[0020] Alternatively, the optional headgear set is a set including optional virtual magnetic shielding headgear, and parameters corresponding to different virtual magnetic shielding headgear in the set cover different discrete sampling value combinations of magnetic permeability, electrical conductivity, thickness and opening method.

[0021] In a second aspect, the present invention provides an individual precise transcranial magnetic stimulation system, which includes a main control module, an individual head model optimization module, a magnetic field excitation module, a stimulation coil, a magnetic shielding headgear, a parameter monitoring module, a power supply module and an interaction module;

[0022] The main control module is respectively connected to the individual head model optimization module, the magnetic field excitation module, the parameter monitoring module, the power module and the interaction module to realize information processing and central function control;

[0023] The power module is used to provide power for the entire transcranial magnetic stimulation system;

[0024] The individual head model optimization module is used to receive input imaging data of the individual to be treated with transcranial magnetic stimulation, and execute the individual head model optimization method for the individual accurate transcranial magnetic stimulation system as described in any one of the solutions of the first aspect above, and send the optimization result to the interaction module to assist in achieving the optimal selection of the magnetic shielding headgear;

[0025] The interaction module is used to provide a human-computer interaction function to the user; the human-computer interaction function includes importing the imaging data and visually displaying the optimization results;

[0026] The magnetic field excitation module is respectively connected to the individual head model optimization module, the parameter monitoring module and the stimulation coil, and is used to output a transcranial magnetic stimulation excitation voltage or current to the stimulation coil under the control of the main control module;

[0027] The stimulation coil is used to cooperate with the magnetic shielding headgear to generate a transcranial magnetic stimulation magnetic field under the stimulation of the magnetic field stimulation module;

[0028] The parameter monitoring module is used to monitor the output current and voltage of the magnetic field excitation module and the temperature of the stimulation coil, and send the monitoring information to the main control module in real time to achieve feedback adjustment of the magnetic field excitation module.

[0029] As a preferred embodiment of the second aspect, the system further includes a communication module connected to the main control module, and the communication module is used to establish a communication connection between the transcranial magnetic stimulation system and an external device.

[0030] As a preferred embodiment of the second aspect, the communication mode of the communication module is wired communication, or wireless Bluetooth or WIFI communication.

[0031] As a preferred embodiment of the above-mentioned second aspect, the interaction module is a local device or a remote device with a display screen, and its interaction method is one or more of GUI interface human-computer interaction, physical button control, and touch button control.

[0032] In a third aspect, the present invention provides a computer-readable storage medium having a computer program stored thereon. When the computer program is executed by a processor, the method for optimizing an individual head model for an individual precise transcranial magnetic stimulation system as described in any one of the schemes of the first aspect above is implemented.

[0033] In a fourth aspect, the present invention provides a computer electronic device comprising a memory and a processor;

[0034] The memory is used to store computer programs;

[0035] The processor is used to implement the individual head model optimization method for an individual precise transcranial magnetic stimulation system as described in any one of the solutions of the first aspect when executing the computer program.

[0036] Compared with the prior art, the present invention has the following beneficial effects:

[0037] (1) The present invention uses magnetic shielding materials with different conductivity, magnetic permeability, structure and thickness to form an easy-to-wear headgear, so that the magnetic shielding headgear can effectively weaken the magnetic field strength induced by TMS and significantly enhance the focus of stimulation. At the same time, the present invention combines individual magnetic resonance data to establish a magnetic stimulation simulation head model, and selects a shielding headgear with appropriate parameters through an optimization algorithm to ensure that the preset focus and induced electric field strength are achieved in the target area, thereby improving the focus of stimulation.

[0038] (2) The present invention does not require any modification to the existing magnetic stimulation coil, and directly integrates the magnetic shielding material into an easy-to-wear headgear, thereby simplifying the application process. Moreover, the magnetic shielding headgear of the present invention can be designed as an easy-to-wear headgear, making clinical application more convenient and quick, increasing the patient's comfort and compliance, and facilitating clinical use.

