Breathing exercise method and related device

Abstract

A breathing exercise method and a related device, capable of providing tactile feedback to a user during a breathing exercise, thereby enabling the user to focus on breathing itself, providing the user with an immersive breathing exercise experience. Moreover, the device can also measure physiological parameters such as blood pressure during a breathing exercise, and provide feedback on the effectiveness of the breathing exercise. The tactile feedback may be generated on the basis of an airbag on a wearable device, and the pressure in the airbag can be changed by inflation and deflation to generate a tactile stimulus. In addition to providing tactile feedback, the airbag on the wearable device can also be used for blood pressure measurement. In this way, the device can achieve the both functions of tactile feedback and blood pressure measurement on the basis of the airbag on the wearable device, thereby reducing design costs and avoiding the need for additional hardware.

Description

Breathing training methods and related equipment

[0001] This application claims priority to Chinese Patent Application No. 202411788408.X, filed on December 5, 2024, entitled “Breathing Training Method and Related Equipment”, the entire contents of which are incorporated herein by reference. Technical Field

[0002] This invention relates to the field of electronic technology, and in particular to breathing training methods and related equipment. Background Technology

[0003] Recent scientific research has shown that breathing exercises can help lower blood pressure and improve vascular health. As a result, several breathing training apps have emerged, such as meditation and yoga apps, becoming helpful tools for people to master breathing techniques and improve their health. However, if users fail to master the correct breathing techniques during training, such as incorrect breathing rhythm, they will not achieve the desired results. Summary of the Invention

[0004] In a first aspect, embodiments of this application provide a breathing training method, which may include: a wearable device initiating a first breathing training session; controlling the inflation and deflation of an airbag on the wearable device according to the breathing rhythm of the first breathing training session; and using the inflated and deflated airbag during the first breathing training session to measure a user's first physiological parameter, including blood pressure. The airbag may be disposed on the surface of the wearable device, and a pressure gauge is disposed within the airbag.

[0005] The method provided in the first aspect can offer tactile feedback during breathing training, enabling users to master the correct breathing rhythm and focus on breathing itself, thus providing an immersive breathing training experience. Furthermore, embodiments of this application can also measure physiological parameters such as blood pressure during the breathing training process, providing feedback on the effectiveness of the breathing training.

[0006] In the first aspect, tactile feedback is generated based on an airbag. Inflating and deflating the airbag changes the pressure within it, thus producing tactile stimulation. The device providing tactile feedback can be a wearable device, with an airbag integrated into its surface. When a user wears the device, the airbag comes into contact with the user's skin, allowing the user to feel the tactile stimulation provided by the airbag's inflation and deflation. Besides providing tactile feedback, the airbag on the wearable device can also be used for blood pressure measurement. Thus, tactile feedback and blood pressure measurement can be combined using the airbag on the wearable device, saving design costs and avoiding additional hardware requirements.

[0007] In the first aspect, the first breathing training can be a breathing training mode or a breathing training course, which can be provided by a sports and health application or by a standalone breathing training application. Alternatively, the first breathing training can be a breathing training function or service that can be integrated into a sports and health application or implemented as a standalone breathing training application.

[0008] In the first aspect, the initiation of the first breathing training can be manually triggered by the user, such as when the user enters a sports and health application and starts the first breathing training. The initiation of the first breathing training can also be triggered by internal device events, such as automatically starting the first breathing training at 8 pm every day, or automatically starting the first breathing training when the user's blood pressure exceeds a preset range.

[0009] In the first aspect, a crucial parameter for the first breath training is the breathing rhythm. The breathing rhythm can be user-defined or a system default. It can include the following parameters: the inhalation time, breath-holding time, and exhalation time for each round of breathing. If the user can inhale during the specified inhalation time, hold their breath during the specified breath-holding time, and exhale during the specified exhalation time—that is, breathe in accordance with the breathing rhythm—they can master the correct breathing technique and achieve better training results. One breath consists of one inhalation, one breath-holding, and one exhalation.

[0010] In conjunction with the first aspect, in some embodiments, before the wearable device controls the inflation and deflation of the airbag on the wearable device according to the breathing rhythm of the first breathing training, the wearable device deliberately acquires the breathing rhythm of the first breathing training, which includes the following parameters: the inhalation time, breath-holding time, and exhalation time of each round of breathing. Specifically, the wearable device can control the inflation of the airbag during the inhalation time, maintain a constant pressure inside the airbag during the breath-holding time, and control the deflation of the airbag during the exhalation time.

