Data acquisition and voltage control method for pulse treatment glasses

Abstract

The invention relates to the technical field of wearable medical electrical stimulation equipment, and particularly discloses a data acquisition and voltage control method for pulse treatment glasses, which comprises the following steps: acquiring skin contact impedance, and calculating an electrode offset distance; distributing the target output current according to the treatment current upper limit and the weight; calculating a current error and a voltage offset factor; updating the output voltage of each channel in combination with a pulse time sequence peak shifting mechanism; and abnormal channel shunting control is executed. In the prior art, dynamic balance and spatial stimulation distribution between channels cannot be considered only based on PID closed-loop adjustment, and especially under non-ideal conditions such as rapid impedance change or electrode contact transaction in a sensitive area of eyes of a user, refined safe stimulation control is difficult to realize. Due to the fact that sensitivity space modeling and a pulse time sequence peak shifting mechanism are introduced, dynamic balance control over multi-channel pulse voltage is achieved, and equipment stimulation safety and output uniformity are improved.

Description

Technical Field

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

[0002] Currently, pulse therapy glasses, as wearable neurostimulation devices, are widely used for relieving visual fatigue, assisting with dry eye treatment, and regulating eye muscles. However, existing devices often use fixed current output or simple single-channel feedback control. These devices lack the precise sensing and control required for varying skin contact conditions and periocular structures. This leads to problems such as uneven current output, concentrated stimulation of the electrode area, and discomfort caused by sudden voltage spikes.

[0003] For example, if some electrodes are poorly connected or located in highly sensitive areas such as the corners of the eyes during wear, traditional control methods cannot dynamically identify and correct the voltage of these channels. This can easily lead to single-channel voltage overshoot and concentrated current discharge, which not only affects the treatment effect but also poses a risk of burning sensation or transient pain. Existing technologies cannot fully meet the requirements for safe, balanced, and comfortable stimulation control of the eye area under complex conditions such as multiple electrode distributions, non-ideal fit, and dynamic impedance changes.

[0004] Therefore, there is an urgent need for a pulse therapy glasses control method that can achieve accurate data acquisition and control, dynamic voltage regulation and abnormal channel identification under multi-channel structure and dynamic physiological changes, so as to improve the uniformity, safety and individual adaptability of electrical stimulation therapy. Summary of the Invention

[0005] In response to the above-mentioned technical deficiencies, the purpose of the present invention is to propose a data acquisition and voltage control method for pulse therapy glasses, aiming to solve the technical problem that the existing technology is only based on PID closed-loop regulation and cannot take into account the dynamic balance between channels and the spatial stimulation distribution, especially under non-ideal conditions such as rapid impedance changes or abnormal electrode contact in the sensitive area of the user's eyes, making it difficult to achieve refined and safe stimulation control.

[0006] In order to solve the above technical problems, the present invention adopts the following technical solutions: The present invention provides a data acquisition and voltage control method for pulse therapy glasses.

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

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

[0009] Step S20: Get the current treatment mode and set the upper limit of the total treatment current to I0, based on the sensitivity weight factor ω i Assign target output current

[0010] 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 Calculating current error and voltage offset factor γ i (t), and further construct the voltage regulation amount;

[0011] Step S40: updating the output voltage of the i-th output electrode channel according to the voltage adjustment amount combined with a preset pulse timing staggered method to obtain an updated output voltage update pulse sequence;

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

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

[0014] Preferably, in step S20, the current treatment mode is obtained and the upper limit of the total treatment current is set to I0, and the sensitivity weight factor ω is used. i Assign target output current The steps specifically include: according to the treatment mode selected or preset by the user, including basic relaxation mode, strong stimulation mode, and intelligent adaptive mode, automatically loading the upper limit of the total treatment current allowed by the current treatment as I0, and the upper limit of the total treatment current I0 is used to represent the total stimulation intensity boundary that the user's skin can tolerate under the current treatment plan; based on the sensitivity weight factor ω i Normalize and weight the total treatment current upper limit I0 to obtain the target output current

[0015] Preferably, in step S30, the current error Voltage offset factor It is used to reflect the relative relationship between the output voltage of the current output electrode channel and the average voltage, where N is the total number of output electrode channels.

