A data acquisition and voltage control method for pulse therapy glasses

Abstract

The present application relates to the technical field of wearable medical electric stimulation devices, and specifically discloses a data acquisition and voltage control method for pulse treatment glasses, comprising: acquiring skin contact impedance and calculating electrode offset distance; distributing target output current according to upper limit of treatment current and weight; calculating current error and voltage offset factor; updating each channel output voltage in combination with pulse timing depeak mechanism; and executing abnormal channel shunt control. Compared with the prior art which only based on PID closed-loop adjustment and cannot balance dynamic balance and spatial stimulation distribution among channels, especially under non-ideal conditions such as rapid impedance change or electrode contact abnormality in the sensitive area of the user's eyes, it is difficult to achieve fine and safe stimulation control. Since the present application introduces sensitivity space modeling and pulse timing depeak mechanism, dynamic balance control of multi-channel pulse voltage is achieved, and the stimulation safety and output uniformity of the device are improved.

Description

TECHNICAL FIELD

[0001] The present application relates to the technical field of wearable medical electrical stimulation devices, in particular to a data acquisition and voltage control method for pulse therapy glasses. BACKGROUND

[0002] At present, as a wearable neuroelectrical stimulation device, pulse therapy glasses have been widely used in visual fatigue relief, dry eye auxiliary treatment and eye muscle adjustment. However, the existing devices mostly adopt fixed current output or single-channel simple feedback regulation mode, which lacks fine perception and control of different skin contact states and eye structure differences, resulting in uneven current output, concentrated stimulation in electrode area, and voltage surge causing discomfort in actual use.

[0003] For example, during the wearing process of the user, if part of the electrodes are poorly contacted or located in the high-sensitive area of the eye corner, the traditional control method cannot dynamically identify and voltage correct such channels, which is prone to cause single-channel voltage too high and current concentrated discharge, affecting the treatment effect, and there is a risk of burning sensation or transient pain. The existing technology cannot fully meet the needs of safe, balanced and comfortable stimulation control of the eye area under the conditions of multi-electrode distribution, non-ideal fitting and dynamic impedance change.

[0004] Therefore, there is an urgent need for a pulse therapy glasses control method that can still achieve accurate data acquisition and control, voltage dynamic adjustment and abnormal channel identification under the conditions of multi-channel structure and dynamic physiological changes, in order to improve the uniformity, safety and individual adaptation ability of electrical stimulation treatment. SUMMARY

[0005] In view of the above technical deficiencies, the purpose of the present application is to provide a data acquisition and voltage control method for pulse therapy glasses, which aims to solve the technical problems that the existing technology cannot balance the dynamic balance between channels and spatial stimulation distribution based on PID closed-loop regulation, especially under non-ideal conditions such as rapid impedance change in sensitive areas of the user's eyes or abnormal electrode contact, it is difficult to achieve fine and safe stimulation control.

[0006] To solve the above technical problems, the present application adopts the following technical scheme: the present application provides a data acquisition and voltage control method for pulse therapy glasses,

[0007] The data acquisition and voltage control method for pulse therapy glasses comprises:

[0008] Step S10: applying a detection pulse voltage of a preset amplitude to the i th output electrode channel in the pulse therapy glasses and measuring the response current calculating the initial skin contact impedance Construct a virtual plane coordinate system to obtain the i-th output electrode channel coordinate and the eye region barycentric coordinate Calculate the geometric offset distance of the i-th output electrode channel relative to the eye region barycentric coordinate And based on the geometric offset distance, construct the sensitivity weight factor ω of the i-th output electrode channel i ;

[0009] Step S20: Obtain the current treatment mode and set the total treatment current upper limit to I0, and allocate the target output current according to the sensitivity weight factor ω i

[0010] Step S30: Real-time acquisition of the output voltage V i (t) and output current I i (t) of the i-th output electrode channel at time t, combine the target output current Calculate the current error and the voltage offset factor γ i (t), and further construct the voltage adjustment amount;

[0011] Step S40: Update the output voltage of the i-th output electrode channel according to the voltage adjustment amount combined with the pre-set pulse timing error peak avoidance method, and obtain the updated output voltage update pulse sequence;

[0012] Step S50: After obtaining the updated output voltage update pulse sequence, calculate the current error and the voltage offset factor γ i (t+1) at time t+1, pre-set current deviation abnormal threshold ε I and voltage offset abnormal threshold ε V When or |γ i (t+1)-1|>ε V , execute abnormal shunt control operation.

