Non-invasive nerve regulation and control system for treating idiopathic tremor by regulating and controlling dentoid nucleus

Abstract

The invention discloses a non-invasive nerve regulation and control system for treating idiopathic tremor by regulating and controlling a dentoid nucleus, and the system comprises a target positioning device which is used for transmitting an electromagnetic wave to a target object, receiving a corresponding feedback signal, constructing a magnetic resonance image of the target object, and positioning the position of the dentoid nucleus; the electric field simulation device is used for carrying out tissue segmentation and conductivity distribution based on the magnetic resonance image, configuring electrodes based on a standard 10-20 EEG system of 32 channels, and carrying out finite element grid division to configure electrode parameters so as to form a target parameter electric field; and the transcranial electrical stimulation module is used for controlling an electrode to form the target parameter electric field so as to regulate and control the dentoid nucleus. And the stimulating electrode is driven to generate a simulated target electric field, so that dentate nucleus nerve regulation and control are carried out in a non-invasive manner, and risks and side effects of a traditional operation are avoided.

Description

Technical Field

[0001] The present invention belongs to the technical field of brain nerve regulation, and in particular relates to a non-invasive nerve regulation system for regulating the dentate nucleus to treat essential tremor. Background Art

[0002] Essential tremor (ET) presents as typical rhythmic movements that primarily affect the upper limbs. Although its exact pathophysiology is not fully understood, current evidence suggests that the cerebello-thalamo-cortical (CTC) circuit is a key circuit for ET, and therefore the development of various neurostimulation strategies targeting specific nodes within the CTC circuit is a major direction in the treatment of ET. The dentate nucleus (DN) is located in an important brain region in the cerebello-thalamo-cortical circuit and is a promising therapeutic target.

[0003] Cerebellar electroencephalographic recordings in patients with ET show strong oscillations in tremor frequency that correlate with symptom severity. The DN is a deep cerebellar nucleus that receives dysregulated input from the cerebellar cortex and projects to the primary motor cortex via the ventral intermediate nucleus (VIM) of the thalamus. In the cerebello-thalamocortical circuit, the dentato-rubro-thalamic tract (DRTT) is a key white matter pathway that mediates cerebellar output from the dentate nucleus to the motor cortex via the red nucleus and the ventral intermediate nucleus of the thalamus. Previous studies have shown that the therapeutic effect of stimulation is negatively correlated with the distance between the stimulation contact and the dentato-rubro-thalamic tract, with closer distances requiring lower stimulation amplitudes. Functional magnetic resonance imaging (fMRI) studies have shown reduced inhibitory drive in the cerebellar cortex and increased activation of the dentate nucleus bilaterally that correlates with tremor severity. Despite these promising mechanistic insights, conventional deep brain stimulation (DBS) techniques that directly target the deep cerebellar nuclei are complicated by the anatomical constraints of the posterior nucleus, while invasive stimulation modalities are difficult to promote in daily treatment due to their traumatic nature. Summary of the invention

[0004] To solve the above problems, the purpose of the present invention is to provide a non-invasive neuroregulatory system for regulating the dentate nucleus to treat essential tremor, which is used to treat or alleviate essential tremor.

[0005] The technical solution provided by the present invention is: a non-invasive neural regulation system for regulating the dentate nucleus to treat essential tremor, comprising: A target positioning device, used to transmit electromagnetic waves to a target object and receive corresponding feedback signals, construct a magnetic resonance image of the target object and locate the position of the dentate nucleus; An electric field simulation device performs tissue segmentation and conductivity allocation based on the magnetic resonance image, configures electrodes based on a standard 10-20 EEG system with 32 channels, and performs finite element meshing to configure electrode parameters to form a target parameter electric field; The transcranial electrical stimulation module controls the electrodes to form the target parameter electric field to regulate the dentate nucleus.

