Electrochromic glasses control method based on health monitoring, glasses, medium and processor

Abstract

The invention discloses an intelligent electrochromic glasses control method based on health monitoring, glasses, a medium and a processor, and relates to the technical field of intelligent glasses color change control. According to the method, physiological health data and ambient light data of a wearer are synchronously collected, a user regulation and control instruction is combined, a visual load state is analyzed in real time, a lens adjustment requirement matched with the physiological state is generated, a coloring and fading control threshold value of an electrochromic lens is adaptively adjusted, and finally the lens is driven to dynamically adjust the coloring state. The system comprises an acquisition module, a main control module and a control module, and realizes intelligent and personalized color change control. The problem that traditional electrochromic glasses only depend on ambient light and cannot adapt to the physiological state of a user is solved, and the visual comfort and health adaptability are improved.

Description

Technical Field

[0001] This invention relates to the field of photochromic control technology for smart glasses, and particularly to a control method, glasses, medium, and processor for electrochromic glasses based on health monitoring. Background Technology

[0002] In the field of smart wearable devices, smart glasses, as a typical wearable device, are seeing a growing trend towards intelligent control of their electrochromic function and multi-parameter health monitoring. Currently, electrochromic smart glasses on the market generally suffer from the following shortcomings: Defects in color-changing threshold control: Most of them can only passively change color based on ambient light intensity, and cannot make personalized and autonomous adjustment of the color-changing threshold according to the user's specific situation (such as usage habits, visual needs under different scenarios and physical conditions). This easily leads to problems such as "insufficient coloring under strong light causing visual stimulation" or "excessive coloring under weak light causing blurred vision", making it difficult to adapt to the visual experience needs of complex scenes and situations.

[0003] Therefore, there is a need for a method for controlling electrochromic glasses based on health monitoring, as well as glasses, media, and processor. Summary of the Invention

[0004] To address the problem that existing technologies struggle to adapt to the visual experience requirements of complex scenes and conditions, this invention provides a control method, glasses, medium, and processor for electrochromic glasses based on health monitoring, capable of adapting to the visual experience needs of complex scenes and conditions. The specific technical solution is as follows: A method for controlling electrochromic glasses based on health monitoring includes the following steps: S1: Synchronously collects the wearer's physiological health data and ambient light data, and listens for control commands from the user via Bluetooth module; S2: When an adjustment command is detected, the wearer's visual load status is analyzed by combining the physiological health data at the time of the adjustment command or within the adjacent time window, and a lens adjustment requirement that matches the actual physiological state is generated based on the visual load status. S3: Adaptively adjust the tinting fading control threshold of the electrochromic lens according to the lens adjustment requirements; S4: Generate lens driving instructions based on the control threshold and the real-time acquired ambient light data; S5: Drive the electrochromic lens to change its coloration state according to the lens driving command.

[0005] Furthermore, in step S2, when an adjustment command is detected, the wearer's visual load status is analyzed by combining the physiological health data within the time window of the adjustment command's occurrence or a nearby time window, and a lens adjustment requirement matching the actual physiological state is generated based on the visual load status, including the following steps: S21: Based on the moment when the control command is triggered, extract heart rate, blood oxygen saturation, and body temperature data within a time window before and after that moment to assess the wearer's visual load status. S22: Determine the demand correction factor based on visual load status. The control commands are then modified to obtain the final lens adjustment requirements. S23: Fine-tune the correction coefficient based on the real-time trend of physiological health data to achieve smooth optimization of adjustment needs during a single command execution, so that the lens status dynamically matches the user's ever-changing physiological needs.

[0006] Furthermore, in step S21, the model for assessing the wearer's visual load state is as follows: ; in, Physiological stress index; The ambient light-physiological coupling coefficient; This is a time-dynamic adjustment factor.

[0007] Furthermore, the physiological stress index determination model is as follows: ; ; ; ; ; in, For dynamic components of heart rate; This refers to the blood oxygen penalty value. This represents the body temperature trend value. The standard deviation of heart rate over the last 30 seconds; The average heart rate over the last 30 seconds; For current real-time heart rate measurement; The user's resting heart rate; This is the maximum heart rate value; This represents the heart rate variability. This is the heart rate sensitivity coefficient; Blood oxygen sensitivity coefficient; This indicates the current real-time blood oxygen saturation. This refers to the current real-time blood oxygen saturation. Normal healthy blood oxygen levels; This is the warning line for low blood oxygen levels; This is the current real-time body surface temperature; Baseline body temperature of the user; The threshold for judging mild fever; The rate of change of body temperature; Trend weight.

[0008] Furthermore, the model for determining the ambient light-physiological coupling coefficient is as follows: ; ; Ideal light intensity; As a baseline stress index; For users' preferred light intensity; Physiological sensitivity coefficient; This is the normalized value of the current ambient light intensity; This indicates a mismatch in weights. It is a non-linear exponent.

[0009] Furthermore, the time-dynamic adjustment factor The defined model is as follows: ; ; in, It is the attenuation constant; This represents the recovery ability value. The start time; Historical VLS values; The current time; The cumulative intensity coefficient; s represents the past time. This is a discount factor for recovery capacity; For real-time heart rate variability; This refers to resting heart rate variability.

[0010] Furthermore, in step S2, the formula for generating lens adjustment requirements that match the actual physiological state based on visual load status is as follows: ; in, This is the final adjustment amount for the lens tinting threshold; The color threshold adjustment amount corresponding to the user's original control command; This is the demand adjustment factor.

[0011] An electrochromic lens based on health monitoring, applied to the aforementioned control method for electrochromic lenses based on health monitoring, includes: The acquisition module is used to synchronously collect the wearer's physiological health data and ambient light data, and listen for control commands from the user via Bluetooth module; The main control module is used to analyze the wearer's visual load state when a control command is detected, in combination with the physiological health data within the time window of the control command occurrence, and generate lens adjustment requirements that match the actual physiological state based on the visual load state; adaptively adjust the color fading control threshold of the electrochromic lens according to the lens adjustment requirements; and generate lens driving commands based on the control threshold and the real-time collected ambient light data. A control module is used to drive the electrochromic lens to change its tinting state according to the lens driving command.

