CN110812693B - Multichannel high-frequency non-invasive accurate positioning nerve stimulation system - Google Patents
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- A61N1/00—Electrotherapy; Circuits therefor
- A61N1/18—Applying electric currents by contact electrodes
- A61N1/32—Applying electric currents by contact electrodes alternating or intermittent currents
- A61N1/36—Applying electric currents by contact electrodes alternating or intermittent currents for stimulation
- A61N1/36014—External stimulators, e.g. with patch electrodes
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- A61N1/04—Electrodes
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
- A61N1/00—Electrotherapy; Circuits therefor
- A61N1/18—Applying electric currents by contact electrodes
- A61N1/32—Applying electric currents by contact electrodes alternating or intermittent currents
- A61N1/36—Applying electric currents by contact electrodes alternating or intermittent currents for stimulation
- A61N1/36014—External stimulators, e.g. with patch electrodes
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Abstract
The invention discloses a multichannel high-frequency non-invasive accurate positioning nerve stimulation system, which comprises modules of a high-frequency signal generating circuit, a signal conditioning circuit, an alternating current constant voltage stimulation circuit, an alternating current constant current stimulation circuit, an isolation circuit, a signal switching circuit and a human-computer interaction unit; the high-frequency signal output by the high-frequency signal generating module outputs a stimulus source signal through a signal conditioning circuit; the stimulation source signal is isolated by the isolation circuit and then is input into the alternating current constant voltage stimulation circuit or the alternating current constant current stimulation circuit through the signal switching circuit; the signal switching circuit is a program-controlled switch and is used for switching the alternating current constant voltage stimulation circuit and the alternating current constant current stimulation circuit to work; the human-computer interaction unit is used for inputting parameter requirements of the high-frequency signals and transmitting the parameter requirements to the high-frequency signal generation module. The invention is safe and effective, the stimulation mode is freely switched, and the impedance can be tested on line.
Description
Technical Field
The invention relates to the fields of neuroscience and biomedical engineering, medicine, electronic information, mechanical engineering and the like, in particular to a nerve regulation and control system for performing noninvasive high-frequency alternating current stimulation by using a multichannel signal interference technology (Temporal interference).
Background
The nerve regulation rehabilitation therapy for the neuropsychiatric diseases is favored by doctors and researchers due to the characteristics of safety, quick effect and small side effect, and is also a hot point for research and attention of physical therapy.
At present, the noninvasive neuromodulation treatment technology mainly comprises Transcranial Magnetic Stimulation (TMS), Transcranial Direct Current Stimulation (TDCS), biofeedback and the like.
TMS is based on the principle of electromagnetic induction and electromagnetic conversion, the magnetic field generated by strong transient current in a stimulation coil penetrates through the skull, the dynamic magnetic field is converted into induced current in the direction opposite to the current direction of the stimulation coil in the skull, and the endogenous induced current stimulates nerve cells to generate a series of physiological and biochemical reactions.
Transcranial Direct Current Stimulation (TDCS) utilizes constant, low-intensity direct current (1-2 mA) to regulate cerebral cortex neuron activity.
The biofeedback technology collects various information generated in the physiological change process through an electrophysiological signal recording system, transmits the information to a data processing and displaying system, converts the information into signals or readings which are easy to understand for patients through processing, and trains under the guidance of medical staff, so that the patients learn to utilize the processed signals to consciously control various physiological and pathological processes in vivo, promote function recovery, and achieve the purpose of treatment.
The nerve activity of the cerebral cortex is regulated through the noninvasive intervention mode, and the aim of regulating the function of a specific brain area by utilizing brain plasticity change is fulfilled, so that the noninvasive intervention mode is widely applied to various nerve or mental diseases such as depression, sleep disorder, drug addiction, stroke, mild cognitive disorder, post-traumatic stress disorder, tension headache and the like in clinic at present, however, the direct action depth of the regulation mode is only limited to the superficial cerebral epidermis layer.