[0013] Preferably, in step S10, the sensitivity weight factor ω Wherein, β is a geometric offset adjustment factor, used to control the influence weight of spatial distance; the sensitivity weight factor ω i is used to evaluate the tolerance and risk of electrode position of the i-th output electrode channel to skin stimulation.

[0014] Preferably, in step S20, the current treatment mode is obtained and the total treatment current upper limit is set to I0, and the target output current is allocated according to the sensitivity weight factor ω i ​​​the step S30, specifically comprising: automatically loading a current treatment allowed total current upper limit I0according to a user selected or preset treatment mode, including a basic relaxation mode, an intensive stimulation mode, and an intelligent adaptive mode, the total current upper limit I0being used to represent a total stimulation intensity boundary that the user's skin can tolerate under the current treatment scheme; based on the sensitivity weight factor ω i normalizing and weighting the total current upper limit I0to obtain a target output current

[0015] Preferably, in the step S30, the current error a voltage offset factor for reflecting a relative relationship between the current output voltage of the i-th output electrode channel and the average voltage, where N is the total number of output electrode channels.

[0016] Preferably, in the step S30, and further constructing a voltage adjustment amount step, specifically comprising:

[0017] according to the current error and the voltage offset factor γ i (t) to construct a voltage adjustment cost function J(U i (t)), which is used to jointly consider the current deviation and the voltage balance among channels, the voltage adjustment cost function wherein α is a weight factor of the current error of the current channel output current; β is an adjustment factor of the relative offset of the current channel output voltage;

[0018] In the control process, by minimizing the voltage adjustment cost function J(U i (t)), the voltage adjustment amount ΔU i (t) used to control the current channel output is obtained.

[0019] Preferably, in the step S40, the output voltage of the i-th output electrode channel is updated according to the voltage adjustment amount combined with a preset pulse timing de-bursting method, to obtain an updated output voltage, and a pulse sequence updating step, specifically comprising:

[0020] based on the voltage adjustment amount obtained in the step S30, weighting and synthesizing it with the current output voltage V i (t) to obtain an updated target voltage:

[0021] adopting the pulse timing de-bursting method to set an output delay time δt i for the i-th output electrode channel, δt i = τ0+ t0· k· (γ i (t)-1), where t0is a preset delay adjustment standard time, τ0is a preset minimum pulse interval time, k is a delay adjustment factor, and γ i (t) is the voltage offset factor.

[0022] According to the output delay time δt i The output schedule is arranged, and all channels output after respective delays, forming a sequence of staggered trigger output voltage update pulses.

[0023] Preferably, the step of abnormally shunting control operation in step S50 specifically includes: first setting the output voltage of the i-th output electrode channel at time t+1 to zero; and then setting the target output current of the i-th output electrode channel to be uniformly distributed to other output electrode channels.

[0024] The application also provides a data acquisition and voltage control system for pulse therapy glasses, comprising:

[0025] An impedance modeling and sensitivity calculation module is configured to apply a preset amplitude of a detection pulse voltage to the i-th output electrode channel in the pulse therapy glasses and measure the response current to calculate the initial skin contact impedance A virtual plane coordinate system is constructed to obtain the coordinates of the i-th output electrode channel and the coordinates of the eye region barycenter The geometric offset distance of the i-th output electrode channel relative to the eye region barycenter coordinates is calculated and the sensitivity weight factor ω of the i-th output electrode channel is constructed based on the geometric offset distance i ;

[0026] A current target distribution module is configured to obtain the current treatment mode and set the upper limit of the total treatment current to I0, and distribute the target output current according to the sensitivity weight factor ω i

[0027] A voltage adjustment amount construction module is configured to collect the output voltage V i (t) and the output current I i (t) of the i-th output electrode channel at time t in real time, combine the target output current to calculate the current error and the voltage offset factor γ i (t), and further construct the voltage adjustment amount;

[0028] A timing staggered update module is configured to update the output voltage of the i-th output electrode channel according to the voltage adjustment amount combined with the preset pulse timing staggered method to obtain the updated output voltage V i (t+1).