[0012] A computer-readable storage medium includes a stored program, wherein, when the program is executed, it controls the device where the computer-readable storage medium is located to perform the above-described electrochromic glasses control method based on health monitoring.

[0013] A processor for running a program, wherein the program executes the above-described electrochromic glasses control method based on health monitoring.

[0014] Compared with the prior art, the beneficial effects of the present invention are as follows: 1. Achieve personalized adaptive adjustment: Breaking through the traditional passive color-changing mode that relies solely on ambient light, it integrates multi-dimensional physiological data such as heart rate, blood oxygen, and body temperature to assess the user's visual load status in real time, so that the color-changing threshold dynamically matches the user's actual physiological needs and fatigue level, thereby improving visual comfort and health protection.

[0015] 2. Enhance system intelligence and fit: Introduce a visual load state (VLS) assessment model, combined with historical data and recovery capability analysis, to achieve smooth optimization and dynamic tracking of the accommodation process, making the lens response closer to the user's real state of instantaneous changes, and reducing the problems of over-adjustment or under-adjustment.

[0016] 3. Optimize power consumption and battery life: By using an on-demand adjustment mechanism based on physiological state, unnecessary frequent color-changing operations are avoided. Combined with low-power hardware design and power management strategies, the overall system power consumption is significantly reduced, the device's battery life is extended, and the ease of use is improved.

[0017] 4. Enhance scene adaptability and user experience: The system can automatically adjust the coloring strategy according to different lighting environments and user physiological states, supports manual intervention and learning optimization by users, takes into account both automation and personalization needs, is suitable for long-term wear in multiple scenarios, and improves product practicality and market competitiveness. Attached Figure Description

[0018] To more clearly illustrate the specific embodiments of the present invention or the technical solutions in the prior art, the accompanying drawings used in the description of the specific embodiments or the prior art will be briefly introduced below. In all the drawings, similar elements or parts are generally identified by similar reference numerals. In the drawings, the elements or parts are not necessarily drawn to scale.

[0019] Figure 1 This is a flowchart illustrating a control method for electrochromic glasses based on health monitoring. Figure 2 This is a schematic diagram of the circuit structure of an electrochromic glasses based on health monitoring. Detailed Implementation

[0020] 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, not all, of the embodiments of the present invention. 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.

[0021] It should be understood that, when used in this application, the terms "comprising" and "including" indicate the presence of the described features, integrals, steps, operations, elements, and / or components, but do not exclude the presence or addition of one or more other features, integrals, steps, operations, elements, components, and / or collections thereof.

[0022] It should also be understood that the terminology used in this specification is for the purpose of describing particular embodiments only and is not intended to limit the invention. As used in this specification and the appended claims, the singular forms “a,” “an,” and “the” are intended to include the plural forms unless the context clearly indicates otherwise.

[0023] It should also be further understood that the term “and / or” as used in this application refers to any combination of one or more of the associated listed items, as well as all possible combinations, and includes such combinations.

[0024] Example 1 like Figure 1 The diagram shows a flowchart of a control method for electrochromic glasses based on health monitoring, applied to smart glasses including a main control module, electrochromic lenses, a health monitoring module, a Bluetooth module, and a photosensitive module. The method includes the following steps: S1: Synchronously collects the wearer's physiological health data and ambient light data, and listens for control commands from the user via Bluetooth module. Specifically, it includes the following: S11: Physiological health data collection: Heart rate and blood oxygen saturation acquisition: The heart rate and blood oxygen module (such as MAX30102) integrated on the inside of the temple periodically acquires the raw photovolume pulse wave (PPG) signal from the skin behind the wearer's ear. The signal is transmitted to the main control MCU via the I²C interface (PB6 / SCL, PB7 / SDA), and the heart rate (HR) and blood oxygen saturation (SpO2) values ​​are analyzed in real time by the built-in algorithm.

[0025] Body temperature acquisition: The body temperature behind the ear is acquired by a body temperature module (such as MLX90614) located on the inside of the temple, using non-contact infrared thermometry. Combined with the ambient temperature compensation algorithm, accurate human body temperature data is output and transmitted to the main control MCU via the I²C bus (PB10 / SCL, PB11 / SDA).

[0026] S12: Ambient light data acquisition: The ambient light intensity is sensed in real time by a photosensitive module (such as TEMT6000) located in the recess of the lens frame. Its output current signal is connected to the ADC channel of the main control MCU through the PA0 pin, converted into a voltage signal and converted into an analog-to-digital signal. Finally, it is mapped to the actual light intensity value in lux through a preset calibration curve.

[0027] S13: User control command monitoring: A communication link is established with the main control MCU via the UART serial port (PA9 / TX, PA10 / RX) of the Bluetooth module (such as HC-05), and the structured control command data packets sent from the paired mobile terminal (such as mobile APP) are monitored and received in real time. The command content includes, but is not limited to: manually adjusting the coloring / fading threshold, switching between adaptive / manual mode, and querying the device status.

[0028] S2: When an adjustment command is detected, the wearer's visual load status is analyzed by combining the physiological health data within the time window of the command's occurrence or a nearby time window. Based on the visual load status, a lens adjustment requirement matching the actual physiological state is intelligently generated. This lens adjustment requirement may be larger or smaller than the adjustment requirement in the control command. Specifically, the following sub-steps are included: S21: Based on the moment the control command is triggered, extract heart rate, blood oxygen saturation, and body temperature data within a time window before and after that moment (e.g., the most recent 30 seconds). Assess the wearer's visual load status using a built-in algorithm model.

[0029] Visual load status It consists of three core dimensions: ; in Physiological stress index; The ambient light-physiological coupling coefficient; This is a time-dynamic adjustment factor.

