Transcranial electrical stimulation device and method compatible with high-field and ultrahigh-field magnetic resonance imaging

Abstract

The invention provides a transcranial electrical stimulation device and method compatible with high-field and ultrahigh-field magnetic resonance imaging, and belongs to the technical field of medical equipment. The device comprises an electrical stimulation module, a multi-stage bidirectional filtering module and a multi-magnetic-conduction compatible electrode, the electrical stimulation module generates an electrical stimulation signal according to an electrical stimulation mode and parameters selected by a user, and sends the electrical stimulation signal to the multi-permeability compatible electrode; after the multi-permeability compatible electrode completes electrical stimulation, corresponding electroencephalogram signals are collected; the bidirectional filtering module carries out filtering processing on bidirectional communication signals in the multi-conductor shielding wire. The problem that high-field and ultrahigh-field nuclear magnetic resonance environments interfere with the electrical stimulation device is solved, the electrical stimulation device does not affect nuclear magnetic resonance imaging, compatibility of high-field and ultrahigh-field nuclear magnetic resonance imaging and the electrical stimulation device is truly achieved, meanwhile, multiple electrical stimulation modes are provided, the multi-channel electroencephalogram collection function and other functions are achieved, and the application range is wide. The newest requirements of clinical use and scientific research are met.

Description

Technical Field

[0001] The present application relates to the field of medical equipment technology, and in particular to a transcranial electrical stimulation device and method compatible with high-field and ultra-high-field magnetic resonance imaging. Background Art

[0002] At present, with the accelerated pace of people's work and life and the aging of the population, the negative impact of brain diseases on human life is becoming more and more serious. Regarding the treatment of brain diseases, compared with drug therapy, the traditional implantable neural electrical stimulation technology has a more significant therapeutic effect, but the implantable technology requires the electrodes and electrical stimulation devices to be buried in the body through surgery, which is accompanied by high surgical risks and a high infection rate.

[0003] In order to overcome the shortcomings of traditional neural electrical stimulation control technology, non-invasive transcranial electrical stimulation (tES) neural control technology came into being. It can affect the excitability of neurons in the cerebral cortex by applying a weak current to the scalp. At present, the means of electrical stimulation include transcranial direct current stimulation (tDCS), transcranial alternating current stimulation (tACS) and other means. Different electrical stimulation means are required for different diseases. Due to the dispersion of current in biological tissues, it is very challenging to achieve high spatial accuracy, especially when stimulating deep areas without contacting superficial neurons.

[0004] To address this problem, researchers have developed a non-invasive deep brain stimulation technology based on phase interference electric fields, referred to as TI (Temporal interference, TI) stimulation technology. This technology pioneered the application of interference current to transcranial electrical stimulation, achieving non-invasive deep brain stimulation, taking into account both spatial focusing and the ability to penetrate deep brain tissue. However, whether it is traditional transcranial electrical stimulation or TI, the mechanism of its action on the brain is still unclear and needs further study.

[0005] Magnetic resonance imaging (MRI), as a non-invasive imaging technique, has been widely used in brain science research. MRI and tES have been used to explore the mechanism of stimulation efficacy, which can provide a theoretical basis for clinical applications such as tES positioning and dose optimization. Functional magnetic resonance imaging (fMRI) can be used to observe the effects of local and whole-brain electrical stimulation, providing an effective means for further exploring and observing the physiological mechanisms of non-invasive deep brain stimulation. Moreover, under high fields (main magnetic field strength: 3T~7T) and ultra-high fields (above 7T), magnetic resonance images are clearer and have higher contrast. The mechanism of electrical stimulation can be studied at a more subtle level, providing a research basis for the regulation of cranial nerves. This is also the current technological trend. However, in high-field and ultra-high-field magnetic resonance environments, electromagnetic interference such as the main magnetic field, radio frequency field, and gradient field are becoming more and more complex, and it is difficult to solve them. At present, there are no electrical stimulation equipment and technologies compatible with high and ultra-high fields.

[0006] On the other hand, current electrical stimulation devices have relatively simple functional modes and lack multi-channel electroencephalogram (EEG) functions. Electrical stimulation research has not formed a closed loop and cannot meet the new needs of current non-invasive brain-computer interface research. Summary of the invention

[0007] The purpose of this application is to provide a transcranial electrical stimulation device and method that are compatible with high-field and ultra-high-field magnetic resonance imaging, so as to solve the compatibility problem between the transcranial electrical stimulation device and the high-field and ultra-high-field nuclear magnetic resonance environment.

