Transcranial magnetic stimulation and electroencephalogram universal synchronization module, method and system

Abstract

The transcranial magnetic stimulation and electroencephalogram general synchronization module, method and system provided by the application rely on a magnetic field sensing unit to pick up the magnetic field change of a TMS coil and output a Hall voltage, generate a synchronization trigger signal after buffering and filtering and hysteresis threshold discrimination, and deliver the synchronization trigger signal to an electroencephalogram acquisition device. The transcranial magnetic stimulation and electroencephalogram general synchronization module adopts a full hardware signal link processing, without delay caused by software scheduling and sound-light propagation. The hysteresis threshold can filter small-amplitude noise fluctuations, can realize microsecond-level low-jitter synchronization marking, avoid synchronization jitter from hiding TMS-induced potential sub-millisecond physiological waveforms, guarantee the scientific nature of electroencephalogram event-related potential analysis, and meet the high real-time feedback timing requirements of closed-loop neural regulation.

Description

Technical Field

[0001] This application relates to the field of biomedical engineering technology, and in particular to a transcranial magnetic stimulation and electroencephalography (EEG) universal synchronization module, method and system. Background Technology

[0002] In neuroscience and clinical practice, simultaneous transcranial magnetic stimulation and electroencephalography (TMS-EEG) recording is crucial for studying brain functional connectivity, assessing neuromodulation effects, and achieving closed-loop therapy.

[0003] Currently, the mainstream solution for achieving high-precision synchronization relies on directly accessing the stimulation control circuitry inside the TMS device to obtain an electrical signal that is strictly synchronized with the pulse emission. The specific path of this technical solution is as follows: First, key circuit nodes need to be identified within the TMS host, such as the gate drive signal controlling the power switching devices (IGBT / MOSFET) or the discharge detection signal of the high-voltage capacitor; then, the electrical signal from this node is physically led out to an external interface by soldering wires. Because the original signal level and noise environment are incompatible with the EEG device, a dedicated signal conditioning box is usually required. This box contains circuits for level conversion, opto-isolation, and pulse shaping, ultimately generating a standard TTL pulse output to the external trigger port of the EEG device. Although this solution can achieve relatively high-precision synchronization at the microsecond level, it essentially requires invasive modifications to a specific TMS device and is highly dependent on the specific internal circuit design of the device, resulting in poor versatility, high implementation risk, and complex maintenance.

[0004] Another alternative is to employ synchronization methods based on software or external sensors. Software synchronization typically relies on an operating system timer, where the control computer simultaneously sends software trigger commands to both the TMS and EEG devices at preset stimulus times. External sensor solutions detect pulse events using dedicated sensors deployed near the TMS coil (such as a microphone to collect the "click" sound of the coil discharging, or a photoelectric sensor to detect the flash of light from the coil's operation), converting them into electrical signals that are then sent to the EEG device. While these methods avoid hardware intrusion, their reliance on sound / light propagation, sensor response, operating system scheduling, and network communication introduces millisecond-level and unstable latency jitter, making them unsuitable for neural response analysis with stringent timing accuracy requirements.

[0005] Existing high-precision time synchronization solutions for TMS-EEG employ synchronization methods based on software or external sensors (such as sound and light signals), which suffer from millisecond-level uncertain delays and jitter, resulting in insufficient timing accuracy. In contrast, TMS evoked potentials possess sub-millisecond-level precise timing characteristics. Large random jitter in the synchronization signal can contaminate or even obliterate effective physiological waveforms, causing event-related potential analysis to lose its scientific rigor. Furthermore, it cannot meet the timing requirements of high-timeliness feedback in closed-loop neuromodulation applications, making it difficult to adapt to the high-standard research and clinical needs. Summary of the Invention

[0006] The technical problem this application aims to solve is that existing high-precision time synchronization schemes for TMS-EEG employ synchronization methods based on software or external sensors (such as sound or light signals), which suffer from millisecond-level uncertain delays and jitter, resulting in insufficient timing accuracy. In contrast, TMS evoked potentials possess sub-millisecond-level precise timing characteristics. Large random jitter in the synchronization signal can contaminate or even obliterate effective physiological waveforms, causing event-related potential analysis to lose its scientific rigor. Furthermore, it cannot meet the timing requirements of high-timeliness feedback in closed-loop neuromodulation applications, making it difficult to adapt to the high-standard research and clinical needs.