Although there are structural and functional connections between brain regions of the brain, it generally takes a long time to indirectly affect the deep brain regions by stimulating the superficial epidermal layer, thereby altering the behavioral response. Because external stimulation directly acts on the superficial epidermal layer, the deep brain region can be affected only by high spatial precision, which causes great individual difference of treatment effect and low durability of treatment effect to a certain extent. In addition, at present, the main non-invasive stimulation modes do not achieve the function of accurately positioning the brain region or adaptively and accurately matching the brain related part according to the treatment scheme. Although TMS stimulation has a relatively high focusing capacity, it has a limited depth of action (2-4 mm subcutaneously) and can only directly affect neural activity in the superficial cerebral cortex. The specific TMS coil can be used for acting on a deep brain region, but the cortical brain activity is correspondingly regulated, and the coil has limited acting target points and poor universality.
Disclosure of Invention
The purpose of the invention is as follows: in order to solve the problems that a noninvasive neurostimulation system in the prior art cannot accurately position a brain region and has limited action depth, the invention provides a multichannel high-frequency noninvasive accurate positioning neurostimulation system.
The technical scheme is as follows: a multichannel high-frequency non-invasive precise positioning nerve stimulation system comprises a high-frequency signal generating circuit, a signal conditioning circuit, an alternating current constant voltage stimulation circuit, an alternating current constant current stimulation circuit, an isolation circuit, a signal switching circuit and a man-machine interaction unit; the high-frequency signal output by the high-frequency signal generating circuit outputs a stimulus source signal through the signal conditioning circuit; the stimulation source signal is isolated by the isolation circuit and then is input into the alternating current constant voltage stimulation circuit or the alternating current constant current stimulation circuit through the signal switching circuit; the signal switching circuit is a program-controlled switch and is used for switching the alternating current constant voltage stimulation circuit and the alternating current constant current stimulation circuit to work; the man-machine interaction unit is used for inputting parameter requirements of the high-frequency signals and transmitting the parameter requirements to the high-frequency signal generating circuit.
Furthermore, the high-frequency signal generating circuit comprises an FPGA high-frequency main signal module and an external modulation signal module; the FPGA high-frequency main signal module is used for generating a high-frequency main signal, the external modulation signal module is used for generating a modulation signal, and the modulation signal is used for modulating with a high-frequency carrier signal.
Furthermore, the alternating current constant voltage stimulation circuit comprises a preceding stage amplification circuit, a power amplification circuit and an AB complementary class push-pull circuit, and the stimulation source signal is output through the preceding stage amplification circuit, the power amplification circuit and the AB complementary class push-pull circuit in sequence;
the system further comprises a fixed gain amplifying circuit, the fixed gain amplifying circuit adopts a current mode operational amplifier AD8009, and signals output by the alternating current constant voltage stimulating circuit are output after being amplified by the fixed gain amplifying circuit.
Furthermore, the alternating current constant current stimulation circuit adopts a chip XTR111, and a stimulation source signal output by the signal conditioning circuit is input from a sixth pin as an input signal of the chip XTR 111; a fourth pin and a fifth pin of the chip XTR111 are connected with a reference voltage; output signals of a second pin and a third pin of the chip XTR111 are output through a gain control circuit;
the system also comprises a gain control circuit, wherein the gain control circuit adopts an FPGA to establish a 16-bit amplitude control register to control the output amplitude of the signal, and the signal output by the alternating current constant current stimulation signal is amplified by the gain control circuit and then output.
Furthermore, the signal conditioning circuit comprises a digital multiplication circuit, a preceding stage amplification circuit, a subsequent stage amplification circuit and a power amplification circuit, and the signal output by the high-frequency signal generating circuit passes through the digital multiplication circuit, the preceding stage amplification circuit, the subsequent stage amplification circuit and the power amplification circuit in sequence and is output from the output end of the power amplification circuit.