[0029] An abnormal shunt control module is configured to calculate the current error​ and voltage offset factor γ i (t+1), preset current deviation abnormal threshold ε I and voltage offset abnormal threshold ε V When the following conditions are met or |γ i (t)-1|>ε V Then the abnormal shunt control operation is performed.

[0030] The application also provides a computer program product comprising a data acquisition and voltage control program for pulse treatment glasses, which, when executed by a processor, implements the data acquisition and voltage control method for pulse treatment glasses.

[0031] The application has the beneficial effects that a data acquisition and control method based on the combination of impedance sensing and spatial modeling is proposed, adaptive recognition and response of multi-channel output electrodes under different skin contact states are realized, and the individual adaptability and control accuracy of the pulse treatment glasses are effectively improved.

[0032] A dynamic regulation mechanism combining current error and voltage offset factor is constructed, and combined with the pulse timing stagger strategy, real-time data acquisition and control of balanced output between channels are realized, the local stimulation risk caused by single-point current aggregation and voltage surge is significantly reduced, and the safety and comfort of electrical stimulation treatment are improved. BRIEF DESCRIPTION OF DRAWINGS

[0033] In order to more clearly illustrate the technical solutions in the embodiments of the application or the prior art, the following will briefly introduce the drawings needed to be used in the embodiment or prior art description. Obviously, the drawings in the following description are only some embodiments of the application, and for those skilled in the art, other drawings can also be obtained without creative labor on the basis of these drawings.

[0034] Figure 1 The flowchart of the first embodiment of the data acquisition and voltage control method for pulse treatment glasses of the application.

[0035] Figure 2 The device schematic diagram of the data acquisition and voltage control method for pulse treatment glasses of the application. DETAILED DESCRIPTION

[0036] The technical solutions of the embodiments of the present invention will be clearly and completely described below with reference to the accompanying drawings. Obviously, the described embodiments are only some embodiments of the present invention, and not all embodiments. Based on the embodiments of the present invention, all other embodiments obtained by those skilled in the art without creative effort are within the scope of protection of the present invention.

[0037] Example 1: As Figure 1 The diagram shown is a flowchart of the first embodiment of the data acquisition and voltage control method for pulse therapy glasses of the present invention, which presents the first embodiment of the data acquisition and voltage control method for pulse therapy glasses of the present invention.

[0038] In the first embodiment, the data acquisition and voltage control method for the pulse therapy glasses includes:

[0039] Step S10: Apply a probe pulse voltage of preset amplitude to the i-th output electrode channel in the pulse therapy glasses. And measure the response current. The initial skin contact resistance was calculated. Construct a virtual planar coordinate system to obtain the coordinates of the i-th output electrode channel. and the coordinates of the eye area's center of gravity Calculate the centroid coordinates of the i-th output electrode channel relative to the eye region. geometric offset distance And based on the geometric offset distance, the sensitivity weighting factor ω of the i-th output electrode channel is constructed. i ;

[0040] It should be noted that in step S10, the sensitivity weighting factor Where β is the geometric offset adjustment factor, used to control the influence weight of spatial distance; the sensitivity weight factor ω i Used to assess the tolerance and risk of skin irritation to the electrode location of the i-th output electrode channel.

[0041] Understandably, the design of this sensitivity weighting factor fully considers the physical contact between the electrode and the skin, as well as the spatial sensitivity distribution of the electrode within the facial area. For example, areas near the lacrimal glands, corners of the eyes, and bridge of the nose have dense nerves and thinner skin, making them more sensitive to electrical stimulation. By using geometric offset modeling, the stimulation priority of these areas is reduced, thereby improving overall wearing safety and user comfort.