[0007] To address the aforementioned issues, this application provides a universal synchronization module, method, and system for transcranial magnetic stimulation and electroencephalography (EEG).

[0008] In a first aspect, the present invention discloses a universal synchronization module for transcranial magnetic stimulation and electroencephalography, which includes a magnetic field sensing unit, a signal buffer conditioning unit, a threshold comparison unit, and an output unit. The magnetic field sensing unit is connected to the signal buffer conditioning unit, the signal buffer conditioning unit is connected to the threshold comparison unit, and the threshold comparison unit is connected to the output unit. The magnetic field sensing unit acquires the magnetic field change signal generated when the TMS stimulation coil is working and outputs the Hall voltage signal. The signal buffering and conditioning unit buffers and filters the Hall voltage signal. The threshold comparison unit compares the Hall voltage signal with the preset hysteresis threshold. If the Hall voltage signal exceeds the preset hysteresis threshold, a synchronous trigger signal is output. The output unit outputs the synchronous trigger signal to the EEG acquisition device.

[0009] Preferably, the magnetic induction module includes a linear Hall effect sensor for acquiring the magnetic field change signal generated when the TMS stimulation coil is working.

[0010] Preferably, the signal buffer conditioning unit includes a buffer subunit and a filter subunit, and the buffer subunit and the filter subunit are connected.

[0011] Preferably, the buffer subunit is a voltage follower; The non-inverting input of the voltage follower receives the Hall voltage signal output by the magnetic field induction unit, and the output of the voltage follower is connected to the inverting input of the voltage follower.

[0012] Preferably, the threshold comparison unit includes a voltage comparison subunit and a pulse shaping subunit, and the voltage comparison subunit and the pulse shaping subunit are connected.

[0013] Preferably, the non-inverting input of the voltage comparator subunit receives the Hall voltage signal, and the inverting input receives a preset hysteresis threshold.

[0014] Preferably, the output unit includes an interface and a protection resistor, with the two ends of the protection resistor connected to the interface and the output terminal of the pulse shaping subunit, respectively.

[0015] Secondly, the present invention discloses a transcranial magnetic stimulation and electroencephalography (EEG) universal synchronization system, which includes the aforementioned transcranial magnetic stimulation and EEG universal synchronization module.

[0016] Preferably, it includes a TMS stimulation coil and an EEG acquisition device, wherein the TMS stimulation coil is connected to a magnetic field induction unit and the EEG acquisition device is connected to an output unit.

[0017] Thirdly, this invention discloses a universal synchronization method for transcranial magnetic stimulation (TMS) and electroencephalography (EEG), applicable to the aforementioned universal synchronization module for TMS and EEG, comprising, The magnetic field change signal generated when the TMS stimulation coil is working is acquired, converted into a Hall voltage signal, and output after preprocessing. A hysteresis threshold is preset, and the preprocessed Hall voltage signal is compared with the hysteresis threshold. When the preprocessed Hall voltage signal exceeds the hysteresis threshold, a synchronization trigger signal is output and sent to the EEG acquisition device.

[0018] The technical solution provided in this application has the following advantages compared with the prior art: The transcranial magnetic stimulation (TMS) and electroencephalography (EEG) synchronization module, method, and system provided in this application, mention that the TMS and EEG synchronization module relies on a magnetic field induction unit to pick up changes in the magnetic field of the TMS coil and outputs a Hall voltage. After buffering, filtering, and hysteresis threshold discrimination, a synchronization trigger signal is generated and sent to the EEG acquisition device. The TMS and EEG synchronization module adopts a fully hardware signal link processing, eliminating delays caused by software scheduling and sound and light propagation. The hysteresis threshold can filter out small noise fluctuations, enabling microsecond-level low-jitter synchronization marking. This avoids synchronization jitter from obscuring the sub-millisecond physiological waveforms of TMS evoked potentials, ensuring the scientific nature of EEG event-related potential analysis and meeting the high real-time feedback timing requirements of closed-loop neural modulation.