[0030] The calculation employs fuzzy logic and nonlinear transformation, focusing not only on absolute values ​​but also on trends and steady-state deviations. ; ; ; in, The standard deviation of heart rate over the last 30 seconds (reflecting a decrease in heart rate variability, HRV); The average heart rate over the last 30 seconds; For current real-time heart rate measurement; The user's resting heart rate; This represents the theoretical maximum heart rate. Innovation: It not only considers the increase in heart rate but also the decrease in heart rate variability (a sign of fatigue). This represents the heart rate variability. This is the heart rate sensitivity coefficient; Blood oxygen sensitivity coefficient; This is the heart rate variability coefficient; The lower the heart rate variability The smaller the value, the higher the stress index; The lower the blood oxygen level, the larger the denominator, but the overall non-linearity is reflected in an exponential form. This indicates the current real-time blood oxygen saturation. This refers to the dynamic components of heart rate.

[0031] ; This refers to the current real-time blood oxygen saturation. Normal healthy blood oxygen levels; This is the warning line for low blood oxygen levels; This is the blood oxygen penalty value. Innovation: Exponential penalty; a slight decrease in blood oxygen (e.g., from 98% to 96%) has little impact, but the penalty increases sharply below 95%.

[0032] ; This is the current real-time body surface temperature; Baseline body temperature of the user; The threshold for judging mild fever; The rate of change in body temperature (the slope of a linear regression over the last 60 seconds) includes the rate of increase; rapid temperature rise reflects stress better than slow temperature rise. Trend weighting; This represents the body temperature trend value.

[0033] Ambient light-physiological coupling coefficient The degree of mismatch between ambient light intensity and physiological response: ; ; Ideal light intensity; The baseline stress index is the Φ value of the user in a baseline state (such as a relaxed state). Based on user preference for light intensity (obtained through historical learning); The physiological sensitivity coefficient (default 0.3); This is the normalized value of the current ambient light intensity; Physiological stress index; The weight for mismatch is 0.8 by default; This is a non-linear exponent, with a default value of 1.5.

[0034] Logic: When heart rate increases, the user's preferred comfortable light intensity decreases.

[0035] Time-based dynamic adjustment factor Considering the cumulative effect of load and recovery capacity, the formula is as follows: ; ; in, The decay constant (e.g., 0.05 / second) represents the load memory duration; This represents the recovery ability value. The start time; Historical VLS values; The current time; The cumulative intensity coefficient; s represents the past time. This is a discount factor for recovery capacity; To measure real-time heart rate variability, a sliding window (e.g., 30 seconds) is used to calculate the standard deviation of heart rate in real time. ; To measure resting heart rate variability, for first-time users or those who actively trigger calibration, measure for 3-5 minutes in a resting state and take the average of the standard deviations of heart rate as the mean. .

[0036] The visual load state was normalized as follows: ; in, This is the minimum value of VLS; This is the maximum value of VLS; This is the normalized value for visual load status.

[0037] This indicates low load and stable condition; This indicates a moderate load and the environmental adaptation period. This indicates a high workload and mild fatigue. This indicates a state of high load and strong stress.

[0038] For example, if the heart rate is consistently high and the blood oxygen saturation is decreasing, combined with strong ambient light, it can be determined that the user may be in a state of "visual fatigue or strong light stress"; conversely, if the physiological data is stable but the ambient light changes drastically, it may be determined as "ambient light adaptation period".

[0039] S22: Determine the demand correction factor based on visual load status. The control commands are then modified to obtain the final lens adjustment requirements. Specifically, this includes: S221: Determine the demand correction factor based on visual load status. The formula is as follows: Note: Under high load, the correction factor decreases linearly with the load (more aggressive protection); under medium load, it fluctuates sinusoidally, simulating natural adjustment fluctuations; under low load, it makes conservative adjustments, close to the user's instructions.

[0040] S222: The control command is modified to obtain the final lens adjustment requirement, as shown in the following formula: ; in, The shading threshold adjustment amount corresponding to the user's original control command is expressed as a percentage of light transmittance. This represents the final adjustment amount for the lens tinting threshold, expressed as a percentage of light transmittance.

[0041] For example, if the user command is "increase shading under strong light" (lower threshold), but the system judges the state as "visual fatigue", it may apply an enhancement factor (such as 1.2) to make the final actual shading requirement stronger than the user command (the threshold is even lower) in order to provide more protection.

[0042] Conversely, if the user's instruction is "increase coloring", but the system judges that the user's physiological state is stable and the visual load is low, a conservative coefficient (such as 0.8) may be applied to avoid over-adjustment and maintain visual transparency.

[0043] S23: Based on the real-time trend of physiological health data (such as whether the heart rate continues to accelerate or whether blood oxygenation has stabilized and recovered), the correction coefficient is finely adjusted to achieve smooth optimization of adjustment needs during a single instruction execution, so that the lens status dynamically matches the user's rapidly changing physiological needs.

[0044] S3: Adaptively adjusts the tinting fading control threshold of the electrochromic lens according to the lens adjustment requirements.

[0045] S31: Obtain the current tinting fading control threshold state of the electrochromic lens.

[0046] S31: Read the currently set shading threshold from system memory. and fading threshold These correspond to the lower limit of light intensity at which the lens begins to color in strong light and the upper limit of light intensity at which it begins to fade in low light. The initial threshold can be set according to user preferences or factory defaults.

[0047] S32: Lens adjustment requirements based on step S2 Combined with real-time ambient light data Calculate the new coloring threshold and fading threshold The formula is adjusted as follows: ; ; in: and These are the unit adjustments for the tinting threshold and fading threshold (unit: Lux / percentage transmittance), pre-calibrated based on the lens response characteristics.

[0048] Direction adjustment instructions: If (If enhanced coloring is needed), then reduce... and This allows the lens to begin tinting even under lower light intensity; if (To reduce coloring), then increase and Delaying the coloring response.

[0049] S33: Perform a reasonableness check and boundary protection on the new threshold to ensure that the new threshold is within the physical working range of the lens. ; ; in, , These are the lower and upper limits of the coloring threshold, respectively; , These are the lower and upper limits of the fading threshold.

[0050] If the value exceeds the limit, it will be automatically truncated to the nearest boundary value, and the out-of-bounds event will be recorded in the system log.

[0051] S34: Update the control threshold and synchronize it to the driver module.