[0042] It should be understood that traditional multi-channel electrical stimulation control methods often adjust the output based solely on impedance or current magnitude, neglecting the differences in facial structure at the anatomical and physiological levels. This can easily lead to current concentration in a single area, causing discomfort such as burning and throbbing. In this invention, by introducing a coupled calculation model of coordinate centroid and offset distance, a quantitative assessment of regional stimulation risk is achieved, realizing "structural cognitive current distribution logic" for the first time in the context of ocular pulse therapy.

[0043] For example, if channel 1 is located at the inner corner of the eye, its initial contact impedance is 2.0 kΩ and its spatial offset distance is 5.0 mm; channel 2 is located in the middle of the upper eyelid, its impedance is 1.2 kΩ, and its offset distance is 1.0 mm; with β = 0.1, we obtain... This indicates that the sensitivity of channel 1 is significantly higher than that of channel 2. In subsequent steps, the system will suppress and control the current to avoid excessive electrical stimulation of the corner of the eye.

[0044] Step S20: Obtain the current treatment mode and set the upper limit of the total treatment current to I0, based on the sensitivity weighting factor ω. i Distribute target output current

[0045] It should be noted that in step S20, the current treatment mode is obtained and the upper limit of the total treatment current is set to I0, based on the sensitivity weighting factor ω. i Distribute target output current The steps specifically include: based on the user-selected or preset treatment mode, including basic relaxation mode, strong stimulation mode, and intelligent adaptive mode, automatically loading the maximum allowable total treatment current I0 for the current treatment. The maximum allowable total treatment current I0 represents the boundary of the total stimulation intensity that the user's skin can tolerate under the current treatment plan; based on the sensitivity weighting factor ω... i The target output current is obtained by normalizing and weighting the total treatment current to an upper limit of I0.

[0046] Understandably, this step ensures that low-sensitivity, low-impedance regions receive high stimulation intensity output while automatically weakening the output of channels near highly sensitive areas such as the corner of the eye and lacrimal gland, without exceeding the upper limit of the total current. This normalized inverse weighting strategy balances the dual objectives of "total safe control" and "local adaptive adjustment," ensuring a balanced distribution of multi-channel pulse stimulation and reducing user discomfort.

[0047] It should be understood that traditional current distribution methods are mostly based on equal distribution or linear adjustment according to impedance magnitude, failing to fully consider the influence of the physiological location and spatial distribution of the electrodes on electrical stimulation tolerance, which can easily lead to excessive current in some areas and insufficient stimulation in others. This invention, by introducing a sensitivity weighting factor and constructing an inverse normalization model, achieves a dynamic distribution method of "inhibition according to sensitivity and release according to tolerance" for channel stimulation current, exhibiting stronger adaptability, safety, and individual difference adjustment capabilities.

[0048] Step S30: Real-time acquisition of the output voltage V of the i-th output electrode channel at time t. i (t) and output current I i (t), combined with the target output current Calculate current error and voltage offset factor γ i (t), and further construct the voltage regulation quantity;

[0049] It should be noted that in step S30, the current error Voltage offset factor This is used to reflect the relative relationship between the current output voltage of the output electrode channel and the average voltage, where N is the total number of output electrode channels. Step S30 further includes the step of constructing the voltage regulation amount, specifically including: based on the current error... and voltage offset factor γ i (t) Construct a voltage regulation cost function J(U) i (t) is used to jointly consider current deviation and inter-channel voltage balance, voltage regulation cost function. Where α is the weighting factor for the current channel output current error; β is the adjustment factor for the relative offset of the current channel output voltage; during the control process, the voltage regulation cost function J(U) is minimized. i (t)), to obtain the voltage regulation amount ΔU used to control the current channel output. i (t).

[0050] Understandably, the aforementioned cost function constructs a joint model of "stimulus achievement" (current error) and "cross-channel balance" (voltage offset), no longer relying on single-channel error control. Instead, by modeling the squared term of the error, it can achieve smooth convergence and dynamic adjustment, adapting to voltage distribution under non-ideal conditions of multi-channel electrodes.