[0019] The transcranial magnetic stimulation and electroencephalography (EEG) universal synchronization module method mentions that synchronization marking is completed through hardware-based steps such as magnetic field acquisition, signal preprocessing, threshold comparison, and trigger output. There are no uncertain delays introduced by the operating system or acoustic / optical media throughout the process. The synchronization timing is highly deterministic and can completely preserve the timing characteristics of sub-millisecond evoked potentials. This solves the problem of insufficient timing accuracy in traditional synchronization methods and provides a reliable timing benchmark for high-precision EEG physiological analysis and real-time closed-loop neuromodulation.

[0020] The transcranial magnetic stimulation and electroencephalogram (EEG) universal synchronization module system mentions that, relying on the pure hardware timing acquisition architecture of the synchronization module, the entire system does not need to rely on acoustic and optical or software synchronization methods. The overall timing is stable with minimal delay and jitter, and it can accurately capture the moment of stimulation and synchronously mark the EEG data stream. It is suitable for various high-precision neuroscientific research and clinical neuromodulation scenarios, and greatly improves the data reliability of TMS-EEG synchronous acquisition. Attached Figure Description

[0021] The accompanying drawings, which are incorporated in and form part of this specification, illustrate embodiments consistent with the invention and, together with the description, serve to explain the principles of the invention.

[0022] To more clearly illustrate the technical solutions in the embodiments of the present invention or the prior art, the drawings used in the description of the embodiments or the prior art will be briefly introduced below. Obviously, for those skilled in the art, other drawings can be obtained based on these drawings without creative effort.

[0023] Figure 1 A module diagram of a universal synchronization module for transcranial magnetic stimulation and electroencephalography provided in this application; Figure 2 A circuit diagram of the magnetic induction unit of a transcranial magnetic stimulation and electroencephalogram (EEG) universal synchronization module provided in this application; Figure 3 A circuit diagram of a signal buffer conditioning unit for a transcranial magnetic stimulation and electroencephalogram (EEG) universal synchronization module provided in this application; Figure 4 A circuit diagram of a threshold comparison unit for a transcranial magnetic stimulation and electroencephalogram (EEG) universal synchronization module provided in this application; Figure 5 A circuit diagram of the output unit of a transcranial magnetic stimulation and electroencephalogram (EEG) universal synchronization module provided in this application; Figure 6 A block diagram of a transcranial magnetic stimulation and electroencephalogram (EEG) synchronization system provided in this application.

[0024] Explanation of reference numerals in the attached figures: 1. A universal synchronization module for transcranial magnetic stimulation and electroencephalography; 11. Magnetic field induction unit; 12. Signal buffering and conditioning unit; 121. Buffer subunit; 122. Filtering subunit; 13. Threshold comparison unit; 131. Voltage comparison subunit; 132. Pulse shaping subunit; 14. Output unit; 141. Interface; 142. Protection resistor; 100. A universal synchronization system for transcranial magnetic stimulation and electroencephalography; 2. TMS stimulation coil; 3. EEG acquisition equipment. Detailed Implementation

[0025] To make the objectives, technical solutions, and advantages of this application clearer, the technical solutions of this application will be clearly and completely described below with reference to the accompanying drawings. Obviously, the described embodiments are only some, not all, of the embodiments of this application. Based on the embodiments of this application, all other embodiments obtained by those skilled in the art without creative effort are within the scope of protection of this application.