Furthermore, the isolation circuit comprises an isolation input part, a 1pF isolation capacitor and an isolation output part, wherein the isolation input part is isolated from the isolation output part through the 1pF isolation capacitor, the isolation input part is a duty ratio modulation signal and is digitally transmitted through a potential barrier, and the isolation output part is used for receiving the modulated signal and converting the modulated signal into an analog voltage; the isolation input part comprises an amplifier and a comparator, wherein an input current and a switching current source are input to a negative end of the amplifier, the amplifier and a resistor capacitor form an integrating circuit, an output end of the integrating circuit is connected with an input end of the comparator, and the comparator and the first sensing amplifier are used for forcing the switching current source to be switched on and off; the output signal of the comparator is isolated by an isolation capacitor, and after the second induction amplifier detects the signal isolated by the isolation capacitor, the second induction amplifier drives a switch current source to enter an integrator and output by a feedback loop, wherein the feedback loop comprises a sample-and-hold amplifier, and the sample-and-hold amplifier is used for removing unnecessary ripple voltage.
Furthermore, ADUM6000 is adopted to isolate the power supplies of the high-frequency signal generating circuit and the signal conditioning circuit from the power supplies of the alternating current constant voltage stimulating circuit and the alternating current constant current stimulating circuit.
The electrode cap comprises a plurality of electrodes, the high-frequency signal generating circuit outputs high-frequency signals of the plurality of channels, and each channel is provided with a signal conditioning circuit, an alternating current constant voltage stimulating circuit, an alternating current constant current stimulating circuit and a signal switching circuit; the signal output end of the channel is connected with the electrode in the electrode cap.
The impedance testing module comprises an input end, a frequency-adjustable excitation source circuit, a gain control circuit, a filter circuit, an AD sampling circuit and an output end, wherein the frequency-adjustable excitation source circuit is used as an impedance testing source; the input end is connected with a tested electrode, and a test signal acquired from the tested electrode is output through the gain control circuit, the filter circuit and the AD sampling circuit; the output end is connected with an upper computer, the upper computer is used for calculating the impedance amplitude and the phase of the test signal through DFT, and the calculation result is displayed on an LCD display screen or the upper computer.
Furthermore, the signal switching circuit, the alternating current constant voltage stimulating circuit and the alternating current constant current stimulating circuit are vertically arranged, the distance between adjacent wires is increased, and the distance between the adjacent wires and the ground plane is reduced.
Has the advantages that: the invention provides a multichannel high-frequency non-invasive accurate positioning nerve stimulation system, which is a safe and effective non-invasive multichannel high-frequency deep nerve regulation and control system compared with the prior art and has the following advantages:
1. the multi-channel high-frequency constant-current/constant-voltage alternating-current stimulation circuit adopts a program-controlled switch to freely switch a stimulation mode, and has high-precision current/voltage resolution.
2. All stimulation channels are strictly isolated no matter in direct current or high-frequency alternating current signals, the maximum crosstalk noise among the channels is less than 3.0 mu Vrms, and the isolation voltage is more than 3500V @1 kHz. The analog isolation among channels is realized by adopting an isolation circuit and a special wiring technology;
3. each channel adopts an electronic building block type structure, any hot plug combination is output, any channel can independently output any signal, a special signal can be output to assist focusing stimulation, and signal output phase difference control can be performed among the channels.
4. And (3) real-time impedance testing: the stimulation is realized, the contact impedance of the stimulation electrode and the head is monitored, whether the stimulation lead is in good contact or not can be prompted in real time, and the threshold value is set for early warning prompt of lead falling.
5. The electrode cap adopts a 10-10 system positioning design, the shapes of the stimulating electrodes are various and can be designed in a circular shape, an annular shape and the like, and an automatic model identification circuit is arranged in the electrode cap.
Drawings
FIG. 1 is a block diagram of the structure of the generation of high frequency stimulus signals;
FIG. 2 is a block diagram of a signal conditioning circuit;
FIG. 3 is a schematic diagram of an AC constant current control circuit;
FIG. 4 is a schematic diagram of a pre-amplifier circuit in an AC constant voltage stimulation circuit;
FIG. 5 is a functional block diagram of an impedance measurement module circuit;
FIG. 6 is a PCB wiring diagram;
fig. 7 is a schematic diagram of an isolation circuit.
Detailed Description
The invention is further described with reference to the following figures and specific examples.