[0008] The first aspect of the present application provides a transcranial electrical stimulation device compatible with high-field and ultra-high-field magnetic resonance imaging, comprising:

[0009] Electrical stimulation module, multi-stage bidirectional filtering module and multi-conductive magnetic compatible electrodes;

[0010] The electrical stimulation module is connected to the multi-conductive magnetically compatible electrode via a multi-conductive shielded line for bidirectional communication, and the multi-stage bidirectional filtering module is sequentially arranged on the communication line of the multi-conductive shielded line;

[0011] The electrical stimulation module is used to provide a variety of electrical stimulation modes, generate electrical stimulation signals according to the electrical stimulation modes and parameters selected by the user, and send the electrical stimulation signals to the multi-magnetic compatible electrodes; after the multi-magnetic compatible electrodes complete the electrical stimulation, collect the corresponding EEG signals;

[0012] The bidirectional filtering module is used to filter the bidirectional communication signal in the multi-conductor shielded cable.

[0013] In a possible implementation, the multi-stage bidirectional filtering module includes a first-stage bidirectional filtering module, a second-stage bidirectional filtering module and a third-stage bidirectional filtering module;

[0014] The electrical stimulation module is located in the control room of the magnetic resonance imaging device, the multi-conductive magnetic compatible electrode is located in the scanning room of the magnetic resonance imaging device, and the control room and the scanning room are separated by a nuclear magnetic shielding wall;

[0015] The first-stage bidirectional filtering module is located in the control room and close to the nuclear magnetic shielding wall;

[0016] The second-stage bidirectional filtering module is located in the scanning room and close to the nuclear magnetic shielding wall;

[0017] The third-stage bidirectional filtering module is located in the scanning room and close to the center of the magnet system of the magnetic resonance imaging device.

[0018] In a possible implementation, the bidirectional filtering module includes:

[0019] A shielding box and a multi-order bidirectional low-pass filter arranged in the shielding box;

[0020] The shielding box is made of metal, and its thickness is calculated by electromagnetic simulation according to the skin effect and the propagation law of high-frequency electromagnetic signals, and the compatible magnetic field strength range is 3T to 14T; the outlet and inlet of the shielding box are designed with non-magnetic connectors, and the shell of the shielding box is grounded;

[0021] The multi-order bidirectional low-pass filter is composed of non-magnetic components.

[0022] In a possible implementation, the shielding box is made entirely of aluminum, and its outermost layer is wrapped with copper foil material.

[0023] In a possible implementation, the multi-conductor shielded cable includes:

[0024] A multi-conductor wire, and a first insulating layer, a first shielding layer, a second insulating layer, a second shielding layer and a third insulating layer which sequentially wrap the multi-conductor wire, wherein the first shielding layer and the second shielding layer are grounded.

[0025] In a possible implementation, the first shielding layer is a copper mesh shielding layer, and the second shielding layer is an aluminum mesh shielding layer.

[0026] In a possible implementation, the magnetically compatible electrode is configured as a ring structure, and the ring structure has an opening.

[0027] In a possible implementation manner, a non-magnetic current limiting resistor is connected to a lead wire of at least one of the magnetically compatible electrodes.

[0028] In a possible implementation, the electrical stimulation module is further used to monitor the waveform of the electrical stimulation signal at the magnetically compatible electrode in real time.

[0029] In a possible implementation manner, the device further includes:

[0030] A temperature sensor is arranged at the magnetically compatible electrode;

[0031] The electrical stimulation module is also used to monitor the temperature of the magnetically compatible electrode in real time through the temperature sensor.

[0032] A second aspect of the present application provides a control method for a transcranial electrical stimulation device, which is applied to the transcranial electrical stimulation device compatible with high-field and ultra-high-field magnetic resonance imaging according to the first aspect, and the method comprises:

[0033] The temperature of the magnetically compatible electrode is monitored in real time by a temperature sensor;

[0034] When the temperature of the magnetically compatible electrode exceeds a preset threshold, an overheated electrode warning message is generated and the device stops working.