[0006] Preferably, receiving the electromagnetic wave reflection signal to construct a magnetic resonance image of the target object further comprises: T1-weighted structural images were acquired based on a T1-weighted 3D fast spoiled gradient echo sequence (T1W-3D FSP); The echo sequence was coregistered with the following parameters: repetition time (TR) = 1900 ms, echo time (TE) = 2.4 ms, inversion time (TI) = 900 ms, flip angle = 8°, field of view = 156 × 188 × 156 mm 2 , matrix size = 223 × 269 × 223, full brain coverage; Imaging was performed using a multi-echo GRE sequence to generate a quantitative susceptibility map (QSM); The following parameters were used to localize the dentate nucleus: TR = 32 ms, TE1 / space / TE8 = 2.6 / 2.6 / 20.8 ms, flip angle = 15°, phase acceleration factor = 2, field of view = 240 × 240 mm2, matrix size = 352 × 352, slice thickness = 2 mm, and 80 consecutive slices.

[0007] Preferably, receiving the electromagnetic wave reflection signal to construct a magnetic resonance image of the target object and locate the dentate nucleus further comprises: Echo planar imaging (EPI) sequence was used to collect resting state functional data as a baseline for subsequent verification of the regulation effect. The parameters were as follows: TR = 2000 ms, TE = 22 ms, flip angle = 90°, field of view = 192 × 192 mm 2 , matrix size = 64 × 64350 volumes, slice thickness = 3 mm, gap 0.75 mm, 36 slices.

[0008] Preferably, performing tissue segmentation and conductivity allocation based on the magnetic resonance image, configuring electrodes based on a standard 10-20 EEG system with 32 channels, and performing finite element meshing to configure electrode parameters to form a target parameter electric field further comprises: Create a three-dimensional model of the scalp, determine the electrode positions, and generate a finite element mesh based on the geometry and size of the scalp model.

[0009] Preferably, the target parameter electric field is: inducing an interference electric field of Δf=130 Hz at the dentate nucleus position, and the electric field strength is 0.65~0.7 V / m.

[0010] Preferably, the electric field simulation device uses iso2mesh to create a volume mesh from a 3D multi-domain image, and then applies SPM12 to segment the magnetic resonance image into gray matter, white matter, cerebrospinal fluid, bone, scalp and air cavity, and calculates its individual conductivity based on the segmented structure using a pixel interpolation matching method, and assigns structural parameters, and then uses the finite element solver getDP to solve the simulation model to predict the generated electric field distribution.

[0011] Preferably, the target localization device processes the resampled T1-weighted images in parallel through the open source software package ROAST to simulate stimulation electrodes and configure them at customized locations on the scalp.

[0012] Preferably, the electric field simulation device selects 2 groups of 4 electrodes, and the two stimulation currents are s1sin(ω1t) and s2sin(ω2t +π), where s1 and s2 are vectors encoding the current source distribution of each frequency ω1 and ω2, respectively. For visualization purposes, a phase difference of 180 degrees is selected. The total electric field caused by the two stimulation currents in the brain is: .

[0013] Preferably, the frequencies of the two groups of stimulation currents selected by the electric field simulation device are f1=2000 Hz and f2=2130 Hz, the interfering electric field frequency Δf=130 Hz, and the total stimulation duration is 20 minutes, including a 30-second current increase at the beginning and a 30-second current decrease at the end.

[0014] Preferably, it also includes a tremor analysis module, which is arranged on the subject's hand to record and analyze the tremor condition to observe whether the tremor condition is improved.

[0015] Due to the adoption of the above technical solution, the present invention has the following advantages and positive effects compared with the prior art: The present invention innovatively selects the dentate nucleus as a new target, constructs a magnetic resonance image of the target object by emitting electromagnetic waves and receiving feedback signals, and further locates the position of the patient's dentate nucleus. The electric field simulation device drives the stimulation electrode to generate a simulated target electric field, and then non-invasively regulates the dentate nucleus nerves, avoiding the risks and side effects of traditional surgery and improving patient acceptance and compliance. The transcranial electrical stimulation module can effectively regulate the dentate nucleus, significantly reduce the symptoms of essential tremor, improve the patient's daily quality of life, and alleviate pain. BRIEF DESCRIPTION OF THE DRAWINGS