A multichannel high-frequency non-invasive precise positioning nerve stimulation system comprises a plurality of stimulation channels and an electrode cap, wherein the electrode cap comprises a plurality of electrodes, a high-frequency signal generating circuit outputs high-frequency signals (the highest frequency exceeds 200kHz and 20mA; the highest frequency of a common stimulator is generally not more than 1kHz and the output current is not more than 2 mA) of the channels, and each channel is provided with a signal conditioning circuit, an alternating current constant voltage stimulation circuit, an alternating current constant current stimulation circuit and a signal switching circuit; the signal output end of the channel is connected with the electrode in the electrode cap. The signal switching circuit realizes the switching of the work of the alternating current constant voltage stimulating circuit and the alternating current constant current stimulating circuit through the program control switch, and the connection relation is shown as the figure 1. The output signal of the high-frequency signal generating circuit and the output signal of the external modulation signal module are modulated by the signal conditioning circuit and then output stimulus source signals; the high-frequency signal generating circuit comprises an FPGA high-frequency main signal module and an external modulation signal module; the FPGA high-frequency main signal module is used for generating a high-frequency main signal, and the external modulation signal module is used for generating a modulation signal and modulating the modulation signal with the high-frequency main signal; the external modulation signal can realize the input of any user signals such as triangular waves, sawtooth waves and the like, and carries out various modulations with the main signal, and the corresponding stimulus source signal can be output by directly inputting related parameters through a touch screen of the man-machine interaction unit; the stimulation source signal is isolated by the isolation circuit and then is input into the alternating current constant voltage stimulation circuit or the alternating current constant current stimulation circuit through the signal switching circuit; the signal switching circuit is realized by a program-controlled switch and is used for switching the alternating current constant voltage stimulation circuit and the alternating current constant current stimulation circuit to work; the man-machine interaction unit is used for inputting parameter requirements of the high-frequency signals and transmitting the parameter requirements to the high-frequency signal generating circuit.
The output of each stimulation channel is high-frequency alternating current constant current or constant voltage output, and the waveform of each channel can be independently controlled through an LCD display touch screen or a regulating knob.
When the FPGA generates a main signal, the original code reconstruction technology is utilized, the waveform jitter is obviously reduced, the second harmonic is more than 5dB lower than the 2 nd harmonic of the DDS technology, and the highest frequency resolution is 0.1 mu Hz.
The signal conditioning circuit comprises a digital multiplication circuit, a preceding stage amplification circuit, a subsequent stage amplification circuit and a power amplification circuit, wherein the output signal of the high-frequency signal generation circuit passes through the digital multiplication circuit, the preceding stage amplification circuit, the subsequent stage amplification circuit and the power amplification circuit in sequence and is output from the output end of the power amplification circuit. The amplitude control circuit and the power amplification circuit which are composed of the pre-stage amplification circuit, the multiplication circuit and the post-stage amplification circuit enable signals to be amplified to 10V peak-to-peak values, as shown in figure 2.
The alternating current constant current stimulation circuit comprises a voltage-controlled mirror current source, a chip XTR111 is adopted, and a stimulation source signal output by the signal conditioning circuit is input from a sixth pin as an input signal of the chip XTR 111; a fourth pin and a fifth pin of the chip XTR111 are connected to a control signal of the FPGA; output signals of a second pin and a third pin of the chip XTR111 are output through an access gain control circuit; the eighth pin is an error flag output, the ninth pin is whether to close the output pin, and the voltage-controlled mirror current source technology is utilized, so that the 0-20mA precision alternating current and constant current output control is realized, as shown in FIG. 3. The voltage-controlled mirror current source mode is adopted, on one hand, the defect that a common virtual earth current source is not used is overcome, and meanwhile, the phenomenon that output is unstable due to the fact that a common positive feedback balanced circuit changes along with load is also overcome, and in addition, the design can rapidly expand the size of output current.