[0052] Those that pass the verification and Write to non-volatile memory (such as EEPROM) and update the threshold register in the main control MCU in real time, so that step S4 can call to generate lens drive instructions.

[0053] S4: Generate lens driving instructions based on the control threshold and the real-time acquired ambient light data.

[0054] Specifically, it includes the following sub-steps: S41: Obtain real-time ambient light intensity.

[0055] Real-time reading of current ambient light intensity value from the photosensor module (Unit: Lux), this value has been converted to actual light intensity using ADC sampling and calibration curves.

[0056] S42: Compare and determine with the adjusted control threshold.

[0057] Read the updated shading threshold in step S34 and fading threshold Perform the following logical judgment: like ≥ This indicates that the current ambient light intensity has exceeded the tinting trigger threshold. The lens tinting should be controlled to reduce light transmittance, and the tinting drive logic should be entered.

[0058] like ≤ This indicates that the current ambient light intensity is below the fading trigger threshold. The lens fading should be controlled to improve light transmittance, and the fading driving logic should be entered.

[0059] like < < This indicates that the current light intensity is in the "maintain range" and there is no need to change the lens condition; the current tinting / fading state will be maintained.

[0060] S43: Combine historical states with hysteresis handling to avoid frequent switching.

[0061] To prevent frequent lens tinting / fading caused by small fluctuations in ambient light around a threshold, a hysteresis range is introduced. and (e.g., ±50 Lux). The actual judgment logic is adjusted as follows: If the current lens is faded and Coloring is only triggered at that time; If the current lens is tinted and Only then will fading be triggered.

[0062] S44: Based on the judgment result, generate the corresponding driving instruction data packet. The driving instruction includes the instruction type, target transmittance, driving voltage, and driving duration. The parameters are determined as follows: I. Instruction Type: Color (ON) / Fade (OFF) / Hold (HOLD); II. Target transmittance: Based on and Calculate the recommended percentage of light transmittance; the target light transmittance reflects the light transmittance state the lens should achieve after this drive, determined by the current light transmittance and accommodation requirements, and is smoothly fine-tuned according to the visual load state: ; ; Drive voltage and duration: Based on the voltage-transmittance response curve of the electrochromic lens, determine the drive voltage value (e.g., ±2.5V) and duration (e.g., 200ms). in, This is the visual load fine-tuning coefficient (default 0.4), used to control the influence of visual load on accommodation within a reasonable range (e.g., ±20%). This coefficient can be set during lens calibration. The current lens transmittance (%) is maintained by the system in real time.

[0063] Value range: ,in , This refers to the physical limits of the lens (e.g., 15%~85%).

[0064] III. Driving Voltage With drive duration Calculation formula.

[0065] The driving voltage and duration need to be determined based on the change in target transmittance ΔT and the electrochemical response characteristics of the lens.

[0066] 1. Driving voltage : ; in, This is the lens drive bias voltage (e.g., +0.8V), which is the minimum voltage required to activate photochromism. The voltage-transmittance change slope (V / %) is obtained from the lens's "voltage-transmittance response curve".

[0067] Voltage polarity: If <0 (colored), output positive voltage (e.g., +). );like >0 (fading), output negative voltage (e.g., -) ).

[0068] 2. Drive duration : ; in, To ensure stable changes in lens state, the minimum driving pulse width (e.g., 80ms) is used. The value represents the change in light transmittance per unit time (ms / %), calibrated by the lens response speed.

[0069] S5: Drive the electrochromic lens to change its coloration state according to the lens driving command, and save the current lens state, physiological health data and adjustment log.

[0070] S51: Drive Instruction Execution and Voltage Output. Based on the lens drive instruction generated by S4, the main control MCU outputs corresponding level signals to the control module through its general-purpose input / output pins (such as PA2 and PA3). If the instruction is "colored" (ON), the PA2 pin outputs a high level for the specified drive duration. If the signal is "faded" (OFF), pin PA3 will output a high level for the corresponding duration. Upon receiving the high-level signal, the control module uses its internal drive circuit to convert the system supply voltage (3.3V or 3.7V) into the target drive voltage required by the lens. The driving voltage is applied to both ends of the conductive layer of the electrochromic lens. The polarity and amplitude of the driving voltage strictly follow the parameter settings in the instructions to ensure that the electrochemical response of the lens coloring or fading process meets expectations.

[0071] S52: Real-time monitoring and feedback of lens status. During the drive process, the main control MCU indirectly determines the progress of lens status transition by monitoring changes in the voltage across the lens or the current through the series sampling resistor. Simultaneously, the system tracks ambient light intensity data in real time and, combined with the lens's expected transmittance change model (based on a calibrated voltage-transmittance curve), estimates the current actual transmittance of the lens. If, after the drive duration ends, the light sensitivity value detected after ambient light passes through the lens does not reach the expected range of change (e.g., the deviation exceeds ±5%), a fine-tuning drive will be automatically triggered to ensure that the lens state is consistent with the command target.

[0072] S53: Status Confirmation and System Update. After the drive process is completed, the main control MCU updates the lens transmittance value in its internal status register. for The system records whether the lens is currently in a "colored" or "faded" state. Simultaneously, it writes the key parameters used in this drive (including drive type, voltage value, duration, target transmittance, and actual estimated transmittance) to a temporary cache for later log storage.

[0073] S54: Multi-source data synchronous storage. The main control MCU packages the following three types of data into a complete adjustment log record and stores it in non-volatile memory (such as EEPROM or Flash): Lens status data: including current light transmittance Coloring / fading status, timestamp; Physiological health data: Heart rate, blood oxygen saturation, body temperature and their changing trends within a time window (e.g., 30 seconds) before and after the moment the driving command is generated; Environmental and command data: Real-time ambient light intensity The tinting / fading threshold used in this study and User's original instructions Revised instructions Visual load status and the correction factors used .

[0074] S55: Log Structure and Circular Storage Management. Each log record uses a fixed-length binary format, including a frame header, data type marker, timestamp, data area, and checksum. The system establishes a circular storage area, automatically overwriting the oldest record when the storage space is full, ensuring continuous preservation of the most recent adjustment history within limited storage capacity. Simultaneously, the system supports uploading logs for a specified time period to paired mobile terminals via Bluetooth for subsequent data analysis and user behavior learning.

