Transcranial magnetic stimulation system and methods

Abstract

This invention discloses a transcranial magnetic stimulation (TMS) system and method. The TMS system includes: a transcranial alternating current (TAC) stimulator for outputting a sinusoidal wave of a specific frequency, which outputs sinusoidal alternating current through stimulation electrodes; a first electroencephalogram (EEG) acquisition device for acquiring target EEG signals from a target brain region; a phase synchronization detection module for generating a detection start signal when the sinusoidal electrical stimulation signal from the TAC stimulator and the target EEG signal are phase-synchronized; a control module for reading the real-time phase of the sinusoidal electrical stimulation signal output from the TAC stimulator based on the detection start signal, and generating a control signal based on the real-time phase and preset conditions; and a TMS stimulator for outputting TMS pulses through a coil to stimulate the target brain region of the target subject based on the TMS pulses. The technical solution based on this invention improves the accuracy of TMS pulse control.

Description

Technical Field

[0001] This invention relates to the field of computer application technology, and in particular to a transcranial magnetic stimulation system and method. Background Technology

[0002] Transcranial magnetic stimulation (TMS) non-invasively delivers magnetic pulses to the brain, modulating neural activity in a network-like manner. It holds significant value in improving motor and cognitive functions. Current research indicates that the regulatory effect of TMS on the brain is related not only to the output parameters of the magnetic pulses, such as stimulation intensity and frequency, but also to the neural oscillation state of the brain at the moment of pulse output. Furthermore, the human brain is composed of countless neurons, each or a cluster of neurons, which operate rhythmically, exhibiting neural oscillations at different frequencies. These oscillations reflect the periodic changes in the excitability levels of neurons or neuronal clusters and are closely related to brain function. It is understandable that the neural oscillation state varies within an individual at different times, and often differs between individuals.

[0003] In existing technologies, transcranial magnetic stimulation (TMS) systems often struggle to achieve high-precision extraction of the real-time phase of brain nerve oscillations. When outputting TMS, they often only consider the regulatory effect of magnetic pulse output parameters on the brain, while ignoring the influence of real-time changes in the neural oscillation state. Furthermore, due to the differences in neural oscillation states within and / or between individuals at different times, the same TMS often has inconsistent effects on the same individual or different individuals, resulting in poor regulatory effects of TMS. Summary of the Invention

[0004] This invention provides a transcranial magnetic stimulation system and method to solve the technical problem of poor modulation effect of transcranial magnetic stimulation.

[0005] According to one aspect of the present invention, a transcranial magnetic stimulation system is provided, wherein the system comprises: a transcranial alternating current stimulator, stimulating electrodes, a first electroencephalogram (EEG) acquisition device, a phase synchronization detection module, a control module, the transcranial magnetic stimulator, and a coil; wherein,

[0006] The transcranial alternating current stimulator is connected to the stimulation electrode and is used to output a sinusoidal wave of a specific frequency. The sinusoidal alternating current is output through the stimulation electrode to stimulate the target brain region of the target subject based on the sinusoidal alternating current, wherein the stimulation electrode is placed at the target brain region.

[0007] The first EEG acquisition device is used to acquire the target EEG signal of the target brain region and input the target EEG signal into the phase synchronization detection module;

[0008] The phase synchronization detection module is connected to the transcranial AC stimulator, the first EEG acquisition device, and the control module, respectively. It is used to generate a detection start signal when the sinusoidal electrical stimulation signal of the transcranial AC stimulator and the target EEG signal are phase synchronized, and to transmit the detection start signal to the control module.

[0009] The control module is connected to the transcranial magnetic stimulator and is used to read the real-time phase of the sinusoidal electrical stimulation signal output by the transcranial AC stimulator based on the detection start signal, generate a control signal based on the real-time phase and preset conditions, and input the control signal to the transcranial magnetic stimulator.

[0010] The transcranial magnetic stimulation device is connected to the coil and is used to output transcranial magnetic stimulation pulses through the coil to stimulate the target brain region of the target subject based on the transcranial magnetic stimulation pulses, wherein the coil is placed at the target brain region.

[0011] According to another aspect of the present invention, a transcranial magnetic stimulation method is provided, wherein the method comprises: a transcranial alternating current stimulator, stimulating electrodes, a first electroencephalogram (EEG) acquisition device, a phase synchronization detection module, a control module, the transcranial magnetic stimulator, and a coil; wherein,

[0012] A sinusoidal wave of a specific frequency is output, and a sinusoidal alternating current is output through the stimulation electrode to stimulate the target brain region of the target subject based on the sinusoidal alternating current, wherein the stimulation electrode is placed at the target brain region.

[0013] Collect the target EEG signal of the target brain region and input the target EEG signal into the phase synchronization detection module;

[0014] When the sinusoidal electrical stimulation signal of the transcranial alternating current stimulator and the target EEG signal are in phase synchronization, a detection start signal is generated and transmitted to the control module.

[0015] Based on the detection start signal, the real-time phase of the sinusoidal electrical stimulation signal output by the transcranial AC stimulator is read, and a control signal is generated based on the real-time phase and preset conditions, and the control signal is input to the transcranial magnetic stimulator.

[0016] Transcranial magnetic stimulation pulses are output through the coil to stimulate the target brain region of the target subject based on the transcranial magnetic stimulation pulses, wherein the coil is placed at the target brain region.