[0051] Step S40: Update the output voltage of the i-th output electrode channel according to the voltage adjustment amount and the preset pulse timing stagger method to obtain the updated output voltage update pulse sequence;

[0052] It should be noted that in step S40, the output voltage of the i th output electrode channel is updated according to the voltage adjustment amount combined with the preset pulse timing stagger peak method, and the updated output voltage is obtained. The pulse sequence is updated. The specific steps include: based on the voltage adjustment amount obtained in step S30, it is combined with the current output voltage V i (t) to obtain the updated target voltage: the pulse timing stagger peak method is used to set the output delay time δt i of the i th output electrode channel i =τ0+t0·k·(γ i (t)-1), where t0 is a preset delay adjustment standard time, τ0 is a preset minimum pulse interval time, k is a delay adjustment factor, γ i (t) is a voltage offset factor; according to the output delay time δt i , all channels are output after delay, forming a staggered peak triggered output voltage update pulse sequence.

[0053] It can be understood that the "pulse timing stagger peak method" introduced in this step is optimized on the basis of the traditional synchronous output mechanism, and is designed to solve the problems of current convergence, excessive electrical stimulation or burning sensation that may occur when multiple channels are activated at the same time. By delaying the trigger timing of the output voltage update, the stimulation energy can be effectively dispersed in the time domain, so as to guide the current to be more evenly distributed on the skin surface space, and reduce the risk of single-point charge accumulation.

[0054] It should be understood that the traditional pulse electrical stimulation system mostly adopts a timer driving + synchronous trigger structure, and its output behavior is easy to cause "peak coupling" in a multi-electrode structure, that is, multiple channels are triggered at the same time. High voltage, causing local instantaneous current density, especially in sensitive areas of the eye, which can cause pain or discomfort to the tissue. The present application designs a dynamic stagger peak strategy based on a voltage offset factor, which first binds the full-channel voltage state feedback to the scheduling time, realizes the "the higher the offset, the more delayed" balance mechanism, and effectively improves the stimulation uniformity and system response stability.

[0055] Step S50: After obtaining the updated output voltage update pulse sequence, the current error and the voltage offset factor γ i (t+1) at time t+1 are calculated, the preset current deviation abnormal threshold ε I and the voltage offset abnormal threshold ε V , when or |γ i (t+1)-1|>ε V , the abnormal shunt control operation is performed.

[0056] It should be noted that in step S50, the step of the abnormal shunt control operation specifically includes: first setting the output voltage of the i th output electrode channel at time t+1 to be zero; then setting the target output current of the i th output electrode channel is uniformly distributed to other output electrode channels.

[0057] It can be understood that the design of the above abnormal shunt mechanism is to prevent the system from being unbalanced due to poor contact, abnormal impedance, local stimulation concentration, etc. during use of a certain electrode channel, and further to cause safety hazards. By actively cutting off the abnormal channel and dynamically adjusting the target current of the remaining channels, the overall treatment process can be ensured not to be disturbed by single-point abnormalities, and "fault-tolerant operation" and "inter-channel collaborative compensation" can be achieved.

[0058] It should be understood that the conventional pulse treatment device often only alarms or suspends all outputs when the channel is abnormal, and lacks the ability of local isolation and current redistribution of the fault channel. The abnormal shunt strategy of the present application not only improves the continuity and stability of the system operation, but also avoids the overvoltage phenomenon of the remaining channels due to "sudden load increase" through the dynamic balance adjustment mechanism of the target current, and realizes more precise safety control.

[0059] Embodiment Two: In addition, the present application provides a data acquisition and voltage control system for a pulse treatment glasses, which adopts the data acquisition and voltage control method for a pulse treatment glasses in the above-mentioned embodiments, and can solve the technical problem of data acquisition and voltage control for a pulse treatment glasses. Compared with the prior art, the beneficial effects of the data acquisition and voltage control system for a pulse treatment glasses provided by the present application are the same as those of the data acquisition and voltage control method for a pulse treatment glasses provided by the above-mentioned embodiments, and other technical features in the data acquisition and voltage control system for a pulse treatment glasses are the same as those disclosed in the above-mentioned embodiment method, which will not be repeated here.