[0026] Firstly, see Figures 1-5 This invention discloses a universal synchronization module 1 for transcranial magnetic stimulation (TMS) and electroencephalography (EEG), comprising a magnetic field sensing unit 11, a signal buffering and conditioning unit 12, a threshold comparison unit 13, and an output unit 14. The magnetic field sensing unit 11 is connected to the signal buffering and conditioning unit 12, the signal buffering and conditioning unit 12 is connected to the threshold comparison unit 13, and the threshold comparison unit 13 is connected to the output unit 14. The magnetic field sensing unit 11 acquires the magnetic field change signal generated when the TMS stimulation coil 2 is working and outputs a Hall voltage signal. The signal buffering and conditioning unit 12 buffers and filters the Hall voltage signal. The threshold comparison unit 13 compares the Hall voltage signal with a preset hysteresis threshold. If the Hall voltage signal exceeds the preset hysteresis threshold, a synchronization trigger signal is output. The output unit 14 outputs the synchronization trigger signal to the EEG acquisition device 3.

[0027] Specifically, in the transcranial magnetic stimulation and electroencephalography (EEG) universal synchronization module 1, the output of the magnetic field sensing unit 11 is connected to the input of the signal buffer conditioning unit 12, the output of the signal buffer conditioning unit 12 is connected to the input of the threshold comparison unit 13, and the output of the threshold comparison unit 13 is connected to the input of the output unit 14. The magnetic field sensing unit 11 is used to collect the magnetic field change signal generated by the TMS stimulation coil 2 and convert it into a Hall voltage signal. The signal buffer conditioning unit 12 receives the Hall voltage signal and performs buffering and filtering preprocessing. The threshold comparison unit 13 receives the preprocessed Hall voltage signal and compares it with a preset hysteresis threshold. When the Hall voltage signal exceeds the hysteresis threshold, a synchronization trigger signal is generated and transmitted to the output unit 14. The output unit 14 receives the synchronization trigger signal and outputs it to the EEG acquisition device 3, thereby realizing the time synchronization marking of TMS stimulation and EEG acquisition. That is, the magnetic field sensing unit 11 picks up the changes in the magnetic field of the TMS coil and outputs the Hall voltage. After buffering and filtering and hysteresis threshold discrimination, a synchronous trigger signal is generated and sent to the EEG acquisition device 3. The transcranial magnetic stimulation and EEG universal synchronization module 1 adopts a fully hardware signal link processing, without the delay caused by software scheduling and sound and light propagation. The hysteresis threshold can filter out small noise fluctuations, and can achieve microsecond-level low jitter synchronization marking. This avoids synchronization jitter from obscuring the sub-millisecond physiological waveform of TMS evoked potentials, ensuring the scientific nature of EEG event-related potential analysis and meeting the high real-time feedback timing requirements of closed-loop neural modulation.

[0028] The magnetic induction module includes a linear Hall effect sensor for acquiring the magnetic field change signal generated when the TMS stimulation coil 2 is working. Specifically, the magnetic field induction unit 11 includes a linear Hall effect sensor, which serves as the core acquisition component of the magnetic field induction unit 11. This linear Hall effect sensor is responsible for picking up the magnetic field change signal generated during the operation of the TMS stimulation coil 2 and converting it into a Hall voltage signal output. The signal output terminal of the magnetic field induction unit 11 is electrically connected to the input terminal of the subsequent signal buffer conditioning unit 12, transmitting the generated Hall voltage signal to the signal buffer conditioning unit 12.

[0029] The linear Hall effect sensor uses the Allegro A1324LUA-T chip. The sensor chip's sensitive axis must be perpendicular to the direction of the main magnetic field generated by the TMS coil during installation to achieve maximum response. The entire module connects to subsequent modules via a lightweight shielded cable and is designed for easy attachment (using medical adhesive tape, Velcro, or custom clamps) to specific locations on any TMS coil surface.

[0030] The signal buffer conditioning unit 12 includes a buffer subunit 121 and a filter subunit 122, which are connected together. The buffer subunit 121 is a voltage follower. The non-inverting input of the voltage follower receives the Hall voltage signal output by the magnetic field induction unit 11, and the output of the voltage follower is connected to the inverting input of the voltage follower.

