Multi-target transcranial electrical stimulation device based on trans-regional phase-locked stimulation

Abstract

The invention discloses a multi-target transcranial electrical stimulation device based on cross-regional phase-locked stimulation, and the device comprises a light electroencephalogram cap which is integrated with at least one pair of electroencephalogram signal collection electrodes located in a first brain region and used for monitoring specific neural oscillation, and is provided with electrode holes used for placing stimulation electrodes in a second brain region; a plurality of stimulating electrodes; a controller, a multi-channel stimulation module, an electroencephalogram signal processing and feedback regulation and control module and a communication module are arranged in the control box; the electroencephalogram signal module is configured to detect the phase of specific neural oscillation of a first brain region in real time; the controller is configured to accurately control the time or phase of stimulation (such as transcranial alternating current stimulation or pulse stimulation) output by the multi-channel stimulation module in the second brain region based on the detected real-time phase information, and cross-region phase-locked stimulation is achieved. The device is suitable for personalized nerve regulation and control application in a family environment while remarkably simplifying user operation, reducing cost and improving comfort and portability.

Description

Technical Field

[0001] The present application relates to the field of medical device technology, and in particular to a multi-target transcranial electrical stimulation device based on cross-region phase-locked stimulation. Background Art

[0002] Transcranial electrical stimulation (TES), such as tDCS and tACS, non-invasively modulates cerebral cortical activity by applying weak electrical currents to the scalp. It has shown promise in the adjunctive treatment of neuropsychiatric disorders and cognitive function research. Electric field simulation systems can help optimize stimulation protocols, but traditional TES is mostly open-loop, stimulating the body according to preset parameters. This approach is unable to adapt to dynamic brain changes in real time, nor can it accurately monitor brain changes and treatment progress.

[0003] Furthermore, achieving precise, low-latency transcranial electrical stimulation is technically challenging, typically requiring complex laboratory-grade equipment (multi-channel EEG systems, high-performance processors, precision stimulators) and specialized operator expertise. This makes the technology difficult to implement in portable devices or at-home settings. In particular, the complex setup, high cost, and discomfort associated with traditional multi-lead EEG systems restrict similar treatments to medical institutions, preventing them from being implemented at home.

[0004] Therefore, the market urgently needs a solution that can overcome the complexity and cost barriers of existing technologies and provide a miniaturized therapeutic device that can achieve precise stimulation and is convenient for ordinary users to use in a home environment. Summary of the Invention

[0005] The main purpose of this application is to provide a multi-target closed-loop transcranial electrical stimulation device that can achieve precise and low-latency phase-locked stimulation, has a simplified device structure, and can be suitable for use in daily environments such as homes.

[0006] In order to achieve the above objectives, the technical solution adopted in this application is: A multi-target transcranial electrical stimulation device based on cross-region phase-locked stimulation, comprising: An EEG cap having a plurality of electrode holes on its surface for mounting stimulation electrodes, the EEG cap having a signal collection area corresponding to a first brain region and a stimulation area corresponding to a second brain region, the signal collection area being equipped with at least one pair of EEG signal collection electrodes for collecting EEG signals from the user's first brain region, the second brain region being different from the first brain region; A plurality of stimulation electrodes, detachably mounted in the electrode holes corresponding to the stimulation areas, for applying electrical stimulation to the user's second brain area; A control box is connected to the at least one pair of EEG signal acquisition electrodes and the plurality of stimulation electrodes. The control box is configured to acquire EEG signals from the EEG signal acquisition electrodes in real time, and to set the time and / or phase of the electrical stimulation applied by the plurality of stimulation electrodes to the second brain region based on the phase information of one or more target neural oscillations of the EEG signals, so as to achieve cross-region phase-locked stimulation.

[0007] This application is a closed-loop transcranial electrical stimulation system that dynamically adjusts stimulation parameters by real-time monitoring of EEG signals of brain activity in order to improve the accuracy and effectiveness of regulation. Cross-regional phase-locked stimulation is used to monitor the phase of neural oscillations in one brain region (such as the temporal region) and regulate stimulation of another different brain region (such as the frontal region) accordingly. Phase-locked stimulation is timed according to the specific phase of endogenous brain waves, which can more effectively affect neural plasticity and rhythmic activity, providing a new approach for studying and regulating the functional connectivity of specific brain networks.