[0060] Embodiment Three: The present application provides a data acquisition and voltage control device for a pulse treatment glasses, please refer to Figure 2A data acquisition and voltage control device for a pulse therapy glasses includes at least one processor; and a memory connected to the at least one processor in communication; wherein the memory stores instructions executable by the at least one processor, the instructions being executed by the at least one processor to enable the at least one processor to perform the data acquisition and voltage control method for a pulse therapy glasses of the above-mentioned embodiment one. The data acquisition and voltage control device for a pulse therapy glasses of the present embodiment can include, but is not limited to, a mobile terminal such as a mobile phone, a notebook, a digital broadcast receiver, a PDA (Personal Digital Assistant), a PAD (Portable Application Description), a PMP (Portable Media Player), a car terminal (for example, a car navigation terminal), and the like, and a fixed terminal such as a digital TV, a desktop computer, and the like. The data acquisition and voltage control device for a pulse therapy glasses is only one example, and should not impose any limitation on the function and use range of the data acquisition and voltage control device for a pulse therapy glasses of the present embodiment. The data acquisition and voltage control device for a pulse therapy glasses can include a processing device 1001 (for example, a central processing unit, a graphic processing unit, and the like) which can perform various appropriate actions and processes according to a program stored in a read only memory (ROM) 1002 or a program loaded from a storage device 1003 to a random access memory (RAM) 1004. In the RAM 1004, various programs and data required for the operation of the data acquisition and voltage control device for a pulse therapy glasses are also stored. The processing device 1001, the ROM 1002, and the RAM 1004 are connected to each other through a bus 1005. An input / output (I / O) interface 1006 is also connected to the bus. Generally, the following systems can be connected to the I / O interface 1006: an input device 1007 including, for example, a touch screen, a touch pad, a keyboard, a mouse, an image sensor, a microphone, an accelerometer, a gyroscope, and the like; an output device 1008 including, for example, a liquid crystal display (LCD), a speaker, a vibrator, and the like; the storage device 1003 including, for example, a magnetic tape, a hard disk, and the like; and a communication device 1009. The communication device 1009 can allow the data acquisition and voltage control device for a pulse therapy glasses to communicate with other devices wirelessly or by wire to exchange data. Although the data acquisition and voltage control device for a pulse therapy glasses having various systems is shown in the figure, it should be understood that all the shown systems are not required to be implemented or provided. More or less systems can be alternatively implemented or provided.

[0061] Embodiment four: the application further provides a computer program product comprising a computer program, which, when executed by a processor, implements the steps of the data acquisition and voltage control method for the pulse treatment glasses as described above. The computer program product provided by the application can solve the technical problem of data acquisition and voltage control for the pulse treatment glasses. Compared with the prior art, the beneficial effects of the computer program product provided by the application are the same as those of the data acquisition and voltage control method for the pulse treatment glasses provided by the above-mentioned embodiment, and are not described here.

[0062] In particular, according to the embodiments disclosed by the application, the processes described above with reference to the flowcharts can be implemented as a computer software program. For example, the embodiments disclosed by the application include a computer program product comprising a computer program carried on a computer readable medium, the computer program comprising program code for executing the method shown in the flowchart. In such embodiments, the computer program can be downloaded and installed from a network through a communication device, or installed from a storage device 1003, or installed from a ROM 1002. When the computer program is executed by a processing device 1001, the above-mentioned functions defined in the method of the embodiments disclosed by the application are executed.

[0063] It should be understood that various parts of the application disclosed can be realized by hardware, software, firmware or a combination thereof. In the description of the above-mentioned embodiments, specific features, structures, materials or characteristics can be combined in any one or more embodiments or examples in a suitable manner.

[0064] Obviously, those skilled in the art can make various modifications and variations to the application without departing from the spirit and scope of the application. Thus, if these modifications and variations of the application belong to the scope of the claims of the application and their equivalent technologies, the application also intends to include these modifications and variations.