[0017] The technical solution of this invention involves a transcranial alternating current (TAC) stimulator connected to stimulation electrodes to output a sinusoidal wave of a specific frequency. The stimulation electrodes output sinusoidal alternating current to stimulate a target brain region of the target subject. The stimulation electrodes are placed at the target brain region, and different specific frequencies are set for different individuals, improving personalized experience and ensuring consistency of effects between and within individuals. A first EEG acquisition device is used to acquire the target EEG signal from the target brain region and input the target EEG signal to the phase synchronization detection module. The phase synchronization detection module is connected to the TAC stimulator, the first EEG acquisition device, and the control module, and is used to generate a phase synchronization signal when the sinusoidal stimulation signal from the TAC stimulator and the target EEG signal are in phase synchronization. A detection start signal is generated and transmitted to the control module. The control module, connected to the transcranial magnetic stimulation device, is used to read the real-time phase of the sinusoidal electrical stimulation signal output by the transcranial AC stimulator based on the detection start signal, and generate a control signal based on the real-time phase and preset conditions, and input the control signal to the transcranial magnetic stimulation device. This solves the problem of low accuracy in directly detecting the real-time phase of the target EEG signal, and indirectly obtains the real-time phase of the target EEG signal through the real-time phase of the sinusoidal electrical stimulation signal, thus improving the accuracy of detecting the real-time phase of the target EEG signal. The transcranial magnetic stimulation device, connected to the coil, is used to output transcranial magnetic stimulation pulses through the coil to stimulate the target brain region of the target object based on the transcranial magnetic stimulation pulses, wherein the coil is placed at the target brain region. Based on the technical solution of this invention, the problems of poor transcranial magnetic stimulation (TMS) effects caused by significant differences in the regulatory effects of TMS on the brain between and within individuals, as well as the low accuracy of real-time phase detection of the target EEG signal, are solved. The solution realizes closed-loop neural modulation based on real-time phase triggering of TMS pulse output using sinusoidal electrical stimulation signals. While ensuring consistency of the regulatory effects between and within individuals, the solution improves the accuracy of TMS pulse control, thereby enhancing the regulatory effect of TMS.

[0018] It should be understood that the description in this section is not intended to identify key or essential features of the embodiments of the present invention, nor is it intended to limit the scope of the invention. Other features of the invention will become readily apparent from the following description. Attached Figure Description

[0019] To more clearly illustrate the technical solutions in the embodiments of the present invention, the accompanying drawings used in the description of the embodiments will be briefly introduced below. Obviously, the accompanying drawings described below are only some embodiments of the present invention. For those skilled in the art, other drawings can be obtained based on these drawings without creative effort.

[0020] Figure 1 This is a schematic diagram of a transcranial magnetic stimulation system according to Embodiment 1 of the present invention;

[0021] Figure 2 This is a scene diagram illustrating the first EEG acquisition device, stimulation electrode, and composite electrode used in an embodiment of the present invention.

[0022] Figure 3 This is an application flowchart of the phase synchronization detection module implemented in this embodiment of the invention;

[0023] Figure 4 This is a hardware connection diagram of the transcranial magnetic stimulation system implementing the embodiments of the present invention;

[0024] Figure 5 This is a flowchart of a transcranial magnetic stimulation method according to Embodiment 2 of the present invention. Detailed Implementation

[0025] To enable those skilled in the art to better understand the present invention, the technical solutions of the present invention will be clearly and completely described below with reference to the accompanying drawings of the embodiments of the present invention. Obviously, the described embodiments are only some embodiments of the present invention, and not all embodiments. Based on the embodiments of the present invention, all other embodiments obtained by those skilled in the art without creative effort should fall within the scope of protection of the present invention.

[0026] It should be noted that the terms "first," "second," etc., in the specification, claims, and accompanying drawings of this invention are used to distinguish similar objects and are not necessarily used to describe a specific order or sequence. It should be understood that such data can be interchanged where appropriate so that the embodiments of the invention described herein can be implemented in orders other than those illustrated or described herein. Furthermore, the terms "comprising" and "having," and any variations thereof, are intended to cover a non-exclusive inclusion; for example, a process, method, system, product, or apparatus that comprises a series of steps or units is not necessarily limited to those steps or units explicitly listed, but may include other steps or units not explicitly listed or inherent to such processes, methods, products, or apparatus.

[0027] Example 1

[0028] Figure 1This is a structural diagram of a transcranial magnetic stimulation system according to Embodiment 1 of the present invention. Figure 1 As shown, the system includes: a transcranial alternating current stimulator 110, a stimulating electrode 120, a first electroencephalogram (EEG) acquisition device 130, a phase synchronization detection module 140, a control module 150, a transcranial magnetic stimulator 160, and a coil 170.

[0029] The transcranial alternating current (TAC) stimulator 110 is connected to a stimulation electrode 120 and is used to output a sinusoidal wave of a specific frequency. The sinusoidal alternating current output through the stimulation electrode 120 is used to stimulate a target brain region of the target subject based on the sinusoidal alternating current. The stimulation electrode 120 is placed at the target brain region. A first EEG acquisition device 130 is used to acquire the target EEG signal from the target brain region and input the target EEG signal to a phase synchronization detection module 140. The phase synchronization detection module 140 is connected to the transcranial AC stimulator 160, the first EEG acquisition device 130, and the control module 150, respectively, and is used to synchronize the sinusoidal electrical stimulation signal from the transcranial AC stimulator 160 with the target brain region. When the phase of the electrical signal is synchronized, a detection start signal is generated and transmitted to the control module 150. The control module 150 is connected to the transcranial magnetic stimulation device 160 and is used to read the real-time phase of the sinusoidal electrical stimulation signal output by the transcranial AC current stimulator 160 based on the detection start signal, generate a control signal based on the real-time phase and preset conditions, and input the control signal to the transcranial magnetic stimulation device 160. The transcranial magnetic stimulation device 160 is connected to the coil 170 and is used to output transcranial magnetic stimulation pulses through the coil 170 to stimulate the target brain region of the target object based on the transcranial magnetic stimulation pulses, wherein the coil 170 is placed at the target brain region.

[0030] The transcranial magnetic stimulation (TMS) device can be configured according to the needs of the scenario, and no specific limitations are made here. Optionally, the TMS device may be equipped with an external input trigger port. Specifically, the feature extraction and storage module can input the pulse control signal into the TMS device through the external input trigger port.

[0031] The coil can be configured according to the needs of the scenario, and no specific limitation is made here. Optionally, the coil can be a figure-eight coil, a biconical coil, or a circular coil that matches the transcranial magnetic stimulation device.

[0032] The transcranial alternating current stimulator can be configured according to the needs of the scenario, and no specific limitations are made here. Optionally, the transcranial alternating current stimulator may be equipped with an external analog output port.