[0008] In one embodiment, the control box has: a controller having an EEG signal processing and feedback control module, the EEG signal processing and feedback control module being electrically connected to the at least one pair of EEG signal acquisition electrodes and configured to acquire EEG signals from the EEG signal acquisition electrodes in real time, process the EEG signals to generate real-time data, and generate a phase-locked stimulation trigger signal based on the real-time data, wherein the real-time data includes phase information representing one or more target neural oscillations; a multi-channel stimulation module, connected to the controller and comprising a plurality of stimulation source modules respectively connected to the stimulation electrodes, and generating a phase-locked electrical stimulation signal based on the phase-locked stimulation trigger signal; The controller is configured to trigger the multi-channel stimulation module to output a single stimulation pulse or a series of short stimulation pulses to the second brain area when the target neural oscillation reaches a preset target phase.

[0009] In one embodiment, the real-time data also includes power spectral density information characterizing the power of a specific frequency band and pattern information characterizing the EEG pattern. The controller is also configured to selectively generate a feedback signal based on the power spectral density information or pattern information, and adjust one or more stimulation parameters output by the multi-channel stimulation module in real time to form a closed-loop control loop in addition to phase-locked stimulation. The stimulation parameters include intensity, frequency and channel combination.

[0010] In one embodiment, the EEG signal processing and feedback control module uses Hilbert transform or bandpass filtering combined with zero-crossing detection to estimate the phase of the target neural oscillation in real time.

[0011] In one embodiment, the multi-channel stimulation module supports a transcranial alternating current stimulation mode, and the controller is configured to continuously adjust the instantaneous phase of the transcranial alternating current stimulation waveform applied to the second brain region so that it maintains a preset phase relationship with the real-time phase of the target neural oscillation detected by the first brain region, and the phase relationship includes being in phase, anti-phase, or maintaining a specific phase difference.

[0012] In one embodiment, the stimulation source module is a constant current source module, and the EEG signal processing and feedback control module also includes a plurality of impedance detection chips for respectively monitoring the impedance of each stimulation channel in real time. The controller is also configured to compensatorily adjust the output of each stimulation channel based on the impedance size of each stimulation channel.

[0013] In one embodiment, the control box further comprises a multi-channel digital-to-analog converter connected to the controller, and output ends of the multi-channel digital-to-analog converter are respectively connected to the plurality of stimulation source modules.

[0014] In one embodiment, the controller further comprises a communication and monitoring module comprising a three-axis accelerometer for detecting abnormal motion states and triggering stimulation interruption.

[0015] In one embodiment, the communication and monitoring module includes a temperature sensor integrated on or near the stimulation electrode, which is used to monitor the changes in scalp temperature at the contact point in real time and adjust or interrupt stimulation when the temperature is abnormal.

[0016] In one embodiment, the communication and monitoring module includes a wireless communication module for communicating with external devices and a watchdog timer for monitoring the operating status of the system.

[0017] In one embodiment, the control box is detachably mounted on the EEG cap, and the control box further comprises: a housing, a quickly replaceable battery compartment, and a built-in charging circuit. The housing of the control box further comprises an indicator device capable of displaying the stimulation status, EEG signal feedback status, phase-locked status, and / or fault code in real time.

[0018] In one embodiment, the EEG cap includes: a cap body and a mandibular fixing strap connected to the bottom of the cap body, and the cap body is made of lightweight materials such as silicone foam material or ABS material.

[0019] In one embodiment, each of the electrode holes is respectively provided with a metal ring-shaped fixing buckle for positioning the stimulation electrode, or a magnetic material fixing buckle is used to cooperate with the magnetic material on the electrode to achieve positioning.

