Multi-channel electric field output control method and device, electronic equipment and storage medium

Abstract

The application discloses a multi-channel electric field output control method and device, electronic equipment and a storage medium. The method comprises the following steps: performing electric field optimization and channel configuration based on a multi-objective optimization function and a current constraint condition, determining a first electrode pair and a second electrode pair; generating a first output control instruction to control the output of a first group of carrier waves to the first electrode pair; generating a second output control instruction to control the output of a second group of carrier waves to the second electrode pair; acquiring the electrical parameters of each output channel, and executing a safety response action when the electrical parameters exceed a preset threshold; and generating a timing control instruction based on preset conduction timing data to control the trigger interval time of the first group of carrier waves and the second group of carrier waves. The application realizes the coordinated electric field output of multi-space coordinate regions, the differential configuration of difference frequency parameters, and the accurate control of trigger timing.

Description

Technical Field

[0001] This application belongs to the field of electrical signal output and control technology, specifically relating to a method and device for the coordinated control of a multi-channel current generator and an electrode array. Background Technology

[0002] In the field of electrical signal output and control technology, there is an increasing demand for coordinated output of signals from complex neural circuits. Such demands typically involve differentiated electric field configurations across multiple spatial coordinate regions, requiring a single control system to simultaneously output multiple sets of difference-frequency signals on the same controlled object, and to perform time-sequential coordinated control of these signals.

[0003] Existing non-invasive electrical output technologies have limitations when adjusting multiple spatial coordinate regions. Traditional correlation devices mainly operate in shallow spatial regions, and due to the attenuation characteristics of physical fields, they struggle to directly focus and deliver effective energy to a predetermined first spatial coordinate region. Furthermore, traditional correlation devices suffer from insufficient spatial resolution when adjusting deep signal outputs, as the electric field often diffuses throughout space and can only achieve monotonic output to a single region. The emerging time-domain coherent electrical output technology, by applying two high-frequency alternating currents of different frequencies, utilizes the interference principle to generate a low-frequency envelope electric field in the deep region, achieving deep-focused output. Existing devices cannot simultaneously output differentiated and antagonistic adjustment electric fields on the same object using a single control system.

[0004] The coordinated control of multi-region signal output is highly dependent on the timing coordination between regions. Existing equipment lacks a precise coordinated control mechanism based on the preset signal transmission timing between regions when applying multi-region regulation. At the same time, it lacks a synchronous feedback closed loop of multimodal physiological signal data, which makes it impossible for the system to objectively and quantitatively characterize the output effect and makes it difficult to achieve individualized electric field optimization allocation and safety protection. Summary of the Invention

[0005] This application provides a multi-channel electric field output control method, device, electronic equipment, and storage medium, which solves the technical problems that multi-channel current generators cannot simultaneously achieve coordinated electric field output in multiple spatial coordinate regions, differentiated configuration of difference frequency parameters, and precise control of trigger timing.

[0006] This application provides a control method applied to a control device comprising a current generator and an electrode array with multiple output channels. The method optimizes the electric field and configures the channels based on a multi-objective optimization function and current constraints to determine a first electrode pair and a second electrode pair. A first output control command is generated to control the output of a first set of carrier waves to the first electrode pair to form a first interference signal. A second output control command is generated to control the output of a second set of carrier waves to the second electrode pair to form a second interference signal. Electrical parameters of each output channel are acquired, and a safety response action is executed when the electrical parameters exceed a preset threshold. Based on preset conduction timing data, a timing control command is generated to control the trigger interval between the first and second sets of carrier waves.

[0007] The first preset spatial coordinate region is a pre-defined first spatial coordinate region, and the second preset spatial coordinate region is a pre-defined second spatial coordinate region.

[0008] The first interference signal is a continuous envelope with a first difference frequency, and the second interference signal is an intermittent envelope with a second difference frequency, wherein the second difference frequency is greater than the first difference frequency.

[0009] The first difference frequency is configured in the low frequency band, preferably 5Hz; the second difference frequency is configured in the frequency band greater than the first difference frequency, preferably 30Hz; the conduction timing data is configured to be 20 to 50ms.