[0033] The first EEG acquisition device includes acquisition electrodes and an EEG analyzer. The acquisition electrodes are connected to the EEG analyzer and placed at the target brain region. The acquisition electrodes are electrodes capable of acquiring raw EEG signals corresponding to the target brain region. In this embodiment, the first EEG acquisition device may have eight acquisition electrodes. Optionally, the first EEG acquisition device may include one target EEG electrode, four spatially filtered EEG electrodes, one ground electrode, and two reference electrodes. The target EEG electrode is placed at a preset spatial location point on the target brain region. The preset spatial location point can be preset according to scenario requirements and is not specifically limited here. The four spatially filtered EEG electrodes are placed anterior and posterior to the target EEG electrode along the same sagittal line and lateral to the target EEG electrode in the same coronal plane, and at the same distance from the target EEG electrode. The ground electrode is placed at the tip of the nose, and the two reference electrodes are placed at the mastoid processes of both ears (reference points). Figure 2 ).

[0034] The EEG device is a device that amplifies the raw EEG signals. Optionally, the EEG device may be an EEG amplifier with eight or more EEG electrodes.

[0035] Specifically, the acquisition electrode is placed on the target brain region target point to acquire the raw EEG signal corresponding to the target brain region target point, and the raw EEG signal is transmitted to the EEG instrument. The EEG instrument amplifies the raw EEG signal to obtain the target EEG signal corresponding to the target brain region target point.

[0036] Optionally, the first EEG acquisition device is provided with acquisition electrodes, wherein the acquisition electrodes and the stimulation electrodes are combined into a composite electrode, the outer ring of the composite electrode is a ring-shaped stimulation electrode, and the inner part of the composite electrode is an acquisition electrode (see reference). Figure 2 The composite electrode is placed at the target brain region.

[0037] Specifically, the stimulating electrode and the acquiring electrode are a combined composite electrode. The outer ring of the composite electrode is a ring-shaped stimulating electrode that can be connected to the transcranial alternating current stimulator to achieve sinusoidal alternating current stimulation of the target brain region. The inner part of the ring-shaped stimulating electrode is the acquiring electrode, which can be connected to the electroencephalogram (EEG) device to acquire and amplify the EEG signals. In this embodiment of the invention, the transcranial alternating current stimulator can be equipped with two stimulating electrodes: one is the ring-shaped stimulating electrode of the composite electrode, placed at the target brain region, and the other is a hollow ring-shaped stimulating electrode placed at the orbitofrontal lobe.

[0038] Among them, the Figure 2It includes a target EEG electrode E0, a spatially filtered EEG electrode E1, a spatially filtered EEG electrode E2, a spatially filtered EEG electrode E3, a spatially filtered EEG electrode E4, a ring-shaped stimulating electrode S1, and a hollow ring-shaped stimulating electrode S2.

[0039] The phase synchronization detection module is used to detect whether the sinusoidal electrical stimulation signal and the target EEG signal are synchronized, and to generate a detection start signal when they are synchronized. Optionally, the phase synchronization detection module can be a lower-level machine based on Simulink, LabVIEW, or ARM.

[0040] Optionally, the phase synchronization detection module specifically includes a phase determination unit, a synchronization judgment unit, and a start signal generation unit;

[0041] The phase determination unit is used to determine the target neural signal in a specific frequency band corresponding to the target EEG signal, and to determine the first phase of the target neural signal and the second phase of the sinusoidal electrical stimulation signal corresponding to the target neural signal.

[0042] The synchronization judgment unit is used to determine whether the sinusoidal electrical stimulation signal and the target EEG signal are synchronized based on the first phase and the second phase.

[0043] The activation signal generation unit is used to generate a detection activation signal when the sinusoidal electrical stimulation signal and the target EEG signal are in phase synchronization.

[0044] The specific frequency band can be understood as the frequency band corresponding to the target neural signal in the target EEG signal. In this embodiment of the invention, the specific frequency band can be preset according to the needs of the scenario, and is not specifically limited here. For example, the specific frequency band can be [8Hz-12Hz] or [12Hz-16Hz], etc.

[0045] The target neural signal can be understood as the neural signal corresponding to the specific frequency band of the target EEG signal.

[0046] The first phase can be understood as the phase corresponding to the target neural signal.

[0047] The sinusoidal electrical stimulation signal can be understood as the signal corresponding to the transcranial alternating current stimulator. In this embodiment of the invention, the phase synchronization detection module can acquire the sinusoidal electrical stimulation signal based on the EEG device included in the first EEG acquisition device.

[0048] The second phase can be understood as the phase corresponding to the sinusoidal electrical stimulation signal.

[0049] The detection start signal can be understood as a signal that activates the control module to read the real-time phase of the sinusoidal electrical stimulation signal output by the transcranial AC stimulator.

[0050] Optionally, the synchronization determination unit is specifically used for:

[0051] Determine whether the first phase and the second phase are the same phase;

[0052] When the first phase and the second phase are the same, determine the phase difference between the first phase and the second phase within a first preset time period after the specific frequency band;

[0053] If the phase difference is less than a preset difference threshold, then the sinusoidal electrical stimulation signal and the target EEG signal are determined to be in phase synchronization.

[0054] The first preset time period can be understood as the time period used to determine the phase difference value. In this embodiment of the invention, the first preset time period can be preset according to scenario requirements, and is not specifically limited here. Optionally, the first preset time period can be a time period located after the specific frequency band. For example, the first preset time period can be 1s, 2s, or 3s, etc.

[0055] The phase difference can be understood as the difference between the first phase and the second phase within a first preset time period. Optionally, the phase difference can be 10°, 20°, or 30°, etc.

[0056] The preset difference threshold can be understood as a threshold used to compare with the phase difference to determine whether the sinusoidal electrical stimulation signal and the target EEG signal are in phase synchronization. In this embodiment of the invention, the preset difference threshold can be preset according to the needs of the scenario, and is not specifically limited here. Optionally, the preset difference threshold can be 20°, 30°, or 50°, etc.

[0057] Specifically, the target neural signal in a specific frequency band corresponding to the target EEG signal is determined, and the phase of the target neural signal, i.e., the first phase, is extracted. The phase 1 is compared with the phase of the sinusoidal electrical stimulation signal output by the transcranial AC stimulator, i.e., the second phase. If the first phase and the second phase are the same, the comparison is performed continuously for 1 second. If the error range of the first phase and the second phase is within 20° within 1 second, it is considered that the sinusoidal AC stimulation output by the transcranial AC stimulator has locked the real-time phase of the target brain region with the real-time phase of the sinusoidal AC. At this time, the phase synchronization detection module outputs a detection start signal to the control module.