[0039] (3) The present invention reduces the electric field intensity in non-target areas by optimizing the electric field distribution, reduces the impact on non-target areas, and improves the safety of treatment. The shielding headgear is relatively simple to design and produce with low cost, which helps to reduce the overall treatment cost and improve the accessibility of the technology. BRIEF DESCRIPTION OF THE DRAWINGS

[0040] In order to more clearly illustrate the embodiments of the present invention or the technical solutions in the prior art, the drawings required for use in the embodiments or the description of the prior art are briefly introduced below. Obviously, the drawings described below are only some embodiments recorded in the present invention. For those of ordinary skill in the art, other drawings can be obtained based on these drawings without creative work.

[0041] Figure 1 It is a schematic diagram of the steps of an individual head model optimization method for an individual precise transcranial magnetic stimulation system in an embodiment of the present invention;

[0042] Figure 2 is a principle block diagram of an individual precise transcranial magnetic stimulation system in an embodiment of the present invention;

[0043] Figure 3 is a principle block diagram of another individual precise transcranial magnetic stimulation system in an embodiment of the present invention;

[0044] Figure 4 It is a structural schematic diagram of a magnetic shielding head cover in an embodiment of the present invention;

[0045] Figure 5 is a flowchart of individual head mold optimization in an embodiment of the present invention;

[0046] Figure 6 It is an exemplary result of the spatial electric field distribution of an individual under the application of magnetic shielding headgear with different thicknesses, opening methods, and magnetic permeabilities in the embodiment of the present invention;

[0047] Figure 7 These are exemplary results of the spatial electric field distribution of an individual under the application of a magnetic shielding headgear with different hole opening methods and conductivity in the embodiment of the present invention.

[0048] In the figure: 1. Main control module; 2. Individual head model optimization module; 3. Magnetic field excitation module; 4. Stimulation coil; 5. Magnetic shielding headgear; 6. Parameter monitoring module; 7. Power supply module; 8. Communication module; 9. Interaction module. DETAILED DESCRIPTION

[0049] In order to make the above-mentioned purpose, features and advantages of the present invention more obvious and easy to understand, the specific implementation mode of the present invention is described in detail below in conjunction with the accompanying drawings. In the following description, many specific details are set forth to facilitate a full understanding of the present invention. However, the present invention can be implemented in many other ways different from those described herein, and those skilled in the art can make similar improvements without violating the connotation of the present invention. Therefore, the present invention is not limited to the specific embodiments disclosed below. The technical features in each embodiment of the present invention can be combined accordingly without conflicting with each other.

[0050] In the description of the present invention, it should be understood that, unless otherwise clearly specified and limited, the terms "installed", "connected", and "connected" should be understood in a broad sense, for example, it can be a fixed connection, a detachable connection, or an integral connection; it can be a mechanical connection or an electrical connection; it can be directly connected or indirectly connected through an intermediate medium, and it can be the internal communication of two components. For ordinary technicians in this field, the specific meanings of the above terms in this application can be understood by specific circumstances.

[0051] See also Figure 1 As shown, in a preferred embodiment of the present invention, a method for optimizing an individual head model of an individual transcranial magnetic stimulation system with individual precision is provided, which includes the following steps S1 to S6. The specific implementation methods of each step are described in detail below.

[0052] S1. Based on the imaging data of the individual to be treated with transcranial magnetic stimulation, an individual head model is constructed through brain tissue segmentation and three-dimensional reconstruction.

[0053] It should be noted that the imaging data of the individual to be intervened by transcranial magnetic stimulation can be imported by the user or automatically associated or read from relevant medical equipment through a software program. In the present invention, the type of imaging data is not limited, for example, magnetic resonance imaging MRI data or CT data can be used to construct an individual head model. Based on the imaging data, the process of constructing an individual head model through brain tissue segmentation and three-dimensional reconstruction belongs to the prior art, which can be specifically selected according to the type of imaging data. Brain tissue segmentation can be achieved through models such as Unet, and the brain area needs to be segmented into tissue components such as scalp, skull, cerebrospinal fluid, gray matter, and white matter. Three-dimensional reconstruction can be achieved through software such as Comsol. Before reconstruction, it is best to perform pre-processing such as smoothing filtering and denoising on the image to ensure the reconstruction effect.

[0054] S2. Select a magnetic shielding headgear from the optional headgear set as the current simulation headgear, and form a magnetic shielding headgear model with the same structure and thickness as the current simulation headgear by expanding the scalp layer in the individual head model outward according to its thickness and opening method; then put the magnetic shielding headgear model on the individual head model, and place the virtualized transcranial magnetic stimulation coil model on the magnetic shielding headgear model at a specified angle, so as to form a finite element simulation model consisting of the individual head model, the magnetic shielding headgear model and the transcranial magnetic stimulation coil model.