[0010] In the execution logic of electric field optimization and channel configuration based on multi-objective optimization functions and current constraints, the system constructs a guiding field matrix based on a preset organization model. Under constraints of maximum total current, single electrode current, and number of activated electrodes, the guiding field matrix is ​​used to perform multi-objective joint solutions for target region envelope peaking and non-target region suppression.

[0011] In the execution logic for multi-objective joint solution of target envelope maximization and non-target suppression, the system assigns a first weight to target envelope maximization and a second weight to non-target suppression, wherein the sum of the first and second weights is constrained to a constant value. Upon receiving adjustment instructions, the system dynamically adjusts the first and second weights within a preset range to complete the objective solution and output the optimal electrode combination as the first electrode pair and the second electrode pair.

[0012] In the execution logic that acquires the electrical parameters of each output channel and executes safety response actions when the electrical parameters exceed preset thresholds, the system monitors the output impedance and output current values ​​of each output channel in real time. It determines whether the output impedance or output current value exceeds a preset threshold. In response to the determination that the preset threshold has been exceeded, tiered actions are triggered according to the degree of exceedance. These tiered actions include limiting current output, disconnecting channel connections, and triggering hardware-level interlocking.

[0013] This method also receives multimodal physiological signal data acquired by external sensors during the signal output cycle. Feature fusion is performed on the multimodal physiological signal data to generate objective state data. The output parameters of the current generator are adjusted based on this objective state data.

[0014] Multimodal physiological signal data includes signal data acquired by functional magnetic resonance imaging (fMRI), electroencephalography (EEG), and autonomic nervous system sensors. Specifically, the fMRI signal data includes blood oxygen dependence and functional connectivity characteristics; the EEG signal data includes frequency band power characteristics and phase synchronization characteristics; and the autonomic nervous system signal data includes heart rate variability and skin conductance activity characteristics.

[0015] In the execution logic of generating objective representation state data by feature fusion of multimodal physiological signal data, the system extracts frequency band power features from the signal data collected by the EEG sensor and calculates neural state indices by combining the rate of change of heart rate variability and skin conductance activity features from the signal data collected by the autonomic nervous system sensor. Blood oxygen dependence features are mapped to the topological connection space of a first preset spatial coordinate region and a second preset spatial coordinate region to evaluate the causal modulation strength between regions. Objective representation state data is generated based on the weighted superposition result of the neural state indices and the causal modulation strength. If the objective representation state data does not meet preset judgment conditions, the target output amplitude parameters of the current generator in the next output cycle are dynamically updated.

[0016] This application also provides a control device, including a channel configuration module, a waveform control module, a physiological feedback acquisition module, a safety protection module, and a timing control module. The channel configuration module is configured to perform electric field optimization and channel configuration based on a multi-objective optimization function and current constraints, determining a first electrode pair and a second electrode pair. The waveform control module is connected to the channel configuration module and is configured to generate carrier output control commands to control the output of a first set of carriers to the first electrode pair for forming a first interference signal, and to control the output of a second set of carriers to the second electrode pair for forming a second interference signal. The physiological feedback acquisition module is configured to receive multimodal physiological signal data acquired by an external sensor. The safety protection module is connected to each output channel and is configured to acquire the electrical parameters of each output channel and execute a safety response action when the electrical parameters exceed a preset threshold. The timing control module is connected to the waveform control module and is configured to generate timing control commands based on preset conduction timing data to control the trigger interval between the first set of carriers and the second set of carriers.

[0017] The first preset spatial coordinate region is a pre-defined first spatial coordinate region, and the second preset spatial coordinate region is a pre-defined second spatial coordinate region. The waveform control module is specifically configured to output a continuous envelope with a first difference frequency as a first interference signal, and output an intermittent envelope with a second difference frequency as a second interference signal, wherein the second difference frequency is greater than the first difference frequency.