[0016] The specific embodiments of the present invention are further described in detail below with reference to the accompanying drawings, wherein: Figure 1 It is a schematic diagram of the system workflow of the present invention; Figure 2 It is a schematic diagram of the electric field simulation effect of the present invention; Figure 3 It is a graph showing the effect of the tremor state during the 7-day treatment period of the present invention; Figure 4 This is a diagram showing the long-term maintenance effect of the treatment of the present invention after review after 4 weeks. DETAILED DESCRIPTION

[0017] The present invention is further described in detail below in conjunction with the accompanying drawings and specific embodiments. The advantages and features of the present invention will become more apparent from the following description and claims. It should be noted that the drawings are all in a very simplified form and use non-precise ratios, which are only used to conveniently and clearly assist in explaining the purpose of the embodiments of the present invention.

[0018] It should be noted that all directional indications in the embodiments of the present invention (such as up, down, left, right, front, back, etc.) are only used to explain the relative position relationship, movement status, etc. between the components under a certain specific posture (as shown in the accompanying drawings). If the specific posture changes, the directional indication will also change accordingly.

[0019] First embodiment This embodiment provides a non-invasive neural regulation system for regulating the dentate nucleus to treat essential tremor, including: A target positioning device, used to transmit electromagnetic waves to a target object and receive corresponding feedback signals, construct a magnetic resonance image of the target object and locate the position of the dentate nucleus; An electric field simulation device performs tissue segmentation and conductivity allocation based on the magnetic resonance image, configures electrodes based on a standard 10-20 EEG system with 32 channels, and performs finite element meshing to configure electrode parameters to form a target parameter electric field; The transcranial electrical stimulation module controls the electrodes to form the target parameter electric field to regulate the dentate nucleus.

[0020] This embodiment innovatively selects the dentate nucleus as a new target, constructs a magnetic resonance image of the target object by emitting electromagnetic waves and receiving feedback signals, and further locates the position of the patient's dentate nucleus. The electric field simulation device drives the stimulation electrode to generate a simulated target electric field, and then non-invasively regulates the dentate nucleus nerves, avoiding the risks and side effects of traditional surgery and improving patient acceptance and compliance. The transcranial electrical stimulation module can effectively regulate the dentate nucleus, significantly reduce the symptoms of essential tremor, improve the patient's daily quality of life, and alleviate pain.

[0021] Preferably, receiving the electromagnetic wave reflection signal to construct a magnetic resonance image of the target object further comprises: T1-weighted structural images were acquired based on a T1-weighted 3D fast spoiled gradient echo sequence (T1W-3D FSP); The echo sequence was coregistered with the following parameters: repetition time (TR) = 1900 ms, echo time (TE) = 2.4 ms, inversion time (TI) = 900 ms, flip angle = 8°, field of view = 156 × 188 × 156 mm2, matrix size = 223 × 269 × 223, whole-brain coverage; Imaging was performed using a multi-echo GRE sequence to generate a quantitative susceptibility map (QSM); The following parameters were used to localize the dentate nucleus: TR = 32 ms, TE1 / space / TE8 = 2.6 / 2.6 / 20.8 ms, flip angle = 15°, phase acceleration factor = 2, field of view = 240 × 240 mm2, matrix size = 352 × 352, slice thickness = 2 mm, and 80 consecutive slices.

[0022] The technical solution of this embodiment takes into account the specificity of each patient. After collecting the electromagnetic wave reflection signal, it is adjusted to a uniform direction and size before locating the dentate nucleus, thereby improving the positioning accuracy of the dentate nucleus.

[0023] Preferably, receiving the electromagnetic wave reflection signal to construct a magnetic resonance image of the target object and locate the dentate nucleus further comprises: An echo planar imaging (EPI) sequence was used to collect resting-state functional data as a baseline for subsequent verification of regulatory effects. The parameters were as follows: TR = 2000 ms, TE = 22 ms, flip angle = 90°, field of view = 192 × 192 mm2, matrix size = 64 × 64350 volumes, slice thickness = 3 mm, gap 0.75 mm, and 36 slices.

[0024] The technical solution of this embodiment uses an echo planar imaging (EPI) sequence to collect resting state functional data as a baseline while constructing a magnetic resonance image, so as to facilitate comparison with the baseline before treatment after subsequent treatment to study the treatment effect.

