CN116236691A - Implantable stimulation system, method, computer device and storage medium - Google Patents

Abstract

The present application relates to an implantable stimulation system, characterized in that the system comprises: an extracorporeal device and an implantable device coupled; the external equipment is used for outputting a biphase resonance signal according to preset parameters; the implantable device is configured to convert the biphasic resonant signal into a biphasic stimulation signal. The method avoids the problem of charge accumulation, reduces possible tissue damage and stimulation electrode corrosion, prolongs the service life of the stimulation electrode and improves the reliability of long-term use.

Description

Implantable stimulation system, method, computer device and storage medium

technical field

The present application relates to the technical field of medical devices, in particular to an implantable stimulation system, method, computer equipment and storage medium.

Background technique

Traditional neurostimulation devices, such as implantable pulse generators (IPG for short), use wired connections to stimulate electrodes and stimulation signal sources, implant the stimulation electrodes into the body of the organism, and then insert wires to generate stimulation signals through the IPG. Common devices include brain pacemakers (DBS), peripheral nerve stimulators (VNS), etc. However, this wired technology needs to be connected to a long wire, and it may be necessary to pass through a tunnel to achieve wire insertion during implantation, which affects the complexity and comfort of the operation.

In recent years, wireless nerve stimulation equipment has gradually appeared. After receiving the signal through magnetic resonance or magnetic induction, it is converted into the actual required stimulation signal by rectification and filtering. The signal is usually a single-phase signal, which lacks the charge output in antiphase with the stimulation signal; or the antiphase signal is out of sync with the stimulation signal, resulting in charge accumulation. Long-term use may cause tissue damage, electrode surface corrosion, and electrode and biological tissue. Problems such as changes in contact impedance affect the stimulation effect.

Contents of the invention

Based on this, it is necessary to provide an implantable stimulation system, method, computer equipment and storage medium for the above technical problems, which are used to solve the problem that the stimulation signal in the prior art is a single-phase signal, which leads to charge accumulation and long-term use affects the stimulation effect. question.

In a first aspect, the present application provides an implantable stimulation system, the system comprising: a coupled external device and an implantable device;

The in vitro device is used to output a biphasic resonance signal according to preset parameters;

The implantable device is used to convert the biphasic resonance signal into a biphasic stimulation signal.

In one of the embodiments, the in vitro device includes: a power supply module, a control module and a first coupling module;

The power supply module is used to provide working voltage for the control module and the first coupling module;

The control module is configured to output a control signal according to the preset parameters, and control the power supply module to charge or discharge the first resonant coupling module, so that the first coupling module generates a two-phase resonant signal.

In one of the embodiments, the power module includes: an energy storage unit and a power manager;

The energy storage unit is used to store electric energy;

The power manager is configured to convert the stored electric energy into a working voltage suitable for the control module and the first coupling module.

In one of the embodiments, the control module includes: a processor, a drive unit and a switch assembly;

The processor is configured to output a corresponding control signal according to the preset parameter;

The driving unit is used to amplify the strength of the control signal;

The switch assembly is configured to control the power supply module to charge or discharge the first resonant coupling module according to the driven control signal.

In one of the embodiments, the control module adopts an H-bridge circuit.

In one of the embodiments, the first coupling module includes two first coupling units, each of the first coupling units includes a first capacitive component and a first coil component, and the first capacitive component and the first The coil components interact to form a first resonant circuit;

Each of the first coupling units works alternately, and couples the biphasic resonance signal to the implantable device through the first resonance circuit.

In one of the embodiments, the first coil component includes a plurality of coils, and two adjacent coils partially overlap each other.

In one of the embodiments, the implantable device includes: a second coupling module and a signal demodulation output module;

The second coupling module is configured to receive the two-phase resonance signal;

The signal demodulation output module is used to convert the biphasic resonance signal into a biphasic stimulation signal.

In one of the embodiments, the second coupling module includes a second coil and a second capacitive component, the second coil and the second capacitive component interact to form a second resonant circuit, and the second coupling module passes The second resonant circuit receives the biphase resonant signal.

In one of the embodiments, the signal demodulation output module includes a voltage limiting unit and a filtering unit;

The voltage limiting unit is used to convert the high frequency signal of the biphase resonance signal into a low frequency signal;

The filtering unit is configured to process the biphasic resonance signal converted into a low-frequency signal, and output a biphasic stimulation signal.

In the second aspect, the present application also provides an implantable stimulation method, which adopts the implantable stimulation system described in any one of the first aspects, and realizes the following method steps:

The in vitro device outputs a biphasic resonance signal according to preset parameters, and couples and transmits it to the implantable device;

The implantable device converts the biphasic resonance signal into a biphasic stimulation signal, and outputs it to the nerves of the target object through stimulating electrodes.

In one embodiment, the method also includes:

During the stimulation process, according to the feedback parameters of the stimulation site, the number of pulses of the biphasic resonance signal is adjusted to adjust the width of the biphasic stimulation signal; and/or, the pulse amplitude of the biphasic resonance signal is adjusted to Adjust the amplitude of the biphasic stimulation signal.

In a third aspect, the present application also provides a computer device. The computer device includes a memory and a processor, the memory stores a computer program, and the processor implements the method steps disclosed in any one of the second aspect when executing the computer program.