[0031] Specifically, the signal buffer conditioning unit 12 consists of an interconnected buffer subunit 121 and a filter subunit 122. The buffer subunit 121 uses a voltage follower. The non-inverting input of the voltage follower is connected to the Hall voltage signal output by the magnetic field induction unit 11. The output of the voltage follower is shorted to its own inverting input to form a closed-loop feedback structure. The voltage follower buffers the Hall voltage signal through impedance isolation and outputs it to the filter subunit 122. The filter subunit 122 filters out high-frequency electromagnetic noise from the buffered signal, completes signal preprocessing, and outputs a stable analog voltage to the subsequent threshold comparison unit 13. The signal is adapted to the output characteristics of the Hall sensor, which outputs a DC-coupled voltage signal (usually with static bias) that is proportional to the instantaneous magnetic field strength. First, it is buffered by a voltage follower composed of a high-input-impedance operational amplifier. The filter subunit 122 uses an RC low-pass filter. The high-frequency noise of the output signal from the buffer subunit 121 is filtered out by the low-pass filter of the filter subunit 122.

[0032] The threshold comparison unit 13 includes a voltage comparison subunit 131 and a pulse shaping subunit 132, which are connected together. The non-inverting input of the voltage comparison subunit 131 receives the Hall voltage signal, and the inverting input receives a preset hysteresis threshold.

[0033] Specifically, the threshold comparison unit 13 consists of a voltage comparison subunit 131 and a pulse shaping subunit 132 connected to each other. The non-inverting input of the voltage comparison subunit 131 receives the pre-processed Hall voltage signal output by the signal buffer conditioning unit 12, and its inverting input is connected to a preset hysteresis threshold generated by a resistor voltage divider network. The voltage comparison subunit 131 compares the Hall voltage signal with the hysteresis threshold in real time, identifies the effective magnetic field pulse, and outputs a level signal with edge jitter to the pulse shaping subunit 132. The pulse shaping subunit 132 shapes and de-jitters the level signal, outputs a synchronous trigger signal with regular edges and no glitches, and transmits it to the output unit 14.

[0034] The voltage comparator subunit 131 includes chip P1, which is a hysteresis comparator. Chip P1 is a TLV3501AIDR. Its non-inverting input receives the conditioned Hall voltage signal, and its inverting input is connected to a fixed reference voltage source to set the magnetic field strength trigger threshold. When the magnetic field strength generated by the TMS coil exceeds the set threshold, the comparator output state flips. The pulse shaping subunit 132 includes chip U3, which is a 74HC14D and has a built-in Schmitt trigger. It can shape the signal output from the voltage comparator subunit 131 to eliminate jitter and generate a clean digital pulse with steep edges.

[0035] The output unit 14 includes an interface 141 and a protection resistor 142. The two ends of the protection resistor 142 are respectively connected to the interface 141 and the output terminal of the pulse shaping subunit 132.

[0036] Specifically, interface 141 adopts the BNC standard interface 141. The standardized signal output interface 141 is compatible with all mainstream EEG acquisition devices on the market, enabling universal connection and quick plug-and-play functionality. Synchronization signal cables can be easily installed and removed in experimental scenarios, and no soldering is required to set up or replace experimental equipment, making it convenient to use. The protection resistor 142 provides current limiting protection. If the external cable of the BNC interface 141 is short-circuited, or if there is a leakage / short-circuit fault at the EEG device input port, it limits the instantaneous large current backflow into the 74HC14D chip, preventing overcurrent burnout of the chip's output pins. Additionally, the protection resistor 142 matches the transmission cable impedance, eliminating signal reflection and ringing interference generated by high-speed digital pulses in the cable, ensuring stable output pulse edges and preventing noise-induced false triggering.