[0055] It should be noted that the magnetic shielding headgear is mainly used to localize the shielding of the magnetic field generated by the stimulation coil to achieve targeted enhancement of transcranial magnetic stimulation. Its shape is similar to that of the EEG cap and is integrated with magnetic shielding materials of different conductivity, magnetic permeability, structure and thickness. The above-mentioned optional headgear set is a pre-constructed set of magnetic shielding headgear participating in the optimization. For this optimization method, each headgear actually corresponds to a set of combined parameters of magnetic permeability, electrical conductivity, thickness and hole opening method. The hole opening method in the present invention includes multiple dimensions such as hole opening position, hole opening pattern and hole opening number.

[0056] Since in actual applications, a series of standard magnetic shielding head covers with different parameters are often prefabricated for users to choose from, in the embodiment of the present invention, the above optional head cover set is preferably a set including all optional prefabricated standard magnetic shielding head covers, and different prefabricated standard magnetic shielding head covers in the set have different magnetic permeability, electrical conductivity, thickness and opening mode (at least one parameter is different). Therefore, through the optimization method of the present invention, one can directly select one from these prefabricated standard magnetic shielding head covers for magnetic stimulation therapy.

[0057] Of course, in other embodiments, the above-mentioned optional headgear set is a set including optional virtual magnetic shielding headgear. The so-called virtual magnetic shielding headgear in the present invention refers to the discrete value sampling of all adjustable parameters of the headgear (magnetic permeability, electrical conductivity, thickness and hole opening method) within their respective value ranges, and then the discrete values ​​obtained by sampling are combined to form different headgear parameter combinations, and each group of headgear parameter combinations corresponds to an optional virtual magnetic shielding headgear. Therefore, the parameters corresponding to different virtual magnetic shielding headgear in the optional headgear set cover different discrete sampling value combinations of magnetic permeability, electrical conductivity, thickness and hole opening method. Based on this optional headgear set, through the optimization method of the present invention, the best parameter combination can be selected from all possible parameter combinations of the magnetic shielding headgear, and then the corresponding magnetic shielding headgear can be processed or the closest headgear can be selected from the existing prefabricated standard magnetic shielding headgear for magnetic stimulation therapy.

[0058] S3. Perform finite element meshing on the above finite element simulation model and assign dielectric parameters to the mesh nodes, wherein the mesh nodes in the individual head model need to be assigned the magnetic permeability and electrical conductivity corresponding to the brain tissue type according to the brain tissue in which they are located, and the mesh nodes in the magnetic shielding headgear model and the transcranial magnetic stimulation coil model need to be assigned the magnetic permeability and electrical conductivity that match the current simulation headgear material.

[0059] It should be noted that finite element meshing of finite element simulation models is a routine operation in finite element analysis, and the specific mesh size can be adjusted according to the requirements of simulation accuracy. Each mesh node needs to be assigned dielectric parameters including magnetic permeability and electrical conductivity according to its own situation. If the mesh node is a certain brain tissue, the dielectric parameters of this brain tissue need to be determined and assigned based on prior knowledge. If the mesh node is a certain component (i.e., magnetic shielding headgear and transcranial magnetic stimulation coil) material, the dielectric parameters of this material need to be determined and assigned based on prior knowledge.

[0060] S4. According to the target excitation parameters of the transcranial magnetic stimulation coil and the target magnetic stimulation target area pre-marked on the individual head model, the finite element simulation model after the parameter assignment is completed is subjected to finite element simulation to obtain the spatial electric field distribution induced by the current simulation headgear in the target magnetic stimulation target area.

[0061] It should be noted that the target magnetic stimulation target area marking of the individual head model can be pre-marked by the user according to the brain area that actually needs to be stimulated. The marking can be done in a visual way. Of course, for this optimization method, marking in a non-visual way is also possible and does not affect the execution of the optimization process.

[0062] S5. For each magnetic shielding headgear in the above optional headgear set, simulate according to S2 to S4 to obtain the spatial electric field distribution induced in the target magnetic stimulation target area.