[0058] Optionally, the phase determination unit specifically includes an EEG signal processing subunit, a forward prediction subunit, and a phase determination subunit; wherein,

[0059] The EEG signal processing subunit is used to preprocess the target EEG signal to obtain the initial neural signal of the specific frequency band, and to process the initial neural signal to obtain the target neural signal of the specific frequency band.

[0060] The forward prediction subunit is used to determine the forward prediction signal corresponding to the target neural signal, wherein the signal acquisition time corresponding to the forward prediction signal is later than the signal prediction time corresponding to the target neural signal.

[0061] The phase determination subunit is used to obtain the first phase of the target neural signal by determining the instantaneous phase value of the forward prediction signal.

[0062] Optionally, the EEG signal processing subunit is specifically used for:

[0063] The target EEG signal is subjected to Laplace spatial filtering to obtain a spatially filtered signal.

[0064] The spatially filtered signal is input into a zero-phase finite impulse response bandpass filter for frequency domain filtering to obtain the initial neural signal for a specific frequency band.

[0065] The distorted signal corresponding to the initial neural signal after the start and before the termination is removed to obtain the target neural signal, wherein the target neural signal is the unfiltered distorted signal segment.

[0066] Specifically, the target EEG signal is subjected to Laplace spatial filtering to improve the signal-to-noise ratio, resulting in a spatially filtered signal. This spatially filtered signal is then input into a zero-phase finite-impact response bandpass filter for frequency domain filtering, yielding an initial neural signal in a specific frequency band, i.e., a frequency-domain filtered signal. The high-pass and low-pass cutoff frequencies of the filter can be determined by the individualized neural oscillation frequency band. It should be understood that frequency domain filtering causes distortion at the beginning and end of the frequency-domain filtered signal. Therefore, the distorted signal after the start and before the end is truncated, and the remaining signal is treated as the unfiltered distortion signal segment, i.e., the target neural signal.

[0067] Furthermore, optionally, the forward prediction subunit is specifically used for:

[0068] The target neural signal is forward predicted by a regression forward prediction model to obtain a forward prediction signal, and / or the target neural signal is forward predicted by a sine wave fitting algorithm to obtain a forward prediction signal.

[0069] Furthermore, the phase determination subunit is specifically used for:

[0070] The instantaneous phase value of the forward prediction signal is determined by Hilbert-Huang transform, thereby obtaining the first phase of the target neural signal.

[0071] In this embodiment of the invention, the application flowchart of the phase synchronization detection module can be referred to. Figure 3 .

[0072] Optionally, the control module includes a real-time phase judgment unit and a level output unit; wherein,

[0073] The real-time phase determination unit is used to determine whether the first real-time phase is in a preset phase;

[0074] The level output unit is used to output a transistor-to-transistor logic level to the transcranial magnetic stimulation device when the first real-time phase is in a preset phase.

[0075] The preset phase may include a peak phase and / or a trough phase.

[0076] Optionally, the level output unit includes a first control subunit and a second control subunit; wherein,

[0077] The first control subunit is used to output a transistor-transistor logic level to the transcranial magnetic stimulation device when the first real-time phase is the peak phase, so as to control the transcranial magnetic stimulation device to output transcranial magnetic stimulation pulses of a first preset frequency with an interval of a first preset period.

[0078] The second control subunit is used to output a transistor-transistor logic level to the transcranial magnetic stimulation device when the real-time phase of the first real-time phase is a trough phase, so as to control the transcranial magnetic stimulation device to output transcranial magnetic stimulation pulses of a second preset frequency with an interval of a second preset period.

[0079] The first preset period, the first preset frequency, the second preset period, and the second preset frequency can be preset according to scenario requirements and are not specifically limited here. Optionally, the first preset period and / or the first preset frequency can be 2, 5, or 10, etc. The first preset frequency and / or the second preset frequency can be 1Hz, 5Hz, or 10Hz, etc.

[0080] Optionally, specifically, after receiving the high-level (Transistor-Transistor Logic, TTL) signal from the phase synchronization detection module, the control module begins to detect the real-time phase of the sinusoidal alternating current output by the transcranial alternating current stimulator. When the real-time phase is at a preset phase, the control module outputs a high-level TTL signal to the external trigger port of the transcranial magnetic stimulator to trigger the output of the transcranial magnetic stimulation pulse, thereby stimulating the target brain region. For example, taking the motor cortex as an example, the μ rhythm (8-12Hz) is the inherent frequency band of the target brain region. When the μ rhythm phase is at its peak, the neuronal clusters in the motor cortex are in a low-excitation state. Therefore, the preset phase can be set to the peak phase. When the control module detects that the external sinusoidal electrical stimulation signal is at its peak phase, it triggers the transcranial magnetic stimulation device to output transcranial magnetic stimulation pulses, and the interval between two magnetic pulse outputs is at least 10 cycles, which can achieve low-frequency transcranial magnetic stimulation of about 1Hz. At this time, the excitability of the motor cortex can be effectively reduced. Conversely, when the μ rhythm phase is at its trough phase, the neuronal clusters in the motor cortex are in a high-excitation state. Therefore, the predicted phase can be set to the trough phase. When the control module detects that the external sinusoidal electrical stimulation signal is at its trough phase, it triggers the transcranial magnetic stimulation device to output transcranial magnetic stimulation pulses, and the interval between two magnetic pulse outputs is at least 1-2 cycles, which can achieve high-frequency transcranial magnetic stimulation of about 5-10Hz, which can effectively increase the excitability of the motor cortex.

[0081] Optionally, the transcranial magnetic stimulation system further includes: a second electroencephalogram (EEG) acquisition device and a specific frequency determination module, wherein,

[0082] The second EEG acquisition device is used to determine the inherent frequency band corresponding to the target brain region and to acquire the reference EEG signal of the target brain region in a preset state during a second preset time period.

[0083] The specific frequency determination module is used to determine the intrinsic frequency value corresponding to the target brain region based on the intrinsic frequency band and the reference EEG signal, and to determine the specific frequency based on the intrinsic frequency value.