[0020] In one embodiment, the first brain region is the temporal region, the target neural oscillation is an alpha neural oscillation, and the second brain region is the dorsolateral prefrontal cortex. By sensing the phase of the temporal alpha rhythm and stimulating the dorsolateral prefrontal cortex at a specific phase, the interaction between these two key regions is influenced, thereby modulating cognitive or emotional regulation functions such as memory, reaction speed, and cognitive flexibility. Compared with the existing technology, the beneficial effects of this application are: by adopting EEG signal acquisition electrodes specifically used to monitor phase-locked signals, advanced cross-regional phase-locked stimulation is achieved, providing the possibility of precisely regulating the functional interaction between different brain regions, which is difficult to achieve in traditional open-loop or simple closed-loop systems; significantly simplifying the device structure, user operation process and electrode wearing process, greatly reducing equipment costs, improving user wearing comfort and device portability, thereby enabling advanced phase-locked stimulation technology to move out of the laboratory and be suitable for daily environments such as home. BRIEF DESCRIPTION OF THE DRAWINGS

[0021] Figure 1 A three-dimensional schematic diagram of a multi-target transcranial electrical stimulation device provided in an embodiment of the present application.

[0022] Figure 2 A schematic diagram of the circuit principle of the control box provided in an embodiment of the present application.

[0023] Figure 3 This is a schematic diagram of the layout of the collection electrodes and stimulation electrodes on the scalp surface provided in an embodiment of the present application.

[0024] Figure 4 A schematic diagram of the cross-region phase-locked stimulation closed-loop control process provided in an embodiment of the present application.

[0025] Figure 5 Schematic diagram of the principle of phase locking of temporal alpha wave phase detection and frontal stimulation provided in an embodiment of the present application.

[0026] Among them: 1. Cap body; 2. Control box; 3. Mandibular fixation strap; 4. Stimulation electrode; 5. Electrode hole; 6. Ventilation hole; 7. Wire; 8. EEG signal acquisition electrode. DETAILED DESCRIPTION

[0027] In order to explain the technical content, structural features, achieved objectives and effects of the present invention in detail, the present invention is described in detail with reference to the accompanying drawings and specific embodiments.

[0028] See also Figure 1As shown, the present application discloses a multi-target transcranial electrical stimulation device based on cross-regional phase-locked stimulation closed-loop control, comprising: an EEG cap 1, at least one pair of EEG signal acquisition electrodes 8, a plurality of stimulation electrodes 4, and a control box 2. The EEG cap 1 has a signal acquisition area corresponding to a first brain region and a stimulation area corresponding to a second brain region. The present application uses a very small number of EEG signal acquisition electrodes to acquire the source signal required for phase locking (the first brain region), and after analysis and processing, generates a multi-target transcranial electrical stimulation signal that acts on the target brain region (the second brain region). This achieves cross-regional phase-locked stimulation (CPS), completing closed-loop control of EEG stimulation. This device can generate or adjust stimulation signals based on real-time changes in EEG signals in the first brain region, providing precise, low-latency stimulation. It can also monitor EEG signal changes in the first brain region in real time, providing feedback on the effectiveness of stimulation, and helping researchers or medical staff analyze and study the user's EEG signal data.

[0029] In this embodiment, a portable transcranial electrical stimulation device for treating depression is provided. The first brain region selected is the temporal region, and the target neural oscillation collected by the EEG signal collection electrode 8 is the alpha neural oscillation. The second brain region selected is the dorsolateral prefrontal cortex.

[0030] The temporal region is a key area of the cerebral cortex, primarily responsible for processing auditory information, language, and some memory functions. Alpha neural oscillations in the temporal region are a type of rhythmic EEG activity detected in the electroencephalogram (EEG). Alpha waves primarily occur during relaxation with eyes closed, but they also occur during certain cognitive tasks. During certain cognitive tasks, alpha waves in the temporal region may phase-lock with neural oscillations in other brain regions (such as theta waves), enabling efficient information transmission. By collecting and analyzing alpha wave signals in the temporal region, we can reveal information such as an individual's level of attention, emotional state, and cognitive load.

[0031] The dorsolateral prefrontal cortex (DLPFC) is a key area in the frontal lobe of the brain, playing an important role in working memory, attention control, and executive function. The DLPFC is also involved in the recognition and regulation of emotions, and together with subcortical structures such as the amygdala, it forms the central emotional pathway. It plays a crucial role in regulating emotional responses and alleviating mood disorders such as anxiety and depression. Furthermore, through its extensive connections across various brain regions, the DLPFC helps people make judgments and execute decisions, coordinates brain activity, and inhibits impulsive behavior.