[0063] It should be noted that for each magnetic shielding headgear in the above optional headgear set, it is necessary to perform the simulation process of S2 to S4 to obtain the spatial electric field distribution induced in the target magnetic stimulation target area. However, this process can be parallel or serial, which can be selected according to the performance of the data processing equipment and the amount of calculation.

[0064] S6. Based on the spatial electric field distribution corresponding to each magnetic shielding headgear in the above optional headgear set, target optimization is performed in combination with a pre-set optimization target to determine the optimal magnetic shielding headgear suitable for the individual to be intervened by transcranial magnetic stimulation.

[0065] It should be noted that when determining the optimal magnetic shielding headgear for individuals to be treated with transcranial magnetic stimulation, the optimization target adopted can be reasonably adjusted according to the needs of transcranial magnetic stimulation. In general, transcranial magnetic stimulation needs to pay attention to two aspects: electric field strength and focusing. The specific basis for selecting the optimal magnetic shielding headgear can be designed according to needs.

[0066] In an embodiment of the present invention, the optimization target needs to consider the induced electric field strength and focusing of transcranial magnetic stimulation in the target magnetic stimulation target area at the same time. Since there is a certain contradiction between the induced electric field strength and focusing, a preferred optimization target setting method is: when the electric field strength of transcranial magnetic stimulation in the target magnetic stimulation target area meets the preset strength, the focusing of transcranial magnetic stimulation in the target magnetic stimulation target area is maximized. Thereby focusing the induced electric field in the target area as much as possible and reducing the electric field strength in the non-target area. Based on this optimization target, after determining the spatial electric field distribution corresponding to each magnetic shielding headgear in the above-mentioned optional headgear set, the respective electric field strength and focusing can be calculated based on the spatial electric field distribution induced by each magnetic shielding headgear in the target magnetic stimulation target area, and then the magnetic shielding headgear whose electric field strength does not meet the set strength range is screened out, and the magnetic shielding headgear with the best focusing is selected from the remaining magnetic shielding headgear as the optimal magnetic shielding headgear suitable for the individual to be intervened by transcranial magnetic stimulation.

[0067] It should be noted that the method steps shown in S1 to S6 above can essentially be implemented in the form of a computer program.

[0068] Therefore, based on the same inventive concept, the present invention also provides a computer electronic device corresponding to the individual head model optimization method for an individual precise transcranial magnetic stimulation system provided in the above embodiment, which includes a memory and a processor;

[0069] The memory is used to store computer programs;

[0070] The processor is used to implement the individual head model optimization method for an individual precise transcranial magnetic stimulation system as described above when executing the computer program;

[0071] In addition, the logic instructions in the above-mentioned memory can be implemented in the form of software functional units and can be stored in a computer-readable storage medium when sold or used as an independent product. Based on such an understanding, the technical solution of the present invention, or the part that contributes to the prior art, or the part of the technical solution, can be embodied in the form of a software product, which is stored in a storage medium and includes a number of instructions for a computer device (which can be a personal computer, a server, or a network device, etc.) to perform all or part of the steps of the method described in each embodiment of the present invention.

[0072] Therefore, based on the same inventive concept, the present invention provides a computer-readable storage medium corresponding to an individual head model optimization method for an individual precise transcranial magnetic stimulation system, and a computer program is stored on the storage medium. When the computer program is executed by a processor, it can implement the individual head model optimization method for an individual precise transcranial magnetic stimulation system as described above.

[0073] Therefore, based on the same inventive concept, the present invention provides a computer program product, including a computer program / instruction, which, when executed by a processor, can implement the individual head model optimization method for an individual precise transcranial magnetic stimulation system as described above.

[0074] It is understandable that the above storage medium may include a random access memory (RAM) or a non-volatile memory (NVM), such as at least one disk storage. The storage medium may also be a U disk, a mobile hard disk, a magnetic disk or an optical disk, etc., which may store program codes.

[0075] It is understandable that the above-mentioned processor can be a general-purpose processor, including a central processing unit (CPU), a network processor (NP), etc.; it can also be a digital signal processor (DSP), an application specific integrated circuit (ASIC), a field programmable gate array (FPGA) or other programmable logic devices, discrete gate or transistor logic devices, discrete hardware components.