[0016] Preferably, in step S30, the step of further constructing the voltage adjustment amount specifically includes:

[0017] According to the current error and voltage offset factor γ i (t) Construct a voltage regulation cost function J(U i (t)), which is used to jointly consider the current deviation and the voltage balance between channels, the voltage regulation cost function Among them, α is the weight factor of the current channel output current error; β is the adjustment factor of the current channel output voltage relative offset;

[0018] In the control process, the voltage regulation cost function J(U i (t)), obtain the voltage adjustment value ΔU used to control the current channel output i (t).

[0019] Preferably, in step S40, the step of updating the output voltage of the i-th output electrode channel according to the voltage adjustment amount in combination with a preset pulse timing staggering method to obtain an updated output voltage updating pulse sequence specifically includes:

[0020] Based on the voltage adjustment amount obtained in step S30, it is combined with the current output voltage V i (t) Perform weighted synthesis to obtain the updated target voltage:

[0021] The pulse timing staggered method is used to set the output delay time δt for the i-th output electrode channel i , δt i =τ0+t0·k·(γ i (t)-1), where t0 is the preset delay adjustment standard time, τ0 is the preset minimum pulse interval time, k is the delay adjustment factor, γ i (t) is the voltage offset factor;

[0022] According to the output delay time δt i Arrange output scheduling so that all channels output after their respective delays, forming an output voltage update pulse sequence with staggered triggering.

[0023] Preferably, in step S50, the abnormal current shunt control operation step specifically includes: first setting the output voltage of the i-th output electrode channel at time t+1 to zero; then setting the target output current of the i-th output electrode channel to zero; Evenly distribute to other output electrode channels.

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

[0025] Impedance modeling and sensitivity calculation module, used to apply a detection pulse voltage of preset amplitude to the i-th output electrode channel in the pulse therapy glasses And measure the response current Calculate the initial skin contact impedance Construct a virtual plane coordinate system to obtain the coordinates of the i-th output electrode channel and the coordinates of the center of gravity of the eye area Calculate the coordinates of the i-th output electrode channel relative to the center of gravity of the eye area Geometric offset distance And construct the sensitivity weight factor ω of the i-th output electrode channel based on the geometric offset distance i ;

[0026] The current target allocation module is used to obtain the current treatment mode and set the upper limit of the total treatment current to I0, based on the sensitivity weight factor ω i Assign target output current

[0027] The voltage regulation module is used to collect the output voltage V of the i-th output electrode channel at time t in real time. i (t) and output current I i (t), combined with the target output current Calculating current error and voltage offset factor γ i (t), and further construct the voltage regulation amount;

[0028] The timing peak shifting update module is used to update the output voltage of the i-th output electrode channel according to the voltage adjustment amount combined with the preset pulse timing peak shifting method to obtain the updated output voltage V i (t+1);

[0029] Abnormal shunt control module, used to calculate the current error at time t+1 after the output voltage is updated and voltage offset factor γ i (t+1), preset current deviation abnormal threshold ε I and voltage deviation abnormal threshold ε V , when satisfied or |γ i (t)-1|>ε V When the abnormal diversion control operation is performed.

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

[0031] The beneficial effects of the present invention are: proposing a data acquisition and control method based on the combination of impedance sensing and spatial modeling, realizing adaptive recognition and response of multi-channel output electrodes under different skin contact states, and effectively improving the individual adaptability and control accuracy of pulse therapy glasses;

[0032] A dynamic control mechanism integrating current error and voltage offset factors was constructed, and combined with a pulse timing staggering strategy, real-time data acquisition and control of balanced output between channels was achieved. This significantly reduced the risk of localized stimulation caused by single-point current accumulation and voltage surges, improving the safety and comfort of electrical stimulation therapy. BRIEF DESCRIPTION OF THE DRAWINGS

[0033] In order to more clearly illustrate the embodiments of the present invention or the technical solutions in the prior art, the following briefly introduces the drawings required for use in the embodiments or the description of the prior art. Obviously, the drawings described below are only some embodiments of the present invention. For ordinary technicians in this field, other drawings can be obtained based on these drawings without paying any creative work.