[0032] By locking the phase of the temporal alpha waves with the dorsolateral prefrontal cortex, it is possible to effectively influence neuroplasticity and rhythmic activity of the brain. By affecting the interaction between these two key areas, it is possible to relieve anxiety and depression, as well as regulate functions such as attention, cognition or impulsive behavior.

[0033] In other embodiments of the present application, in addition to the combination of collecting data from the temporal area and stimulating the dorsolateral prefrontal cortex, brain areas that can also be collected and stimulated include the occipital area, temporal area, parietal area, frontal area, etc., and treatable diseases include depression, obsessive-compulsive disorder, anxiety disorder, etc.

[0034] Please continue reading Figure 1 The EEG cap 1 is made of a lightweight, biocompatible material (such as silicone foam, ABS, or carbon fiber). Silicone ribs may be provided on the inside to enhance comfort. A chin strap 3 is attached to the underside of the cap to ensure a secure fit. Several electrode holes 5 are provided on the cap surface to accommodate and position electrodes.

[0035] In this embodiment, there are two EEG signal acquisition electrodes, which are used to collect alpha waves in the left and right temporal regions respectively. The two EEG signal acquisition electrodes 8 are fixedly integrated into the inner surfaces of the acquisition areas on the left and right sides of the EEG cap 1 to ensure that they can stably cover the user's first brain area (temporal lobe) each time they are worn, such as near the T7 / T8 or T3 / T4 points of the international 10-20 system. The EEG signal acquisition electrodes 8 are dry electrodes or small pre-gel electrodes. The use of only one pair of acquisition electrodes is intended to ensure that the phase information of the dominant rhythm (alpha wave) of the target area (temporal region) is captured, while minimizing the difficulty of user operation and equipment cost.

[0036] Multiple stimulation electrodes 4 are removably mounted in each electrode hole. According to a preset scheme (designed by medical staff), the user installs one or more stimulation electrodes 4 in the electrode hole 5 of the EEG cap's stimulation area (e.g., the frontal region, such as around F3 or F4 in the international 10-20 standard lead system scalp electrode diagram). Several stimulation electrodes can be arranged in single-channel or multi-channel configurations, using single-channel stimulation (one stimulation electrode plus a distal return electrode) or multi-channel high-density stimulation (such as a central electrode surrounded by electrodes in a HD transcranial electrical stimulation configuration) to optimize the stimulation effect. The stimulation electrodes 4 are preferably disposable sponge electrodes or other conductive gel electrodes, removably mounted in the electrode hole 5 by means of snaps, magnets, or threads. To dissipate heat and reduce weight, the cap may also include several ventilation holes 6.

[0037] In one embodiment of the present application, the user can place multiple sets of stimulation electrodes at different locations of the EEG cap and adopt multi-target stimulation schemes (including stimulation parameters and time sequences) to achieve more complex neuroregulatory strategies or perform combined interventions for different symptoms.

[0038] The control box 2 is removably attached to the rear side of the EEG cap 1. It comprises a housing, a quickly replaceable battery compartment, a built-in charging circuit, and a control circuit. Because the control box 2 has a separate battery compartment, it can be powered by batteries, making the entire device extremely lightweight and portable, suitable for home use. The housing of the control box 2 also features an indicator that displays real-time information such as stimulation status, EEG signal feedback status, phase lock status, and / or fault codes.

[0039] Figure 2 This is a schematic diagram of the control box's circuitry, highlighting the EEG signal processing, phase-locked control logic, and stimulation output pathways. The control circuitry of control box 2 includes: The controller may be a microcontroller unit (MCU). The controller has an EEG signal processing and feedback control module, which is connected to the EEG signal acquisition electrode 8. The controller is used to filter, analyze and calculate the EEG signals collected in real time from the EEG signal acquisition electrode 8 to generate real-time data, and generate a phase-locked stimulation trigger signal based on the real-time data. The real-time data includes phase information representing one or more target neural oscillations. In this embodiment, the target neural oscillation takes the Alpha wave as an example. In other embodiments, theta waves or delta waves may also be used.

