CN116726393A - Charge balance system - Google Patents
Charge balance system Download PDFInfo
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- CN116726393A CN116726393A CN202311016747.1A CN202311016747A CN116726393A CN 116726393 A CN116726393 A CN 116726393A CN 202311016747 A CN202311016747 A CN 202311016747A CN 116726393 A CN116726393 A CN 116726393A
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- storage capacitor
- energy storage
- charge balance
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- 239000003990 capacitor Substances 0.000 claims abstract description 119
- 238000004146 energy storage Methods 0.000 claims abstract description 50
- 230000004936 stimulating effect Effects 0.000 claims abstract description 6
- 230000000638 stimulation Effects 0.000 claims description 30
- 230000000630 rising effect Effects 0.000 claims description 6
- 230000000694 effects Effects 0.000 abstract description 20
- 210000005036 nerve Anatomy 0.000 abstract description 4
- 230000008901 benefit Effects 0.000 description 4
- 230000003111 delayed effect Effects 0.000 description 2
- 238000013461 design Methods 0.000 description 2
- 238000007599 discharging Methods 0.000 description 2
- 238000000034 method Methods 0.000 description 2
- 230000000737 periodic effect Effects 0.000 description 2
- 230000008569 process Effects 0.000 description 2
- 230000009286 beneficial effect Effects 0.000 description 1
- 230000005540 biological transmission Effects 0.000 description 1
- 230000008859 change Effects 0.000 description 1
- 238000004891 communication Methods 0.000 description 1
- 230000001627 detrimental effect Effects 0.000 description 1
- 238000011161 development Methods 0.000 description 1
- 238000010586 diagram Methods 0.000 description 1
- 238000002474 experimental method Methods 0.000 description 1
- 230000036541 health Effects 0.000 description 1
- 230000017525 heat dissipation Effects 0.000 description 1
- 238000001727 in vivo Methods 0.000 description 1
- 230000001537 neural effect Effects 0.000 description 1
- 230000002093 peripheral effect Effects 0.000 description 1
- 230000001737 promoting effect Effects 0.000 description 1
- 238000011160 research Methods 0.000 description 1
Classifications
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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
- A61N1/3605—Implantable neurostimulators for stimulating central or peripheral nerve system
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
- A61N1/00—Electrotherapy; Circuits therefor
- A61N1/02—Details
- A61N1/04—Electrodes
- A61N1/05—Electrodes for implantation or insertion into the body, e.g. heart electrode
-
- 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
- A61N1/3605—Implantable neurostimulators for stimulating central or peripheral nerve system
- A61N1/3606—Implantable neurostimulators for stimulating central or peripheral nerve system adapted for a particular treatment
- A61N1/36103—Neuro-rehabilitation; Repair or reorganisation of neural tissue, e.g. after stroke
Abstract
The application relates to a charge balance system, which relates to the field of implantable nerve stimulators and comprises a signal input end, a rectifying unit, a shunt unit, a first energy storage capacitor, a first resistor for simulating a radio frequency chip and a second resistor for simulating human tissues, wherein the first resistor is used for simulating human tissues; the signal input end is used for accessing sinusoidal signals, the rectifying unit is connected with the signal input end, the first energy storage capacitor is connected with the rectifying unit, the first resistor is connected in parallel with the first energy storage capacitor, the shunt unit is connected with the second resistor in series, the shunt unit is connected with the second resistor in parallel with the first resistor, the shunt unit is used for changing the current direction in a certain time to form current opposite to the stimulating current, and two ends of the second resistor are used as signal output ends. The application has the effect of realizing charge balance with low cost.
Description
Technical Field
The present application relates to the field of implantable neurostimulators, and more particularly to a charge balancing system.
Background
When the implanted nerve stimulator discharges in the human body in the form of a periodic signal, the human body tissue carries charges with a certain polarity in the discharge time period of each period, and the charges carried on the human body tissue automatically run off in a certain time after the discharge is finished. Among them, an implantable neurostimulator is a medical device that can be implanted into a patient to treat a focal site. The implanted nerve stimulator can carry out radio frequency communication and energy transmission with the external energy controller, and is powered by the external energy controller in real time to drive the electrodes of the implanted nerve stimulator to generate a stimulation signal, namely a stimulation current.