[0084] The second EEG acquisition device may include acquisition electrodes and an EEG analyzer, wherein the acquisition electrodes are connected to the EEG analyzer and placed at the target brain region. In this embodiment of the invention, the first EEG acquisition device and the second EEG acquisition device may be the same or different.

[0085] The inherent frequency band can be understood as the frequency band used to determine the inherent frequency value. In this embodiment of the invention, the inherent frequency band can be preset according to scenario requirements, and is not specifically limited here. Optionally, the inherent frequency band can be the frequency band [f1, f2] corresponding to the target brain region determined based on common sense in neurophysiology. For example, the inherent frequency band can be [8Hz, 12Hz].

[0086] The second preset time period can be understood as a preset time period for collecting the reference EEG signal. In this embodiment of the invention, the second preset time period can be preset according to the needs of the scenario, and is not specifically limited here. Optionally, the second preset time period can be 2 minutes, 3 minutes, or 5 minutes, etc.

[0087] The preset state can be understood as the state corresponding to the target brain region when the reference EEG signal is acquired. Optionally, the preset state can be an open-eye resting state.

[0088] The reference EEG signal can be understood as an EEG signal used to determine the intrinsic frequency value.

[0089] The inherent frequency value can be understood as the frequency value corresponding to the target brain region based on the inherent frequency band and the reference EEG signal.

[0090] The specific frequency can be understood as a specific frequency determined based on the inherent frequency value. It is understood that, in this embodiment of the invention, the determined specific frequency is used to set the transcranial alternating current stimulator to output a sine wave of a specific frequency.

[0091] Specifically, based on common sense in neurophysiology, the inherent frequency band [f1, f2] of the target brain region is determined. Before formally conducting the experiment of transcranial alternating current stimulation combined with transcranial magnetic stimulation to regulate brain activity, a reference EEG signal of the target brain region in an open-eye resting state is collected for 2 minutes. The spectrum of the reference EEG signal is obtained through fast Fourier transform, and the peak value of the spectrum is obtained within the inherent frequency band of the target brain region. The frequency corresponding to the peak value is taken as the inherent frequency value of the target brain region, and the specific frequency is set according to the inherent frequency value. Further, the stimulation electrode of the transcranial alternating current stimulator is placed on the target brain region to stimulate the target brain region with a sinusoidal alternating current of the same inherent frequency as the target brain region. It is understood that the inherent frequency value corresponding to the target brain region is not the same for different people. In this embodiment of the invention, the characteristic of setting corresponding personalized specific frequencies for different individuals is ensured, which improves the personalized experience of users and realizes personalized control of transcranial magnetic stimulation pulses for different individuals.

[0092] For example, taking the motor cortex as an example, according to common sense in neurophysiology, the μ rhythm (8-12Hz) is the inherent frequency band of the target brain region. Before the formal experiment, acquisition electrodes are placed in the motor cortex to collect a 2-minute resting-state reference EEG signal with eyes open. The spectrum of the reference EEG signal is obtained by fast Fourier transform, and the peak value is obtained in the 8-12Hz frequency band. The frequency corresponding to the peak value is the inherent frequency of the individualized motor cortex.

[0093] Optional, specific, such as Figure 4 As shown, the hardware connection of the transcranial magnetic stimulation system can be:

[0094] The stimulation electrodes of the transcranial alternating current stimulator are placed at the target brain region. The target brain region is also connected to the electroencephalogram (EEG) device via a data acquisition electrode. The phase synchronization detection module is connected to both the EEG device and the transcranial alternating current stimulator. The phase synchronization detection module is also connected to the control module. The control module is connected to the external port of the transcranial magnetic stimulator. The transcranial magnetic stimulator is placed at the target brain region via a coil.

[0095] Specifically, the transcranial alternating current (TAC) stimulator outputs a sinusoidal wave of a specific frequency, and outputs sinusoidal alternating current through the stimulation electrodes to stimulate a target brain region of the target subject. A first EEG acquisition device is placed at the target brain region to collect the target EEG signal. The target EEG signal is an amplified EEG signal after being processed by the first EEG acquisition device. The first EEG acquisition device inputs the target EEG signal to a phase synchronization detection module. Simultaneously, the phase synchronization detection module also receives the sinusoidal electrical stimulation signal from the TAC stimulator. The phase synchronization detection module incorporates a phase synchronization detection algorithm to calculate the sinusoidal electrical stimulation of the TAC stimulator. If the real-time phase of the transcranial alternating current (TAC) stimulator is not synchronized with the real-time phase of the target EEG signal, the TAC stimulator continues to stimulate the target brain region and the real-time phase of the two signals is continuously monitored until a real-time phase lock is detected. At this point, the phase synchronization detection module outputs a high-level signal to the control module. The control module then begins to read the real-time phase of the sinusoidal electrical stimulation signal output by the TAC stimulator. When the phase meets the preset conditions, the control module outputs a high-level signal to the external trigger port of the TAC stimulator, triggering the TAC stimulator to output transcranial magnetic stimulation pulses, which reach the target brain region via coils, thereby achieving the regulation of the target brain region.

[0096] It is important to understand that using rhythmic sinusoidal alternating current to stimulate the target brain region can stimulate neural oscillations within the brain to synchronize with the sinusoidal electrical stimulation signal output by the transcranial alternating current stimulator. Furthermore, it can achieve phase locking between the target EEG signal corresponding to the neural oscillation and the sinusoidal electrical stimulation signal. Therefore, based on the phenomenon of synchronization between brain neural oscillations and external rhythms, and the correlation between the brain's response to external stimuli and the brain's oscillation state at the moment of application of the external stimulus, this invention achieves phase locking between the alternating current signal and brain neural oscillations through transcranial alternating current stimulation. Then, it indirectly obtains the real-time phase of the target EEG signal corresponding to the brain neural oscillations through the real-time phase of the alternating current signal. Finally, it triggers the output of transcranial magnetic stimulation pulses through the real-time phase of the alternating current signal, thereby achieving neuromodulation based on the brain neural oscillation state controlling transcranial magnetic stimulation.