[0025] Preferably, performing tissue segmentation and conductivity allocation based on the magnetic resonance image, configuring electrodes based on a standard 10-20 EEG system with 32 channels, and performing finite element meshing to configure electrode parameters to form a target parameter electric field further comprises: Create a three-dimensional model of the scalp, determine the electrode positions, and generate a finite element mesh based on the geometry and size of the scalp model; This embodiment creates a three-dimensional model of the scalp based on the magnetic resonance image. The model reflects the geometry and size of the head in detail, providing accurate basic data for the subsequent determination of the electrode position. According to the geometry and size of the three-dimensional model of the head, the position of the standard 10-20 EEG system electrodes of 32 channels is determined. Then SPM12 is used to segment the magnetic resonance image of the head into gray matter, white matter, cerebrospinal fluid, bone, scalp and air cavity, and the individual conductivity of the gray matter, white matter, cerebrospinal fluid, bone, scalp and air cavity structure after segmentation is calculated using the pixel interpolation matching method, and the structural parameters are assigned. This process helps to simulate the distribution of the electric field in the scalp and optimize the electrode parameter configuration. The simulation model is then solved using the finite element solver getDP to predict the generated electric field distribution so that the target parameter electric field meets the preset conditions.

[0026] Preferably, the target parameter electric field is: inducing an interference electric field of Δf=130 Hz at the dentate nucleus position, and the electric field strength is 0.65~0.7 V / m.

[0027] Inducing an interfering electric field of Δf=130 Hz at the dentate nucleus, electrical stimulation at this specific frequency can effectively regulate brain activity and reduce the occurrence of tremor symptoms. The electric field strength is set at 0.65~0.7 V / m. The electric field strength within this range can provide sufficient stimulation to achieve effective regulation of the dentate nucleus while avoiding unnecessary damage to surrounding tissues.

[0028] Preferably, the target localization device processes the resampled T1-weighted images in parallel through the open source software package ROAST to simulate stimulation electrodes and configure them at customized locations on the scalp.

[0029] Preferably, the electric field simulation device selects 2 groups of 4 electrodes, and the two stimulation currents are s1sin(ω1t) and s2sin(ω2t +π), where s1 and s2 are vectors encoding the current source distribution of each frequency ω1 and ω2, respectively. For visualization purposes, a phase difference of 180 degrees is selected. The total electric field caused by the two stimulation currents in the brain is: .

[0030] Preferably, the frequencies of the two groups of stimulation currents selected by the electric field simulation device are f1=2000 Hz and f2=2130 Hz, the interfering electric field frequency Δf=130 Hz, and the total stimulation duration is 20 minutes, including a 30-second current increase at the beginning and a 30-second current decrease at the end.

[0031] For example, the subject first undergoes a functional magnetic resonance (fMRI) scan to obtain its structural functional magnetic resonance image. All magnetic resonance data in this embodiment are collected using the United Imaging 3.0T whole-body 89 cm caliber magnetic resonance body scanner of Shanghai Ruijin Hospital. T1-weighted structural images are also collected based on a T1-weighted 3D fast spoiled gradient echo sequence (T1W-3D FSP), which is used for co-registration with the following parameters: repetition time (TR) = 1900 ms, echo time (TE) = 2.4 ms, inversion time (TI) = 900 ms, flip angle = 8°, field of view = 156×188×156 mm2, matrix size = 223×269×223, and full brain coverage. For each subject, resting-state functional data were collected once using an echo planar imaging (EPI) sequence with the following parameters: TR = 2000 ms, TE = 22 ms, flip angle = 90°, field of view = 192 × 192 mm2, matrix size = 64 × 64350 volumes, slice thickness = 3 mm, gap 0.75 mm, 36 slices. Next, all patients were imaged using a multi-echo GRE sequence to generate quantitative susceptibility maps (QSMs) and localize the dentate nucleus using the following parameters: TR = 32 ms, TE1 / space / TE8 = 2.6 / 2.6 / 20.8 ms, flip angle = 15°, phase acceleration factor = 2, field of view = 240 × 240 mm2, matrix size = 352 × 352, slice thickness = 2 mm, 80 consecutive slices.