It can be appreciated that when the period of the periodic signal is short, there may be situations where charge balance cannot be achieved, so that the stimulated region in the human tissue carries charges of the same polarity for a long period of time, which is detrimental to human health. In the related art, an implantable neurostimulator is mainly used to apply a reverse signal immediately after discharging to promote charge balance of stimulated tissue.
However, a circuit structure with a chip is generally used to realize the active charge balance function. The chip sends instructions to its peripheral circuitry to control the direction and amplitude of the stimulus signal over a period of time. Any form of waveform can be implemented using a circuit configuration with a chip, for example, in the present application, the chip can control the signal to reverse direction for a certain period of time to achieve active charge balance. However, the circuit structure with the chip is complex, the research, development and use costs are high, meanwhile, the power consumption generated by the chip in the use process is high, and the heat dissipation design difficulty is high, so that the transmitting power of the energy supply module is required to be further improved, and the design difficulty of the radio frequency part is increased.
Disclosure of Invention
In order to achieve charge balance at low cost, the present application provides a charge balance system.
The application provides a charge balance system, which adopts the following technical scheme:
a charge balance system comprises a signal input end, a rectifying unit, a shunt unit, a first energy storage capacitor, a first resistor for simulating a radio frequency chip and a second resistor for simulating human tissue;
the signal input end is used for accessing sinusoidal signals, the rectifying unit is connected with the signal input end, the first energy storage capacitor is connected with the rectifying unit, the first resistor is connected in parallel with the first energy storage capacitor, the shunt unit is connected with the second resistor in series, the shunt unit is connected with the second resistor in parallel with the first resistor, the shunt unit is used for changing the current direction in a certain time to form current opposite to the stimulating current, and two ends of the second resistor are used as signal output ends.
By adopting the technical scheme, the first resistor is used for simulating the radio frequency chip implanted in the patient, the second resistor is used for simulating the human body resistance, when the signal input end is connected with a sinusoidal signal, the signal output end outputs a square wave signal through the rectifying unit, the first energy storage capacitor and the first resistor, and the current direction can be changed within a certain time by the shunt unit, so that the current opposite to the stimulation current is formed, and the charge balance is promoted. Compared with a chip capable of realizing charge balance, the circuit structure of the application is simpler, and has the advantage of low cost.
Optionally, the shunt unit includes a first capacitor and a second capacitor;
the first capacitor, the second resistor and the second capacitor are sequentially connected in series.
By adopting the technical scheme, the first energy storage capacitor has an energy storage function, a part of current of the first capacitor can be released in a lagging way and flows into the second capacitor through the first resistor, so that current in the other direction is generated.
Optionally, the circuit further comprises a diode, wherein the diode is arranged on a circuit of one end of the first energy storage capacitor connected with the first resistor and the common end of the first resistor and the first capacitor, the anode of the diode is connected with the first energy storage capacitor, and the cathode of the diode is connected with the common end of the first resistor and the first capacitor.
By adopting the technical scheme, the diode is used as the clamping piece, so that the current flow direction can be limited.
Optionally, the capacitance value of the first capacitor is equal to the capacitance value of the second capacitor.
By adopting the technical scheme, the circuit symmetry at the two ends of the load can be realized.
Optionally, the product of the capacitance value of the first storage capacitor and the resistance value of the first resistor does not exceed 0.3uf·kΩ.
By adopting the technical scheme, the product of the capacitor of the first energy storage capacitor and the resistance value of the first resistor can influence the forward voltage amplitude, and when the product is not more than 0.3uF kΩ, the forward voltage higher than 3.6V can be obtained to meet the requirement.
Optionally, the capacitance value of the first storage capacitor does not exceed 0.4uF.