[0018] The channel configuration module includes a matrix construction unit and a joint solution unit. The matrix construction unit is configured to construct a guiding field matrix based on a preset organization model. The joint solution unit is connected to the matrix construction unit and is configured to perform multi-objective joint solution of target envelope maximization and non-target suppression using the guiding field matrix under constraints of maximum total current, single electrode current, and number of activated electrodes.

[0019] This application also provides an electronic device, including a memory and a processor. The memory is configured to store a computer program. The processor is connected to the memory and configured to execute the computer program to implement the aforementioned device control method.

[0020] This application also provides a computer-readable storage medium storing a computer program, which, when executed by a processor, implements the aforementioned device control method.

[0021] This application introduces a multi-output channel current generator and combines it with multi-objective joint electric field optimization logic based on a finite element model to achieve coordinated electric field output and precise positioning across multiple spatial coordinate regions at the underlying hardware and control logic levels. By configuring differentiated difference-frequency signals and output modes for different regions and introducing a coordinated control mechanism based on preset conduction timing data on the time axis, this application achieves multi-channel coordinated electric field output. By integrating objective characterization data from multimodal physiological signals with multi-level safety monitoring and response links, the safety boundary of the electric field output and the accuracy of closed-loop control are maintained. Attached Figure Description

[0022] Figure 1 This is a flowchart of the device control method provided in an embodiment of the present invention.

[0023] Figure 2 This is a logic structure block diagram of the control device provided in the embodiments of the present invention.

[0024] Figure 3 This is a data characteristic curve diagram of the principle and parameter configuration of the electric field output signal provided in the embodiment of the present invention.

[0025] Figure 4 This is a side sectional view of the brain spatial positioning and electrode action path provided in an embodiment of the present invention.

[0026] Figure 5This is a virtual simulation test diagram of electrode positioning and electric field distribution provided in an embodiment of the present invention.

[0027] Explanation of reference numerals in the attached figures In the diagram: 201 - Channel configuration module, 202 - Waveform control module, 203 - Physiological feedback acquisition module, 204 - Safety protection module, 205 - Timing control module, 301 - First group of waveform signals, 302 - Second group of waveform signals, 303 - Interference envelope curve, 401 - First current source, 402 - Second current source, 403 - First preset spatial coordinate region, 404 - Second preset spatial coordinate region, 405 - First interference path, 501 - First electrode node, 502 - Second electrode node, 503 - Interference path, 504 - Preset coordinate reference direction. Detailed Implementation

[0028] To make the objectives, technical solutions, and advantages of this application clearer, the following detailed description is provided in conjunction with the accompanying drawings and embodiments. It should be understood that the specific embodiments described herein are merely illustrative and not intended to limit the scope of this application.

[0029] It should be noted that the device control method and regulation device involved in this application are executed by a physical computing terminal or medical electronic control console with data calculation, signal generation, and parameter regulation capabilities. The underlying hardware base of this terminal includes a main control processor, such as a microcontroller based on a general-purpose processing architecture or a high-performance programmable gate array (PLA) arithmetic unit, as well as memory, a digital-to-analog converter channel, a multi-channel direct digital frequency synthesizer (DCF) generation module, and a multi-modal data acquisition interface. In the following embodiments, the actions of control, generation, and application refer to the control electrical signals issued by the system processor to the hardware execution unit and their corresponding physical response processes.

[0030] like Figure 1 As shown, this application provides a device control method applied to a control device comprising a current generator with multiple output channels and an electrode array. The main execution logic of this method includes the following steps: Step S101: Based on the multi-objective optimization function and current constraint conditions, perform electric field optimization and channel configuration to determine the first electrode pair and the second electrode pair.

[0031] The processor acquires preset head image data and establishes a three-dimensional finite element model containing various tissues based on the image data. Based on this finite element tissue model, the processor constructs the guiding field matrix from the electrode array to each spatial voxel point in the cranium.