[0076] See also Figure 2 As shown, in another embodiment of the present invention, an individual precise transcranial magnetic stimulation system matching the above-mentioned individual precise transcranial magnetic stimulation method is also provided, and the functional modules constituting the system include a main control module 1, an individual head model optimization module 2, a magnetic field excitation module 3, a stimulation coil 4, a magnetic shielding headgear 5, a parameter monitoring module 6, a power supply module 7 and an interaction module 9.

[0077] In the transcranial magnetic stimulation system, the main control module 1 is respectively connected to the individual head model optimization module 2, the magnetic field excitation module 3, the parameter monitoring module 6, the power module 7 and the interaction module 9 to realize information processing and central function control. In an embodiment of the present invention, the main control module 1 can be composed of a microprocessor.

[0078] In the transcranial magnetic stimulation system, the power module 7 is used to provide power for the entire transcranial magnetic stimulation system. The power module 7 is mainly composed of a power conditioning circuit, and provides the required voltage for other modules in the system through the main control module 1.

[0079] In the transcranial magnetic stimulation system, the individual head model optimization module 2 is used to receive input imaging data of the individual to be treated with transcranial magnetic stimulation, and execute the individual accurate transcranial magnetic stimulation system individual head model optimization method as described in S1 to S6 in the above embodiments, and send the optimization result to the above interaction module 9 to assist the user in achieving the optimal selection of the magnetic shielding head cover 5. Considering that the individual head model optimization module 2 needs to perform a large amount of simulation calculations, a separate data processing unit composed of a computing unit and a graphics processing unit can be additionally set to achieve it.

[0080] It should be noted that the imaging data of the individual to be treated with transcranial magnetic stimulation can be imported into the individual head model optimization module 2 by the user or automatically read from relevant medical equipment through a software program and imported into the individual head model optimization module 2. In an embodiment of the present invention, the import function can be provided by the subsequent interactive module 9.

[0081] In the transcranial magnetic stimulation system, the interaction module 9 is used to provide the user with a human-computer interaction function, wherein the specific function setting of the human-computer interaction function can be reasonably adjusted according to the actual system usage requirements, which may include importing the above-mentioned imaging data and visually displaying the optimization results of the individual head model optimization module 2.

[0082] It should be noted that when the optimization results of the individual head model optimization module 2 are visualized in the above-mentioned interactive module 9, the specific visualization display method can be adjusted and optimized according to actual needs. For example, when displaying the optimization results of the optimal headgear, the magnetic permeability, electrical conductivity, thickness and opening method can be used for users to select the corresponding headgear, or the number of the optimal prefabricated standard magnetic shielding headgear can be directly displayed. At the same time, the relevant information pages of other headgears except the optimal headgear can also be displayed on the display interface for users to select. In addition, in addition to displaying the optimization results of the optimal headgear, the spatial electric field distribution corresponding to the optimal headgear can also be further displayed on the individual headgear.

[0083] In the transcranial magnetic stimulation system, the magnetic field excitation module 3 is respectively connected to the individual head model optimization module, the parameter monitoring module 6 and the stimulation coil, and is used to output a transcranial magnetic stimulation excitation voltage or current to the stimulation coil 4 under the control of the main control module 1. The stimulation coil 4 is used to cooperate with the magnetic shielding headgear 5 to generate a transcranial magnetic stimulation magnetic field under the excitation of the magnetic field excitation module 3. The specific implementation of the magnetic field excitation module 3 and the stimulation coil 4 in the present invention is similar to that of the traditional transcranial magnetic stimulation system, which will not be repeated here.

[0084] In the transcranial magnetic stimulation system, the parameter monitoring module 6 is used to monitor the output current and voltage of the magnetic field excitation module 3 and the temperature of the stimulation coil 4, and send the monitoring information to the main control module 1 in real time, thereby realizing feedback adjustment of the magnetic field excitation module 3.

[0085] See also Figure 2 As shown, in another embodiment of the present invention, see Figure 5 As shown, a communication module 8 can also be provided in the individual precise transcranial magnetic stimulation system as needed, and the communication module 8 can be connected to the control unit 1. The communication module 8 is used to establish a communication connection between the transcranial magnetic stimulation system and an external device. The communication method is wired communication or wireless Bluetooth WIFI communication. The wired communication can use Ethernet or USB interface, and the wireless communication can use Wi-Fi or Bluetooth module. The external device can be a local device, such as a host computer, an integrated display terminal, or a cloud device, such as a remote server, a cloud server, a remotely accessed mobile device, and the like.