[0097] This invention modulates the neural oscillations of the target brain region by using transcranial alternating current stimulation with the same oscillation frequency as the target EEG signal of the target brain region. This locks the phase of the target EEG signal corresponding to the neural oscillation of the target brain region with the sinusoidal electrical stimulation signal of the externally applied transcranial alternating current stimulator. Then, by detecting the real-time phase of the sinusoidal electrical stimulation signal output by the transcranial alternating current stimulator, the output of transcranial magnetic stimulation pulses is triggered. This achieves closed-loop neural modulation based on the individual's brain neural oscillation phase to trigger the output of transcranial magnetic stimulation pulses, thereby improving the modulation effect of transcranial magnetic stimulation and enhancing the consistency of modulation effects between and within individuals.

[0098] This invention outputs transcranial magnetic stimulation (TMS) pulses based on the real-time changes in brain nerve oscillations. Instead of directly detecting brain nerve oscillations to trigger TMS pulse output, it applies a sinusoidal alternating current to the target brain region. When the nerve oscillations at the target brain region are synchronized with the external sinusoidal electrical stimulation signal, the real-time phase of the external sinusoidal electrical stimulation signal is detected to control the TMS pulse output.

[0099] The technical solution of this invention involves a transcranial alternating current (TAC) stimulator connected to stimulation electrodes to output a sinusoidal wave of a specific frequency. The stimulation electrodes output sinusoidal alternating current to stimulate a target brain region of the target subject. The stimulation electrodes are placed at the target brain region, and different specific frequencies are set for different individuals, improving personalized experience and ensuring consistency of effects between and within individuals. A first EEG acquisition device is used to acquire the target EEG signal from the target brain region and input the target EEG signal to the phase synchronization detection module. The phase synchronization detection module is connected to the TAC stimulator, the first EEG acquisition device, and the control module, and is used to generate a phase synchronization signal when the sinusoidal stimulation signal from the TAC stimulator and the target EEG signal are in phase synchronization. A detection start signal is generated and transmitted to the control module. The control module, connected to the transcranial magnetic stimulation device, is used to read the real-time phase of the sinusoidal electrical stimulation signal output by the transcranial AC stimulator based on the detection start signal, and generate a control signal based on the real-time phase and preset conditions, and input the control signal to the transcranial magnetic stimulation device. This solves the problem of low accuracy in directly detecting the real-time phase of the target EEG signal, and indirectly obtains the real-time phase of the target EEG signal through the real-time phase of the sinusoidal electrical stimulation signal, thus improving the accuracy of detecting the real-time phase of the target EEG signal. The transcranial magnetic stimulation device, connected to the coil, is used to output transcranial magnetic stimulation pulses through the coil to stimulate the target brain region of the target object based on the transcranial magnetic stimulation pulses, wherein the coil is placed at the target brain region. Based on the technical solution of this invention, the problems of poor transcranial magnetic stimulation (TMS) effects caused by significant differences in the regulatory effects of TMS on the brain between and within individuals, as well as the low accuracy of real-time phase detection of the target EEG signal, are solved. The solution realizes closed-loop neural modulation based on real-time phase triggering of TMS pulse output using sinusoidal electrical stimulation signals. While ensuring consistency of the regulatory effects between and within individuals, the solution improves the accuracy of TMS pulse control, thereby enhancing the regulatory effect of TMS.

[0100] Example 2

[0101] Figure 5 This is a flowchart of a transcranial magnetic stimulation (TMS) method according to Embodiment 2 of the present invention. The TMS method can be used in a transcranial magnetic stimulation (TMS) system. Figure 5 As shown, the transcranial magnetic stimulation method specifically includes:

[0102] S210. Output a sine wave of a specific frequency, and output a sinusoidal alternating current through the stimulation electrode to stimulate the target brain region of the target subject based on the sinusoidal alternating current, wherein the stimulation electrode is placed at the target brain region.

[0103] S220. Collect the target EEG signal of the target brain region and input the target EEG signal into the phase synchronization detection module.

[0104] S230, when the sinusoidal electrical stimulation signal of the transcranial AC stimulator and the target EEG signal are in phase synchronization, a detection start signal is generated and the detection start signal is transmitted to the control module.

[0105] S240. Based on the detection start signal, read the real-time phase of the sinusoidal electrical stimulation signal output by the transcranial AC stimulator, generate a control signal based on the real-time phase and preset conditions, and input the control signal to the transcranial magnetic stimulator.

[0106] S250. Transcranial magnetic stimulation pulses are output through the coil to stimulate the target brain region of the target subject based on the transcranial magnetic stimulation pulses, wherein the coil is placed at the target brain region.

[0107] Specifically, the transcranial alternating current (TAC) stimulator outputs a sinusoidal wave of a specific frequency. This sinusoidal alternating current is then output through the stimulation electrodes to stimulate the target brain region of the target subject. The first EEG acquisition device collects the target brain region's EEG signal and inputs it to the phase synchronization detection module. The module receives the sinusoidal stimulation signal from the TAC stimulator and calculates the real-time phase of the TAC stimulator's sinusoidal stimulation and the real-time phase of the target EEG signal. If the two real-time phases are not synchronized, the TAC stimulator continues to stimulate the target brain region, and the synchronization of the two real-time phases continues until a real-time phase lock is detected. Then, the phase synchronization detection module outputs a high-level signal to the control module. The control module reads the real-time phase of the sinusoidal stimulation signal output by the TAC stimulator. When the phase meets a preset condition, a high-level signal is output, triggering the transcranial magnetic stimulation (TMS) device to output transcranial magnetic stimulation pulses, which reach the target brain region through a coil, thus achieving the regulation of the target brain region.

[0108] Optionally, the first EEG acquisition device is provided with an acquisition electrode, wherein the acquisition electrode and the stimulation electrode are a combined composite electrode, the outer ring of the composite electrode is a ring-shaped stimulation electrode, and the interior of the composite electrode is an acquisition electrode, wherein the composite electrode is placed at the target brain region.

[0109] Optionally, the phase synchronization detection module specifically includes a phase determination unit, a synchronization judgment unit, and a start signal generation unit; wherein,

[0110] The phase determination unit determines the target neural signal in a specific frequency band corresponding to the target EEG signal, and determines the first phase of the target neural signal and the second phase of the sinusoidal electrical stimulation signal corresponding to the target neural signal. The synchronization judgment unit determines whether the sinusoidal electrical stimulation signal is synchronized with the target EEG signal based on the first phase and the second phase. The activation signal generation unit generates a detection activation signal when the sinusoidal electrical stimulation signal and the target EEG signal are in phase synchronization.