[0032] The processor invokes the optimization algorithm engine to perform a multi-objective joint solution for target envelope peening and non-target area suppression under constraints of maximum total current, single electrode current, and the number of activated electrodes, using the guiding field matrix. The system assigns a first weight to target envelope peening and a second weight to non-target area suppression. To obtain the optimal electrode input current vector, the system calculates the product of the sum of squares of the low-frequency interference envelope electric field intensity vectors of all target areas and the first weight, subtracts the product of the sum of squares of the low-frequency interference envelope electric field intensity vectors of all non-target areas and the second weight, and calculates the injection current distribution matrix when this difference is maximized. The following multi-objective optimization objective function is constructed: ; Where, vector The variable w1 represents the injection current distribution matrix of each output channel to be solved in the system; the variable w2 represents the second weighting parameter for the target envelope peening configuration; the variable w1 represents the second weighting parameter for the non-target suppression configuration; the variable w2 represents the third weighting parameter for the non-target suppression configuration. This represents the low-frequency interference envelope electric field intensity vector generated at the j-th voxel position within the target area; variable This represents the low-frequency interference envelope electric field intensity vector generated at the k-th voxel location within the non-target region.

[0033] In this embodiment, the system supports receiving adjustment commands and dynamically adjusting the first weight w1 and the second weight w2 within a preset range. The sum of the first weight and the second weight is constrained to a constant value, and the adjustment range of both is limited to a specific numerical range. The system solves the quadratic programming problem and outputs the optimal solution under the safety conditions of satisfying the hardware boundaries. The current constraint condition of this safety boundary is that the upper limit of the safe current of a single electrode is limited to the range of 1 to 2 mA, and the upper limit of the total current of the entire device is limited to the range of 4 to 8 mA. At the same time, the maximum number of active electrodes constraint condition of the optimization algorithm is configured to a specific value to limit the number of electrodes that can be used simultaneously on the electrode cap. According to the optimal electrode arrangement and current distribution parameters output by the solution, the system maps them to the physical control plane and determines the first electrode pair responsible for suppressing the output and the second electrode pair responsible for activating the output.

[0034] Step S102: Output a first set of carrier waves to the first electrode pair, and form a first interference signal by interference in a first preset spatial coordinate region; output a second set of carrier waves to the second electrode pair, and form a second interference signal by interference in a second preset spatial coordinate region.

[0035] After completing the channel configuration, the processor issues waveform control commands. The first preset spatial coordinate region is a pre-defined first spatial coordinate region; the second preset spatial coordinate region is a pre-defined second spatial coordinate region.

[0036] After channel configuration is completed, the processor issues waveform control commands and maps parameters to specific current sources and output channels via the system's internal bus, thereby driving the corresponding electrode groups to form a closed loop. The first preset spatial coordinate region is a pre-defined first spatial coordinate region; the second preset spatial coordinate region is a pre-defined second spatial coordinate region. The system drives the corresponding channels to generate coordinated output characteristics. For the first channel, the system's underlying high-frequency synthesis circuit generates two high-frequency currents, which are injected into the load via the first electrode pair through an independent current drive module. The carrier frequency variables of the first electric field output channel waveform signals of these two carriers are defined as I1(f1) and I2(f1), respectively. The two signals meet in the first preset spatial coordinate region and undergo spatial physical interference, superimposing to produce a frequency of... The low-frequency envelope waveform. The difference-frequency envelope function is expressed as... The system defines the first interference signal as a first difference frequency continuity envelope. The system configures the first difference frequency in the low-frequency band, preferably 5Hz, thus generating a continuous low-frequency envelope of approximately 5Hz.

[0037] For the second channel, the system controls another synthesis circuit to generate a high-frequency current with the characteristics of the second set of carrier frequencies. The carrier frequency variable of the waveform signal is defined as I2(f2) and The signal is then output to the second electrode pair. After interference in the second preset spatial coordinate region, a second interference signal is formed. The system configures this second interference signal as a second difference frequency intermittent envelope, specifying that the second difference frequency is greater than the first difference frequency. The system configures the second difference frequency in a frequency band preferably 30Hz and controls it to be released in an intermittent burst mode.