[0037] Secondly, see Figure 6 The present invention discloses a transcranial magnetic stimulation and electroencephalography (EEG) universal synchronization system 100, which includes the above-mentioned transcranial magnetic stimulation and EEG universal synchronization module 1, TMS stimulation coil 2 and EEG acquisition device 3. The TMS stimulation coil 2 is connected to the magnetic field induction unit 11, and the EEG acquisition device 3 is connected to the output unit 14.

[0038] Specifically, the time-varying magnetic field generated by the TMS stimulation coil 2 during operation triggers the EEG acquisition device 3 to obtain the corresponding EEG signal. Relying on the pure hardware timing acquisition architecture of the synchronization module, the entire system does not need to rely on audio-visual or software synchronization methods. The overall timing is stable with minimal delay and jitter. It can accurately capture the moment of stimulation and synchronously mark the EEG data stream, making it suitable for various high-precision neuroscience research and clinical neuromodulation scenarios, and significantly improving the data reliability of TMS-EEG synchronous acquisition.

[0039] Thirdly, this invention discloses a universal synchronization method for transcranial magnetic stimulation (TMS) and electroencephalography (EEG), applicable to the aforementioned universal synchronization module for TMS and EEG, comprising, Step S1: Acquire the magnetic field change signal generated when the TMS stimulation coil is working, convert it into a Hall voltage signal, and output the preprocessed Hall voltage signal after preprocessing. Step S2: Preset hysteresis threshold, compare the preprocessed Hall voltage signal with the hysteresis threshold, and when the preprocessed Hall voltage signal exceeds the hysteresis threshold, output a synchronization trigger signal, which is then output to the EEG acquisition device.

[0040] In step S1, the magnetic field sensing unit is attached to the surface of the TMS stimulation coil. The sensor's sensitive axis is adjusted to be perpendicular to the coil's main magnetic field. When the TMS stimulation coil releases stimulation pulses, the coil generates an alternating magnetic field. The magnetic field sensing unit senses the changes in magnetic field strength and linearly converts the magnetic field physical signal into a raw Hall analog voltage signal with static bias. This signal is transmitted backward through a shielded cable. The raw Hall voltage is sent to a buffer subunit. The non-inverting input of the voltage follower in the buffer subunit is connected to the Hall output, and the inverting input is directly connected to its own output. The high input impedance characteristic is used to completely acquire the Hall voltage, avoiding sensor load loss. The output of the voltage follower is connected to a filtering subunit containing an RC low-pass filter to filter out high-frequency electromagnetic interference noise from the environment, completing signal preprocessing. The stable analog voltage after filtering and noise reduction is used as the preprocessed Hall voltage signal and sent to the threshold comparison unit. This completes the acquisition and purification of the raw physical signal of TMS stimulation, converting the magnetic field physical quantity into a stable analog voltage that can be recognized by the back-end circuit. This eliminates signal distortion caused by impedance mismatch and high-frequency electromagnetic noise, providing a clean and attenuated input signal for subsequent threshold discrimination, and avoiding noise-induced missynchronization markers from the source.

[0041] In step S2, the threshold comparison unit acquires a preset hysteresis threshold and compares it with the input preprocessed Hall voltage signal. When the preprocessed Hall voltage signal exceeds the hysteresis threshold, the output state of the hysteresis comparator flips, and the output level is sent to the pulse shaping subunit for edge shaping to eliminate glitches and jitter, generating a clean digital pulse. The pulse shaping subunit completes the level drive and converts it into a standard voltage of 5V TTL synchronous trigger signal. After passing through the protection current limiting resistor, it is output through the interface of the output unit. The cable is connected to the external event trigger port of the EEG acquisition device to synchronously mark the TMS stimulation time in the EEG data stream.

[0042] By distinguishing effective TMS pulses from stray noise using a hysteresis threshold, jitter-induced false triggering caused by small signal fluctuations is eliminated, generating standard digital synchronization pulses with regular edges, and outputting TTL trigger signals adapted to EEG devices. This achieves microsecond-level precise timing marking, solves the millisecond-level jitter defects of traditional acoustic-optical and software synchronization, and fully preserves the sub-millisecond physiological timing characteristics of TMS evoked potentials.