[0040] EEG signals can be analyzed and calculated using a variety of methods. For example, analyzing the amplitude and frequency changes of alpha waves can reveal an individual's level of concentration. For example, when attention is focused, the amplitude of alpha waves decreases.

[0041] Analyzing alpha wave asymmetry (e.g., higher alpha wave amplitude in the left temporal region compared to the right) can provide insights into an individual's emotional state. For example, increased alpha wave amplitude in the left temporal region may be associated with positive emotions.

[0042] By analyzing changes in alpha wave amplitude and frequency, we can also understand the magnitude of an individual's current cognitive load. For example, when the difficulty of a task increases, the alpha wave amplitude may increase.

[0043] In the EEG signal processing and feedback control module, EEG signals acquired by the collection electrodes are amplified by a low-noise preamplifier and then passed through a high-precision bandpass filter (e.g., 8-13 Hz) to extract the target alpha band signal. The controller rapidly analyzes and estimates the real-time phase. For example, it calculates the Hilbert transform of the filtered signal to directly obtain the instantaneous phase angle, or infers the alpha wave phase by detecting the zero crossings of the filtered signal and combining it with frequency information. The latency of the entire signal processing chain is strictly controlled to the millisecond level, a prerequisite for achieving precise phase lock.

[0044] A multi-channel digital-to-analog converter (DAC) is connected to the controller, and the output ends of the multi-channel digital-to-analog converter are respectively connected to the multi-channel stimulation source modules, and is used to convert the stimulation trigger signal generated by the controller into a modulation signal.

[0045] A multi-channel stimulation module is connected to a multi-channel digital-to-analog converter and includes multiple stimulation source modules, each of which is connected to each stimulation electrode 4. The multi-channel stimulation module converts the modulated signal into a phase-locked electrical stimulation signal, and parameters such as stimulation intensity and current density are limited to a safe range. The multi-channel stimulation module supports a transcranial alternating current stimulation mode, and the controller is configured to continuously adjust the instantaneous phase of the transcranial alternating current stimulation waveform applied to the second brain region so that it maintains a preset phase relationship with the real-time phase of the target neural oscillation detected in the first brain region. The phase relationship includes being in phase, antiphase, or maintaining a specific phase difference.

[0046] In one embodiment of the present application, the stimulation source module is a constant current source module, and the EEG signal processing and feedback control module also includes a plurality of impedance detection chips for respectively monitoring the impedance of each stimulation channel in real time. The controller is also configured to compensatorily adjust the output of each stimulation channel, such as the stimulation current size, based on the impedance size of each stimulation channel.

[0047] The channel converter is electrically connected to the multi-channel stimulation module and the plurality of stimulation electrodes respectively. The electrical stimulation signals output by the plurality of constant current source modules can be selectively applied to the stimulation electrodes respectively with the help of the channel converter.

[0048] In one embodiment of the present application, the controller has two phase-locking modes: phase-locked pulse mode and phase-locked tACS mode. Based on the calculated real-time phase of the temporal alpha wave, as well as preset target phases (e.g., peaks, troughs, etc.) and phase-locking mode, the controller can precisely control stimulation of the second brain region (dorsolateral prefrontal cortex).

[0049] Phase-locked pulse mode: When the alpha phase in the temporal region reaches a target phase (e.g., a specific phase angle at a peak, trough, rising edge, or falling edge), the controller immediately triggers a short pulse or series of pulses to be sent to the stimulation electrode 4 in the prefrontal lobe via the multi-channel stimulation module. Parameters such as pulse width, frequency, and intensity can be preset.

[0050] In phase-locked tACS mode, the controller continuously monitors the temporal alpha phase and adjusts the instantaneous phase of the tACS stimulation waveform applied to the prefrontal cortex in real time, maintaining a fixed, preset phase difference (e.g., 0, 90, 180 degrees) with the temporal alpha phase. This requires the multi-channel DAC and stimulus source module to quickly respond to dynamic phase adjustment commands.