[0086] In addition, in order to facilitate the local implementation of a series of control and interactive functions of the transcranial magnetic stimulation system, the above-mentioned interactive module 9 can be implemented by a local device or a remote device with a display screen, and its interactive mode is one or more of GUI interface human-computer interaction, physical button control, and touch key control. Preferably, a touch-sensitive GUI interface can be set on a local LCD touch screen, LED display screen and other devices to provide human-computer interaction functions, and the user can directly adjust some setting parameters of the system through the GUI interface, import image data, view or export optimization results, etc.

[0087] It should also be noted that those skilled in the art can clearly understand that for the convenience and simplicity of description, the division of steps or modules in the above-described system and method is only a logical function division, and there may be other division methods in actual implementation, such as multiple modules or steps can be combined or integrated together, and a module or step can also be split. For example, for the main control module 1, it can distinguish functions according to the amount of calculation, and some functions with small amount of calculation are implemented in the lower computer, while functions with large amount of calculation (such as individual head model optimization module) are implemented by additionally setting up a host computer or a data processing unit (mainly composed of a computing unit and a graphics processing unit). Similarly, some human-computer interaction functions in the interactive module 9 can also be implemented in a dispersed manner through different devices, or integrated on the same display device.

[0088] In order to better demonstrate the technical effects that can be achieved by the system and optimization method of the present invention, some specific cases are described below. Figure 4 This is a schematic diagram of the structure of an exemplary magnetic shielding headgear of the present invention, which includes several different thicknesses and perforation patterns for determining the best shielding effect for subsequent individual applications. The optimizable parameters of the magnetic shielding headgear in this example include magnetic permeability, electrical conductivity, thickness, and hole opening method (hole position, number of holes, and hole size). Among them, the thickness of the magnetic shielding headgear can be selected as 0.5 mm, 1 mm, and 1.5 mm, and the hole pattern can be selected as circular perforations with a diameter of 1 cm or 3 cm. The hole position is located in the center (Cz) area. Of course, the hole position of the magnetic shielding headgear can also be opened according to the corresponding relevant position of the target brain target area marked by the user.

[0089] See also Figure 5 As shown, a flowchart of an optimization method that can be specifically executed in the individual head model optimization module 2 based on the above exemplary magnetic shielding headgear is shown. The flow mainly includes two parts: individual head model construction and individualized headgear optimization method.

[0090] As for the individual head model construction part, firstly, the magnetic resonance data of the individual to be intervened by transcranial magnetic stimulation is imported through the human-computer interaction interface. The individual head model optimization module of the system of the present invention will perform brain tissue segmentation (generally including tissue components such as scalp, skull, cerebrospinal fluid, gray matter, white matter, etc.) after preprocessing the individual magnetic resonance data, and then post-process the image after tissue segmentation (including steps such as smoothing filtering and denoising), and reconstruct the individual head model after post-processing in three dimensions, and then expand the scalp layer of the individual head model outward according to the thickness of the magnetic shielding head cover, and according to the target magnetic stimulation target area marked by the user on the individual head cover, for each magnetic shielding head cover in the optional head cover set, a magnetic shielding head cover model with a corresponding opening method and thickness can be formed through tissue structure processing, and the magnetic shielding head cover model is placed on the individual head cover, and at the same time, the virtualized transcranial magnetic stimulation coil model is placed on the magnetic shielding head cover model according to the actual situation, and the individual head cover after the magnetic shielding head cover model and the transcranial magnetic stimulation coil model are placed is finite element meshed.

[0091] As for the individualized headgear optimization method, for each magnetic shielding headgear in the optional headgear set, the corresponding node parameters (magnetic permeability μ, electrical conductivity σ) of different tissues and components of the head model will be assigned according to the actual brain tissue and component (transcranial magnetic stimulation coil and magnetic shielding headgear) material conditions, and finite element solution calculations will be performed. By traversing all magnetic shielding headgear, the spatial electric field distribution A (μ, σ, d, m) generated in the head model under the settings of magnetic shielding headgear with different magnetic permeability μ, electrical conductivity σ, thickness d, and opening method m can be obtained cyclically. Then, according to the preset electric field strength and focusing requirements of the target area, the optimization results can be obtained and visualized through multi-objective parameter optimization. In this example, according to the preset target area electric field strength and direction, the headgear parameters (μ) that meet the optimal focusing under the electric field strength can be selected. T ,σ T ,d T ,m T ), and then according to the headgear parameter settings, select the appropriate magnetic shielding headgear to perform precise transcranial magnetic stimulation on the individual.