[0034] Figure 1 This is a flow chart of a first embodiment of a data acquisition and voltage control method for pulse therapy glasses according to the present invention.

[0035] Figure 2 This is a schematic diagram of the equipment for the data acquisition and voltage control method for pulse therapy glasses of the present invention. DETAILED DESCRIPTION

[0036] The following will clearly and completely describe the technical solutions in the embodiments of the present invention in conjunction with the accompanying drawings. Obviously, the described embodiments are only part of the embodiments of the present invention, not all of the embodiments. Based on the embodiments of the present invention, all other embodiments obtained by ordinary technicians in this field without making creative efforts are within the scope of protection of the present invention.

[0037] Example 1: Figure 1 FIG. 1 is a flow chart of a first embodiment of a method for data collection and voltage control for pulse therapy glasses according to the present invention, and provides a first embodiment of a method for data collection and voltage control for pulse therapy glasses according to the present invention.

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

[0039] Step S10: Apply a detection pulse voltage of a preset amplitude to the i-th output electrode channel in the pulse therapy glasses And measure the response current Calculate the initial skin contact impedance Construct a virtual plane coordinate system to obtain the coordinates of the i-th output electrode channel and the coordinates of the center of gravity of the eye area Calculate the coordinates of the i-th output electrode channel relative to the center of gravity of the eye area Geometric offset distance And construct the sensitivity weight factor ω of the i-th output electrode channel based on the geometric offset distance i ;

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

[0041] It's understandable that 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 electrodes across the face. For example, areas near the tear glands, the corners of the eyes, and the bridge of the nose, where nerves are dense and skin is thinner, are more sensitive to electrical stimulation. Geometric offset modeling reduces the stimulation priority in these areas, thereby improving overall wearing safety and user comfort.

[0042] It should be understood that traditional multi-channel electrical stimulation control methods often adjust output based solely on impedance or current magnitude, ignoring the anatomical and physiological differences in facial structure. This can easily lead to current concentration in a single area, causing discomfort such as burning and throbbing pain. This invention, by introducing a coupled calculation model of coordinate center of gravity and offset distance, achieves a quantitative assessment of regional stimulation risk, realizing "structurally-aware current allocation logic" for the first time in an ocular pulse therapy scenario.

[0043] For example, if the first channel is located at the inner canthus, its initial contact impedance is 2.0 kΩ and the spatial offset distance is 5.0 mm; the second channel is located at the middle of the upper eyelid, its impedance is 1.2 kΩ and the offset distance is 1.0 mm; when β is set to 0.1, we get 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 its current to avoid excessive electrical stimulation in the corner of the eye area.

[0044] Step S20: Get the current treatment mode and set the upper limit of the total treatment current to I0, based on the sensitivity weight factor ω i Assign 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, according to the sensitivity weight factor ω i Assign target output current The steps specifically include: according to the treatment mode selected or preset by the user, including basic relaxation mode, strong stimulation mode, and intelligent adaptive mode, automatically loading the upper limit of the total treatment current allowed by the current treatment as I0, and the upper limit of the total treatment current I0 is used to represent the total stimulation intensity boundary that the user's skin can tolerate under the current treatment plan; based on the sensitivity weight factor ω i Normalize and weight the total treatment current upper limit I0 to obtain the target output current

[0046] It's understandable that this step ensures higher stimulation intensity output in less sensitive, low-impedance areas without exceeding the total current limit, while automatically weakening the output in channels near highly sensitive areas like the corners of the eyes and lacrimal glands. This normalized inversely proportional weighting strategy balances the dual goals of "total safety control" and "local adaptive regulation," ensuring balanced distribution of multi-channel pulse stimulation and minimizing user discomfort.