Through adopting above-mentioned technical scheme, the rising time and the fall time of output signal can be influenced to first energy storage capacitor's size, and the capacitance value of first energy storage capacitor is the smaller, and rising time, fall time are the shorter, and when the capacitance value of first energy storage capacitor does not exceed 0.4uF, corresponding rising time and fall time can satisfy the requirement.
Optionally, the rising time of the stimulation signal output by the signal output end is less than 30us, and the falling time is less than 70us.
By adopting the technical scheme, the stimulation effect can be better.
Optionally, the capacitance value of the first energy storage capacitor is limited by the resistance value of the first resistor.
By adopting the technical scheme, the radio frequency chip can be simulated by the first resistor, the resistance is fixed, and then the capacitance value of the first energy storage capacitor can be determined. The product of the capacitance value of the first energy storage capacitor and the resistance value of the first resistor can influence the amplitude of the forward voltage, the larger the product is, the smaller the amplitude of the forward voltage is, the smaller the product is, the larger the amplitude of the forward voltage is, and the forward voltage is not changed after reaching a certain value. The smaller the capacitance value of the first energy storage capacitor is, the longer the output signal zeroing time is, and conversely, the larger the capacitance value of the first energy storage capacitor is, the shorter the output signal zeroing time is. Therefore, the influence of two indexes, namely the amplitude value and the zeroing time of the forward voltage on the capacitance value should be considered when the capacitance value of the first energy storage capacitor is selected.
Optionally, the duty ratio of the sinusoidal signal is 2% -10%.
In summary, the present application includes at least one of the following beneficial technical effects:
in the application, the first resistor is used for simulating a radio frequency chip implanted in a patient, the second resistor is used for simulating human body resistance, when the signal input end is connected with a sinusoidal signal, the signal output end outputs a square wave signal through the rectifying unit, the first energy storage capacitor and the first resistor, and the current direction can be changed within a certain time by the shunt unit, so that current opposite to the stimulation current is formed, and the charge balance is promoted. Compared with a chip capable of realizing charge balance, the circuit structure of the application is simpler, and has the advantage of low cost.
Drawings
FIG. 1 is a schematic circuit diagram of a charge balancing system according to an embodiment of the present application.
Reference numerals illustrate: 1. a signal input terminal; 2. a rectifying unit; 3. a first energy storage capacitor; 4. a first resistor; 5. a first capacitor; 6. a second capacitor; 7. a second resistor; 8. a signal output terminal; 9. and a shunt unit.
Detailed Description
In order to make the objects, technical solutions and advantages of the present application more apparent, the present application will be further described in detail with reference to fig. 1 and the embodiment. It should be understood that the specific embodiments described herein are for purposes of illustration only and are not intended to limit the scope of the application.
The embodiment of the application discloses a charge balance system which acts on an implantable neural stimulator, so that when a stimulation signal acts on human tissues, the reverse part of the stimulation signal can promote the charge in the human tissues to realize rapid balance.
It can be appreciated that, in order to achieve a better effect of stimulating human tissues and achieving a better effect of balancing charges, the charge balancing system of the present application can simulate the environment of stimulating human tissues to ensure that the waveform and parameters of the stimulation signals applied to human tissues can meet the requirements.
Referring to fig. 1, the charge balancing system includes a signal input terminal 1, a rectifying unit 2, a first storage capacitor 3, a first resistor 4, a shunt unit 9, and a second resistor 7.
Wherein the signal input 1 is used for switching in a sinusoidal signal. The frequency and the duty ratio of the sinusoidal signal have some influence on the stimulation effect and the charge balance effect generated by the stimulation signal, that is, the conditions that the frequency and the duty ratio of the sinusoidal signal need to be met are that the square wave signal obtained by the change of the sinusoidal signal enables the first energy storage capacitor 3 to complete the charging and discharging process in one period, so that the stimulation effect and the charge balance effect generated by the stimulation signal can be ensured. Preferably, the frequency of the square wave signal is 50 Hz-5 kHz, and the duty ratio is 2% -10%.