[0092] See also Figure 6 As shown in the figure, the simulation results of the spatial electric field distribution in the individual head model under the magnetic shielding headgear with different thicknesses, perforation patterns, and magnetic permeabilities are shown in the figure. The thickness and perforation pattern of the magnetic shielding headgear considered in this example are shown in the figure. Figure 4 As shown in Figure 2, the optimization process takes into account the influence of headgear materials with different magnetic permeabilities and electrical conductivities on the electric field distribution caused by TMS. r to 1, 50, and 100. The default parameters for the magnetic shielding headgear are set to a relative conductivity of 1 S / m. For the purpose of presenting example results, the widely used MNI-152 template was selected as the basis for building an accurate simulation model. Figure 6 It can be seen from the results that when shielding headgear with different magnetic permeabilities was used, a significant attenuation of the TMS-induced electric field in the brain was observed compared to the case where the magnetic permeability was 1 (analogous to air). The higher the magnetic permeability, the greater the attenuation of the induced electric field. In addition, as the thickness of the magnetic shielding material increases, the induced electric field strength decreases significantly. In addition, the size of the perforations in the magnetic shielding headgear (diameter of 1cm to 3cm) also affects the distribution of the induced electric field. Larger perforation diameters lead to higher induced magnetic field strengths and wider electric field influence ranges), verifying the feasibility of the individual precise transcranial magnetic stimulation system and method proposed in the present invention.

[0093] See also Figure 7 As shown in the figure, the spatial electric field distribution results in the individual head model under the application of the magnetic shielding headgear with different hole opening methods and conductivity in this example are further shown, where the conductivity σ of the magnetic shielding headgear is 1 S / m, 10000 S / m, 100000 S / m, 1000000 S / m, 10000000 S / m and 50000000 S / m. The default parameters of the magnetic shielding headgear are set to a relative magnetic permeability of 1 and a thickness of 1mm. It can be observed from the figure that as the conductivity of the magnetic shielding headgear continues to increase beyond this point, the induced electric field intensity in the brain decreases significantly, further verifying the feasibility of the individual precise transcranial magnetic stimulation system and application method proposed in the present invention.

[0094] The above-described embodiments are only some preferred solutions of the present invention, but are not intended to limit the present invention. A person skilled in the relevant technical field may make various changes and modifications without departing from the spirit and scope of the present invention. Therefore, any technical solution obtained by equivalent replacement or equivalent transformation falls within the protection scope of the present invention.

Claims

1. A method for optimizing an individual head model for an individual transcranial magnetic stimulation system with high precision, characterized in that: include: S1. Based on the imaging data of the individual to be treated with transcranial magnetic stimulation, an individual head model is constructed through brain tissue segmentation and three-dimensional reconstruction; S2. Select a magnetic shielding headgear from the optional headgear set as the current simulation headgear, and form a magnetic shielding headgear model with the same structure and thickness as the current simulation headgear by expanding the scalp layer in the individual head model outward according to its thickness and opening method; then put the magnetic shielding headgear model on the individual head model, and place the virtualized transcranial magnetic stimulation coil model on the magnetic shielding headgear model at a specified angle to form a finite element simulation model consisting of the individual head model, the magnetic shielding headgear model and the transcranial magnetic stimulation coil model; different headgears in the optional headgear set have different magnetic permeability, electrical conductivity, thickness and opening method; S3. Perform finite element meshing on the finite element simulation model and assign dielectric parameters to the mesh nodes, wherein the mesh nodes in the individual head model need to be assigned magnetic permeability and electrical conductivity corresponding to the brain tissue type according to the brain tissue in which they are located, and the mesh nodes in the magnetic shielding headgear model and the transcranial magnetic stimulation coil model need to be assigned magnetic permeability and electrical conductivity matching the current simulation headgear material; S4, according to the target excitation parameters of the transcranial magnetic stimulation coil and the target magnetic stimulation target area pre-marked on the individual head model, the finite element simulation model after the parameter assignment is completed is performed to obtain the spatial electric field distribution induced by the current simulation headgear in the target magnetic stimulation target area; S5, for each magnetic shielding headgear in the optional headgear set, respectively simulate according to S2 to S4 to obtain the spatial electric field distribution induced in the target magnetic stimulation target area; S6. Based on the spatial electric field distribution corresponding to each magnetic shielding headgear in the optional headgear set, target optimization is performed in combination with a pre-set optimization target to select the optimal magnetic shielding headgear suitable for the individual to be treated with transcranial magnetic stimulation.