[0075] S56: Status Synchronization and User Feedback. After completing the drive and save operations, the main control MCU sends a status synchronization message to the connected mobile terminal (such as a mobile APP) via Bluetooth module. The message includes the current lens status, key physiological parameters, and a summary of the most recent adjustment, so that the user can view the glasses' working status and health data trend graph in real time on the APP interface.

[0076] In practice, the following steps may also be included: Data fusion and wireless transmission: The main control MCU packages light intensity data, physiological parameters (heart rate, blood oxygen, body temperature), and system status (battery power, current lens transmittance, etc.) into fixed-length binary data frames, and sends them to the mobile APP via Bluetooth module. The mobile phone can then visualize the data (real-time curves, digital displays) and store it locally.

[0077] In practice, the following steps are also included: Charging Management: Centered on the TP4056 charging chip, it provides a complete lithium battery charging solution. Its PROG pin, connected to an external 1.2kΩ precision resistor, ensures a balance between charging speed and battery life. When the battery voltage drops below 4.2V, it enters constant current charging mode. Once the voltage reaches 4.2V, it automatically switches to constant voltage trickle charging until the current drops to the cutoff threshold, at which point charging stops.

[0078] System Power Supply: A nominal 3.7V lithium battery serves as the main power source, outputting a stable 3.3V voltage through a low-dropout linear regulator (LDO) to power the STM32 main controller, various sensors, and communication modules. In the power supply chain, key nodes are equipped with a composite filter network consisting of 10μF electrolytic capacitors and 100nF ceramic capacitors to effectively suppress low-frequency ripple and high-frequency noise, ensuring stable and reliable voltage for each module during power-on, operation, and communication.

[0079] In practice, the following steps are also included: The HC-05 Bluetooth module connects to the main control MCU via a UART serial port (PA9 / TX, PA10 / RX), with a default baud rate of 9600bps (which can be increased to 115200bps as needed), and uses the 8N1 communication format. The mobile app sends structured command data packets via Bluetooth. The main control MCU receives and parses the command type and parameters, and dynamically calculates and updates the internal high and low threshold variables based on other detection parameters, ensuring that users can set different color-changing thresholds according to their preferences.

[0080] Example 2 like Figure 2 The diagram shows a circuit structure of electrochromic glasses based on health monitoring, used to implement the electrochromic glasses control method based on health monitoring in Embodiment 1. It includes a frame, temples, electrochromic lenses, a main control module, a control module, a data acquisition unit, a Bluetooth module, a power supply module, a grounding converter, and an external interface. The data acquisition unit includes a photosensitizing module, a heart rate and blood oxygenation module, and a body temperature module.

[0081] The acquisition unit is used to simultaneously collect the wearer's physiological health data and ambient light data, and listen for control commands from the user via Bluetooth module.

[0082] The photosensitive module is located inside the recessed area of ​​the left lens frame, employing a TEMT6000 phototransistor as its core photosensitive device. This device operates based on the photoelectric effect: when ambient light shines on its photosensitive area (collector junction), photon energy excites the semiconductor material to generate electron-hole pairs, thus forming a photocurrent. This photocurrent serves as the equivalent input to the base current, is amplified by the transistor structure, and ultimately generates an output current at the output terminal (between the collector and emitter) that varies proportionally to the light intensity. This working principle helps the photosensitive module accurately sense ambient light intensity. Simultaneously, the photosensitive module connects to the ADC pin of the main control MCU via the PA0 pin, converting this current signal into a corresponding analog voltage signal and transmitting it to the main control MCU. The main control MCU performs analog-to-digital conversion using its built-in ADC to obtain the precise light intensity value. The TEMT6000, with its spectral response closely resembling the human eye's visual curve, features precise perception, strong scene adaptability, fast response speed, and high cost-effectiveness, enabling high-precision real-time monitoring of ambient light, perfectly meeting the application requirements of smart photochromic lenses. Furthermore, the VDD pin of the TEMT6000 photosensitive module is connected to 3.7V, and GND is grounded. A 100nF filter capacitor is connected in series to filter out power supply noise, accurately acquiring ambient light intensity in real time and transmitting it to the main control MCU. Further, the TEMT6000 photosensitive chip acts as an ambient light sensor; its photocurrent is proportional to the light intensity, and the output voltage (connected to PA0) changes linearly with the light intensity, ranging from approximately 0 to 3.3V. The main control MCU has a built-in 12-bit ADC that samples the PA0 pin voltage at a period of 100ms, obtaining a raw digital value within the range of 0–4095. Using a preset calibration curve (which can be obtained through experimental calibration), the raw ADC value is converted into an actual light intensity value in lux for subsequent logic judgment.

[0083] The heart rate and blood oxygenation module is located in the mounting cavity of the left temple, fitting snugly behind the ear. This module uses a MAX30102 sensor chip and an LP5910 power management chip, integrating a photodetector, optical components, and low-noise electronics with ambient light suppression capabilities. It integrates an LED reflective heart rate monitor and a pulse oximeter, enabling high-precision, high signal-to-noise ratio heart rate and blood oxygen saturation data acquisition. Data is stably transmitted to the main control MCU via two signal lines, SCL (PB6) and SDA (PB7), using the I²C communication protocol. This design not only ensures accurate data acquisition and rapid response but also, due to its ultra-low power consumption, high stability, and strong anti-interference capabilities, helps extend the overall battery life of the smart glasses and enrich its health monitoring functions.

[0084] The body temperature module is also located in the mounting cavity of the left temple, fitting snugly against the skin behind the ear for measurement. The module uses the MLX90614 chip, which integrates a complete infrared thermopile temperature measurement system, enabling non-contact, high-precision human body temperature data acquisition. The module efficiently transmits data to the main control MCU via the I²C communication protocol through the SCL (PB10) and SDA (PB11) pins. This integrated solution not only improves the reliability and speed of data acquisition but also, thanks to the low power consumption and high anti-interference characteristics of I²C communication, further enhances the smart glasses' battery life and functional practicality, providing users with a continuous and stable body temperature monitoring experience.