The alternating current constant voltage stimulation circuit comprises a preceding stage amplification circuit, a power amplification circuit and an AB complementary type push-pull circuit, wherein the preceding stage amplification circuit is in the front, and the power amplification circuit and the AB complementary type push-pull circuit are integrated in the back. The power amplifying circuit and the complementary push-pull circuit are designed by themselves, and can ensure high fidelity signals. As shown in fig. 4, the input IOUT-C of the pre-stage amplifier circuit is connected to the signal output by the signal conditioning circuit, and the output P of the pre-stage amplifier circuit is connected to the subsequent power amplifier circuit and the AB complement push-pull circuit. Driven by a high-speed wide-range precision rail-to-rail operational amplifier, an alternating voltage signal of Vpp =90V is achieved. The power amplifying circuit mainly aims at improving the power of output signals, AD811 produced by AD company is used for pre-amplification, AD811 is a current feedback type broadband operational amplifier, the unit gain bandwidth is very wide, 15V is used for power supply, and-3 dB bandwidth reaches 100MHz under the condition that the gain is +10, so that the power amplifying circuit is very suitable for the broadband amplification requirement of the system, and the power amplifying circuit adopts a three-stage complementary amplifying circuit consisting of high-frequency triodes, is used for power supply by 45V, so that the maximum 90V output signal range is met.
The common stimulation circuit does not have a real-time impedance analysis function in a stimulation mode, usually tests an equivalent impedance according to a specific frequency signal before stimulation, and further does not have a phase analysis function. The present embodiment further includes an impedance testing module, which can perform impedance measurement on line, as shown in fig. 5, and the impedance testing module includes an input end, a frequency-adjustable excitation source circuit, a gain control circuit, a filter circuit, an AD sampling circuit, and an output end, where the frequency-adjustable excitation source circuit is used as an impedance testing source; the input end is connected with a tested electrode, and a test signal acquired from the tested electrode is output through the gain control circuit, the filter circuit and the AD sampling circuit; the output end is connected with an upper computer, the upper computer is used for calculating the impedance amplitude and the phase of the test signal through DFT, and the calculation result is displayed on an LCD display screen or the upper computer. The equivalent impedance is represented as Z (w), SDA and SCL are control lines of an I2C protocol, MCLK is a clock signal, impedance = measured voltage/known current, and a frequency-adjustable 0.1 muA constant-current excitation source circuit is used as an impedance test source; the output end is connected with an upper computer, and the upper computer is used for calculating the impedance amplitude and the phase of the output signal through DFT. The corresponding voltage drop generated on the tested electrode is sampled and analyzed through a 12-bit 1MSPS ADC circuit, and the impedance amplitude and phase are obtained through DFT calculation, so that equivalent complex impedance is obtained and displayed on an LCD screen and an upper computer software interface, and the stimulation state is effectively monitored.
The constant-voltage AC constant-voltage stimulation circuit is characterized by further comprising a fixed gain amplifying circuit and a gain control circuit, wherein the fixed gain amplifying circuit is embedded in a constant-voltage mode, signals output by the AC constant-voltage stimulation circuit are amplified by the fixed gain amplifying circuit and then output, the signals are amplified again in the constant-voltage mode, the fixed gain amplifying circuit adopts a current type operational amplifier AD8009, the fixed gain amplifying circuit has a slew rate of 5500V/mu s, the bandwidth of a small signal is 700MHz, the bandwidth of a large signal is 440MHz, the two times of the amplification of the filtered signals reach 1Vpp, and the signals are primarily amplified and then sent to a secondary amplifying circuit. Current mode op-amps are suitable for use in high speed applications because they are not limited by the fundamental gain-bandwidth product. The gain control circuit adopts FPGA to establish a 16-bit amplitude control register, controls the output amplitude of a signal, controls the amplitude resolution to reach 3 muV, and can further control the current output with the precision of 10 muA. And the signal output by the alternating current constant current stimulation signal is amplified by the gain control circuit and then output.
The stimulator is a signal generating device, and different channels can generate space radiation under the condition of high frequency and mutually interfere with each other when in stimulation. By means of a high-speed PCB wiring technology, aiming at the characteristics and requirements of ground potential in a system, an isolation circuit and a special wiring technology are adopted to realize analog isolation among channels, so that intermodulation interference among the channels is reduced, and the method is shown in figure 6.
1. All channel back-stage power supplies are isolated from the front-stage power supply. The design adopts ADUM6000 to realize positive power isolation, and adopts ADUM6000 to isolate the power supplies of the high-frequency signal generating circuit and the signal conditioning circuit from the power supplies of the alternating current constant voltage stimulating circuit and the alternating current constant current stimulating circuit.