In a fourth aspect, the present application also provides a computer-readable storage medium. The computer-readable storage medium has a computer program stored thereon, and when the computer program is executed by a processor, the method steps disclosed in any one of the second aspect are implemented.

The above-mentioned implantable stimulation system, method, computer equipment and storage medium have at least the following advantages:

The in vitro device of the present application can generate a biphasic resonance signal according to preset parameters, and transmit it to the implantable device through a wireless transmission link. The implantable device generates a biphasic stimulation signal according to the biphasic resonance signal, and outputs it through the stimulating electrode to the nerves of the target subject. This application avoids the problem of charge accumulation, reduces possible tissue damage and stimulation electrode corrosion, prolongs the life of the stimulation electrode, and improves the reliability of long-term use.

Description of drawings

The accompanying drawings constituting a part of this application are used to provide further understanding of the present invention, and the schematic embodiments and descriptions of the present invention are used to explain the present invention, and do not constitute an improper limitation of the present invention.

In order to more clearly illustrate the technical solutions in the embodiments of the present invention, the drawings that need to be used in the description of the embodiments will be briefly introduced below. Obviously, the drawings in the following description are only some embodiments of the present invention. For those skilled in the art, other drawings can also be obtained based on these drawings without creative effort.

Fig. 1 is a structural block diagram of an implantable stimulation system in an embodiment;

Fig. 2 is a structural block diagram of an in vitro device in an embodiment;

Fig. 3 is a structural block diagram of an in vitro device in another embodiment;

Fig. 4 is a schematic diagram of wiring of two first coupling units in one embodiment;

Fig. 5 is a schematic structural diagram of a first coil assembly in an embodiment;

6 is a schematic diagram of the junction of the first coil assembly in another embodiment;

Fig. 7 is a schematic structural diagram of a control module in an embodiment;

Fig. 8 is a schematic structural diagram of a control module and a schematic diagram of a current flow in another embodiment;

Fig. 9 is a timing diagram of the positive phase signal of the control module in one embodiment;

Figure 10 is a structural block diagram of an implantable device in an embodiment;

Fig. 11 is a structural block diagram of an implantable device in another embodiment;

Fig. 12 is a schematic diagram of wiring of an implantable device in an embodiment;

Fig. 13 is a schematic structural diagram of a control module and another schematic diagram of current flow in another embodiment;

FIG. 14 is a timing diagram of an inversion signal of a control module in an embodiment;

Fig. 15 is a positive half segment waveform diagram of the input and output of the implantable device in one embodiment;

Figure 16 is a negative half segment waveform diagram of the input and output of the implantable device in one embodiment;

Figure 17 is a waveform diagram of the output of the implantable device in one embodiment;

Fig. 18 is a waveform diagram output by an implantable device in another embodiment;

Fig. 19 is a waveform diagram output by an implantable device in another embodiment;

Figure 20 is a schematic flow chart of an implantable stimulation method in one embodiment;

Figure 21 is a diagram of the internal structure of a computer device in one embodiment.

Detailed ways

Embodiments of the present invention are described below through specific examples, and those skilled in the art can easily understand other advantages and effects of the present invention from the content disclosed in this specification. The present invention can also be implemented or applied through other different specific implementation modes, and various modifications or changes can be made to the details in this specification based on different viewpoints and applications without departing from the spirit of the present invention. It should be noted that, in the case of no conflict, the following embodiments and features in the embodiments can be combined with each other.

While a few exemplary embodiments of the invention have been described for purposes of illustration, it is to be understood that the invention may be practiced otherwise than specifically shown in the drawings.

Please refer to Figure 1. In a feasible embodiment, the embodiment of the present application provides an implantable stimulation system, including: extracorporeal equipment and implantable equipment, and the extracorporeal equipment and implantable equipment can be coupled to realize wireless Energy transfer and data transfer.

An in vitro device for outputting biphasic resonance signals according to preset parameters.

An implantable device for converting biphasic resonance signals into biphasic stimulation signals.

Specifically, the preset parameters include information such as the amplitude, frequency, and number of pulses of the output signal, which can be preset according to the physical condition of the target object, so that the external device can output a biphasic resonance signal of appropriate strength, and then the implantable The device outputs the corresponding biphasic stimulation signal to the target subject for treatment, and in the process of treatment, the preset parameters are adjusted accordingly according to the development of the target subject's condition, and then the intensity of the stimulation signal is adjusted to achieve better results. stimulating effect.

In the above-mentioned implantable stimulation system, the external device can generate a biphasic resonance signal according to preset parameters, and transmit it to the implantable device through a wireless transmission link, and the implantable device generates a biphasic stimulation signal according to the biphasic resonance signal, and Nerves output to the target subject through stimulation electrodes. This application avoids the problem of charge accumulation, reduces possible tissue damage and stimulation electrode corrosion, prolongs the life of the stimulation electrode, and improves the reliability of long-term use.

Please refer to FIG. 2 , in a feasible embodiment, the in vitro device includes: a power supply module, a control module and a first coupling module.

The power supply module is used to provide the electrical energy required for the implantable stimulation system to work. Specifically, the power supply module provides working voltage for the control module and the first coupling module, and can generate single or multiple stable DC power supplies as required. After the control module is powered on, it outputs a control signal according to preset parameters, and controls the power supply module to charge or discharge the first resonant coupling module, so that the first coupling module generates a biphase resonant signal, which is coupled and transmitted to the implanted device.