[0047] It should be understood that traditional current distribution methods are mostly based on equal distribution or linear adjustment based on impedance size. They fail to fully consider the impact of the physiological position and spatial distribution of electrodes on electrical stimulation tolerance, which can easily lead to excessive current in some areas and insufficient stimulation in others. However, by introducing a sensitivity weighting factor and constructing an inverse normalization model, this present invention achieves a dynamic distribution method for channel stimulation current, "suppressing by sensitivity and releasing by tolerance," which has greater adaptability, safety, and the ability to adjust to individual differences.

[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 Calculating current error and voltage offset factor γ i (t), and further construct the voltage regulation amount;

[0049] It should be noted that in step S30, the current error Voltage offset factor It is used to reflect the relative relationship between the current output electrode channel output voltage and the average voltage, where N is the total number of output electrode channels. In step S30, the step of further constructing the voltage adjustment amount specifically includes: according to the current error and voltage offset factor γ i (t) Construct a voltage regulation cost function J(U i (t)), which is used to jointly consider the current deviation and the voltage balance between channels, the voltage regulation cost function Among them, α is the weight factor of the current channel output current error; β is the adjustment factor of the current channel output voltage relative offset; in the control process, by minimizing the voltage regulation cost function J(U i (t)), obtain the voltage adjustment value ΔU used to control the current channel output i (t).

[0050] It can be understood that the above cost function constructs a joint model of "stimulation compliance" (current error) and "cross-channel balance" (voltage offset). It no longer relies on single-channel error control, but instead achieves dynamic adjustment with smooth convergence by modeling the squared error term, and adapts to the voltage allocation under non-ideal conditions of multi-channel electrodes.

[0051] Step S40: updating the output voltage of the i-th output electrode channel according to the voltage adjustment amount combined with a preset pulse timing staggered method to obtain an 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 regulation amount combined with the preset pulse timing staggering method to obtain the updated output voltage update pulse sequence, which specifically includes: based on the voltage regulation amount obtained in step S30, it is combined with the current output voltage V i (t) is weighted and synthesized to obtain the updated target voltage: the pulse timing staggered method is used to set the output delay time δt for the i-th output electrode channel i , δt i =τ0+t0·k·(γ i (t)-1), where t0 is the preset delay adjustment standard time, τ0 is the preset minimum pulse interval time, k is the delay adjustment factor, γ i (t) is the voltage offset factor; according to the output delay time δt i Arrange output scheduling so that all channels output after their respective delays, forming an output voltage update pulse sequence with staggered triggering.

[0053] It's understandable that the "pulse timing staggering" method introduced in this step is an optimization based on the traditional synchronous output mechanism. It aims to address issues such as current convergence, excessive electrical stimulation, and burning sensations that can arise when multiple channels are activated simultaneously. By delaying the triggering of output voltage updates, the stimulation energy is effectively dispersed in the temporal domain, guiding the current to be more evenly distributed across the skin surface, reducing the risk of single-point charge accumulation.

[0054] It should be understood that traditional pulsed electrical stimulation systems mostly use a timer-driven, synchronously triggered structure. This output behavior can easily cause "peak coupling" in multi-electrode structures, where multiple channels trigger at high voltage at the same time, resulting in localized instantaneous current density, which can cause pain or tissue discomfort, particularly in sensitive areas of the eye. This invention, by designing a dynamic peak-shifting strategy based on a voltage offset factor, binds full-channel voltage state feedback to the scheduling time for the first time, achieving a "higher the bias, the greater the delay" balancing mechanism, effectively improving stimulation uniformity and system response stability.