[0032] After obtaining the structural functional magnetic resonance image of each subject, the image was imported into the electric field simulation module of the present invention. Specifically, we segmented the tissue and assigned conductivity, placed electrodes according to the standard 10-20 EEG system with 32 channels, performed finite element meshing, and then calculated the electric field. Because the dentate nucleus is the target area that needs to be regulated, the goal of the modeling is to develop an electrode placement scheme that induces an interfering electric field of 130 Hz in this area. The present invention first uses the open source software package ROAST to parallel process the resampled T1-weighted images (1.0 mm×1.0 mm×1.0 mm). Then SPM12 is applied to segment the magnetic resonance images into gray matter, white matter, cerebrospinal fluid, bone, scalp, and air cavity. The stimulation electrodes are simulated and placed at custom locations on the scalp. The present invention uses iso2mesh to create volumetric meshes from 3D multi-domain images, and uses the pixel interpolation matching method to calculate their individual conductivity based on the segmented gray matter, white matter, cerebrospinal fluid, bone, scalp, and air cavity structures, and assigns structural parameters. The present invention then solves the simulation model using the finite element solver getDP to predict the resulting electric field distribution. The distribution of the interfering electric field and the amplitude modulation envelope are visualized using the methods described previously. The two stimulation currents are s1sin(ω1t) and s2sin(ω2t + π), where s1 and s2 are vectors encoding the current source distribution for each frequency ω1 and ω2, respectively. For visualization purposes, a phase difference of 180 degrees was chosen. The total electric field induced in the brain by these two stimulation currents is According to the simulation results, the electrode positions and the associated currents resulted in an electric field on the target that was required to be in the interval of 0.65 to 0.7 V / m. The frequencies f1 = 2000 Hz and f2 = 2130 Hz were the same for all participants, resulting in an interfering electric field frequency Δf = 130 Hz. The total stimulation duration was 20 minutes, including a 30-second current ramp-up at the beginning and a 30-second current ramp-down at the end.

[0033] Based on the above modeling method, we defined the location of the stimulation electrodes, current intensity and frequency within the framework of the 10-20 EEG system. The simulation results are shown in Figure 2. Figure 2 As shown. In terms of exposure intensity and selectivity of dentate nucleus stimulation regulation, the optimal sites for the 15 subjects recruited in this example are composed of the electrodes shown in Table 1.

[0034] Table 1: After completing the electric field simulation, the modulated current will be delivered through the transcranial electrical stimulation module of the present invention using an interferential neuromodulation system (Neuroplus, China). Before stimulation, a 32-lead electrode cap was installed according to the head size to ensure correct electrode placement. A set of customized 4×1 gel-filled cup electrodes was used to produce focused stimulation. The cup electrode has a volume of 5 ml and consists of a 2-cm diameter plastic cylinder mounted in an EEG cap (Greentek, China). Before the stimulating AgCl ring electrode (Greentek, China) was fixed to the cup, 5 ml of conductive gel (Greectek, China) was filled into the cup electrode to ensure that the device resistance was less than 15 kΩ. The position of the electrodes was determined by the results of individual modeling (Table 1), and there were two pairs of stimulation electrodes and return electrodes.

[0035] Preferably, it also includes a tremor analysis module, which is arranged on the subject's hand to record and analyze the tremor condition to observe whether the tremor condition is improved.

[0036] After the transcranial electrical stimulation module of the present invention is fixed, the accelerometer contained in the tremor analysis module of the present invention is fixed to the back of the subject's hand through a strap, and then the initial tremor state assessment is started. The subject is required to stretch both hands straight forward and hold them horizontally, with the palms facing down, for 1 minute. After completing the horizontal holding action, the palms of both hands are placed flat on the chest with the fingertips facing down, and the opposite position is maintained for 1 minute. During this period, the tremor analysis module of the present invention records and analyzes the tremor amplitude of the back of both hands. After the horizontal holding in the opposite position is completed, the subject returns to a normal sitting position, keeps relaxed, and then starts the transcranial electrical stimulation module of the present invention to start 20 minutes of transcranial electrical stimulation according to the set current intensity and frequency. After completing the 20-minute transcranial electrical stimulation treatment, the subject is required to perform a set of 1-minute horizontal holding posture and a set of 1-minute opposite holding posture again, and cooperate with the experimenter to complete the scoring of the Fahn Tolosa-Marin Tremor Rating Scale (FTM-TRS) and the scoring of the spiral curve drawing score.