Referring to Fig. 3, optionally, the power module includes: an energy storage unit and a power manager.

An energy storage unit for storing electrical energy. Exemplarily, the energy storage unit may adopt a single-cell battery, a multi-cell battery pack, or an energy storage element such as a supercapacitor.

A power manager for converting the stored electrical energy into an operating voltage suitable for the control module and the first coupling module. Exemplarily, the power manager may employ a low dropout linear converter (LDO), a direct current-direct current converter (DC-DC), or a combination of both. Further, by adjusting the component parameters of the power manager, the output voltage value of the power manager can be adjusted to adapt to various usage scenarios.

Referring to Fig. 3, optionally, the control module includes: a processor, a drive unit and a switch assembly.

The processor is configured to output corresponding control signals according to preset parameters. It should be understood that the control signal is a waveform signal with a specific duty ratio, and the duty ratio is associated with preset parameters, and is used to control the charging time or discharging time of the first coupling module. Exemplarily, the processor can be a microcontroller (MCU), a field programmable gate array (FPGA), a complex programmable logic device (CPLD), a digital signal processor (DSP), an application specific integrated circuit (ASIC) or other devices with the above functions.

The driving unit is used to increase the strength of the amplified control signal and improve the driving capability of the output terminal of the processor. Exemplarily, the driving unit may adopt an operational amplifier, a diode or an integrated chip capable of outputting a large current.

The switch assembly is used to switch on or off the loop between the power supply module and the first resonant module according to the driven control signal, so as to control the power supply module to charge or discharge the first resonant coupling module. Exemplarily, the control module may be an analog switch array composed of discrete devices such as Metal Field Effect Transistors (MOSFETs) or Triodes (BJTs), or may be an integrated analog switch chip.

Furthermore, in practical applications, the switch array can also cooperate with devices such as multiplexers and inverters to reduce the number of output pins required by the processor.

Referring to FIG. 3, optionally, the first coupling module includes two first coupling units, and each first coupling unit includes a first capacitive component and a first coil component, wherein the first capacitive component and the first coil component interact form the first resonant circuit. Each first coupling unit works alternately, generates a changing electromagnetic field with a specific frequency through the first resonance circuit, and couples the biphasic resonance signal to the implanted device in a wireless manner. Exemplarily, the first coil component adopts a planar helical antenna, the shape may be circular, square, etc., and the number may be one or more. The first capacitor component and the first coil component may be connected in series or in parallel to form a first resonance circuit, and the number of the first capacitor component and the first coil component may be one or more.

Please refer to FIG. 4. Optionally, the capacitor constituting the first capacitor component can be a fixed-capacitance capacitor, or a variable capacitor, or a combination of the two, and the adjustment of the variable capacitor includes but is not limited to mechanical adjustment or Voltage control regulation. Different first coupling units may share resonant capacitors, and different coils may be selected through switches to form different resonant circuits. For example, as shown in FIG. 4, L1 is a first coil assembly, L2 is another first coil assembly, and capacitor C1 and variable capacitor Cx form the first capacitor assembly. When switch S1 is turned on and switch S2 is turned off, L1 , C1 and Cx form a resonant circuit; when the switch S1 is turned off and the switch S2 is turned on, L1, C1 and Cx form another resonant circuit, thereby achieving multiplexing of the resonant capacitor.

Referring to FIG. 5 , when the first coil assembly includes multiple coils, an induced magnetic field with opposite directions will be generated between two adjacent coils, resulting in opposite directions of induced currents on the two coils, thereby canceling the output signal. In view of this, the present application partially overlaps two adjacent coils, so that the induced magnetic fields in one of the coils cancel each other out, so that no induced current is generated on the coil.

Referring to FIG. 6 , optionally, the number of coils included in the first coil assembly may be 2N, where N represents a natural number. Divide 2N coils into odd groups and even groups, two groups of coils work alternately, and all coils in each group of coils work together. Multiple coils are distributed at different angles in space, which can reduce the decrease in coupling efficiency of the receiving coil due to center offset; when the first coil assembly is fixed on the body surface of the target object, it will produce a certain degree of deformation, resulting in the axial displacement of each coil. Differently, the above arrangement can also reduce the drop in coupling efficiency caused by the axial offset of the receiving coil. Moreover, the multiple coils partially overlap each other, which also cancels the induced magnetic field generated when other coils are working.

Exemplarily, the control module adopts an H-bridge circuit.

Please refer to Figure 7. Figure 7 shows a schematic structural diagram of the control module. The following takes the control module using the H-bridge circuit in Figure 7 as an example to describe the working principle of the in vitro device in detail:

The switch assembly among Fig. 7 comprises switch SW1, switch SW2, switch SW3, switch SW4, switch SPDT1, switch SPDT2, wherein, switch SW1-SW4 is single-throw switch, switch SPDT1-SPDT2 is double-throw switch, above-mentioned single-throw switch or A double-throw switch only indicates its switching characteristics. In actual use, it can be composed of one or more analog devices or digital devices with switching characteristics.

For convenience of description, another first coupling unit is marked as a second coupling unit in FIG. 7 .

The processor of the control module is used to output a control signal, which is amplified by the drive unit to control the switch on or off.