The rectifying unit 2 is connected to the signal input terminal 1 and is used for receiving a sinusoidal signal and rectifying the sinusoidal signal. Specifically, the rectifying unit 2 includes four diodes D1 to D4. The anode of the diode D1 is connected with one end of the signal input end 1, the cathode of the diode D2 is connected with the cathode of the diode D1, the anode of the diode D2 is connected with the other end of the signal input end 1, the cathode of the diode D3 is connected with the common end of the diode D1 and the signal input end 1, the anode of the diode D4 is connected with the anode of the diode D3, and the cathode of the diode D4 is connected with the common end of the diode D2 and the signal input end 1. Wherein the common terminal of the diode D1 and the diode D2, and the common terminal of the diode D3 and the diode D4 are used as output terminals for outputting rectified sinusoidal signals.
The first energy storage capacitor 3 is connected with the output end of the rectifying unit 2, the first resistor 4 is connected in parallel with the first energy storage capacitor 3, the shunt unit 9 and the second resistor 7 are connected in series, the shunt unit 9 and the second resistor 7 are connected in parallel with the first resistor 4, and two ends of the second resistor 7 serve as signal output ends 8.
Wherein the shunt unit 9 is used for changing the current direction within a certain time to form a current opposite to the stimulation current. Which comprises a first capacitor 5 and a second capacitor 6. Specifically, the first capacitor 5, the second resistor 7, and the second capacitor 6 are sequentially connected in series.
In order to achieve a better stimulation effect and charge balance effect, the values of the first energy storage capacitor 3, the first resistor 4, the first capacitor 5, the second resistor 7 and the second capacitor 6 are important.
Firstly, it can be understood that the sinusoidal signal forms a unidirectional waveform after being rectified by the rectifying unit 2, and then the signal forms a constant voltage signal after passing through the first energy storage capacitor 3 and the first resistor 4, and the external energy controller can realize square wave signals with duty ratio at two ends of the electrode by controlling the on-off of the signal. During each period of the square wave signal, during the falling of the high level to 0 v, a part of the current flowing through the first capacitor 5 is released in a delayed manner due to the energy storage effect of the capacitor, and flows into the second capacitor 6 through the first resistor 4, so that the stimulating signal output by the signal output terminal 8 generates a current opposite to the previous state, namely a reverse current, to achieve the effect of promoting charge balance.
In other embodiments, a diode D5 is also provided on the line of the end of the first storage capacitor 3 connected to the first resistor 4 and the common end of the first resistor 4 to the first capacitor 5. The anode of the diode D5 is connected to the first energy storage capacitor 3, and the cathode is connected to the common terminal of the first resistor 4 and the first capacitor 5, and serves as a clamping member to limit the current flow.
After a plurality of groups of experiments, the values of the first energy storage capacitor 3, the first resistor 4, the first capacitor 5 and the second capacitor 6 and the waveforms and parameters of the stimulation signals can be obtained, and the correlation is as follows:
the magnitude of the capacitance of the first storage capacitor 3 can influence the rise and fall times of the voltage in each period of the stimulus signal, as well as the time for the return of the reverse voltage to zero. That is, the larger the capacitance value of the first storage capacitor 3 is, the longer the rise time and the fall time are, whereas the smaller the capacitance value of the first storage capacitor 3 is, the shorter the rise time and the fall time are, but the time for the reverse voltage to return to zero is also correspondingly longer.
It should be noted that, since the first resistor 4 is used to simulate the rf chip, the resistance of the first resistor 4 is fixed and depends on the resistance of the rf chip. In several embodiments, the resistance of the rf chip is 1kΩ to 3kΩ, and thus the resistance of the first resistor 4 is also 1kΩ to 3kΩ.
Further, the product of the capacitance value of the first storage capacitor 3 and the resistance value of the first resistor 4 can also have an influence on the magnitude of the forward voltage of the stimulus signal. That is, the larger the product of the capacitance value of the first storage capacitor 3 and the resistance value of the first resistor 4, the smaller the magnitude of the forward voltage of the stimulus signal, whereas the smaller the product of the capacitance value of the first storage capacitor 3 and the resistance value of the first resistor 4, the larger the magnitude of the forward voltage of the stimulus signal, and the magnitude remains substantially unchanged when the magnitude is large to a certain extent.