[0035] Compared with the prior art, the transcranial electrical stimulation device compatible with high-field and ultra-high-field magnetic resonance imaging provided by the present application includes: an electrical stimulation module, a multi-stage bidirectional filtering module and a multi-conductive magnetically compatible electrode; the electrical stimulation module and the multi-conductive magnetically compatible electrode are bidirectionally connected through a multi-conductive shielded wire, and the multi-stage bidirectional filtering module is sequentially arranged on the communication line of the multi-conductive shielded wire; the electrical stimulation module is used to provide a variety of electrical stimulation modes, generate electrical stimulation signals according to the electrical stimulation mode and parameters selected by the user, and send the electrical stimulation signals to the multi-conductive magnetically compatible electrode; after the multi-conductive magnetically compatible electrode completes the electrical stimulation, the corresponding electroencephalogram signal is collected; the bidirectional filtering module is used to filter the bidirectional communication signal in the multi-conductive shielded wire. It can be seen that the present application effectively solves the problem of interference of high-field and ultra-high-field MRI environments on the electric stimulation device through multi-stage bidirectional filtering and multi-conductor shielded cables, and the electric stimulation device will not affect the MRI imaging, truly realizing the compatibility of high-field and ultra-high-field MRI with the electric stimulation device. At the same time, it also provides a variety of electric stimulation modes and has functions such as multi-channel EEG acquisition, which greatly meets the latest needs of current clinical use and scientific research. BRIEF DESCRIPTION OF THE DRAWINGS

[0036] Various other advantages and benefits will become apparent to those of ordinary skill in the art by reading the detailed description of the preferred embodiments below. The accompanying drawings are only for the purpose of illustrating the preferred embodiments and are not to be considered as limiting the present application. Also, the same reference symbols are used throughout the accompanying drawings to represent the same components. In the accompanying drawings:

[0037] Figure 1 A schematic diagram of the overall structure of a transcranial electrical stimulation device compatible with high-field and ultra-high-field magnetic resonance imaging provided by the present application is shown;

[0038] Figure 2 A schematic structural diagram of a shielding box provided by the present application is shown;

[0039] Figure 3 A circuit diagram of a multi-order bidirectional low-pass filter provided by the present application is shown;

[0040] Figure 4 A schematic structural diagram of a multi-conductor shielded cable provided by the present application is shown;

[0041] Figure 5 A schematic structural diagram of a magnetically compatible electrode provided by the present application is shown;

[0042] Figure 6 A schematic diagram of the structure of an electrode lead wire provided by the present application is shown;

[0043] Figure 7 A schematic diagram of a scenario in which the transcranial electrical stimulation device provided by the present application is applied in a high-field or ultra-high-field nuclear magnetic resonance environment is shown. DETAILED DESCRIPTION

[0044] The exemplary embodiments of the present disclosure will be described in more detail below with reference to the accompanying drawings. Although the exemplary embodiments of the present disclosure are shown in the accompanying drawings, it should be understood that the present disclosure can be implemented in various forms and should not be limited by the embodiments described herein. On the contrary, these embodiments are provided in order to enable a more thorough understanding of the present disclosure and to fully convey the scope of the present disclosure to those skilled in the art.

[0045] It should be noted that, unless otherwise specified, the technical terms or scientific terms used in this application should have the common meanings understood by technicians in the field to which this application belongs.

[0046] In addition, the terms "first" and "second" etc. are used to distinguish different objects, rather than to describe a specific order. In addition, the terms "including" and "having" and any variations thereof are intended to cover non-exclusive inclusions. For example, a process, method, system, product or device that includes a series of steps or units is not limited to the listed steps or units, but may optionally include steps or units that are not listed, or may optionally include other steps or units that are inherent to these processes, methods, products or devices.

[0047] At present, the main problems faced in combining transcranial electrical stimulation with magnetic resonance imaging technology (MRI) are: the interference of the three major magnetic fields of the magnetic resonance equipment: the main magnetic field, the gradient field and the radio frequency field on the electrical stimulation device, and the impact of the electrical stimulation device on magnetic resonance imaging. At the same time, the safety of the electrical stimulation process and the EEG acquisition process must be ensured.