First enter the normal phase launch phase:

The switch SPDT1 and the switch SPDT2 enable the first coupling unit, and at the same time, the switch SW2 and the switch SW3 are turned on, and the switch SW1 and the switch SW4 are turned off, and the current flows along the direction of the power module, the switch SW1, the first coupling unit, and the switch SW4. The direction is positive.

After a period of time T, the first coupling unit is continued to be disabled through the switch SPDT1 and the switch SPDT2, and the first coupling unit starts to emit a resonance signal, which is recorded as a positive phase. At the same time, the second coupling unit is enabled through the switch SPDT1 and the switch SPDT2, the switch SW2 and the switch SW3 are opened, the switch SW1 and the switch SW4 are closed, and the current still passes through the second coupling unit in the same direction as above.

After a period of time T, the second coupling unit is disabled through the switch SPDT1 and the switch SPDT2, and the second coupling unit starts to transmit the resonant signal. Since the initial current direction is the same, the transmitted signal is still in positive phase at this time. If the normal-phase emission is not over, repeat the above steps, open the switch SW2 and the switch SW3, close the switch SW1 and the switch SW4, and the current still passes through the first coupling unit or the second coupling unit along the aforementioned forward direction.

If the positive launch phase is over, enter the negative launch phase:

The switch SPDT1 and the switch SPDT2 enable the first coupling unit, at the same time the switch SW1 and the switch SW4 are opened, the switch SW2 and the switch SW3 are closed, and the current flows along the direction of the power module, the switch SW2, the first coupling unit, and the switch SW3, which is the same as the normal-phase emission Phases are reversed, denoted as reverse.

After a period of time T, the first coupling unit is then disabled through the switch SPDT1 and the switch SPDT2, and the first coupling unit starts to emit a resonance signal, which is recorded as an inverse phase. At the same time, the second coupling unit is enabled through the switch SPDT1 and the switch SPDT2, the switch SW1 and the switch SW4 are opened, the switch SW2 and the switch SW3 are closed, and the current still passes through the second coupling unit in the reverse direction.

After a period of time T, the second coupling unit is disabled through the switch SPDT1 and the switch SPDT2, and the second coupling unit starts to transmit the resonant signal. Since the initial current direction is the same, the transmitted signal is still out of phase at this time. If the anti-phase emission is not finished, repeat the above steps, open the switch SW1 and the switch SW4, close the switch SW2 and the switch SW3, and the current still passes through the first coupling unit or the second coupling unit along the aforementioned reverse direction.

Please refer to FIG. 8 . FIG. 8 is a schematic diagram of a current flow of the control module. Exemplarily, the control module adopts an H-bridge circuit composed of multiple transistors (MOSFETs).

Among them, the inductor L1 and the capacitor C1 form the first coupling unit, the inductor L2 and the capacitor C2 form the second coupling unit; a transistor and a diode form a single-throw switch loop, such as a transistor Q1 and a diode D1, and the four single-throw switch loops are in Topologically located in four quadrants; PG1-PG8 are the high and low level control signals output by the processor through the drive unit, and the control signals correspond to the transistors one by one.

Please refer to Figure 9. In the t1 phase, PG1 and PG3 are at high level, and PG2 and PG4 are at low level, so transistor Q1 and transistor Q4 are turned off, transistor Q2 and transistor Q3 are turned on, and the power module charges the first coupling unit, and the current The direction is shown by the dotted arrow in Fig. 8; PG5 and PG6 are at high level, PG7 and PG8 are at low level, transistors Q5-Q8 are all turned off, and the second coupling unit does not work. At this time, the signal voltages U _TX1 and U _TX2 on the coil L1 and the coil L2 are both low level.

In the t2 stage, PG1 and PG2 are at high level, and PG3 and PG4 are at low level, so transistors Q1~Q4 are closed, and the first coupling unit starts to generate a resonance signal, and its voltage waveform UTX1 is the positive half of the sine wave; PG5 and PG7 is high level, PG6 and PG8 are low level, transistor Q5 and transistor Q8 are turned off, transistor Q6 and transistor Q7 are turned on, the power module charges the second coupling unit, the current direction is shown by the dotted arrow in Figure 8, and the coil L2 The signal voltage on UTX2 is low level.

In the t3 stage, PG1 and PG3 are at high level, and PG2 and PG4 are at low level, so transistor Q1 and transistor Q4 are turned off, transistor Q2 and transistor Q3 are turned on, and the power module charges the first coupling unit, and the current direction is shown in Figure 8 As shown by the dotted arrow, the signal voltage UTX1 on the coil L1 is at low level; PG5 and PG6 are at high level, PG7 and PG8 are at low level, transistors Q5~Q8 are all turned off, and the second coupling unit starts to generate a resonance signal. Its voltage waveform UTX2 is the positive half of the sine wave.

In the t4 stage, same as the t2 stage, a resonant signal is generated on the coil L1, and the coil L2 starts charging, and the waveforms of U _TX1 and U _TX2 are shown in FIG. 9 .

The resonance signals generated by the two first coupling units of the first coupling module appear alternately and are always the positive half of the sine wave, so the signal received by the implantable device is a continuous positive half of the sine wave, and its voltage waveform U _RX is as follows Figure 9 shows.

Referring to FIG. 10 , optionally, the implantable device includes: a second coupling module and a signal demodulation output module.

The second coupling module is configured to receive the biphase resonance signal output by the first coupling module.