[0085] Furthermore, the body temperature module MLX90614 and the heart rate and blood oxygenation modules MAX30102 and LR5910 are integrated and packaged, and then embedded in the inside of the temple of the glasses, fitting against the skin behind the ear; the sensor VDD pins of the two modules are connected to a 3.7V regulated voltage, and GND is grounded. At the same time, both LR5910-1.8DRVR and MAX30102 are connected in series with a 100nF filter capacitor to filter out power supply noise and improve working stability.

[0086] The main control module, which contains a main control MCU ( Figure 2 The main control chip (in the system) is used to analyze the wearer's visual experience and actual adjustment needs when a control command is detected, combining the physiological health data within the time window of the control command's occurrence or a nearby time window. The actual adjustment needs may be larger or smaller than the adjustment needs in the control command, depending on the physiological health data. The color fading control threshold of the electrochromic lens is adaptively adjusted according to the actual adjustment needs. The lens driving command is generated based on a comprehensive judgment of the control threshold and the real-time collected ambient light data. The current lens status, physiological health data, and adjustment log are saved.

[0087] In practice, the main control MCU is installed in a pre-reserved mounting cavity inside the temple of the lens. An STM32F103C8T6 microcontroller is used, featuring high-efficiency computing and low power consumption. It can quickly process signals transmitted from various modules and units and issue lens drive commands, ensuring stable system operation. It achieves global management and control through the following logic: receiving ambient light intensity and physiological parameters from the photosensitive module, heart rate and blood oxygenation module, and body temperature module, and performing rapid calculations and logical analysis. Simultaneously, it issues lens drive commands to the control module to adjust the tinting depth of the electrochromic lens, sends data transmission commands to the Bluetooth module to achieve interaction with external terminals, and receives commands transmitted from the Bluetooth module to calculate and change the color-changing threshold. It also manages the power consumption of the control module, power supply module, and other power units, achieving low-power battery life while ensuring stable system operation.

[0088] Furthermore, the main control module connects to the OSC_IN and OSC_OUT pins of a circuit consisting of two 22nF ceramic capacitors and an 8Hz passive crystal oscillator via the PD0-OSC_IN and PD1-OSC_OUT pins, providing a precise reference clock signal to the chip. The main control module connects to the first filter capacitor group via the VDD_1 pin to filter out high-frequency noise on the power line. The PA2 and PA3 pins of the main control module are connected to the PA2 and PA3 pins of the control module to adjust the duration of the high and low levels of the control module. Simultaneously, pins 1 and 2 of the control module are connected to a diode-transistor and a 10KΩ current-limiting resistor to regulate the voltage magnitude and supply time. The main control module connects to pin 1 (PA0) of the photosensitive module via the PA0-WKUP pin to receive light intensity signals. The photosensitive module has a 100nF capacitor connected to it to filter out power supply noise. The main control module connects to the SCL-M and SDA-M pins of the body temperature module via pins PB10 and PB11 to receive body temperature data. A 100nF capacitor is connected to the VSS and VDD pins of the body temperature module to filter out power supply noise. The main control module also connects to the SCL-T and SDA-T pins of the heart rate and blood oxygenation module via pins PB7 and PB6 to receive heart rate and blood oxygenation data. A 4.7KΩ current-limiting resistor is connected to the INT, SCL, VDD, and SDA pins of the heart rate and blood oxygenation module to ensure a consistent voltage level in non-operating states, improve anti-interference capabilities, and ensure stable bus voltage levels. Additionally, 100nF and 10uF capacitors are connected to the VDD, SDA, IN, and OUT pins to filter out high-frequency noise. The main control module connects to pin 1 of the power module SW1 switch via the VDD_1 pin to control the power supply of the entire hardware circuit. The BAT and VCC pins of the TP4056 chip in the power module are connected to 100nF and 10uF capacitors respectively to filter out high-frequency noise, forming a tiered filter to ensure power supply purity. The TEMR, PROG, and GND pins are connected to 1.2KΩ current-limiting resistors to improve the module's anti-interference capability. The main control module connects to the TXD and RXD pins of the HC05 Bluetooth module via PA10 and PA9 pins to enable terminal interaction of physiological data and adjust the color-changing threshold. The PLO8, PLO11, and RST pins of the Bluetooth module are connected to 1KΩ, 10KΩ, and 10KΩ current-limiting resistors respectively, which improve the module circuit's anti-interference capability and enhance signal integrity.

[0089] Furthermore, the main control module collects physiological health data through the I²C bus; the PA10 and PA9 pins of the main control module are connected to the TXD and RXD pins of the HC05 Bluetooth module to realize data interaction, and the PA2 and PA3 pins of the main control module are connected to the PA2 and PA3 pins of the control module to transmit digital voltage signals to the control module. In conjunction with the voltage divider peripheral circuit, the lens fading and coloring function is realized.

[0090] A control module is used to drive the electrochromic lens to change its tinting state according to the lens driving command.

[0091] In practice, the control module is located in the mounting cavity at the rear of the left temple, closely connected to the electrochromic film of the electrochromic lens. When the analog voltage received by the main control MCU and its peripheral circuit modules from the photosensitive module exceeds the control threshold set by the main control MCU, the main control MCU transmits a signal from its output pin PA2 to the control module, thereby raising the PA2 pin in the control module that controls lens tinting and driving the electrochromic film to tint. When the analog voltage received by the main control MCU and its peripheral circuit modules from the photosensitive module is lower than the set threshold, the main control MCU also transmits a signal from its output pin PA3 to the control module, thereby raising the PA3 pin in the control module that controls the fading of the electrochromic film and driving the lens to fade. The tinting and fading of the lens are directly controlled by high and low level signals.

[0092] Furthermore, the control module is installed inside the temple to control the output voltage intensity. It is also closely connected to the electrochromic film to ensure that the lens fading and coloring function works normally.