Furthermore, in consideration of symmetry of the electrodes, when the capacitance value of the first capacitor 5 and the capacitance value of the second capacitor 6 are selected, capacitors having the same capacitance value should be selected as the first capacitor 5 and the second capacitor 6. The capacitance value of the first capacitor 5 can also influence the level reversal capability of the stimulus signal and the time of level reversal return to zero. That is, the larger the capacitance value of the first capacitor 5, the worse the level reversal capability, and the longer the time for the level reversal to return to zero, whereas the smaller the capacitance value of the first capacitor 5, the better the level reversal capability, and the shorter the time for the level reversal to return to zero.
Obviously, according to the above-mentioned correlation between the values of the first energy storage capacitor 3, the first resistor 4, the first capacitor 5 and the second capacitor 6 and the waveform and parameters of the stimulus signal, it can be determined that the capacitance value of the first energy storage capacitor 3 and the capacitance value of the first capacitor 5 both have an effect on the time of level reversal and zero, but the product of the capacitance value of the first energy storage capacitor 3 and the resistance value of the first resistor 4 needs to be considered when the capacitance value of the first energy storage capacitor 3 is selected, so that the capacitance value of the first capacitor 5 needs to be determined first.
Preferably, in the present application, the capacitance value of the first capacitor 5 is 5uF to obtain a larger reverse voltage, and the time for which the voltage can be reversely zeroed is shorter. When the amplitude of the reverse voltage is larger, the quantity of charges with the same polarity as the charges carried by the internal tissues after the internal tissues are subjected to the electric stimulation can be increased, so that the charge balance is promoted. Further, when the time for the voltage to return to zero is short, that is, the time for the stimulation signal to provide the same polarity of the electric charge as that carried by the tissue in the body after the electric stimulation is also short, the time for the electric charge to reach balance can be shortened to a certain extent.
It can be appreciated that in order to make the stimulation signal have a better stimulation effect on the electrical stimulation of the in vivo resistance, the magnitude of the forward voltage in the stimulation signal needs to reach more than 3.6 volts. Accordingly, it is required that the product of the capacitance value of the first storage capacitor 3 and the resistance value of the first resistor 4 does not exceed 0.3 ufkΩ.
When the capacitance value of the first energy storage capacitor 3 is selected, the magnitude of the stimulus signal limits the product of the capacitance value of the first energy storage capacitor 3 and the resistance value of the first resistor 4, and the resistance value of the first resistor 4 is fixed, so that the capacitance value of the first energy storage capacitor 3 is limited by the resistance value of the first resistor 4. Specifically, when the resistance value of the first resistor 4 is small, it is necessary to ensure that the product of the capacitance value of the first energy storage capacitor 3 and the resistance value of the first resistor 4 does not exceed 0.3uf·kΩ first, and then, it is necessary to ensure that the capacitance value of the first energy storage capacitor 3 cannot be excessively large. Since the capacitance value of the first energy storage capacitor 3 can affect the rising time and the falling time of the medium voltage of the stimulation signal, that is, the effective stimulation duration of the stimulation signal to electrically stimulate the tissue in the body can be affected, in order to ensure the stimulation effect, the capacitance value of the first energy storage capacitor 3 needs to be selected to meet the requirement that the capacitance value does not exceed 0.4uF. When the resistance value of the first resistor 4 is large, a capacitor having a small capacitance value needs to be selected as the first storage capacitor 3. However, when the capacitance value of the first energy storage capacitor 3 is selected, it is not preferable to select a capacitor having a capacitance value too small. When the capacitance value of the first storage capacitor 3 is smaller, the time for the reverse voltage of the stimulus signal to return to zero will be correspondingly longer, thereby affecting the effect of charge balance.
In the present application, in order to achieve both the stimulation effect and the charge balance effect to a good effect, it is required that the rise time of the stimulation signal is less than 30us and the fall time is less than 70us. In this case, the capacitance value of the first storage capacitor 3 is preferably 0.1uF.