[0048] In view of this, an embodiment of the present application provides a transcranial electrical stimulation device and a control method thereof that are compatible with high-field and ultra-high-field magnetic resonance imaging, which are described below in conjunction with the accompanying drawings.

[0049] Please refer to Figure 1 , Figure 1 The figure shows the overall structure of a transcranial electrical stimulation device compatible with high-field and ultra-high-field magnetic resonance imaging provided by the present application.

[0050] like Figure 1 As shown, the transcranial electrical stimulation device 10 provided by the present application and compatible with high-field and ultra-high-field magnetic resonance imaging includes: an electrical stimulation module 110, a multi-stage bidirectional filtering module 120 and a multi-conductive magnetic compatible electrode 130. The electrical stimulation module 110 is bidirectionally connected with the multi-conductive magnetic compatible electrode 130 through a multi-conductive shielded wire, and the multi-stage bidirectional filtering module 120 is sequentially arranged on the communication line of the multi-conductive shielded wire.

[0051] The electrical stimulation module 110 is used to provide a variety of electrical stimulation modes, such as transcranial direct current stimulation (tDCS), transcranial alternating current stimulation (tACS), transcranial pulse stimulation (tPCS), transcranial random noise stimulation (tRNS) and TI stimulation. After the user selects the electrical stimulation mode and inputs parameters, an electrical stimulation signal is generated according to the electrical stimulation mode and parameters selected by the user, and the electrical stimulation signal is sent to the multi-magnetic compatible electrode 130. After the multi-magnetic compatible electrode 130 completes the electrical stimulation, the corresponding EEG signal is collected.

[0052] Each stage of the two-way filtering module 120 performs a filtering process on the two-way communication signal in the multi-conductor shielded wire. The multi-stage two-way filtering module 120 can perform multiple filtering processes on the two-way communication signal in the multi-conductor shielded wire to ensure that the signal is free of interference.

[0053] Specifically, the electrical stimulation module 110 can be an integrated multi-mode electrical stimulation and EEG acquisition device, which provides an interactive interface. The user selects the electrical stimulation mode and inputs parameters in the interactive interface. The electrical stimulation module 110 sends stimulation instructions and signals according to the electrical stimulation mode and parameters set in the interactive interface. The stimulation and EEG signal acquisition are completed by reaching the electrode end through a multi-conductor shielded cable and multi-stage bidirectional filtering.

[0054] Specifically, the bidirectional filtering module 120 includes: a shielding box and a multi-order bidirectional low-pass filter disposed in the shielding box. Figure 2 FIG. 1 is a schematic diagram of the structure of a shielding box provided by the present application. Figure 3 Shown is a circuit diagram of a multi-order bidirectional low-pass filter provided by the present application.

[0055] like Figure 2 As shown, the material of the shielding box is metal. Specifically, the overall material of the shielding box is aluminum, and the outermost layer is wrapped with copper foil. The thickness of the shielding box is calculated by electromagnetic simulation according to the skin effect and the propagation law of high-frequency electromagnetic signals. The compatible magnetic field strength range is greater than 3T, for example, it can be used in 3T to 14T, or higher magnetic field strength; the outlet and inlet of the shielding box are designed with non-magnetic connectors, and the shell of the shielding box is grounded; the shielding box contains a multi-order bidirectional low-pass filter to filter out the interference of radio frequency signals, protect equipment and instruments, and also protect the normal output signal to avoid interference from radio frequency signals.

[0056] like Figure 3 As shown, the multi-order bidirectional low-pass filter can be an RC filter, and the capacitors and resistors in the filter are all non-magnetic components, which can effectively filter out the radio frequency field and other interference components of the magnetic resonance system.

[0057] Figure 4 This is a schematic diagram of the structure of a multi-conductor shielded cable provided in this application. Figure 4 As shown, the multi-conductor shielded wire includes: a multi-conductor wire, and a first insulating layer, a first shielding layer, a second insulating layer, a second shielding layer and a third insulating layer that sequentially wrap the multi-conductor wire, and the first shielding layer and the second shielding layer are grounded. A shell may be wrapped outside the third insulating layer, specifically a rubber wire shell. Specifically, the first shielding layer is a copper mesh shielding layer, and the second shielding layer is an aluminum mesh shielding layer.