The signal demodulation output module is used to convert the biphasic resonance signal into a biphasic stimulation signal, and transform the space electromagnetic wave signal acquired through coupling into a final output stimulation waveform signal. Exemplarily, the signal demodulation output module adopts a low-pass filter circuit.

Please refer to FIG. 11. Optionally, the second coupling module includes a second coil and a second capacitive component. The second coil and the second capacitive component interact to form a second resonant circuit. The second coupling module receives the dual coil through the second resonant circuit. phase resonance signal. The second coupling module can receive the changing electromagnetic field of a specific frequency through the principle of resonance, and generate an induced electrical signal. The second coil of the second coupling module may be a planar helical antenna or a wire-wound inductor, the shape may be circular, square or other, and the number may be one or more. The second capacitor component and the second coil can be connected in series or in parallel to form a second resonant circuit, and the number of the second capacitor component and the second coil can be one or more. Exemplarily, the capacitor constituting the second capacitor component may be a fixed-value capacitor, or a variable capacitor, or a combination of both, and the adjustment of the variable capacitor includes but not limited to mechanical adjustment or voltage control adjustment.

Optionally, the signal demodulation output module includes a voltage limiting unit and a filtering unit.

The voltage limiting unit is used to limit the amplitude of the biphase resonance signal. Exemplarily, the voltage limiting unit uses a Zener diode to limit excessive voltage stimulation.

The filter unit is used to convert the high-frequency signal of the biphasic resonance signal into a low-frequency signal, and output a biphasic stimulation signal. Exemplarily, the filtering unit adopts a low-pass circuit, which may be composed of a capacitor alone, or may be composed of a cascaded capacitor and a resistor to form a filtering network.

Please refer to Fig. 12. Fig. 12 is a schematic wiring diagram of an implantable device, in which the coil L3 and the capacitor C3 constitute the second coupling module to receive the biphase resonance signal output by the first coupling module; the Zener diode D10 is a voltage limiting Unit, select the type of diode according to the needs, so as to limit the voltage within an appropriate range; capacitor C4 is a filter unit, which filters the voltage at both ends of the Zener diode D10 to make the voltage of the input electrode more stable.

Please refer to FIG. 13 . FIG. 13 shows another schematic diagram of the current flow direction of the control module. Its structure is the same as that in FIG. 8 , only the current flow direction is different.

Please refer to Figure 14. In the t6 stage, PG1 and PG3 are at low level, and PG2 and PG4 are at high level, so transistor Q1 and transistor Q4 are turned on, transistor Q2 and transistor Q3 are turned off, and the power module charges the first coupling unit, and the current The direction is shown by the dotted arrow in Fig. 13; PG5 and PG6 are at high level, PG7 and PG8 are at low level, transistors Q5-Q8 are all turned off, and the second coupling unit does not work. At this time, the signal voltages U _TX1 and U _TX2 on the coil L1 and the coil L2 are both low level.

In the t7 stage, PG1 and PG2 are at high level, and PG3 and PG4 are at low level, so transistors Q1~Q4 are turned off, and the first coupling unit starts to generate a resonance signal, because the initial current direction is opposite to the current direction in Figure 8, so a The polarity of the voltage waveform is also opposite, which is the negative half of the sine wave; PG5 and PG7 are at low level, PG6 and PG8 are at high level, transistor Q5 and transistor Q8 are turned on, transistor Q6 and transistor Q7 are turned off, and the power module gives the second The coupling unit is charged, and the current direction is shown by the dotted arrow in FIG. 13 , and the signal voltage U _TX2 on the coil L2 is at a low level.

In the t8 stage, PG1 and PG3 are low level, PG2 and PG4 are high level, so transistor Q1 and transistor Q4 are turned on, transistor Q2 and transistor Q3 are turned off, the power module charges the first coupling unit, and the current direction is shown in Figure 13 As shown by the dashed arrow, the signal voltage U _TX1 on the coil L1 is at low level; PG5 and PG6 are at high level, PG7 and PG8 are at low level, transistors Q5~Q8 are all turned off, and the second coupling unit starts to generate a resonance signal , because the direction of the initial current is opposite to that in Figure 8, the polarity of the generated voltage waveform is also opposite, which is the negative half of the sine wave.

In the t9 stage, same as the t7 stage, a resonant signal is generated on the coil L1, and the coil L2 starts charging, and the waveforms of U _TX1 and U _TX2 are shown in FIG. 14 .

The resonance signals generated by the two first coupling units of the first coupling module appear alternately, and are always the negative half of the sine wave, so the signal received by the implantable device is a continuous negative half of the sine wave, and its voltage waveform U _RX is as follows Figure 14 shows.

Please refer to Figure 15 and Figure 16. Figure 15 shows the waveform diagram of the positive half sine wave received by the implantable device. The desired positive half low-frequency stimulation signal. Figure 16 shows the waveform diagram of the negative half of the sine wave received by the implantable device. After the waveform is processed by the signal demodulation output module, the high-frequency components are filtered out and become the actual negative half of the low-frequency stimulation signal. .

Please refer to Figure 17, it can be seen that by controlling the timing of the output of the in vitro device, the final stimulation signal can present a positive and negative biphasic, which reduces the stimulation to the biological tissue and reduces the corrosion of the electrode. Since the positive-phase signal generates an action potential and induces a stimulating effect, and the anti-phase signal is used to eliminate the accumulated charge, for example, in order to prevent the anti-phase signal from hindering the stimulation action, it is also possible to generate a delay by controlling the interval between the positive and negative phases. biphasic balanced signal. It should be understood that the interval time may be adjusted according to the actual situation of the target object.