The implementation principle of the charge balance system of the embodiment of the application is as follows: the first resistor 4 is used for simulating a radio frequency chip implanted in a patient, the second resistor 7 is used for simulating human body resistance, when the signal input end 1 is connected with a sinusoidal signal, the signal output end 8 outputs a square wave signal through the rectifying unit 2, the first energy storage capacitor 3, the first resistor 4, the first capacitor 5 and the second capacitor 6, but as the capacitor has an energy storage function, a part of current of the first capacitor 5 is delayed to be released and flows into the second capacitor 6 through the first resistor 4, so that current in the other direction is generated to promote charge balance. Compared with a chip capable of realizing charge balance, the circuit structure of the application is simpler, and has the advantage of low cost.
The foregoing description of the preferred embodiments of the application is not intended to limit the scope of the application in any way, including the abstract and drawings, in which case any feature disclosed in this specification (including abstract and drawings) may be replaced by alternative features serving the same, equivalent purpose, unless expressly stated otherwise. That is, each feature is one example only of a generic series of equivalent or similar features, unless expressly stated otherwise.
Claims (9)
1. A charge balance system, characterized by: the device comprises a signal input end (1), a rectifying unit (2), a shunt unit (9), a first energy storage capacitor (3), a first resistor (4) for simulating a radio frequency chip and a second resistor (7) for simulating human tissue;
the signal input end (1) is used for accessing sinusoidal signals, the rectifying unit (2) is connected with the signal input end (1), the rectifying unit (2) is connected to the first energy storage capacitor (3), the first resistor (4) is connected in parallel with the first energy storage capacitor (3), the shunt unit (9) and the second resistor (7) are connected in series, and the shunt unit (9) and the second resistor (7) are connected in parallel with the first resistor (4), the shunt unit (9) is used for changing the current direction in a certain time, and forms the electric current opposite to the stimulating current, and the two ends of the second resistor (7) serve as signal output ends (8).
2. The charge balance system of claim 1, wherein: the shunt unit (9) comprises a first capacitor (5) and a second capacitor (6);
the first capacitor (5), the second resistor (7) and the second capacitor (6) are sequentially connected in series.
3. The charge balance system of claim 2, wherein: the energy-saving capacitor is characterized by further comprising a diode, wherein the diode is arranged on a circuit of one end of the first energy-saving capacitor (3) connected with the first resistor (4) and the public end of the first resistor (4) connected with the first capacitor (5), the anode of the diode is connected with the first energy-saving capacitor (3), and the cathode of the diode is connected with the public end of the first resistor (4) and the first capacitor (5).
4. A charge balancing system according to claim 3, wherein: the capacitance value of the first capacitor (5) is equal to the capacitance value of the second capacitor (6).
5. A charge balancing system according to claim 3, wherein: the product of the capacitance value of the first energy storage capacitor (3) and the resistance value of the first resistor (4) is not more than 0.3 uF.k omega.
6. The charge balance system of claim 5, wherein: the capacitance value of the first storage capacitor (3) does not exceed 0.4uF.
7. The charge balance system of claim 6, wherein: the rising time of the stimulation signal output by the signal output end (8) is less than 30us, and the falling time is less than 70us.
8. The charge balance system of claim 7, wherein: the capacitance value of the first energy storage capacitor (3) is limited by the resistance value of the first resistor (4).
9. The charge balance system of claim 8, wherein: the duty ratio of the sinusoidal signal is 2% -10%.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN202311016747.1A CN116726393A (en) | 2023-08-14 | 2023-08-14 | Charge balance system |
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| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN202311016747.1A CN116726393A (en) | 2023-08-14 | 2023-08-14 | Charge balance system |
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| Publication Number | Publication Date |
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| CN116726393A true CN116726393A (en) | 2023-09-12 |
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| Application Number | Title | Priority Date | Filing Date |
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| CN202311016747.1A Pending CN116726393A (en) | 2023-08-14 | 2023-08-14 | Charge balance system |
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| CN (1) | CN116726393A (en) |
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2023
- 2023-08-14 CN CN202311016747.1A patent/CN116726393A/en active Pending
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