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

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

[0057] Understandably, the design of this abnormal current diversion mechanism is intended to prevent system imbalances and potential safety hazards caused by poor contact, abnormal impedance, or concentrated local stimulation in a single electrode channel during use. By proactively shutting off abnormal channels and dynamically adjusting the target currents in the remaining channels, the overall treatment process is protected from single-point anomalies, achieving "fault-tolerant operation" and "inter-channel coordinated compensation."

[0058] It should be understood that traditional pulse therapy devices often only issue an alarm or suspend all output when a channel anomaly occurs, lacking the ability to locally isolate the faulty channel and redistribute current. The proposed abnormal current diversion strategy not only improves the continuity and stability of system operation, but also, through a dynamic balancing mechanism for target current, avoids overvoltage in the remaining channels due to "sudden load increases," achieving more refined safety control.

[0059] Example 2: Furthermore, the present invention provides a data acquisition and voltage control system for pulse therapy glasses, which utilizes the data acquisition and voltage control method for pulse therapy glasses described in the above-mentioned embodiment, thereby resolving the technical issues surrounding data acquisition and voltage control for pulse therapy glasses. Compared to the prior art, the data acquisition and voltage control system for pulse therapy glasses provided by the present invention achieves the same beneficial effects as the data acquisition and voltage control method for pulse therapy glasses provided in the above-mentioned embodiment. Other technical features of the data acquisition and voltage control system for pulse therapy glasses are the same as those disclosed in the above-mentioned embodiment and are not further elaborated here.

[0060] Example 3: The present invention provides a data acquisition and voltage control device for pulse therapy glasses, please refer to Figure 2A data acquisition and voltage control device for pulse therapy glasses includes: at least one processor; and a memory communicatively connected to the at least one processor; wherein the memory stores instructions executable by the at least one processor, and the instructions are executed by the at least one processor to enable the at least one processor to perform the data acquisition and voltage control method for pulse therapy glasses described in the first embodiment. The data acquisition and voltage control device for pulse therapy glasses in the embodiments of the present invention may include, but is not limited to, mobile terminals such as mobile phones, laptop computers, digital broadcast receivers, PDAs (Personal Digital Assistants), PADs (Portable Application Descriptions), PMPs (Portable Media Players), in-vehicle terminals (e.g., in-vehicle navigation terminals), and fixed terminals such as digital TVs and desktop computers. The data acquisition and voltage control device for pulse therapy glasses is merely an example and should not limit the functionality or scope of use of the embodiments of the present invention. A data acquisition and voltage control device for pulse therapy glasses may include a processing device 1001 (e.g., a central processing unit, a graphics processing unit, etc.), which can perform various appropriate actions and processes based on programs stored in a read-only memory (ROM) 1002 or programs loaded from a storage device 1003 into a random access memory (RAM) 1004. RAM 1004 also stores various programs and data required for the operation of the data acquisition and voltage control device for pulse therapy glasses. Processing device 1001, ROM 1002, and RAM 1004 are interconnected via a bus 1005. An input / output (I / O) interface 1006 is also connected to the bus. Typically, the following systems can be connected to the I / O interface 1006: input devices 1007 including, for example, a touch screen, touchpad, keyboard, mouse, image sensor, microphone, accelerometer, gyroscope, etc.; output devices 1008 including, for example, a liquid crystal display (LCD), speaker, vibrator, etc.; storage devices 1003 including, for example, a magnetic tape, hard disk, etc.; and communication devices 1009. Communication devices 1009 can allow a data acquisition and voltage control device for pulse therapy glasses to communicate wirelessly or wired with other devices to exchange data. While the figure shows a data acquisition and voltage control device for pulse therapy glasses having various systems, it should be understood that implementation or presence of all the illustrated systems is not required. More or fewer systems may alternatively be implemented or present.

[0061] Example 4: The present invention also provides a computer program product, comprising a computer program. When executed by a processor, the computer program implements the steps of the aforementioned method for data acquisition and voltage control for pulse therapy glasses. The computer program product provided by the present invention can solve the technical problem of data acquisition and voltage control for pulse therapy glasses. Compared to the prior art, the beneficial effects of the computer program product provided by the present invention are similar to those of the method for data acquisition and voltage control for pulse therapy glasses provided in the aforementioned embodiments, and are not further elaborated here.