[0051] The controller of the present application instructs the multi-channel stimulation module to apply stimulation at a precise time point or in a specific phase relationship through the stimulation electrode 4 located in the second brain area based on the real-time phase information of the EEG signal collected from the first brain area (for example, triggering a prefrontal stimulation pulse at a specific phase of the alpha wave, or precisely locking the phase of the transcranial alternating current stimulation applied to the prefrontal lobe to the phase of the alpha wave in the temporal area), thereby achieving precise regulation of functional interaction between different brain areas, which is difficult to achieve in traditional open-loop or simple closed-loop systems. Figure 5 A diagram showing the relationship between the unilateral acquisition waveform and the acquisition waveform phase of the first brain region and the stimulation waveform of the second brain region in one embodiment is shown.

[0052] Figure 4 This is a schematic diagram of the control flow for this application, illustrating the complete steps from EEG signal acquisition to phase-locked stimulation output. The controller MCU is the core of the entire phase-locking process, with high-speed computing power to perform: real-time EEG signal acquisition in the first brain area, real-time filtering, real-time phase calculation, comparison with the target phase (such as peaks and troughs) pre-stored in the controller, and generation of the phase-locked stimulation trigger signal. All steps must be tightly coordinated to ensure timing accuracy.

[0053] In one embodiment, in addition to core phase-locked stimulation, the controller of this device can also implement other closed-loop strategies. For example, it can calculate the power spectral density of specific frequency bands (such as Theta, Beta, etc.) of the EEG signal and, based on comparisons with preset target ranges, adjust the intensity and frequency of electrical stimulation in real time, or select different stimulation channel combinations. This enables a wider range of personalized neuromodulation (such as promoting relaxation and improving attention). Users can select different closed-loop control modes on the control panel or in the accompanying software. Real-time data can also include power spectral density information representing the power of specific frequency bands and pattern information representing EEG patterns. The controller can selectively generate feedback signals based on the power spectral density or pattern information to adjust one or more stimulation parameters output by the multi-channel stimulation module in real time, thereby forming a closed-loop control loop in addition to phase-locked stimulation. Stimulation parameters include intensity, frequency, and channel combination.

[0054] In one embodiment, each electrode hole 5 is respectively provided with a metal ring-shaped fixing buckle for positioning the stimulation electrode 4, or a magnetic material fixing buckle is used to cooperate with the magnetic material on the electrode to achieve positioning.

[0055] See also Figure 2 In one embodiment, the EEG signal processing and feedback control module includes a multi-channel impedance detection function that can monitor the contact impedance of each stimulation channel in real time before and during stimulation. The controller determines whether the electrode contact is good based on the impedance value and prompts the user to adjust it if necessary. In the constant current source stimulation mode, the controller can fine-tune the output voltage based on real-time impedance feedback to ensure a constant current intensity applied to the tissue and accurate stimulation dosage.

[0056] The transcranial electrical stimulation device of the present application also includes impedance monitoring, safety monitoring (such as motion detection, temperature monitoring, watchdog) and practical functions (such as wireless communication, battery power supply, status indication).

[0057] The control box of the transcranial electrical stimulation device of the present application also includes a communication and monitoring module, which contains a three-axis accelerometer that can detect whether the user has abnormal large-scale movements such as falling, and automatically interrupt the stimulation to achieve movement safety monitoring.

[0058] The communication and monitoring module also includes a temperature sensor integrated on or near the stimulation electrode 4, which is used to monitor the temperature changes of the scalp at the contact point in real time to prevent overheating and burns, and automatically reduce the intensity or stop the stimulation when the temperature exceeds the limit.

[0059] The communication and monitoring module also includes a wireless communication module (such as Bluetooth or Wi-Fi) for communicating with external devices and a watchdog timer for monitoring the system's operating status to prevent program failure and continuous abnormal stimulation. The transcranial electrical stimulation device of this application can be connected to a smartphone or tablet via a wireless communication module (such as Bluetooth BLE), using a supporting application for program selection, parameter setting, start / stop control, status monitoring, and data recording.