Claims

1. A data acquisition and voltage control method for a pulsed therapeutic eyeglass, characterized by, The method comprises: Step S10: [The text abruptly ends here, likely due to an incomplete sentence or a formatting error.] Each output electrode channel is subjected to a probe pulse voltage of a preset amplitude. And measure the response current. The initial skin contact resistance was calculated. Construct a virtual planar coordinate system and obtain the first... Coordinates of each output electrode channel and the coordinates of the eye area's center of gravity Calculate the first Each output electrode channel relative to the centroid coordinates of the eye region geometric offset distance And construct the first based on geometric offset distance Sensitivity weighting factor for each output electrode channel Among them, the sensitivity weighting factor ,in, This is a geometric offset adjustment factor used to control the weighting of spatial distance; sensitivity weighting factor. Used to evaluate the The tolerance and risk of skin irritation to the electrode positions of each output electrode channel; Step S20: Obtain the current treatment mode and set the upper limit of the total treatment current to , according to the sensitivity weight factor to allocate the target output current ; Step S30: collecting the output voltage and output current of the first output electrode channel at time t in real time , calculating the current error and the voltage offset factor in combination with the target output current , and further constructing the voltage adjustment amount; wherein the step of further constructing the voltage adjustment amount specifically comprises:​​​​ According to the current error and a voltage offset factor constructing a voltage regulation cost function for jointly considering the current deviation and the voltage balance among channels, the voltage regulation cost function wherein, is a weight factor of the current error of the current channel output current; is a regulation factor of the relative offset of the current channel output voltage. In the control process, a voltage adjustment amount for controlling the current channel output is obtained by minimizing a voltage adjustment cost function ;​ Step S40: Update the voltage regulation value based on the preset pulse timing staggered peak method. The output voltage of each output electrode channel is used to obtain the updated output voltage update pulse sequence; among which, the voltage adjustment amount is combined with the preset pulse timing stagger method to update the first output voltage. The steps for obtaining the updated output voltage update pulse sequence from the output voltage of each output electrode channel specifically include: Based on the obtained voltage adjustment amount, it is weighted and synthesized with the current output voltage to obtain an updated target voltage: The pulse timing staggered peak method is used to set an output delay time for the first output electrode channel , wherein is a preset delay adjustment standard time, is a preset minimum pulse interval time, is a delay adjustment factor, is a voltage offset factor; According to the output delay time The output schedule is arranged, all channels output after respective delays, forming a sequence of staggered triggered output voltage update pulses; Step S50: after obtaining the updated output voltage update pulse sequence, calculate the current error at time t+1 and a voltage offset factor , a preset current deviation abnormal threshold and a voltage offset abnormal threshold , when the following conditions are met or , then execute an abnormal shunt control operation; wherein the steps of the abnormal shunt control operation specifically include: first setting the output voltage of the first output electrode channel at time t+1 to zero; then evenly distributing the target output current of the first output electrode channel to other output electrode channels.

2. The method for data acquisition and voltage control for a pulsed therapeutic eyewear as claimed in claim 1, wherein, In step S20, the current treatment mode is obtained and the treatment total current upper limit is set as , and the target output current is allocated according to the sensitivity weight factor . Specifically, according to the user-selected or preset treatment mode, including the basic relaxation mode, the strong stimulation mode, and the intelligent adaptive mode, the current treatment allowed treatment total current upper limit is automatically loaded, the treatment total current upper limit is used to represent the total stimulation intensity boundary that the user's skin can tolerate under the current treatment scheme; and the treatment total current upper limit is normalized and weighted allocated based on the sensitivity weight factor to obtain the target output current .

3. The method for data collection and voltage control for a pulsed therapeutic eyewear of claim 1, wherein, In step S30, the current error ; a voltage offset factor for reflecting the relative relationship between the current output electrode channel output voltage and the average voltage, wherein N is the total number of output electrode channels.