[0037] The above treatment process will be repeated for 7 days. We use the tremor analysis module of the present invention and the FTM-TRS scale and spiral curve scale to track and score the treatment effect during these 7 days. The results are as follows: Figure 3 As shown, it can be seen that both the tremor status results given by the tremor analysis module of the present invention and the scale scores and the spiral curve drawing scores all show a downward trend with the treatment process. The tremor status and score results before the start of treatment and after 7 days of treatment were further statistically analyzed, and both showed a significant decrease. This result shows that the treatment site and stimulation means of the present invention can significantly improve the tremor symptoms of the subject after 7 days of treatment.

[0038] After completing the 7-day treatment, the subjects were asked to return to the hospital for a reexamination 4 weeks later. The reexamination task was to wear the tremor analysis module of the present invention to perform a set of 1-minute horizontal lifting postures and a set of 1-minute opposite lifting postures, and cooperate with the experimenter to complete the scoring of the FTM-TRS scale and the spiral curve drawing score. We analyzed and counted the tremor status, FTM-TRS scale score, and spiral curve score of all the subjects who participated in the reexamination at three time points: before the start of treatment, after 7 days of treatment, and after 4 weeks. The results are as follows: Figure 4 The results showed that 4 weeks after stopping the stimulation treatment, the FTM-TRS scale score, the tremor power in the horizontal and opposite postures, and the mean error distance of the spiral curve tracking were still significantly reduced compared with the baseline. And these indicators remained at the same level as when the 7-day treatment just ended.

[0039] Taken together, these findings suggest that the immediate benefits of treatment with the present invention, including reduced tremor severity and improved task performance, persist for at least 4 weeks following treatment.

[0040] If implemented in the form of program instructions and sold or used as an independent product, it can be stored in a computer-readable storage medium. Based on this understanding, the technical solution of this embodiment is essentially or the part that contributes to the prior art or all or part of the technical solution can be embodied in the form of software, and the computer software is stored in a storage medium, including several instructions to enable a computer device (which can be a personal computer, server, or network device, etc.) to perform all or part of the steps of the method described in each embodiment of the present disclosure. The aforementioned storage medium includes: U disk, mobile hard disk, read-only memory (ROM), random access memory (RAM), disk or optical disk, etc., various media that can store program code.

[0041] Those skilled in the art can clearly understand that, for the sake of convenience and brevity in description, the identification content specifically executed by the above-described system and device can refer to the corresponding process in the aforementioned method embodiment.

[0042] The embodiments of the present invention are described in detail above in conjunction with the accompanying drawings, but the present invention is not limited to the above embodiments. Even if various changes are made to the present invention, if these changes fall within the scope of the claims of the present invention and their equivalents, they still fall within the protection scope of the present invention.

Claims

1. A non-invasive neural regulation system for regulating the dentate nucleus to treat essential tremor, characterized in that: include: A target positioning device, used to transmit electromagnetic waves to a target object and receive corresponding feedback signals, construct a magnetic resonance image of the target object and locate the position of the dentate nucleus; An electric field simulation device performs tissue segmentation and conductivity allocation based on the magnetic resonance image, configures electrodes based on a standard 10-20 EEG system with 32 channels, and performs finite element meshing to configure electrode parameters to form a target parameter electric field; The transcranial electrical stimulation module controls the electrodes to form the target parameter electric field to regulate the dentate nucleus.