[0111] Optionally, a synchronization judgment unit determines whether the first phase and the second phase are in phase; if the first phase and the second phase are in phase, the phase difference between the first phase and the second phase within a first preset time period after the specific frequency band is determined; if the phase difference is less than a preset difference threshold, the sinusoidal electrical stimulation signal and the target EEG signal are determined to be in phase synchronization.

[0112] Optionally, the phase determination unit specifically includes an EEG signal processing subunit, a forward prediction subunit, and a phase determination subunit; wherein,

[0113] The EEG signal processing subunit preprocesses the target EEG signal to obtain an initial neural signal in the specific frequency band, and processes the initial neural signal to obtain the target neural signal in the specific frequency band. The forward prediction subunit determines the forward prediction signal corresponding to the target neural signal, wherein the signal acquisition time corresponding to the forward prediction signal is later than the signal prediction time corresponding to the target neural signal. The phase determination subunit determines the first phase of the target neural signal by determining the instantaneous phase value of the forward prediction signal.

[0114] Optionally, the forward prediction subunit can perform forward prediction on the input target neural signal using a regression forward prediction model to obtain a forward prediction signal, and / or can perform forward prediction on the target neural signal using a sine wave fitting algorithm to obtain a forward prediction signal.

[0115] Optionally, the control module includes a real-time phase judgment unit and a level output unit; wherein,

[0116] The real-time phase determination unit determines whether the first real-time phase is in a preset phase.

[0117] When the first real-time phase is in a preset phase, the level output unit outputs a transistor-to-transistor logic level to the transcranial magnetic stimulation device.

[0118] Optionally, the level output unit includes a first control subunit and a second control subunit; wherein,

[0119] The first control subunit outputs a transistor-to-transistor logic level to the transcranial magnetic stimulation (TMS) device when the first real-time phase is at its peak, thereby controlling the TMS device to output TMS pulses at a first preset frequency with a first preset period interval. The second control subunit outputs a transistor-to-transistor logic level to the TMS device when the real-time phase of the first real-time phase is at its trough, thereby controlling the TMS device to output TMS pulses at a second preset frequency with a second preset period interval.

[0120] Optionally, the transcranial magnetic stimulation method further includes: determining the inherent frequency band corresponding to the target brain region using the second EEG acquisition device, and acquiring a reference EEG signal of a preset state during a second preset time period corresponding to the target brain region; and using the specific frequency determination module to determine the inherent frequency value corresponding to the target brain region based on the inherent frequency band and the reference EEG signal, and to determine the specific frequency based on the inherent frequency value.

[0121] The technical solution of this invention involves outputting a sinusoidal wave of a specific frequency and then outputting sinusoidal alternating current through the stimulation electrode to stimulate a target brain region of the target subject based on the sinusoidal alternating current, wherein the stimulation electrode is placed at the target brain region; acquiring the target EEG signal of the target brain region and inputting the target EEG signal to the phase synchronization detection module; generating a detection start signal when the sinusoidal electrical stimulation signal of the transcranial alternating current stimulator and the target EEG signal are in phase synchronization, and transmitting the detection start signal to the control module; reading the real-time phase of the sinusoidal electrical stimulation signal output by the transcranial alternating current stimulator based on the detection start signal, generating a control signal based on the real-time phase and preset conditions, and inputting the control signal to the transcranial magnetic stimulation device; and outputting transcranial magnetic stimulation pulses through the coil to stimulate the target brain region of the target subject based on the transcranial magnetic stimulation pulses, wherein the coil is placed at the target brain region. Based on the technical solution of this invention, the problems of poor transcranial magnetic stimulation (TMS) effects caused by significant differences in the regulatory effects of TMS on the brain between and within individuals, and the low accuracy of real-time phase detection of target EEG signals, are solved. The solution achieves closed-loop neural modulation based on real-time phase triggering of TMS pulse output using sinusoidal electrical stimulation signals. While ensuring consistency in regulatory effects between and within individuals, the solution improves the accuracy of TMS pulse control, thereby enhancing the regulatory effect of TMS.

[0122] It should be understood that the above-described process can be used to rearrange, add, or delete steps. For example, the steps described in this invention can be executed in parallel, sequentially, or in different orders, as long as the desired result of the technical solution of this invention can be achieved, and this is not limited herein.

[0123] The specific embodiments described above do not constitute a limitation on the scope of protection of this invention. Those skilled in the art should understand that various modifications, combinations, sub-combinations, and substitutions can be made according to design requirements and other factors. Any modifications, equivalent substitutions, and improvements made within the spirit and principles of this invention should be included within the scope of protection of this invention.

Claims

1. A transcranial magnetic stimulation system, characterized by, The transcranial alternating current stimulation instrument, the stimulation electrode, the first electroencephalogram acquisition device, the phase synchronization detection module, the control module, the transcranial magnetic stimulation instrument and the coil are included. The transcranial alternating current stimulation instrument is connected with the stimulation electrode and is used for outputting a sine wave of a specific frequency, outputting a sine alternating current through the stimulation electrode, and stimulating a target point of a target brain area of a target object based on the sine alternating current, wherein the stimulation electrode is placed at the target point of the target brain area. The first electroencephalogram acquisition device is used for acquiring a target electroencephalogram signal of the target brain area target point and inputting the target electroencephalogram signal to the phase synchronization detection module. The phase synchronization detection module is connected with the transcranial alternating current stimulation instrument, the first electroencephalogram acquisition device and the control module respectively, is used for generating a detection start signal in the case that the phase of the sine electric stimulation signal of the transcranial alternating current stimulation instrument and the target electroencephalogram signal are synchronized, and transmitting the detection start signal to the control module. The control module is connected with the transcranial magnetic stimulation instrument, is used for reading a real-time phase of the sine electric stimulation signal output by the transcranial alternating current stimulation instrument based on the detection start signal, generating a control signal based on the real-time phase and a preset condition, and inputting the control signal to the transcranial magnetic stimulation instrument. The transcranial magnetic stimulation instrument is connected with the coil, is used for outputting a transcranial magnetic stimulation pulse through the coil, and stimulating the target point of the target brain area of the target object based on the transcranial magnetic stimulation pulse, wherein the coil is placed at the target point of the target brain area. The phase synchronization detection module specifically includes a phase determination unit, a synchronization judgment unit and a start signal generation unit. The phase determination unit is used for determining a target neural signal of a specific frequency band corresponding to the target electroencephalogram signal, determining a first phase of the target neural signal, and determining a second phase of the sine electric stimulation signal corresponding to the target neural signal. The synchronization judgment unit is used for determining whether the sine electric stimulation signal and the target electroencephalogram signal are synchronized based on the first phase and the second phase. The start signal generation unit is used for generating a detection start signal in the case that the phase of the sine electric stimulation signal and the target electroencephalogram signal are synchronized. The synchronization judgment unit is specifically used for: determining whether the first phase and the second phase are the same in phase; in the case that the first phase and the second phase are the same in phase, determining a phase difference value of the first phase and the second phase within a first preset time period after the specific frequency band; in the case that the phase difference value is less than a preset difference threshold value, it is determined that the phase of the sine electric stimulation signal and the target electroencephalogram signal is synchronized. The first electroencephalogram acquisition device is provided with an acquisition electrode, the acquisition electrode and the stimulation electrode are a two-in-one composite electrode, the outer ring of the composite electrode is a ring-shaped stimulation electrode, and the inside of the composite electrode is an acquisition electrode, wherein the composite electrode is placed at the target point of the target brain area.