[0038] This application embodiment lists a set of electric field output parameter configuration tables executed by the underlying hardware, as shown in the table below:

[0039] When generating the I2(f2) signal group, the system's bottom-level controller uses carrier pairing of 2000Hz and 2030Hz to form a 30Hz difference frequency, and executes intermittent burst control according to the timing sequence, thereby forming an interference signal that conforms to preset characteristics in the second preset spatial coordinate region. When generating the I1(f1) signal group, it uses carrier pairing of 2000Hz and 2005Hz to form a low difference frequency of 5Hz, and executes uninterrupted continuous output to achieve deep focusing output.

[0040] Step S103: Obtain the electrical parameters of each output channel, and execute a safety response action when the electrical parameters exceed a preset threshold.

[0041] The system's motherboard is equipped with an independent impedance monitoring module and a Hall current sensor. During operation, the processor acquires the output impedance and output current values ​​of each output channel in real time. The system's internal logic unit continuously compares these electrical parameters with the set current upper limit and impedance safety boundary threshold in real time.

[0042] When the output impedance or output current value exceeds a preset threshold, the system responds to the degree of over-limit triggering graded actions: if it is a slight abnormality that deviates from the normal value by a very small range, the underlying control circuit automatically fine-tunes and weakens the output drive strength of the channel through a closed-loop negative feedback mechanism; if the value reaches the warning boundary, the system calls the speaker, LED indicator and host computer interface to trigger an alarm; if a serious abnormality occurs, the system generates the highest priority interrupt signal, triggers the hardware-level interlocking mechanism of the solid-state relay, and immediately cuts off the electrical connection of the channel.

[0043] Step S104: Based on the transmission timing between the first preset spatial coordinate region and the second preset spatial coordinate region, control the trigger interval time of the first group of carriers and the second group of carriers.

[0044] There is a preset physical and signal transmission delay between the first and second preset spatial coordinate regions. The system timing controller sets the trigger interval between channels according to the preset conduction timing data. The system sets the conduction timing data within a parameter range of 20 to 50 milliseconds. After the first channel releases the first interference signal at a specific phase point of the first interference signal cycle, the system starts a high-precision timer. After a delay of 20 to 50 milliseconds, the second channel is triggered to release the second interference signal in the second preset spatial coordinate region. By adjusting the trigger time offset, the occurrence time of the physical electric field envelope is adapted to the preset signal transmission timing.

[0045] Within the basic operating cycle, this embodiment provides closed-loop processing branch logic for multimodal physiological feedback.

[0046] The system includes a peripheral interface bus for synchronously receiving multimodal physiological signal data acquired by external sensors during the signal output cycle. This multimodal physiological signal data encompasses signal data acquired by functional magnetic resonance imaging (fMRI), electroencephalography (EEG), and autonomic nervous system sensors, such as heart rate variability and skin conductance characteristics. For the raw data, the system's digital signal processor performs feature fusion calculations to generate objective representational state data.

[0047] In the feature fusion calculation step, the processor extracts frequency band power features and phase synchronization features from the signal data acquired by the EEG sensor; it also calculates the rate of change of heart rate variability and skin conductance activity features from the signal data acquired by the autonomic nervous system sensor in parallel, and uses polynomial fitting to calculate the current neural state index. The system analyzes the blood oxygen dependence features and functional connectivity features from the signal data acquired by the functional magnetic resonance imaging sensor, maps these spatial sequence features to the topological connectivity space of a first preset spatial coordinate region and a second preset spatial coordinate region, and evaluates the causal modulation strength between the two regions through partial correlation analysis.

[0048] The system generates final objective representation state data based on the weighted sum of neural state indicators and causal regulation strength. In each feedback evaluation cycle, the processor compares this state data with the system's preset judgment threshold. When the objective representation state data does not meet the preset judgment conditions, the system dynamically updates the target output amplitude parameter of the current generator in the next output cycle, thus completing parameter correction driven by objective indicators.

[0049] Corresponding to the aforementioned equipment control method, this application provides a physical operation control device. For example... Figure 2 As shown, the control device includes: a channel configuration module 201, a waveform control module 202, a physiological feedback acquisition module 203, a safety protection module 204, and a timing control module 205 that is communicatively connected to the waveform control module.