4. A data acquisition and voltage control system for a pulsed therapeutic eyeglass, applied to the data acquisition and voltage control method for a pulsed therapeutic eyeglass according to any one of claims 1 to 3, characterized in that, The data acquisition and voltage control system for the pulse treatment glasses comprises: The impedance modeling and sensitivity calculation module is used to analyze the impedance of the first pulse therapy glasses. Each output electrode channel is subjected to a probe pulse voltage of a preset amplitude. And measure the response current. The initial skin contact resistance was calculated. Construct a virtual planar coordinate system and obtain the first... Coordinates of each output electrode channel and the coordinates of the eye area's center of gravity Calculate the first Each output electrode channel relative to the centroid coordinates of the eye region geometric offset distance And construct the first based on geometric offset distance Sensitivity weighting factor for each output electrode channel Among them, the sensitivity weighting factor ,in, This is a geometric offset adjustment factor used to control the weighting of spatial distance; sensitivity weighting factor. Used to evaluate the The tolerance and risk of skin irritation to the electrode positions of each output electrode channel; The current target allocation module is used to obtain the current treatment mode and set the upper limit of the total treatment current. Based on sensitivity weighting factor Distribute target output current ; The voltage regulation quantity construction module is used to collect the voltage regulation quantity at time t in real time. Output voltage of each output electrode channel and output current Combined with the target output current Calculate current error and voltage offset factor Furthermore, the voltage regulation quantity is constructed; specifically, the step of further constructing the voltage regulation quantity includes: According to the current error and a voltage offset factor constructing a voltage regulation cost function for jointly considering the current deviation and the voltage balance among channels, the voltage regulation cost function wherein, is a weight factor of the current error of the current channel output; is a regulation factor of the relative offset of the current channel output voltage; In the control process, a voltage adjustment amount for controlling the current channel output is obtained by minimizing a voltage adjustment cost function ;​ The timing peak-shaving updating module is configured to update the output voltage of the first output electrode channel according to the voltage adjustment amount and a preset pulse timing peak-shaving method to obtain an updated output voltage updating pulse sequence. The step of updating the output voltage of the first output electrode channel according to the voltage adjustment amount and the preset pulse timing peak-shaving method to obtain the updated output voltage updating pulse sequence specifically includes: The step of updating the output voltage of the first output electrode channel according to the voltage adjustment amount and the preset pulse timing peak-shaving method to obtain the updated output voltage updating pulse sequence specifically includes: Based on the obtained voltage adjustment amount, it is weighted and synthesized with the current output voltage to obtain an updated target voltage: The pulse timing staggered peak method is used to set an output delay time for the first output electrode channel , wherein, is a preset delay adjustment standard time, is a preset minimum pulse interval time, is a delay adjustment factor, is a voltage offset factor; According to the output delay time The output schedule is arranged, all channels output after respective delays, forming a sequence of staggered triggered output voltage update pulses; an abnormal shunt control module, configured to calculate the current error at time t+1 after obtaining the updated output voltage update pulse sequence and a voltage offset factor , a preset current deviation abnormal threshold and a voltage offset abnormal threshold , when the following conditions are met or , an abnormal shunt control operation is performed; wherein the steps of the abnormal shunt control operation specifically include: first setting the output voltage of the first output electrode channel at time t+1 to zero; and then uniformly distributing the target output current of the first output electrode channel to other output electrode channels.

5. A data acquisition and voltage control device for a pulsed therapeutic eyeglass, comprising: The data acquisition and voltage control device for the pulse treatment glasses comprises a memory, a processor, and a data acquisition and voltage control program for the pulse treatment glasses stored in the memory and executable on the processor, and the data acquisition and voltage control program for the pulse treatment glasses, when executed by the processor, implements the data acquisition and voltage control method for the pulse treatment glasses in any one of claims 1 to 3.

6. A computer program product, characterised in that, The computer program product comprises a data acquisition and voltage control program for the pulse treatment glasses, and the data acquisition and voltage control program for the pulse treatment glasses, when executed by the processor, implements the data acquisition and voltage control method for the pulse treatment glasses in any one of claims 1 to 3.

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