Exemplarily, the treatment process of the target object can also be monitored, and the width and amplitude of the stimulation signal can be controlled according to the feedback parameters of the stimulation site, so that the total areas of the anti-phase signal and the normal-phase signal are equal or close to each other, so that the stimulation signal appears biphasic Charge balance slow inversion or biphasic charge balance fast inversion. Alternatively, by controlling the width and amplitude of the stimulation signal, the total area of the anti-phase signal is not equal to that of the normal-phase signal, so that the final stimulation signal appears as biphasic charge imbalance and anti-phase. Wherein, the feedback parameter includes at least one of perception threshold, action potential, biological tissue tolerance and electrode corrosion.

Optionally, the width of the biphasic stimulation signal can be adjusted by changing the number of pulses generated by the in vitro device. Taking the high-frequency pulse output frequency f=1MHz of the external equipment as an example, its forward pulse width W=(1/f)/2=0.5us; if it is expected to generate a stimulation signal with a width of 100us, the external equipment needs to generate at least 100/f 0.5 = 200 pulses.

The amplitude of the biphasic stimulation signal is positively correlated with the amplitude of the resonant signal of the external device, so the amplitude of the stimulating signal can be adjusted by changing the amplitude of the resonant signal output by the external device. The amplitude of the resonant signal of the in vitro device can be adjusted by changing the power supply voltage or charging time. Furthermore, changing the charging voltage can be realized by changing the output of the power module; changing the charging time can be realized by changing the turn-on time of the switch array.

Please refer to Figure 18. By changing the width and amplitude of the anti-phase signal, an anti-phase signal with low amplitude, large width, and a total area equal to or close to that of the normal-phase signal can be obtained. The final stimulation signal appears as a biphasic charge balance and slow anti-phase .

Please refer to Figure 19, change the width and amplitude of the anti-phase signal, so that the amplitude gradually decreases, and keep the total area equal to or close to that of the normal-phase signal, and finally the stimulation signal presents a biphasic charge balance and rapid anti-phase.

In the above embodiments, the feedback parameters of the stimulation site are obtained by monitoring the treatment process of the target object, and the width and amplitude of the stimulation signal are controlled according to the feedback parameters, so as to precisely stimulate the target object. Each module in the above-mentioned implantable stimulation system can be fully or partially realized by software, hardware and a combination thereof. The above-mentioned modules can be embedded in or independent of the processor in the computer device in the form of hardware, and can also be stored in the memory of the computer device in the form of software, so that the processor can invoke and execute the corresponding operations of the above-mentioned modules.

Based on the same inventive concept, the embodiment of the present application also provides an implantable stimulation method for realizing the above mentioned implantable stimulation system. The solution to the problem provided by this method is similar to the implementation described in the above method, so the specific limitations in one or more embodiments of the implantable stimulation system provided below can be referred to above for implantable stimulation The limitation of the method will not be repeated here.

Please refer to Figure 20. In a feasible embodiment, the embodiment of the present application provides an implantable stimulation method, including:

In step S2002, the in vitro device outputs a biphasic resonance signal according to preset parameters, and couples and transmits it to the implantable device.

In step S2004, the implantable device converts the biphasic resonance signal into a biphasic stimulation signal, and outputs it to the nerve of the target subject through the stimulating electrodes.

Specifically, the extracorporeal device includes: a power supply module, a control module and a first coupling module.

The power module provides the electrical energy required for the implantable stimulation system, including: energy storage unit and power manager. The energy storage unit is used for storing electric energy; the power manager is used for converting the stored electric energy into a working voltage suitable for the control module and the first coupling module.

Optionally, the control module includes: a processor, a drive unit and a switch assembly.

The processor is used to output the corresponding control signal according to the preset parameters; the driving unit is used to increase the strength of the amplified control signal and improve the driving capability of the output terminal of the processor; the switch component is used to switch on or off according to the driven control signal. Closing the loop between the power module and the first resonant module, so as to control the power module to charge or discharge the first resonant coupling module.

The first coupling module includes two first coupling units, and each first coupling unit includes a first capacitor component and a first coil component, wherein the first capacitor component and the first coil component interact to form a first resonant circuit. Each first coupling unit works alternately, generates a changing electromagnetic field with a specific frequency through the first resonance circuit, and couples the biphasic resonance signal to the implanted device in a wireless manner.

The implantable device includes: a second coupling module and a signal demodulation output module.

The second coupling module is used to receive the two-phase resonance signal output by the first coupling module, including a second coil and a second capacitor component, the second coil and the second capacitor component interact to form a second resonance circuit, and the second coupling module passes through The second resonance circuit receives the biphase resonance signal.

The signal demodulation output module is used to convert the biphasic resonance signal into a biphasic stimulation signal, and convert the space electromagnetic wave signal obtained through coupling into a final output stimulation waveform signal.

Optionally, the signal demodulation output module includes a voltage limiting unit and a filtering unit.

The voltage limiting unit is used to limit the amplitude of the biphase resonance signal.

The filter unit is used to convert the high-frequency signal of the biphasic resonance signal into a low-frequency signal, and output a biphasic stimulation signal.