[0058] The above-mentioned multi-conductor shielded wire of the present application is a self-made shielded transmission line, which can specifically include two layers of metal braided mesh shielding layers (copper mesh and aluminum mesh), and an insulating layer is filled between the mesh shielding layers. The thickness of the metal braided mesh and the thickness of the insulating layer are calculated by electromagnetic simulation software according to the main magnetic field, gradient field, and radio frequency field frequency characteristics in high field and ultra-high field. The two layers of metal shielding mesh are connected to the three-stage bidirectional filter module housing and grounded. Among them, the multi-conductor wire can be a multi-conductor copper wire, which can support multi-conductor stimulation and EEG signal acquisition.

[0059] Figure 5 This is a schematic diagram of the structure of a magnetically compatible electrode provided in this application. Figure 5 As shown, the magnetically compatible electrode is configured as a ring structure, and the ring structure has an opening.

[0060] Specifically, the material of the magnetically compatible electrode can be silver chloride (AgCl). The magnetically compatible electrode of the present application adopts a ring structure and an open setting, which can effectively avoid the occurrence of artifacts during magnetic resonance imaging. At the same time, it can also effectively reduce eddy currents and prevent the electrode from generating strong eddy currents and heating, which may burn the patient.

[0061] The electrical stimulation device provided by the present invention is compatible with high-field and ultra-high-field nuclear magnetic resonance imaging equipment, which solves two problems in the application under the MRI environment. The first is the influence of the MRI equipment on the electrical stimulation device, including interference with the normal output signal, the radio frequency field coupling into the lead wire and the electrode to generate strong eddy currents, causing serious heating of the electrode, causing safety hazards, etc.; the second is that in clinical applications and scientific research, fMRI research needs to be done simultaneously during the implementation of electrical stimulation to evaluate the effect and mechanism of action of electrical stimulation. At this time, it is necessary to solve the problem that the electrodes and lead wires cannot affect the MRI imaging when entering the MRI chamber, otherwise it will cause artifacts in the MRI imaging. The special electrode design structure of the present invention can effectively avoid the above two situations.

[0062] The magnetically compatible electrode is connected to the multi-conductor shielded wire through a lead wire, and a non-magnetic current limiting resistor is connected to the lead wire of at least one magnetically compatible electrode. Figure 6 As shown, the lead wires of the three magnetically compatible electrodes are connected with non-magnetic current limiting resistors R. Connecting a non-magnetic current limiting resistor between the magnetically compatible electrodes and the multi-conductor shielding wire body can limit the induced current of the device in the complex environment of nuclear magnetic resonance, thereby protecting the patient from being burned by strong eddy currents during use.

[0063] The transcranial electrical stimulation device of the present application can be used in high-field and ultra-high-field nuclear magnetic resonance environments, specifically, Figure 7In the illustrated scenario, the electrical stimulation module 110 is located in the control room of the magnetic resonance imaging device, and the multi-magnetic compatible electrode 130 is located in the scanning room of the magnetic resonance imaging device. The control room and the scanning room are separated by a nuclear magnetic shielding wall.

[0064] like Figure 7 As shown, the multi-stage bidirectional filtering module includes a first-stage bidirectional filtering module 121 , a second-stage bidirectional filtering module 122 and a third-stage bidirectional filtering module 123 .

[0065] The first-stage bidirectional filtering module 121 is located in the control room and close to the nuclear magnetic shielding wall;

[0066] The second-stage bidirectional filtering module 122 is located in the scanning room and close to the nuclear magnetic shielding wall;

[0067] The third-stage bidirectional filtering module 123 is located in the scanning room and close to the center of the magnet system of the magnetic resonance imaging device.

[0068] In some embodiments, a real-time signal waveform monitoring function may be provided in the electrical stimulation module 110 so as to monitor the waveform of the electrical stimulation signal at the magnetically compatible electrode in real time during the electrical stimulation process.

[0069] In this embodiment, the shielding effect of the transcranial electrical stimulation device on the interference signal of the magnetic resonance device can be verified by looking back to see whether the electrical stimulation signal at the electrode end is normal. When collecting EEG, the real-time monitoring function of the signal waveform in the electrical stimulation module 110 can also be used to check the collected EEG signals and compare them with the EEG signals collected in the non-MRI environment to ensure the effectiveness of the MRI-compatible components of the transcranial electrical stimulation device.