[0050] The channel configuration module 201 is configured to perform electric field optimization and channel configuration based on a multi-objective optimization function and current constraints, determining the first electrode pair and the second electrode pair. Internally, the channel configuration module 201 includes a matrix construction unit and a joint solution unit. The matrix construction unit is used to construct a guiding field matrix based on a preset organization model; the joint solution unit is connected to the matrix construction unit and is equipped with a built-in heuristic algorithm chip, capable of performing multi-objective joint solutions for target region envelope maximization and non-target region suppression using the guiding field matrix under constraints of maximum total current, single electrode current, and the number of activated electrodes.

[0051] The waveform control module 202 integrates a dual-channel current generator, such as a direct digital synthesis circuit. Its configuration controls the dual-channel current generator to generate a first set of carrier waves, which are output to the first electrode pair, interfering in a first preset spatial coordinate region to form a first interference signal. Simultaneously, it controls the generation of a second carrier wave, which is output to the second electrode pair, interfering in a second preset spatial coordinate region to form a second interference signal. This ensures that the second difference frequency is always greater than the first difference frequency. Figure 3 The signal characteristic curves in the diagram visually demonstrate the corresponding physical behavior of the high-frequency carrier frequency variable group generated by the waveform control module 202 and the low-frequency interference difference frequency envelope formed by its final modulation.

[0052] The safety protection module 204 is hardwired to each physical output channel and the electrode impedance monitoring unit. It has a high sampling rate analog-to-digital converter and is configured to continuously acquire the output impedance and output current values ​​of each output channel. When the impedance, current, or other parameters exceed the system's current limit or impedance threshold, a graded response mechanism, including an emergency circuit cutoff action, is automatically executed.

[0053] Figure 2 It includes a physiological feedback acquisition module 203, which receives data from external functional magnetic resonance imaging units, electroencephalograms and autonomic nerve sensors via peripheral interfaces, and delivers the data to the main processor for closed-loop updates.

[0054] The timing control module 205 in the control device has a built-in high-precision clock oscillator, which is configured to precisely control the relative trigger interval time between the first group of carriers in the first channel and the second group of carriers in the second channel based on preset conduction timing data.

[0055] like Figure 4 As shown in the side sectional view, the first current source 401 driven by the system is connected via wires to a first electrode pair arranged on one side of the headpiece. This electrode pair is positioned over a first preset spatial coordinate region 403. The spacing between the first electrode pairs is typically configured within a specific parameter range to ensure that the spatial current vectors they generate intersect at depth. The second current source 402 of the system is connected to a second electrode pair arranged on the top of the headpiece. This region points directly to a second preset spatial coordinate region 404, where the spacing between the electrode pairs is moderately increased to enhance the electric field penetration density across the region. Figure 4 The first interference path 405 reflects the path through which energy is focused to each region.

[0056] like Figure 5 As shown in the top view and coronal simulation test diagram, the first electrode node 501 is arranged in the front or top area and the second electrode node 502 is arranged in the side area, with the preset coordinate reference direction 504 as the reference. Figure 5 The electric field intensity distribution diagram on the right verifies that after the optimization calculation by the channel configuration module, the high-frequency second interference path 503 introduced by the electrode can generate electric field accumulation deep within the target, and the diffuse field intensity in the non-target area is suppressed.

[0057] In another optional implementation, the channel configuration module 201 has a built-in phase optimization and sparsification algorithm engine. After completing the initial allocation of electrode pairs and current magnitudes, the processor extracts the initial phase difference between the first and second electrode pairs. By adding a phase scanning variable to the objective function, a secondary phase optimization iterative algorithm is executed for the initial phase difference, causing the phase shift of the two high-frequency waves to converge to the extreme point when they reach the core region of the nucleus. Based on the optimized electrode weights, the processor executes sparsification electrode configuration instructions. The system sets a threshold number of active electrodes to retain, disconnects redundant electrode channels with smaller weight contributions and sets them to zero, retaining only the physical electrodes that contribute the most to the interference focus, thus reducing the parasitic electric field output effect of the peripheral non-target tissue. By employing this combination of sparsification and phase optimization, the resolution of the microscopic electric field is improved.