[0062] In particular, according to the embodiments disclosed in the present invention, the processes described above with reference to the flowcharts can be implemented as computer software programs. For example, the embodiments disclosed in the present invention 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 an embodiment, the computer program can be downloaded and installed from a network via a communication device, or installed from a storage device 1003, or installed from a ROM 1002. When the computer program is executed by the processing device 1001, the above-mentioned functions defined in the method of the embodiment disclosed in the present invention are performed.

[0063] It should be understood that the various parts disclosed in the present invention can be implemented using hardware, software, firmware, or a combination thereof. In the description of the above embodiments, specific features, structures, materials, or characteristics can be combined in any appropriate manner in any one or more embodiments or examples.

[0064] Obviously, those skilled in the art may make various changes and modifications to the present invention without departing from the spirit and scope of the present invention. Thus, if such changes and modifications fall within the scope of the claims and their equivalents, the present invention is intended to include such changes and modifications.

Claims

1. A data acquisition and voltage control method for pulse therapy glasses, characterized in that: Methods include: Step S10: Apply a detection pulse voltage of a preset amplitude to the i-th output electrode channel in the pulse therapy glasses and measure the response current Calculate the initial skin contact impedance Construct a virtual plane coordinate system to obtain the coordinates of the i-th output electrode channel and the coordinates of the center of gravity of the eye area Calculate the coordinates of the i-th output electrode channel relative to the center of gravity of the eye area Geometric offset distance And construct the sensitivity weight factor ω of the i-th output electrode channel based on the geometric offset distance i ; Step S20: Get the current treatment mode and set the upper limit of the total treatment current to I0, based on the sensitivity weight factor ω i Assign target output current 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 Calculating current error and voltage offset factor γ i (t), and further construct the voltage regulation amount; Step S40: updating the output voltage of the i-th output electrode channel according to the voltage adjustment amount combined with a preset pulse timing staggered method to obtain an updated output voltage update pulse sequence; Step S50: After obtaining the updated output voltage update pulse sequence, calculate the current error at time t+1 and voltage offset factor γ i (t+1), preset current deviation abnormal threshold ε I and voltage deviation abnormal threshold ε V , when satisfied or |γ i (t+1)-1|>ε V When the abnormal diversion control operation is performed.

2. The data acquisition and voltage control method for pulse therapy glasses according to claim 1, characterized in that: In step S10, the sensitivity weight factor Among them, β is the geometric offset adjustment factor, which is used to control the influence weight of spatial distance; the sensitivity weight factor ω i Used to evaluate the tolerance and risk of skin irritation at the electrode position of the i-th output electrode channel.

3. The data acquisition and voltage control method for pulse therapy glasses according to claim 1, characterized in that: In step S20, the current treatment mode is obtained and the upper limit of the total treatment current is set to I0, according to the sensitivity weight factor ω i Assign target output current The steps specifically include: according to the treatment mode selected or preset by the user, including basic relaxation mode, strong stimulation mode, and intelligent adaptive mode, automatically loading the upper limit of the total treatment current allowed by the current treatment as I0, and the upper limit of the total treatment current I0 is used to represent the total stimulation intensity boundary that the user's skin can tolerate under the current treatment plan; based on the sensitivity weight factor ω i Normalize and weight the total treatment current upper limit I0 to obtain the target output current 4. The data acquisition and voltage control method for pulse therapy glasses according to claim 1, characterized in that: In step S30, the current error Voltage offset factor It is used to reflect the relative relationship between the output voltage of the current output electrode channel and the average voltage, where N is the total number of output electrode channels.