[0070] In some embodiments, a real-time temperature monitoring function may be provided in the electrical stimulation module 110 so as to monitor the temperature of the magnetically compatible electrode in real time during the electrical stimulation process. Figure 7 As shown, a temperature sensor 131 may be provided at the magnetically compatible electrode to monitor the temperature of the magnetically compatible electrode.

[0071] In this embodiment, the magnetically compatible electrode adopts a special structure and is equipped with a temperature sensor, which can monitor the temperature rise of the electrode due to eddy current heating during the execution of the magnetic resonance sequence in real time. If the electrode temperature rises above the preset threshold, the electrode temperature warning mechanism will be triggered, and an electrode temperature overheating warning box will appear on the interactive interface of the device. At the same time, the device stops working. After the warning box is manually removed and the electrode temperature returns to normal, electrical stimulation can be carried out normally. At the same time, when performing electrical stimulation, EEG signals can also be collected synchronously when scanning a specific nuclear magnetic resonance sequence.

[0072] The transcranial electrical stimulation device of the present application is applied to high-field and ultra-high-field nuclear magnetic resonance scenarios, and a three-stage bidirectional filtering module is adopted. The outer shells of the filtering modules are all made of anti-interference magnetic shielding materials (the main material is aluminum, and the outside is wrapped with copper foil); the filter modules are connected by homemade shielding wires, and there are transmission channels inside the shielding wires that can transmit electrical stimulation signals, and there are also channels that can review the electrical stimulation signals at the electrode end in real time; at the same time, a temperature sensor is provided at the electrode end, and the multi-mode electrical stimulation and EEG acquisition integrated equipment is equipped with an electrode temperature real-time monitoring function, which can monitor the temperature of the electrode in real time. The outer shell of the three-stage filtering module and the metal mesh shielding layer of the shielding wire are connected to the nuclear magnetic shielding wall, which can achieve a better shielding effect.

[0073] The present application also provides a control method for a transcranial electrical stimulation device, using the transcranial electrical stimulation device compatible with high-field and ultra-high-field magnetic resonance imaging of the above embodiment, the method comprising:

[0074] The temperature of the magnetically compatible electrode is monitored in real time by a temperature sensor;

[0075] When the temperature of the magnetically compatible electrode exceeds a preset threshold, an overheated electrode warning message is generated and the device stops working.

[0076] The transcranial electrical stimulation device and control method thereof provided by the present application, which are compatible with high-field and ultra-high-field magnetic resonance imaging, can provide multifunctional multi-channel transcranial electrical stimulation and EEG acquisition compatible with high-field and ultra-high-field nuclear magnetic resonance environments. The problem of interference of magnetic resonance hardware equipment with the electrical stimulation device and EEG equipment is solved by multi-stage bidirectional filtering and self-made multi-conductor shielded wires. At the same time, the stimulation electrode method of reducing eddy current is adopted to reduce the influence of the electrode on magnetic resonance imaging, and the temperature of the electrode is monitored in real time to ensure the safety of the electrical stimulation and EEG acquisition process. The present application can provide a variety of electrical stimulation modes, and also has functions such as multi-channel EEG (EEG) acquisition, which greatly meets the latest needs of current clinical use and scientific research.

[0077] Finally, it should be noted that the above embodiments are only used to illustrate the technical solutions of the present application, rather than to limit it. Although the present application has been described in detail with reference to the aforementioned embodiments, those skilled in the art should understand that they can still modify the technical solutions described in the aforementioned embodiments, or replace some or all of the technical features therein by equivalents. These modifications or replacements do not deviate the essence of the corresponding technical solutions from the scope of the technical solutions of the embodiments of the present application, and they should all be included in the scope of the claims and specification of the present application.

Claims

1. A transcranial electrical stimulation device compatible with high-field and ultra-high-field magnetic resonance imaging, characterized in that: include: Electrical stimulation module, multi-stage bidirectional filtering module and multi-conductive magnetic compatible electrodes; The electrical stimulation module is connected to the multi-conductive magnetically compatible electrode via a multi-conductive shielded line for bidirectional communication, and the multi-stage bidirectional filtering module is sequentially arranged on the communication line of the multi-conductive shielded line; The electrical stimulation module is used to provide a variety of electrical stimulation modes, generate electrical stimulation signals according to the electrical stimulation modes and parameters selected by the user, and send the electrical stimulation signals to the multi-magnetic compatible electrodes; after the multi-magnetic compatible electrodes complete the electrical stimulation, collect the corresponding EEG signals; The bidirectional filtering module is used to filter the bidirectional communication signal in the multi-conductor shielded cable.