[0058] The timing control module 205 supports multi-cycle cyclic control. The system supports receiving preset timing extension parameters to lengthen the sequential application time interval between the suppression of the first preset spatial coordinate region and the activation of the second preset spatial coordinate region. By utilizing the cyclic interval design and the time window of the signal transmission hysteresis effect, long-term intervention on the output response of the target region can be achieved.

[0059] The system mandates that the wires and electrode materials that directly contact the output object be non-magnetic and compatible with functional magnetic resonance imaging (fMRI) hardware. An external noise-reducing shielding layer based on carbon fiber or non-ferromagnetic braided material is added to the external connection cable from the generator output to the electrodes. This shielding design utilizes the Faraday cage effect to block radio frequency interference from the high-frequency carrier wave to the nuclear magnetic resonance coil, ensuring synchronized operation of blood oxygenation data and scalp signal data under high-fidelity acquisition.

[0060] This application provides an electronic device. The electronic device includes a processor and a memory. The memory is configured to store a computer program. The processor is connected to the memory and configured to call and execute the computer program, thereby controlling an underlying digital-to-analog generator and impedance detection and other auxiliary hardware to implement the aforementioned device control method.

[0061] This application provides a computer-readable storage medium. The computer-readable storage medium stores a computer program. When the computer program is executed by a microprocessor, it can complete the construction of a finite element model, the solution of multi-objective optimization equations, the setting of multi-channel carrier and difference frequency parameters, the feedback fusion of multi-modal physiological indicators, and the triggering of a hierarchical security mechanism.

[0062] The above description is merely a preferred embodiment of this application and is not intended to limit this application. Any modifications, equivalent substitutions, and improvements made within the spirit and principles of this application should be included within the protection scope of this application.

Claims

1. A control method applied to a control device comprising a current generator with multiple output channels and an electrode array, characterized in that, include: Electric field optimization and channel configuration are performed based on multi-objective optimization functions and current constraints to determine the first electrode pair and the second electrode pair. A first output control command is generated to control the output of a first set of carrier waves to the first electrode pair, which are used to form a first interference signal in a first preset spatial coordinate region; A second output control command is generated to control the output of a second set of carrier waves to the second electrode pair, which are used to form a second interference signal in a second preset spatial coordinate region; Acquire the electrical parameters of each output channel, and execute a safety response action when the electrical parameters exceed a preset threshold; Based on preset transmission timing data, timing control commands are generated to control the trigger interval between the first group of carriers and the second group of carriers.

2. The method as described in claim 1, characterized in that, The first preset spatial coordinate region is a pre-defined first spatial coordinate region; the second preset spatial coordinate region is a pre-defined second spatial coordinate region.

3. The method as described in claim 2, characterized in that, The first interference signal is a continuous envelope with a first difference frequency; the second interference signal is an intermittent envelope with a second difference frequency, wherein the second difference frequency is greater than the first difference frequency.

4. The method as described in claim 3, characterized in that, The first difference frequency is configured in the low frequency band, preferably 5Hz; the second difference frequency is configured in the frequency band greater than the first difference frequency, preferably 30Hz; the conduction timing data is configured to be 20 to 50ms.

5. The method as described in claim 1, characterized in that, The steps of optimizing the electric field and configuring the channel based on the multi-objective optimization function and current constraints to determine the first electrode pair and the second electrode pair include: constructing a guiding field matrix based on a preset tissue model; and using the guiding field matrix to perform multi-objective joint solution for target region envelope peaking and non-target region suppression under the constraints of maximum total current, single electrode current and number of activated electrodes.

6. The method as described in claim 5, characterized in that, The steps of performing multi-objective joint solution for target envelope peaking and non-target suppression include: configuring a first weight for the target envelope peaking and configuring a second weight for the non-target suppression, wherein the sum of the first weight and the second weight is a constant value; receiving an adjustment command, dynamically adjusting the first weight and the second weight within a preset range, completing the objective solution and outputting the optimal electrode combination as the first electrode pair and the second electrode pair.