[0043] Specifically, synchronization marking is completed through hardware-based steps of magnetic field acquisition, signal preprocessing, threshold comparison, and trigger output. There are no uncertain delays introduced by the operating system or acoustic / optical media throughout the process. The synchronization timing is highly deterministic and can completely preserve the timing characteristics of sub-millisecond evoked potentials. This solves the problem of insufficient timing accuracy in traditional synchronization methods and provides a reliable timing benchmark for high-precision EEG physiological analysis and real-time closed-loop neuromodulation.

[0044] In one embodiment, the hysteresis comparator is input with a reference voltage source (5V) and two sets of judgment benchmarks are fixedly generated: a high-level threshold of 0.52V and a low-level threshold of 0.32V. The pre-processed Hall voltage signal is input to the inverting input of the hysteresis comparator and compared in real time with the dynamically changing reference voltage at the non-inverting input. When the voltage rises to the high threshold of 0.52V, it is determined to be an effective TMS stimulation magnetic field, and the comparator level flips. When the voltage falls back to the low threshold of 0.32V, the level returns to normal. Small voltage fluctuations in the 0.32V-0.52V range will not change the output state, thus filtering out noise interference.

[0045] In the above embodiments, the descriptions of each embodiment have different focuses. For parts that are not described in detail in a certain embodiment, please refer to the relevant descriptions in other embodiments.

[0046] In the description of this invention, it should be understood that the terms "center," "longitudinal," "lateral," "length," "width," "thickness," "upper," "lower," "front," "rear," "left," "right," "vertical," "horizontal," "top," "bottom," "inner," "outer," "clockwise," and "counterclockwise," etc., indicate the orientation or positional relationship based on the orientation or positional relationship shown in the accompanying drawings. They are only for the convenience of describing this invention and simplifying the description, and do not indicate or imply that the device or element referred to must have a specific orientation, or be constructed and operated in a specific orientation. Therefore, they should not be construed as limitations on this invention.

[0047] Furthermore, the terms "first" and "second" are used for descriptive purposes only and should not be construed as indicating or implying relative importance or implicitly specifying the number of technical features indicated. Thus, a feature defined as "first" or "second" may explicitly or implicitly include one or more of that feature. In the description of this invention, "a plurality of" means two or more, unless otherwise explicitly specified.

[0048] In this invention, unless otherwise explicitly specified and limited, the terms "installation," "connection," "linking," and "fixing," etc., should be interpreted broadly. For example, they can refer to a connection, a detachable connection, or an integral part; they can refer to a mechanical connection or an electrical connection; they can refer to a direct connection or an indirect connection through an intermediate medium; they can refer to the internal communication of two components or the interaction between two components. Those skilled in the art can understand the specific meaning of the above terms in this invention according to the specific circumstances.

[0049] In this invention, unless otherwise explicitly specified and limited, "above" or "below" the second feature can include direct contact between the first and second features, or contact between the first and second features through another feature between them. Furthermore, "above," "over," and "on top" of the second feature includes the first feature directly above or diagonally above the second feature, or simply indicates that the first feature is at a higher horizontal level than the second feature. "Below," "below," and "under" the second feature includes the first feature directly below or diagonally below the second feature, or simply indicates that the first feature is at a lower horizontal level than the second feature.

[0050] In the description of this specification, the references to terms such as "one embodiment," "some embodiments," "example," "specific example," or "some examples," etc., indicate that a specific feature, structure, material, or characteristic described in connection with that embodiment or example is included in at least one embodiment or example of the invention. The illustrative expressions of the above terms in this specification should not be construed as necessarily referring to the same embodiment or example. Furthermore, the specific features, structures, materials, or characteristics described may be combined in any suitable manner in one or more embodiments or examples. In addition, those skilled in the art can combine and integrate the different embodiments or examples described in this specification.