5. The data acquisition and voltage control method for pulse therapy glasses according to claim 1, characterized in that: In step S30, the step of further constructing the voltage adjustment amount specifically includes: According to the current error and voltage offset factor γ i (t) Construct a voltage regulation cost function J(U i (t)), which is used to jointly consider the current deviation and the voltage balance between channels, the voltage regulation cost function Among them, α is the weight factor of the current channel output current error; β is the adjustment factor of the current channel output voltage relative offset; In the control process, the voltage regulation cost function J(U i (t)), obtain the voltage adjustment value ΔU used to control the current channel output i (t).

6. The data acquisition and voltage control method for pulse therapy glasses according to claim 1, characterized in that: In step S40, the output voltage of the i-th output electrode channel is updated according to the voltage adjustment amount in combination with the preset pulse timing staggering method to obtain an updated output voltage update pulse sequence, which specifically includes: Based on the voltage adjustment amount obtained in step S30, it is combined with the current output voltage V i (t) Perform weighted synthesis to obtain the updated target voltage: The pulse timing staggered method is used to set the output delay time δt for the i-th output electrode channel i , δt i =τ0+t0·k·(γ i (t)-1), where t0 is the preset delay adjustment standard time, τ0 is the preset minimum pulse interval time, k is the delay adjustment factor, γ i (t) is the voltage offset factor; According to the output delay time δt i Arrange output scheduling so that all channels output after their respective delays, forming an output voltage update pulse sequence with staggered triggering.

7. The data acquisition and voltage control method for pulse therapy glasses according to claim 1, characterized in that: In step S50, the abnormal current shunt control operation specifically includes: first setting the output voltage of the i-th output electrode channel at time t+1 to zero; then setting the target output current of the i-th output electrode channel to zero; Evenly distribute to other output electrode channels.

8. A data acquisition and voltage control system for pulse therapy glasses, applied to a data acquisition and voltage control method for pulse therapy glasses according to any one of claims 1 to 7, characterized in that: The data acquisition and voltage control system for the pulse therapy glasses includes: Impedance modeling and sensitivity calculation module, used to apply a detection pulse voltage of preset amplitude to the i-th output electrode channel in the pulse therapy glasses And measure the response current Calculate the initial skin contact impedance Construct a virtual plane coordinate system to obtain the coordinates of the i-th output electrode channel and the coordinates of the center of gravity of the eye area Calculate the coordinates of the i-th output electrode channel relative to the center of gravity of the eye area Geometric offset distance And construct the sensitivity weight factor ω of the i-th output electrode channel based on the geometric offset distance i ; The current target allocation module is used to obtain the current treatment mode and set the upper limit of the total treatment current to I0, based on the sensitivity weight factor ω i Assign target output current The voltage regulation module is used to collect the output voltage V of the i-th output electrode channel at time t in real time. i (t) and output current I i (t), combined with the target output current Calculating current error and voltage offset factor γ i (t), and further construct the voltage regulation amount; The timing peak shifting update module is used to update the output voltage of the i-th output electrode channel according to the voltage adjustment amount combined with the preset pulse timing peak shifting method to obtain the updated output voltage V i (t+1); Abnormal shunt control module, used to calculate the current error at time t+1 after the output voltage is updated and voltage offset factor γ i (t+1), preset current deviation abnormal threshold ε I and voltage deviation abnormal threshold ε V , when satisfied or |γ i (t)-1|>ε V When the abnormal diversion control operation is performed.

9. A data acquisition and voltage control device for pulse therapy glasses, characterized in that: The data acquisition and voltage control device for pulse therapy glasses includes: a memory, a processor, and a data acquisition and voltage control program for pulse therapy glasses stored in the memory and runnable on the processor. When the data acquisition and voltage control program for pulse therapy glasses is executed by the processor, a data acquisition and voltage control method for pulse therapy glasses according to any one of claims 1 to 7 is implemented.

10. A computer program product, characterized in that The computer program product includes a data acquisition and voltage control program for pulse therapy glasses. When the data acquisition and voltage control program for pulse therapy glasses is executed by a processor, a data acquisition and voltage control method for pulse therapy glasses according to any one of claims 1 to 7 is implemented.

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