7. The method as described in claim 1, characterized in that, The steps of acquiring the electrical parameters of each output channel and executing a safety response action when the electrical parameters exceed a preset threshold include: real-time monitoring of the output impedance value and output current value of each output channel; determining whether the output impedance value or the output current value exceeds a preset threshold; and triggering graded actions according to the degree of exceeding the preset threshold in response to the determination result. The graded actions include limiting current output, cutting off channel connection, and triggering hardware-level interlocking.

8. The method as described in claim 1, characterized in that, Also includes: During the signal output cycle, it receives multimodal physiological signal data collected by external sensors; Feature fusion is performed on the multimodal physiological signal data to generate objective representation state data; The output parameters of the current generator are adjusted based on the objective characterization data.

9. The method as described in claim 8, characterized in that, The multimodal physiological signal data includes signal data acquired by a functional magnetic resonance imaging (fMRI) sensor, signal data acquired by an electroencephalogram (EEG) sensor, and signal data acquired by an autonomic nervous system sensor. The signal data acquired by the fMRI sensor includes blood oxygen dependence characteristics and functional connectivity characteristics; the signal data acquired by the EEG sensor includes frequency band power characteristics and phase synchronization characteristics; and the signal data acquired by the autonomic nervous system sensor includes heart rate variability characteristics and skin conductance activity characteristics.

10. The method as described in claim 9, characterized in that, The step of performing feature fusion on the multimodal physiological signal data to generate objective representation state data includes: extracting frequency band power features from the signal data collected by the EEG sensor, and calculating neural state indicators by combining the rate of change of heart rate variability features and skin conductance activity features from the signal data collected by the autonomic nervous system sensor; mapping the blood oxygen dependence features to the topological connection space of the first preset spatial coordinate region and the second preset spatial coordinate region, and evaluating the causal regulation strength between regions; generating the objective representation state data based on the weighted superposition result of the neural state indicators and the causal regulation strength, and dynamically updating the target output amplitude parameter of the current generator in the next output cycle when the objective representation state data does not meet the preset judgment conditions.

11. A control device, characterized in that, include: The channel configuration module (201) is configured to perform electric field optimization and channel configuration based on a multi-objective optimization function and current constraint conditions, and to determine the first electrode pair and the second electrode pair. The waveform control module (202) is connected to the channel configuration module (201) and is configured to generate a carrier output control command to control the output of a first set of carriers to the first electrode pair for forming a first interference signal in a first preset spatial coordinate region, and to control the output of a second set of carriers to the second electrode pair for forming a second interference signal in a second preset spatial coordinate region. The physiological feedback acquisition module (203) is configured to receive multimodal physiological signal data acquired by an external sensor; The safety protection module (204) is connected to each output channel and configured to acquire the electrical parameters of each output channel and perform a safety response action when the electrical parameters exceed a preset threshold. The timing control module (205) is connected to the waveform control module (202) and is configured to generate timing control commands based on preset transmission timing data to control the trigger interval time of the first group of carriers and the second group of carriers.

12. The apparatus as claimed in claim 11, characterized in that, The first preset spatial coordinate region is a pre-defined first spatial coordinate region, and the second preset spatial coordinate region is a pre-defined second spatial coordinate region; the first interference signal is a continuous envelope with a first difference frequency; the second interference signal is an intermittent envelope with a second difference frequency, wherein the second difference frequency is greater than the first difference frequency.

13. The apparatus as claimed in claim 11, characterized in that, The channel configuration module (201) includes: a matrix construction unit configured to construct a guiding field matrix based on a preset organization model; and a joint solution unit connected to the matrix construction unit, configured to perform multi-objective joint solution of target region envelope maximization and non-target region suppression using the guiding field matrix under the constraints of maximum total current, single electrode current and number of activated electrodes.

14. An electronic device, characterized in that, include: Memory, configured to store computer programs; A processor, connected to the memory, configured to execute the computer program to implement the method as claimed in any one of claims 1 to 10.

15. A computer-readable storage medium, characterized in that, The computer-readable storage medium stores a computer program that, when executed by a processor, implements the method as described in any one of claims 1 to 10.

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