2. The driving stage signal (signal before the change-over switch) is physically isolated from the rear stage (change-over switch, AC constant voltage stimulating circuit, AC constant current stimulating circuit).
The isolation circuit comprises an isolation input part, a 1pF isolation capacitor and an isolation output part, wherein the isolation input part is isolated from the isolation output part through the 1pF isolation capacitor, the isolation input part is a duty ratio modulation signal and is digitally transmitted through a potential barrier, and the isolation output part is used for receiving the modulated signal, converting the modulated signal into analog voltage and removing inherent ripples in demodulation.
As shown in FIG. 7, an input current (Vin/200 k Ω) and a 100 μ A switched current source are input to the negative side of the amplifier A1, the 100 μ A current source being implemented by a 200uA switchable current source and a 100 μ A fixed current sink. The integrator circuit output, consisting of a1 and a resistor-capacitor, will ramp in one direction until the comparator B1 threshold is exceeded, and the comparator and Sense amplifier Sense will force the current source to switch; the resulting signal is a triangular waveform with a 50% duty cycle. The internal oscillator forces the current source to switch at 500kHz, and the resulting capacitive drive is a complementary duty cycle modulated square wave. The Sense amplifier Sense detects the signal across the capacitor and drives the switched current source into integrator a 2. The output uses a 200k Ω feedback resistor, ensuring that the average value of Vout is equal to Vin. The sample-and-hold amplifier S/H in the output feedback loop is used to remove the unwanted ripple voltage inherent in the demodulation process.
In addition, in the rear-stage amplification circuit, all signal impedances need to be subjected to wiring matching, reflection is reduced, the ground adverse effect is reduced, all wirings are vertically arranged, the distance between two signal layers is increased, and the distance between the signal layers and an adjacent reference plane is reduced. Widening the distance between the signal lines and keeping the height of the medium more than three times; the signal line is close to the ground plane as much as possible, is tightly coupled with the ground plane and is decoupled from the adjacent signal; the parallel routing length between single-ended signals is reduced, the wires are as short as possible, so that crosstalk caused by long coupling between networks is reduced, and the packet ground processing is carried out on key signal wires (such as the final-stage output signal possibly with the maximum current output). The distance between the centers of adjacent tracks is kept at a distance of 4 times the width of the tracks.
Claims (8)
1. A multichannel high-frequency non-invasive precise positioning nerve stimulation system is characterized by comprising a high-frequency signal generating circuit, a signal conditioning circuit, an alternating current constant voltage stimulation circuit, an alternating current constant current stimulation circuit, an isolation circuit, a signal switching circuit, a gain control circuit and a human-computer interaction unit; the high-frequency signal output by the high-frequency signal generating circuit outputs a stimulus source signal through the signal conditioning circuit; the stimulation source signal is isolated by the isolation circuit and then is input into the alternating current constant voltage stimulation circuit or the alternating current constant current stimulation circuit through the signal switching circuit; the signal switching circuit is a program-controlled switch and is used for switching the alternating current constant voltage stimulation circuit and the alternating current constant current stimulation circuit to work; the human-computer interaction unit is used for inputting parameter requirements of the high-frequency signal and transmitting the parameter requirements to the high-frequency signal generation circuit;
the gain control circuit is constructed by a 16-bit amplitude control register created by the FPGA, the gain control circuit is connected with the AC constant current stimulation circuit in a butt joint mode, and the gain control circuit performs signal amplitude control and amplification on signals output by the AC constant current stimulation circuit and outputs the signals;
based on the design, the system also comprises an impedance testing module, a plurality of channels and an electrode cap; the electrode cap comprises a plurality of electrodes, the high-frequency signal generating circuit outputs high-frequency signals of a plurality of channels, and each channel is provided with a signal conditioning circuit, an alternating current constant voltage stimulating circuit, an alternating current constant current stimulating circuit and a signal switching circuit; the signal output tail end of the channel is connected with an electrode in the electrode cap;
the impedance test module comprises an input end, a frequency-adjustable excitation source circuit, a gain control circuit, a filter circuit, an AD sampling circuit and an output end, wherein the frequency-adjustable excitation source circuit is used as an impedance test source; the input end is connected with a tested electrode, and a test signal acquired from the tested electrode is output through the gain control circuit, the filter circuit and the AD sampling circuit; the output end is connected with an upper computer, the upper computer is used for calculating the impedance amplitude and the phase of the test signal through DFT, and the calculation result is displayed on an LCD display screen or the upper computer.