In the above implantable stimulation method, the in vitro device can generate a biphasic resonance signal according to preset parameters, and transmit it to the implantable device through a wireless transmission link, and the implantable device generates a biphasic stimulation signal according to the biphasic resonance signal, and Nerves output to the target subject through stimulation electrodes. This application avoids the problem of charge accumulation, reduces possible tissue damage and stimulation electrode corrosion, prolongs the life of the stimulation electrode, and improves the reliability of long-term use.

In a feasible embodiment, the implantable stimulation method of the embodiment of the present application further includes:

During the stimulation process, according to the feedback parameters of the stimulation site, the number of pulses of the biphasic resonance signal is adjusted to adjust the width of the biphasic stimulation signal; and/or, the pulse amplitude of the biphasic resonance signal is adjusted to adjust the biphasic stimulation signal signal amplitude. Wherein, the feedback parameter includes at least one of perception threshold, action potential, biological tissue tolerance and electrode corrosion.

Optionally, the way to adjust the width of the biphasic stimulation signal includes: changing the number of pulses generated by the external device.

Optionally, the manner of adjusting the amplitude of the biphasic stimulation signal includes: changing the amplitude of the resonance signal output by the external device. Further, the amplitude of the resonant signal of the in vitro device can be adjusted by changing the power supply voltage or the charging time. Changing the charging voltage can be realized by changing the output of the power module; changing the charging time can be realized by changing the turn-on time of the switch array.

In the above implantable stimulation method, the in vitro device can generate a biphasic resonance signal according to preset parameters, and transmit it to the implantable device through a wireless transmission link, and the implantable device generates a biphasic stimulation signal according to the biphasic resonance signal, and Nerves output to the target subject through stimulation electrodes. This application avoids the problem of charge accumulation, reduces possible tissue damage and stimulation electrode corrosion, prolongs the life of the stimulation electrode, and improves the reliability of long-term use. At the same time, during the stimulation process, by monitoring the treatment process of the target object, the feedback parameters of the stimulation site are obtained, and the width and amplitude of the stimulation signal are controlled according to the feedback parameters, so as to accurately stimulate the target object.

It should be understood that although the steps in the flow charts involved in the above embodiments are shown sequentially according to the arrows, these steps are not necessarily executed sequentially in the order indicated by the arrows. Unless otherwise specified herein, there is no strict order restriction on the execution of these steps, and these steps can be executed in other orders. Moreover, at least some of the steps in the flow charts involved in the above-mentioned embodiments may include multiple steps or stages, and these steps or stages are not necessarily executed at the same time, but may be performed at different times For execution, the execution order of these steps or stages is not necessarily performed sequentially, but may be executed in turn or alternately with other steps or at least a part of steps or stages in other steps.

In a feasible embodiment, a computer device is provided. The computer device may be a terminal, and its internal structure may be as shown in FIG. 21 . The computer device includes a processor, a memory, an input/output interface, a communication interface, a display unit and an input device. Wherein, the processor, the memory and the input/output interface are connected through the system bus, and the communication interface, the display unit and the input device are connected to the system bus through the input/output interface. Wherein, the processor of the computer device is used to provide calculation and control capabilities. The memory of the computer device includes a non-volatile storage medium and an internal memory. The non-volatile storage medium stores an operating system and computer programs. The internal memory provides an environment for the operation of the operating system and computer programs in the non-volatile storage medium. The input/output interface of the computer device is used for exchanging information between the processor and external devices. The communication interface of the computer device is used to communicate with an external terminal in a wired or wireless manner, and the wireless manner can be realized through WIFI, mobile cellular network, NFC (Near Field Communication) or other technologies. When the computer program is executed by the processor, an implantable stimulation method is realized. The display unit of the computer equipment is used to form a visually visible picture, which may be a display screen, a projection device or a virtual reality imaging device. The display screen may be a liquid crystal display screen or an electronic ink display screen, and the input device of the computer device may be a touch layer covered on the display screen, or a button, a trackball or a touch pad set on the casing of the computer device, or a External keyboard, touchpad or mouse etc.

Those skilled in the art can understand that the structure shown in Figure 21 is only a block diagram of a partial structure related to the solution of this application, and does not constitute a limitation to the computer equipment on which the solution of this application is applied. The specific computer equipment can be More or fewer components than shown in the figures may be included, or some components may be combined, or have a different arrangement of components.

In a feasible embodiment, a computer device is provided, including a memory and a processor, where a computer program is stored in the memory, and the processor implements the method steps in the above-mentioned implantable stimulation method when executing the computer program.

In a feasible embodiment, a computer-readable storage medium is provided, on which a computer program is stored, and when the computer program is executed by a processor, the method steps in the above implantable stimulation method are implemented.

In a feasible embodiment, a computer program product is provided, including a computer program, and when the computer program is executed by a processor, the method steps in the above implantable stimulation method are implemented.

It should be noted that the user information (including but not limited to user equipment information, user personal information, etc.) and data (including but not limited to data used for analysis, stored data, displayed data, etc.) involved in this application are all It is information and data authorized by the user or fully authorized by all parties, and the collection, use and processing of relevant data need to comply with relevant laws, regulations and standards of relevant countries and regions.