2. The system of claim 1, wherein, ​ 3. The system of claim 1, wherein, The phase determination unit specifically comprises an electroencephalogram signal processing subunit, a forward prediction subunit and a phase determination subunit; wherein, The electroencephalogram signal processing subunit is configured to obtain an initial neural signal of the specific frequency band by preprocessing the target electroencephalogram signal, and obtain a target neural signal of the specific frequency band by processing the initial neural signal; The forward prediction subunit is configured to determine a forward prediction signal corresponding to the target neural signal, wherein the signal acquisition time corresponding to the forward prediction signal is later than the signal prediction time corresponding to the target neural signal; The phase determination subunit is configured to obtain the first phase of the target neural signal by determining the instantaneous phase value of the forward prediction signal.

4. The system of claim 3, wherein, The forward prediction subunit is specifically configured to: perform forward prediction on the input target neural signal through a regression forward prediction model to obtain a forward prediction signal, and / or perform forward prediction on the target neural signal through a sine wave fitting algorithm to obtain a forward prediction signal.

5. The system of claim 1, wherein, The control module comprises a real-time phase judgment unit and a level output unit; wherein, The real-time phase judgment unit is configured to judge whether the first real-time phase is in a preset phase; The level output unit is configured to output a transistor-transistor logic level to the transcranial magnetic stimulation instrument in the case that the first real-time phase is in the preset phase.

6. The system of claim 5, wherein, The level output unit comprises a first control subunit and a second control subunit; wherein, The first control subunit is configured to output a transistor-transistor logic level to the transcranial magnetic stimulation instrument to control the transcranial magnetic stimulation instrument to output transcranial magnetic stimulation pulses of a first preset frequency with a first preset period interval when the first real-time phase is a peak phase; The second control subunit is configured to output a transistor-transistor logic level to the transcranial magnetic stimulation instrument to control the transcranial magnetic stimulation instrument to output transcranial magnetic stimulation pulses of a second preset frequency with a second preset period interval when the real-time phase of the first real-time phase is a trough phase.

7. The system of claim 1, wherein, Further comprising: A second electroencephalogram acquisition device and a specific frequency determination module, wherein, The second electroencephalogram acquisition device is configured to determine an inherent frequency band corresponding to the target brain area target point, and acquire reference electroencephalogram signals of a preset state of a second preset time period corresponding to the target brain area target point; The specific frequency determination module is configured to determine an inherent frequency value corresponding to the target brain area target point according to the inherent frequency band and the reference electroencephalogram signals, and determine the specific frequency according to the inherent frequency value.

8. A transcranial magnetic stimulation method characterized by comprising: Comprising: A transcranial alternating current stimulation instrument, a stimulation electrode, a first electroencephalogram acquisition device, a phase synchronization detection module, a control module, a transcranial magnetic stimulation instrument and a coil; wherein, A sine wave of a specific frequency is output, and a sine alternating current is output through the stimulation electrode to stimulate a target brain area target point of a target object based on the sine alternating current, wherein the stimulation electrode is placed at the target brain area target point; Target electroencephalogram signals of the target brain area target point are acquired, and the target electroencephalogram signals are input to the phase synchronization detection module; In the case that the phase of the sinusoidal electric stimulation signal of the transcranial alternating current stimulator and the target brain electrical signal are synchronized, a detection start signal is generated and transmitted to the control module; Based on the detection start signal, the real-time phase of the sinusoidal electric stimulation signal output by the transcranial alternating current stimulator is read, and a control signal is generated based on the real-time phase and a preset condition, and the control signal is input to the transcranial magnetic stimulator; The transcranial magnetic stimulation pulse is output through the coil to stimulate the target brain region target point of the target object based on the transcranial magnetic stimulation pulse, wherein the coil is placed at the target brain region target point; The in the case that the phase of the sinusoidal electric stimulation signal of the transcranial alternating current stimulator and the target brain electrical signal are synchronized, a detection start signal is generated, comprising: Determine the target neural signal of the specific frequency band corresponding to the target brain electrical signal, and determine the first phase of the target neural signal, and determine the second phase of the sinusoidal electric stimulation signal corresponding to the target neural signal; Based on the first phase and the second phase, it is determined whether the sinusoidal electric stimulation signal and the target brain electrical signal are synchronized; In the case that the phase of the sinusoidal electric stimulation signal and the target brain electrical signal are synchronized, a detection start signal is generated; The based on the first phase and the second phase, it is determined whether the sinusoidal electric stimulation signal and the target brain electrical signal are synchronized, comprising: Determine whether the first phase and the second phase are the same phase; In the case that the first phase and the second phase are the same phase, the phase difference value of the first phase and the second phase within a first preset time period after the specific frequency band is determined; In the case that the phase difference value is less than a preset difference threshold, then it is determined that the phase of the sinusoidal electric stimulation signal and the target brain electrical signal are synchronized.

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