2. The non-invasive neuromodulatory system for regulating the dentate nucleus to treat essential tremor according to claim 1, characterized in that: Receiving the electromagnetic wave reflection signal to construct a magnetic resonance image of the target object further includes: T1-weighted structural images were acquired based on the T1-weighted 3D fast spoiled gradient echo sequence T1W-3D FSP; The echo sequence was co-registered with the following parameters: repetition time TR = 1900 ms, echo time TE = 2.4 ms, inversion time TI = 900 ms, flip angle = 8°, field of view = 156 × 188 × 156 mm 2 , matrix size = 223 × 269 × 223, full brain coverage; Imaging was performed using a multi-echo GRE sequence to generate a quantitative susceptibility map (QSM); The following parameters were used to localize the dentate nucleus: TR = 32 ms, TE1 / space / TE8 = 2.6 / 2.6 / 20.8 ms, flip angle = 15°, phase acceleration factor = 2, field of view = 240 × 240 mm2, matrix size = 352 × 352, slice thickness = 2 mm, and 80 consecutive slices.

3. The non-invasive neuromodulatory system for regulating the dentate nucleus to treat essential tremor according to claim 1 or 2, characterized in that: Receiving the electromagnetic wave reflection signal to construct a magnetic resonance image of the target object and locate the dentate nucleus further includes: Echoplanar imaging (EPI) sequence was used to collect resting state functional data as a baseline for subsequent verification of the control effect. The parameters were as follows: TR = 2000 ms, TE = 22 ms, flip angle = 90°, field of view = 192 × 192 mm 2 , matrix size = 64 × 64350 volumes, slice thickness = 3 mm, gap 0.75 mm, 36 slices.

4. The non-invasive neuromodulatory system for regulating the dentate nucleus to treat essential tremor according to claim 1, characterized in that: Performing tissue segmentation and conductivity allocation based on the magnetic resonance image, configuring electrodes based on a standard 10-20 EEG system with 32 channels, and performing finite element meshing to configure electrode parameters to form a target parameter electric field further includes: Create a three-dimensional model of the scalp, determine the electrode positions, and generate a finite element mesh based on the geometry and size of the scalp model.

5. The non-invasive neuromodulatory system for regulating the dentate nucleus to treat essential tremor according to claim 4, characterized in that: The target parameter electric field is: inducing an interference electric field of Δf=130 Hz at the dentate nucleus position, and the electric field strength is 0.65~0.7 V / m.

6. The non-invasive neuromodulatory system for regulating the dentate nucleus to treat essential tremor according to claim 5, characterized in that: The electric field simulation device uses iso2mesh to create a volume grid from a 3D multi-domain image, and then applies SPM12 to segment the magnetic resonance image into gray matter, white matter, cerebrospinal fluid, bone, scalp and air cavity, and calculates its individual conductivity based on the segmented structure using the pixel interpolation matching method, assigns structural parameters, and then uses the finite element solver getDP to solve the simulation model to predict the generated electric field distribution; the target positioning device uses the open source software package ROAST to parallelly process the resampled T1-weighted images to simulate the customized position of the stimulation electrode configuration on the scalp.

7. The non-invasive neuromodulatory system for regulating the dentate nucleus to treat essential tremor according to claim 1, characterized in that: The electric field simulation device selects 2 groups of 4 electrodes, and the two stimulation currents are s1sin(ω1t) and s2sin(ω2t +π), where s1 and s2 are vectors encoding the current source distribution of each frequency ω1 and ω2 respectively. For visualization purposes, a phase difference of 180 degrees is selected. The total electric field caused by the two stimulation currents in the brain is: .

8. The non-invasive neuromodulatory system for regulating the dentate nucleus to treat essential tremor according to claim 7, characterized in that: The frequencies of the two groups of stimulation currents selected by the electric field simulation device are f1=2000 Hz and f2=2130 Hz, respectively, the interfering electric field frequency Δf=130 Hz, and the total stimulation duration is 20 minutes, including a 30-second current increase at the beginning and a 30-second current decrease at the end.

9. The non-invasive neuromodulatory system for regulating the dentate nucleus to treat essential tremor according to claim 1, characterized in that: It also includes a tremor analysis module, which is set on the subject's hand to record and analyze the tremor condition to observe whether the tremor condition has improved.

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