Those of ordinary skill in the art can understand that all or part of the processes in the methods of the above-mentioned embodiments can be completed by instructing related hardware through computer programs, and the computer programs can be stored in a non-volatile computer-readable memory In the medium, when the computer program is executed, it may include the processes of the embodiments of the above-mentioned methods. Wherein, any reference to storage, database or other media used in the various embodiments provided in the present application may include at least one of non-volatile and volatile storage. Non-volatile memory can include read-only memory (Read-Only Memory, ROM), magnetic tape, floppy disk, flash memory, optical memory, high-density embedded non-volatile memory, resistive variable memory (ReRAM), magnetic variable memory (Magnetoresistive Random Access Memory, MRAM), Ferroelectric Random Access Memory (FRAM), Phase Change Memory (Phase Change Memory, PCM), graphene memory, etc. The volatile memory may include random access memory (Random Access Memory, RAM) or external cache memory. As an illustration and not a limitation, RAM can be in various forms, such as Static Random Access Memory (SRAM) or Dynamic Random Access Memory (Dynamic Random Access Memory, DRAM). The databases involved in the various embodiments provided in this application may include at least one of a relational database and a non-relational database. The non-relational database may include a blockchain-based distributed database, etc., but is not limited thereto. The processors involved in the various embodiments provided by this application can be general-purpose processors, central processing units, graphics processors, digital signal processors, programmable logic devices, data processing logic devices based on quantum computing, etc., and are not limited to this.

The technical features of the above embodiments can be combined arbitrarily. To make the description concise, all possible combinations of the technical features in the above embodiments are not described. However, as long as there is no contradiction in the combination of these technical features, they should be It is considered to be within the range described in this specification.

The above-mentioned embodiments only express several implementation modes of the present application, and the description thereof is relatively specific and detailed, but should not be construed as limiting the patent scope of the present application. It should be noted that those skilled in the art can make several modifications and improvements without departing from the concept of the present application, and these all belong to the protection scope of the present application. Therefore, the protection scope of the present application should be determined by the appended claims.

Claims (14)

1. An implantable stimulation system, the system comprising: an extracorporeal device and an implantable device coupled;

the external equipment is used for outputting a biphase resonance signal according to preset parameters;

the implantable device is configured to convert the biphasic resonant signal into a biphasic stimulation signal.

2. The system of claim 1, wherein the extracorporeal device comprises: the device comprises a power supply module, a control module and a first coupling module;

The power supply module is used for providing working voltage for the control module and the first coupling module;

and the control module is used for outputting a control signal according to the preset parameter and controlling the power supply module to charge or discharge the first resonant coupling module so as to enable the first coupling module to generate a biphase resonant signal.

3. The system of claim 2, wherein the power module comprises: an energy storage unit and a power manager;

the energy storage unit is used for storing electric energy;

the power manager is configured to convert the stored electrical energy into an operating voltage suitable for the control module and the first coupling module.

4. The system of claim 2, wherein the control module comprises: a processor, a drive unit and a switch assembly;

the processor is used for outputting a corresponding control signal according to the preset parameter;

the driving unit is used for amplifying the intensity of the control signal;

and the switch assembly is used for controlling the power supply module to charge or discharge the first resonant coupling module according to the driven control signal.

5. The system of claim 4, wherein the control module employs an H-bridge circuit.

6. The system of claim 2, wherein the first coupling module comprises two first coupling units, each of the first coupling units comprising a first capacitive component and a first coil component, the first capacitive component and the first coil component interacting to form a first resonant tank;

each of the first coupling units alternately operates to couple a dual-phase resonant signal to the implantable device through the first resonant tank.

7. The system of claim 6, wherein the first coil assembly comprises a plurality of coils, adjacent two of the coils partially overlapping.

8. The system of claim 1, wherein the implantable device comprises: the second coupling module and the signal demodulation output module;

the second coupling module is used for receiving the biphase resonance signal;

the signal demodulation output module is used for converting the biphase resonance signal into a biphase stimulation signal.

9. The system of claim 8, wherein the second coupling module comprises a second coil and a second capacitive component that interact to form a second resonant tank through which the second coupling module receives the two-phase resonant signal.

10. The system of claim 8, wherein the signal demodulation output module comprises a voltage limiting unit and a filtering unit;

the voltage limiting unit is used for limiting the amplitude of the biphase resonance signal;

the filtering unit is used for converting the high-frequency signal of the biphase resonance signal into a low-frequency signal and outputting a biphase stimulation signal.

11. An implantable stimulation method characterized in that the following method steps are implemented with an implantable stimulation system according to any one of claims 1-10:

the external equipment outputs a biphase resonance signal according to preset parameters and is coupled and transmitted to the implanted equipment;

the implantable device converts the biphasic resonance signal into a biphasic stimulation signal and outputs the biphasic stimulation signal to a nerve of a target object through a stimulation electrode.

12. The method as recited in claim 11, further comprising:

in the stimulation process, the pulse number of the biphase resonance signal is adjusted according to the feedback parameters of the stimulation part so as to adjust the width of the biphase stimulation signal; and/or adjusting the pulse amplitude of the biphasic resonance signal to adjust the amplitude of the biphasic stimulation signal.

13. A computer device comprising a memory and a processor, the memory storing a computer program, characterized in that the processor implements the steps of the method of any of claims 11 to 12 when the computer program is executed.

14. A computer readable storage medium, on which a computer program is stored, characterized in that the computer program, when being executed by a processor, implements the steps of the method of any of claims 11 to 12.

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