[0051] Obviously, those skilled in the art can make various modifications and variations to this invention without departing from its spirit and scope. Since these modifications and variations fall within the scope of the claims and their equivalents, this invention also intends to include these modifications and variations.

[0052] The above description describes specific embodiments of the present invention, but the scope of protection of the present invention is not limited thereto. Any person skilled in the art can easily conceive of various equivalent modifications or substitutions within the technical scope disclosed in the present invention, and these modifications or substitutions should all be covered within the scope of protection of the present invention. Therefore, the scope of protection of the present invention should be determined by the scope of the claims.

Claims

1. A universal synchronization module for transcranial magnetic stimulation and electroencephalography, characterized in that, It includes a magnetic field sensing unit, a signal buffer conditioning unit, a threshold comparison unit, and an output unit. The magnetic field sensing unit is connected to the signal buffer conditioning unit, the signal buffer conditioning unit is connected to the threshold comparison unit, and the threshold comparison unit is connected to the output unit. The magnetic field sensing unit acquires the magnetic field change signal generated when the TMS stimulation coil is working and outputs the Hall voltage signal. The signal buffering and conditioning unit buffers and filters the Hall voltage signal. The threshold comparison unit compares the Hall voltage signal with the preset hysteresis threshold. If the Hall voltage signal exceeds the preset hysteresis threshold, a synchronous trigger signal is output. The output unit outputs the synchronous trigger signal to the EEG acquisition device.

2. The transcranial magnetic stimulation and electroencephalogram (EEG) universal synchronization module according to claim 1, characterized in that, The magnetic induction module includes a linear Hall effect sensor, which is used to acquire the magnetic field change signal generated when the TMS stimulation coil is working.

3. The transcranial magnetic stimulation and electroencephalogram (EEG) universal synchronization module according to claim 1, characterized in that, The signal buffer conditioning unit includes a buffer subunit and a filter subunit, which are connected together.

4. The transcranial magnetic stimulation and electroencephalogram (EEG) universal synchronization module according to claim 1, characterized in that, The buffer subunit is a voltage follower; The non-inverting input of the voltage follower receives the Hall voltage signal output by the magnetic field induction unit, and the output of the voltage follower is connected to the inverting input of the voltage follower.

5. The transcranial magnetic stimulation and electroencephalogram (EEG) universal synchronization module according to claim 1, characterized in that, The threshold comparison unit includes a voltage comparison subunit and a pulse shaping subunit, which are connected together.

6. The transcranial magnetic stimulation and electroencephalogram (EEG) universal synchronization module according to claim 1, characterized in that, The non-inverting input of the voltage comparator subunit receives the Hall voltage signal, and the inverting input receives the preset hysteresis threshold.

7. The transcranial magnetic stimulation and electroencephalogram (EEG) universal synchronization module according to claim 1, characterized in that, The output unit includes an interface and a protection resistor. The two ends of the protection resistor are connected to the output terminals of the interface and the pulse shaping subunit, respectively.

8. A universal synchronization system for transcranial magnetic stimulation and electroencephalography, characterized in that, Includes the transcranial magnetic stimulation and electroencephalogram (EEG) universal synchronization module as described in any one of claims 1-7.

9. The transcranial magnetic stimulation and electroencephalogram (EEG) universal synchronization system according to claim 8, characterized in that, It includes a TMS stimulation coil and an EEG acquisition device. The TMS stimulation coil is connected to a magnetic field induction unit, and the EEG acquisition device is connected to an output unit.

10. A universal synchronization method for transcranial magnetic stimulation (TMS) and electroencephalography (EEG), applicable to the universal synchronization module for TMS and EEG described in any one of claims 1-7, characterized in that, include, The magnetic field change signal generated when the TMS stimulation coil is working is acquired, converted into a Hall voltage signal, and output after preprocessing. A hysteresis threshold is preset, and the preprocessed Hall voltage signal is compared with the hysteresis threshold. When the preprocessed Hall voltage signal exceeds the hysteresis threshold, a synchronization trigger signal is output and sent to the EEG acquisition device.

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