2. The multichannel high-frequency noninvasive precise positioning nerve stimulation system as claimed in claim 1, characterized in that the high-frequency signal generating circuit comprises an FPGA high-frequency main signal module and an external modulation signal module; the FPGA high-frequency main signal module is used for generating a high-frequency main signal, the external modulation signal module is used for generating a modulation signal, and the modulation signal is used for modulating with a high-frequency carrier signal.
3. The multichannel high-frequency non-invasive precise positioning nerve stimulation system according to claim 1, wherein the alternating current constant voltage stimulation circuit comprises a pre-stage amplification circuit, a power amplification circuit and an AB complementary class-A push-pull circuit, and the stimulation source signal is output through the pre-stage amplification circuit, the power amplification circuit and the AB complementary class-A push-pull circuit in sequence;
the system further comprises a fixed gain amplifying circuit, the fixed gain amplifying circuit adopts a current mode operational amplifier AD8009, and signals output by the alternating current constant voltage stimulating circuit are output after being amplified by the fixed gain amplifying circuit.
4. The multi-channel high-frequency non-invasive precise positioning nerve stimulation system according to claim 1, wherein the alternating current constant current stimulation circuit adopts a chip XTR111, and a stimulus source signal output by the signal conditioning circuit is input from a sixth pin as an input signal of the chip XTR 111; a fourth pin and a fifth pin of the chip XTR111 are connected with a reference voltage; the output signals of the second pin and the third pin of the chip XTR111 are output through the gain control circuit.
5. The multi-channel high-frequency non-invasive precise positioning neurostimulation system as claimed in claim 1, wherein the signal conditioning circuit comprises a digital multiplication circuit, a pre-stage amplification circuit, a post-stage amplification circuit and a power amplification circuit, and a signal output by the high-frequency signal generating circuit passes through the digital multiplication circuit, the pre-stage amplification circuit, the post-stage amplification circuit and the power amplification circuit in sequence and is output from an output end of the power amplification circuit.
6. The multichannel high-frequency non-invasive precise positioning neurostimulation system as claimed in claim 1, wherein the isolation circuit comprises an isolation input part, a 1pF isolation capacitor and an isolation output part, the isolation input part and the isolation output part are isolated by the 1pF isolation capacitor, the isolation input part is a duty cycle modulation signal and is digitally transmitted through a potential barrier, and the isolation output part is used for receiving the modulated signal and converting the modulated signal into an analog voltage; the isolation input part comprises an amplifier and a comparator, wherein an input current and a switching current source are input to a negative end of the amplifier, the amplifier and a resistor capacitor form an integrating circuit, an output end of the integrating circuit is connected with an input end of the comparator, and the comparator and the first sensing amplifier are used for forcing the switching current source to be switched on and off; the output signal of the comparator is isolated by an isolation capacitor, and after the second induction amplifier detects the signal isolated by the isolation capacitor, the second induction amplifier drives a switch current source to enter an integrator and output by a feedback loop, wherein the feedback loop comprises a sample-and-hold amplifier, and the sample-and-hold amplifier is used for removing unnecessary ripple voltage.
7. The multi-channel high-frequency non-invasive precise positioning neurostimulation system as claimed in claim 6, wherein ADUM6000 is adopted to isolate the power supplies of the high-frequency signal generating circuit and the signal conditioning circuit from the power supplies of the alternating current constant voltage stimulation circuit and the alternating current constant current stimulation circuit.
8. The multi-channel high-frequency non-invasive precise positioning neurostimulation system as claimed in claim 1, wherein the signal switching circuit, the alternating current constant voltage stimulation circuit and the alternating current constant current stimulation circuit are vertically arranged, and the distance between adjacent wires is increased and reduced.
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