[0060] Before using the device of this application, the user needs to have a doctor develop a treatment or intervention plan at a medical institution and input the treatment plan into the transcranial electrical stimulation device through wireless or wired communication. Before starting each treatment, the user needs to select a treatment / intervention plan in the accompanying application. The plan includes: stimulation target (such as the frontal lobe), stimulation mode (such as phase-locked pulse), phase-locking basis (such as temporal alpha peak), stimulation parameter range, etc. The usage process is as follows: The user wears the EEG cap and ensures good contact between the two fixed EEG signal acquisition electrodes 8 in the temporal region. According to the application prompts, insert the stimulation electrode 4 into the corresponding electrode hole 5 in the frontal lobe region and ensure contact.

[0061] Turn on the control box 2 and connect the device to the application via Bluetooth.

[0062] The application or device automatically performs impedance detection and prompts the user to adjust the collection electrodes and stimulation electrodes until good contact is achieved.

[0063] The user initiates a treatment or intervention plan on the app. The EEG cap begins real-time monitoring of the temporal alpha wave phase and delivers phase-locked stimulation to the prefrontal cortex when the target phase is reached. The app also displays partial EEG signal information, phase-lock success rate, and stimulation status in real time.

[0064] After the treatment / intervention is completed, the EEG cap will stop automatically, and the data generated during the process (such as stimulation logs and partial EEG signal fragments) can be uploaded and saved.

[0065] By cleverly combining advanced cross-regional phase-locked stimulation technology with a minimalist (e.g., one-pair) EEG sensor design, this invention successfully transforms previously complex and expensive laboratory-grade neuromodulation capabilities into an easy-to-use, cost-effective, comfortable, and portable device. This device not only offers unprecedented possibilities for precise control of specific brain network activity, but also retains multi-target, multi-modal stimulation, and other closed-loop feedback capabilities, such as those based on power spectrum. This significantly expands the application prospects of transcranial electrical stimulation technology in scientific research, clinical support, and home health management.

[0066] The transcranial electrical stimulation device of the present application has the following advantages: Achieve advanced cross-region phase-locked stimulation: Provides the possibility of precisely regulating functional interactions between different brain regions, which is difficult to achieve in traditional open-loop or simple closed-loop systems.

[0067] High-precision and low-latency design: Optimized signal processing algorithms and control logic are designed to achieve low-latency real-time phase detection and precise stimulation timing / phase control.

[0068] Simplified EEG signal sensing solution: Using very few EEG signal acquisition electrodes to collect the source signal required for phase locking (such as temporal alpha), completely avoiding the complexity and inconvenience of multi-lead EEG signals, greatly facilitating users to wear and use it themselves, significantly reducing equipment costs, and improving comfort and portability.

[0069] Versatile and flexible: In addition to core phase-locked stimulation, it also supports multi-target stimulation, multiple stimulation modes (DC stimulation, AC stimulation, pulse stimulation, etc.), and other closed-loop control strategies based on EEG signal characteristics (such as power spectrum), with strong adaptability.

[0070] Highly integrated and user-friendly: The product is designed as an integrated portable structure with a compact and lightweight overall design. It is battery-powered, has wireless communication, and clear status indication, aiming to provide a safe and convenient home use experience.

Claims

1. A multi-target transcranial electrical stimulation device based on cross-region phase-locked stimulation, characterized in that: include: An electroencephalogram cap (1) is provided with a plurality of electrode holes (5) on its surface for mounting stimulation electrodes, the electroencephalogram cap (1) having a signal collection area corresponding to a first brain region and a stimulation area corresponding to a second brain region, the signal collection area being provided with at least one pair of electroencephalogram signal collection electrodes (8) for collecting electroencephalogram signals from the user's first brain region, the second brain region being different from the first brain region; A plurality of stimulation electrodes (4) are detachably mounted in the electrode holes (5) corresponding to the stimulation areas, and are used to apply electrical stimulation to the second brain area of the user; A control box (2) is connected to the at least one pair of EEG signal acquisition electrodes (8) and the plurality of stimulation electrodes (4). The control box (2) is configured to acquire EEG signals from the EEG signal acquisition electrodes (8) in real time, and to set the time and / or phase of the electrical stimulation applied by the plurality of stimulation electrodes (4) to the second brain region based on the phase information of one or more target neural oscillations of the EEG signals, so as to achieve cross-region phase-locked stimulation.