[0093] In specific implementation, the electrochromic lens features a thin film (hereinafter referred to as: electrochromic film) made using ultra-stable dual-band electrochromic technology achieved through shear-phase niobium oxide, which is the core technology component of the electrochromic glasses. This ultra-stable dual-band electrochromic technology enables spectral selectivity between the visible light (VIS) and near-infrared (NIR) bands, that is, independently adjusting the transmittance of these two bands. This allows for changes in transmittance under different lighting and thermal environments to meet varying energy-saving and comfort requirements. The core advantages of the electrochromic film include: a. Dual-band modulation mechanism: Through the electrochemical charging process, niobium oxide materials exhibit different absorption behaviors in different bands, corresponding to local surface plasmon resonance (LSPR) and polaron absorption effects, respectively, thus achieving independent control of visible and near-infrared light.

[0094] b. Super stability: Exhibits excellent memory effect and maintains good performance after multiple electrochemical cycles, with excellent cycle life and structural stability, suitable for long-term use.

[0095] C. Solution fabrication: Supports solution fabrication on glass or flexible substrates, with the potential for low-cost, large-area fabrication, suitable for a variety of applications.

[0096] Electrochromic lenses ensure the stability, feasibility, and environmental adaptability of electrochromic lenses during the electrochromic process. They are connected to a control module and adjust the tinting degree of the electrochromic lens by receiving different voltage values ​​from the control module, thereby controlling the light transmittance and ultimately realizing the core electrochromic function of the glasses.

[0097] In specific implementation, the Bluetooth module adopts the HC05 Bluetooth serial communication module. Its RXD and TXD pins are bidirectionally electrically connected to the PA9 and PA10 pins of the main control module via a USART serial port, supporting short-range wireless communication. It can transmit physiological health data processed by the main control MCU to mobile terminals such as smartphones, and can also receive light intensity threshold adjustment commands from mobile terminals, enabling user-defined control. It can also be used to record user habits, maximizing the user experience in specific environments. Furthermore, the VDD pin of the HC05 Bluetooth module is connected to 3.7V, GND is grounded, and the baud rate is set to 9600bps, establishing a wireless connection with the mobile APP to achieve bidirectional data transmission.

[0098] In practice, the power module consists of a 3.7V lithium battery and a charging module (TP4056 chip). The lithium battery is installed in the mounting cavity of the right temple, with a capacity of 3000mA to ensure battery life. The charging management submodule uses the TP4056 charging chip as its core to achieve constant current / constant voltage safe charging of the lithium battery, and has overcharge and over-discharge protection functions. Series filter capacitors (100uF tantalum capacitor and 100nF ceramic capacitor) in the power supply link effectively filter out voltage ripple, ensuring the power supply stability of each functional module (main control MCU, control module, acquisition unit, etc.) and avoiding interference from voltage fluctuations on signal acquisition and drive control. Furthermore, the power supply pin VCC of the power module charging chip is connected to 5V, and GND is grounded, providing a stable 3.7V voltage in conjunction with the lithium battery H5.

[0099] In practical implementation, the ground conversion and external interface module provides hardware-level configuration signals to ensure stable data and power transmission. Furthermore, the main control module incorporates a data filtering algorithm to filter the raw data collected by the acquisition unit, removing interference signals and improving the accuracy of physiological data detection. Simultaneously, the main control module's MCU also supports a low-power mode, automatically switching to sleep mode when idle to reduce power consumption.

[0100] Example 3 A computer-readable storage medium includes a stored program, wherein, when the program is executed, it controls the device where the computer-readable storage medium is located to perform the above-described electrochromic glasses control method based on health monitoring.

[0101] Example 4 A processor for running a program, wherein the program executes the above-described electrochromic glasses control method based on health monitoring.

[0102] Beneficial effects: Compared to existing technologies, this application's electrochromic glasses based on health monitoring achieve autonomous adjustment of the color-changing control threshold through the collaborative design of the main control MCU, control module, Bluetooth module, and photosensor module. This allows for better adaptation to different lighting environments and significantly improved flexibility. Simultaneously, while maintaining the glasses' lightweight design, it expands the functionality to include real-time measurement of body temperature, heart rate, and blood oxygen, overcoming the limitations of existing glasses with limited functionality. This solution features a simple overall structure, a reasonable hardware layout, and balances portability and practicality, adapting to various daily life scenarios. It reduces the design and manufacturing costs of multifunctional smart glasses while also improving battery life, giving it stronger market competitiveness.

[0103] This application discloses a control method, glasses, medium, and processor for smart electrochromic glasses based on health monitoring, relating to the field of smart glasses photochromic control technology. The method synchronously collects the wearer's physiological health data and ambient light data, combines this with user control commands, analyzes visual load status in real time, generates lens adjustment needs matching the physiological state, and adaptively adjusts the tinting fading control threshold of the electrochromic lens, ultimately driving the lens to dynamically adjust its tinting state. The system includes a data acquisition module, a main control module, and a control module, achieving intelligent and personalized photochromic control. This application solves the problem that traditional electrochromic glasses rely solely on ambient light and cannot adapt to the user's physiological state, improving visual comfort and health adaptability.

[0104] Those skilled in the art will recognize that the units of the various examples described in connection with the embodiments disclosed herein can be implemented in electronic hardware, computer software, or a combination of both. To clearly illustrate the interchangeability of hardware and software, the components of the various examples have been generally described in terms of functionality in the foregoing description. Whether these functions are implemented in hardware or software depends on the specific application and design constraints of the technical solution. Those skilled in the art can use different methods to implement the described functions for each specific application, but such implementations should not be considered beyond the scope of the invention.

[0105] In the embodiments provided by the present invention, it should be understood that the division of units is only a logical functional division. In actual implementation, there may be other division methods, such as multiple units can be combined into one unit, one unit can be split into multiple units, or some features can be ignored.

[0106] Furthermore, the functional units in the various embodiments of the present invention can be integrated into one processing unit, or each unit can exist physically separately, or two or more units can be integrated into one unit. The integrated unit can be implemented in hardware or as a software functional unit.