2. The method for optimizing an individual head model for an individual transcranial magnetic stimulation system according to claim 1, characterized in that: The imaging data is magnetic resonance imaging data or CT data.

3. The method for optimizing an individual head model for an individual transcranial magnetic stimulation system according to claim 1, characterized in that: The optimization goal needs to take into account both the electric field strength and focusing of transcranial magnetic stimulation within the target magnetic stimulation area.

4. The method for optimizing an individual head model for an individual transcranial magnetic stimulation system according to claim 1, wherein: The optional head cover set is a set including all optional prefabricated standard magnetic shielding head covers, and different prefabricated standard magnetic shielding head covers in the set have different magnetic permeability, electrical conductivity, thickness and opening methods; Alternatively, the optional headgear set is a set including optional virtual magnetic shielding headgear, and parameters corresponding to different virtual magnetic shielding headgear in the set cover different discrete sampling value combinations of magnetic permeability, electrical conductivity, thickness and opening method.

5. An individual precise transcranial magnetic stimulation system, characterized in that: It includes a main control module, an individual head model optimization module, a magnetic field excitation module, a stimulation coil, a magnetic shielding headgear, a parameter monitoring module, a power supply module and an interaction module; The main control module is respectively connected to the individual head model optimization module, the magnetic field excitation module, the parameter monitoring module, the power module and the interaction module to realize information processing and central function control; The power module is used to provide power for the entire transcranial magnetic stimulation system; The individual head model optimization module is used to receive input imaging data of an individual to be treated with transcranial magnetic stimulation, and execute the individual head model optimization method for an individual accurate transcranial magnetic stimulation system as claimed in any one of claims 1 to 3, and send the optimization result to the interaction module to assist in achieving the optimal selection of the magnetic shielding headgear; The interaction module is used to provide a human-computer interaction function to the user; the human-computer interaction function includes importing the imaging data and visually displaying the optimization results; The magnetic field excitation module is respectively connected to the individual head model optimization module, the parameter monitoring module and the stimulation coil, and is used to output a transcranial magnetic stimulation excitation voltage or current to the stimulation coil under the control of the main control module; The stimulation coil is used to cooperate with the magnetic shielding headgear to generate a transcranial magnetic stimulation magnetic field under the stimulation of the magnetic field stimulation module; The parameter monitoring module is used to monitor the output current and voltage of the magnetic field excitation module and the temperature of the stimulation coil, and send the monitoring information to the main control module in real time to achieve feedback adjustment of the magnetic field excitation module.

6. The individual precise transcranial magnetic stimulation system according to claim 5, characterized in that: It also includes a communication module connected to the main control module, and the communication module is used to establish a communication connection between the transcranial magnetic stimulation system and an external device.

7. The individual precise transcranial magnetic stimulation system according to claim 6, characterized in that: The communication mode of the communication module is wired communication, or wireless Bluetooth or WIFI communication.

8. The individual precise transcranial magnetic stimulation system according to claim 5, characterized in that: The interaction module is a local device or a remote device with a display screen, and its interaction mode is one or more of GUI interface human-computer interaction, physical button control, and touch button control.

9. A computer-readable storage medium, characterized in that: The storage medium stores a computer program, and when the computer program is executed by the processor, the individual head model optimization method for an individual precise transcranial magnetic stimulation system as described in any one of claims 1 to 4 is implemented.

10. A computer electronic device, characterized in that: including memory and processor; The memory is used to store computer programs; The processor is used to implement the individual head model optimization method for an individual precise transcranial magnetic stimulation system as described in any one of claims 1 to 4 when executing the computer program.

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