2. The device according to claim 1, characterized in that The control box (2) has: A controller having an EEG signal processing and feedback control module, the EEG signal processing and feedback control module being electrically connected to the at least one pair of EEG signal acquisition electrodes (8), for real-time acquisition of EEG signals from the EEG signal acquisition electrodes (8), processing the EEG signals to generate real-time data, and generating a phase-locked stimulation trigger signal based on the real-time data, wherein the real-time data includes phase information representing one or more target neural oscillations; A multi-channel stimulation module is connected to the controller and includes a plurality of stimulation source modules respectively connected to the stimulation electrodes (4), and generates a phase-locked electrical stimulation signal based on the phase-locked stimulation trigger signal; The controller is configured to trigger the multi-channel stimulation module to output a single stimulation pulse or a series of short stimulation pulses to the second brain area when the target neural oscillation reaches a preset target phase.

3. The device according to claim 2, characterized in that The real-time data also includes power spectrum density information representing the power of a specific frequency band and pattern information representing the EEG pattern. The controller is also configured to selectively generate a feedback signal based on the power spectrum density information or pattern information, and adjust one or more stimulation parameters output by the multi-channel stimulation module in real time to form a closed-loop control loop in addition to phase-locked stimulation. The stimulation parameters include intensity, frequency and channel combination.

4. The device according to claim 2, characterized in that The EEG signal processing and feedback control module uses Hilbert transform or bandpass filtering combined with zero-crossing detection to estimate the phase of the target neural oscillation in real time.

5. The device according to claim 2, characterized in that The multi-channel stimulation module supports a transcranial alternating current stimulation mode, and the controller is configured to continuously adjust the instantaneous phase of the transcranial alternating current stimulation waveform applied to the second brain region so that it maintains a preset phase relationship with the real-time phase of the target neural oscillation detected in the first brain region, and the phase relationship includes being in phase, anti-phase, or maintaining a specific phase difference.

6. The device according to claim 2, characterized in that The stimulation source module is a constant current source module, and the EEG signal processing and feedback control module also includes a plurality of impedance detection chips for respectively monitoring the impedance of each stimulation channel in real time. The controller is also configured to compensatorily adjust the output of each stimulation channel based on the impedance size of each stimulation channel.

7. The device according to claim 2, characterized in that The control box (2) further comprises a multi-channel digital-to-analog converter connected to the controller, and the output ends of the multi-channel digital-to-analog converter are respectively connected to the plurality of stimulation source modules.

8. The device according to claim 2, characterized in that The controller also includes a communication and monitoring module, which includes a three-axis accelerometer for detecting abnormal motion states and triggering stimulation interruption.

9. The device according to claim 8, characterized in that The communication and monitoring module includes a temperature sensor integrated on or near the stimulation electrode (4), which is used to monitor the temperature changes of the scalp at the contact point in real time and adjust or interrupt the stimulation when the temperature is abnormal.

10. The device according to claim 8, characterized in that The communication and monitoring module includes a wireless communication module for communicating with external devices and a watchdog timer for monitoring the operating status of the system.

11. The device according to claim 1, characterized in that The control box (2) is detachably mounted on the EEG cap (1). The control box (2) further comprises: a housing, a quickly replaceable battery compartment, and a built-in charging circuit. The housing of the control box (2) further comprises an indicator device capable of displaying the stimulation status, EEG signal feedback status, phase-locked status, and / or fault code in real time.

12. The device according to claim 1, characterized in that The first brain region is the temporal region, and the target neural oscillation is an alpha neural oscillation.

13. The device according to claim 1, characterized in that The second brain region is the dorsolateral prefrontal cortex.

14. The device according to claim 1, wherein The EEG cap (1) comprises a cap body and a mandibular fixing band (3) connected below the cap body, wherein the cap body is made of a lightweight material such as organic silicon foam material or ABS material.

15. The device according to claim 1, characterized in that Each of the electrode holes (5) is provided with a metal ring-shaped fixing buckle for positioning the stimulation electrode (4), or a magnetic material fixing buckle is used to cooperate with the magnetic material on the electrode to achieve positioning.

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