2. The transcranial electrical stimulation device compatible with high-field and ultra-high-field magnetic resonance imaging according to claim 1, characterized in that: The multi-stage bidirectional filtering module includes a first-stage bidirectional filtering module, a second-stage bidirectional filtering module and a third-stage bidirectional filtering module; The electrical stimulation module is located in the control room of the magnetic resonance imaging device, the multi-conductive magnetic compatible electrode is located in the scanning room of the magnetic resonance imaging device, and the control room and the scanning room are separated by a nuclear magnetic shielding wall; The first-stage bidirectional filtering module is located in the control room and close to the nuclear magnetic shielding wall; The second-stage bidirectional filtering module is located in the scanning room and close to the nuclear magnetic shielding wall; The third-stage bidirectional filtering module is located in the scanning room and close to the center of the magnet system of the magnetic resonance imaging device.

3. The transcranial electrical stimulation device compatible with high-field and ultra-high-field magnetic resonance imaging according to claim 1, characterized in that: The bidirectional filtering module comprises: A shielding box and a multi-order bidirectional low-pass filter arranged in the shielding box; The shielding box is made of metal, and its thickness is calculated by electromagnetic simulation according to the skin effect and the propagation law of high-frequency electromagnetic signals, and the compatible magnetic field strength range is 3T to 14T; the outlet and inlet of the shielding box are designed with non-magnetic connectors, and the shell of the shielding box is grounded; The multi-order bidirectional low-pass filter is constructed using non-magnetic components.

4. The transcranial electrical stimulation device compatible with high-field and ultra-high-field magnetic resonance imaging according to claim 3, characterized in that: The shielding box is made entirely of aluminum, and its outermost layer is wrapped with copper foil.

5. The transcranial electrical stimulation device compatible with high-field and ultra-high-field magnetic resonance imaging according to claim 1, characterized in that: The multi-conductor shielded cable comprises: A multi-conductor wire, and a first insulating layer, a first shielding layer, a second insulating layer, a second shielding layer and a third insulating layer which sequentially wrap the multi-conductor wire, wherein the first shielding layer and the second shielding layer are grounded.

6. The transcranial electrical stimulation device compatible with high-field and ultra-high-field magnetic resonance imaging according to claim 5, characterized in that: The first shielding layer is a copper mesh shielding layer, and the second shielding layer is an aluminum mesh shielding layer.

7. The transcranial electrical stimulation device compatible with high-field and ultra-high-field magnetic resonance imaging according to claim 1, characterized in that: The magnetically compatible electrode is configured as a ring structure, and the ring structure has an opening.

8. The transcranial electrical stimulation device compatible with high-field and ultra-high-field magnetic resonance imaging according to claim 7, characterized in that: A non-magnetic current limiting resistor is connected to the lead wire of at least one of the magnetically compatible electrodes.

9. A transcranial electrical stimulation device compatible with high-field and ultra-high-field magnetic resonance imaging according to any one of claims 1 to 8, characterized in that: The electrical stimulation module is also used to monitor the waveform of the electrical stimulation signal at the magnetically compatible electrode in real time.

10. A transcranial electrical stimulation device compatible with high-field and ultra-high-field magnetic resonance imaging according to any one of claims 1 to 8, characterized in that: The device also includes: A temperature sensor is arranged at the magnetically compatible electrode; The electrical stimulation module is also used to monitor the temperature of the magnetically compatible electrode in real time through the temperature sensor.

11. A method for controlling a transcranial electrical stimulation device, characterized in that: The method applied to the transcranial electrical stimulation device compatible with high-field and ultra-high-field magnetic resonance imaging as claimed in claim 10 comprises: The temperature of the magnetically compatible electrode is monitored in real time by a temperature sensor; When the temperature of the magnetically compatible electrode exceeds a preset threshold, an overheated electrode warning message is generated and the device stops working.

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