[0107] If the integrated unit is implemented as a software functional unit and sold or used as an independent product, it can be stored in a computer-readable storage medium. Based on this understanding, the technical solution of the present invention, in essence, or the part that contributes to the prior art, or all or part of the technical solution, can be embodied in the form of a software product. This computer software product is stored in a storage medium and includes several instructions to cause a computer device (which may be a personal computer, server, or network device, etc.) to execute all or part of the steps of the methods described in the various embodiments of the present invention. The aforementioned storage medium includes various media capable of storing program code, such as USB flash drives, read-only memory (ROM), random access memory (RAM), portable hard drives, magnetic disks, or optical disks.

[0108] Finally, it should be noted that the above embodiments are only used to illustrate the technical solutions of the present invention, and not to limit them. Although the present invention has been described in detail with reference to the foregoing embodiments, those skilled in the art should understand that modifications can still be made to the technical solutions described in the foregoing embodiments, or equivalent substitutions can be made to some or all of the technical features therein. Such modifications or substitutions do not cause the essence of the corresponding technical solutions to deviate from the scope of the technical solutions of the embodiments of the present invention, and they should all be covered within the scope of this application.

Claims

1. A method for controlling electrochromic glasses based on health monitoring, characterized in that, Includes the following steps: S1: Synchronously collects the wearer's physiological health data and ambient light data, and listens for control commands from the user via Bluetooth module; S2: When an adjustment command is detected, the wearer's visual load status is analyzed by combining the physiological health data at the time of the adjustment command or within the adjacent time window, and a lens adjustment requirement that matches the actual physiological state is generated based on the visual load status. S3: Adaptively adjust the tinting fading control threshold of the electrochromic lens according to the lens adjustment requirements; S4: Generate lens driving instructions based on the control threshold and the real-time acquired ambient light data; S5: Drive the electrochromic lens to change its coloration state according to the lens driving command.

2. The method for controlling electrochromic glasses based on health monitoring according to claim 1, characterized in that, In step S2, when an adjustment command is detected, the wearer's visual load status is analyzed by combining the physiological health data within the time window of the adjustment command's occurrence or a nearby time window, and a lens adjustment requirement matching the actual physiological state is generated based on the visual load status. This includes the following steps: S21: Based on the moment when the control command is triggered, extract heart rate, blood oxygen saturation, and body temperature data within a time window before and after that moment to assess the wearer's visual load status. S22: Determine the demand correction factor based on visual load status. The control commands are then modified to obtain the final lens adjustment requirements. S23: Fine-tune the correction coefficient based on the real-time trend of physiological health data to achieve smooth optimization of adjustment needs during a single command execution, so that the lens status dynamically matches the user's ever-changing physiological needs.

3. The method for controlling electrochromic glasses based on health monitoring according to claim 2, characterized in that, In step S21, the model for assessing the wearer's visual load state is as follows: ； in, Physiological stress index; The ambient light-physiological coupling coefficient; This is a time-dynamic adjustment factor.

4. The method for controlling electrochromic glasses based on health monitoring according to claim 3, characterized in that, The physiological stress index determination model is as follows: ； ； ； ； ； in, For dynamic components of heart rate; This refers to the blood oxygen penalty value. This represents the body temperature trend value. The standard deviation of heart rate over the last 30 seconds; The average heart rate over the last 30 seconds; For current real-time heart rate measurement; The user's resting heart rate; This is the maximum heart rate value; This represents the heart rate variability. This is the heart rate sensitivity coefficient; This refers to the blood oxygen sensitivity coefficient. This indicates the current real-time blood oxygen saturation. This refers to the current real-time blood oxygen saturation. Normal healthy blood oxygen levels; This is the warning line for low blood oxygen levels; This is the current real-time body surface temperature; Baseline body temperature of the user; The threshold for judging mild fever; The rate of change of body temperature; Trend weight.

5. The method for controlling electrochromic glasses based on health monitoring according to claim 4, characterized in that, The model for determining the ambient light-physiological coupling coefficient is as follows: ； ； Ideal light intensity; As a baseline stress index; For users' preferred light intensity; Physiological sensitivity coefficient; This is the normalized value of the current ambient light intensity; This indicates a mismatch in weights. It is a non-linear exponent.

6. The method for controlling electrochromic glasses based on health monitoring according to claim 4, characterized in that, The time-dynamic adjustment factor The defined model is as follows: ； ； in, It is the attenuation constant; This represents the recovery ability value. The start time; Historical VLS values; The current time; The cumulative intensity coefficient; s represents the past time. This is a discount factor for recovery capacity; For real-time heart rate variability; This refers to resting heart rate variability.

7. The method for controlling electrochromic glasses based on health monitoring according to claim 2, characterized in that, In step S2, the formula for generating lens adjustment requirements that match the actual physiological state based on visual load status is as follows: ； in, This is the final adjustment amount for the lens tinting threshold; The color threshold adjustment amount corresponding to the user's original control command; This is the demand adjustment factor.

8. A type of electrochromic glasses based on health monitoring, characterized in that, The method for controlling electrochromic glasses based on health monitoring, as described in any one of claims 1 to 7, comprises: The acquisition module is used to synchronously collect the wearer's physiological health data and ambient light data, and listen for control commands from the user via Bluetooth module; The main control module is used to analyze the wearer's visual load state when a control command is detected, in combination with the physiological health data within the time window of the control command occurrence, and generate lens adjustment requirements that match the actual physiological state based on the visual load state; adaptively adjust the color fading control threshold of the electrochromic lens according to the lens adjustment requirements; and generate lens driving commands based on the control threshold and the real-time collected ambient light data. A control module is used to drive the electrochromic lens to change its tinting state according to the lens driving command.

9. A computer-readable storage medium, characterized in that, The computer-readable storage medium includes a stored program, wherein, when the program is executed, it controls the device containing the computer-readable storage medium to perform the electrochromic glasses control method based on health monitoring as described in any one of claims 1 to 7.

10. A processor, characterized in that, The processor is used to run a program, wherein the program executes the electrochromic glasses control method based on health monitoring as described in any one of claims 1 to 7.

Images