[0011] The first breathing training may also include one or more of the following parameters: training rounds, training duration, and target value of the first physiological parameter. The training rounds refer to the total number of breathing rounds included in the first breathing training, such as 100 breaths; the training duration refers to the total training time of the first breathing training, such as 30 minutes; the target value of the first physiological parameter refers to the training objective of the first breathing training on the first physiological parameter, which may include blood pressure, blood pressure changes, etc., for example, the target value is a reduction of blood pressure by 10 mmHg. These parameters may be user-defined or system defaults.

[0012] In conjunction with the first aspect, in some embodiments, the wearable device can detect that it is in a wearing state before controlling the inflation and deflation of the airbag on the wearable device according to the breathing rhythm of the first breathing training. That is, the prerequisite for providing tactile feedback based on the airbag may include that the wearable device is in a wearing state. In specific implementations, the wearable device can determine whether it is in a wearing state by detecting temperature changes through a temperature sensor set on the wearing surface. When in a wearing state, this temperature change will occur within a predicted temperature range. The wearable device can also detect whether it is in a wearing state through devices such as infrared sensors and capacitance detection modules, which are not limited in this application embodiment.

[0013] In conjunction with the first aspect, in some embodiments, after the wearable device initiates the first breathing training, it can also display a breathing guidance animation based on the breathing rhythm of the first breathing training. This breathing guidance animation serves to prompt the breathing rhythm. That is, while providing tactile feedback based on the airbag, the wearable device can also display a breathing guidance animation based on the breathing rhythm of the first breathing training, which serves to prompt the breathing rhythm. The breathing animation, along with the inflation and deflation of the airbag, provides the user with comprehensive breathing training guidance. Specifically, the wearable device can also differentiate the breathing training guidance method based on whether it is being worn. For example, when worn, it can provide tactile feedback through the airbag to guide the user in breathing training, while when not worn, it can provide visual feedback through the breathing guidance animation to guide the user in breathing training.

[0014] In conjunction with the first aspect, in some embodiments, before the wearable device initiates the first breathing training, the wearable device may also display a first user interface, which displays one or more breathing training exercises and detects that the user selects the first breathing training exercise from one or more breathing training exercises.

[0015] In conjunction with the first aspect, in some embodiments, the wearable device can also determine whether the first breathing training meets the termination conditions. If it does, the first breathing training is terminated. The termination conditions may include one or more of the following: the number of training rounds has reached the required number of training rounds for the first breathing training; the training duration has reached the required training duration for the first breathing training; or the measured value of the first physiological parameter has reached the target value for the first physiological parameter in the first breathing training.

[0016] In conjunction with the first aspect, in some embodiments, the breathing rhythm and termination conditions of the first breathing training can be adaptively adjusted based on the training effect. Specifically, the wearable device can adjust one or more of the following training parameters of the first breathing training based on the deviation between the first physiological parameter and the training goal of the first breathing training: training rounds, training duration, training goal, and breathing rhythm. For example, if the user's blood pressure does not decrease by 10 mmHg during the first breathing training, i.e., the blood pressure reduction has not reached the training goal, one or more of the following adjustments can be performed: increasing the number of training rounds, increasing the training duration, lowering the training goal, and adjusting the breathing rhythm to deep inhalation and deep exhalation to help the user's blood pressure decrease to reach the training goal.

[0017] In conjunction with the first aspect, in some embodiments, after measuring the user's first physiological parameter, the wearable device can also present the training effect of the first breathing training based on the measured value of the first physiological parameter. The training effect may include one or more of the following: the measured value of the first physiological parameter, the change in the measured value of the first physiological parameter, and the difference between the measured value of the first physiological parameter and the target value of the first physiological parameter.

[0018] In conjunction with the first aspect, in some embodiments, the wearable device measures a user's first physiological parameter using an airbag that inflates and deflates during the first breathing training process. Specific implementation methods may include:

[0019] In one implementation, during the rest interval of the first breathing training, the airbag is first inflated until the pressure inside the airbag exceeds a first pressure value, and then the airbag is deflated. The first physiological parameter is measured using the inflated / deflated airbag during the rest interval. The first pressure value is greater than a second pressure value, which is the maximum pressure value of the airbag when it is inflated / deflated according to the breathing rhythm of the first breathing training. That is, the wearable device can measure the user's blood pressure using traditional blood pressure measurement methods during the rest interval of the breathing training: controlling the airbag inflation to generate a sufficiently large force to compress the blood vessel, blocking blood flow, collecting the oscillation wave signal transmitted by the blood vessel during the process of blocking blood flow without external force affecting it, and calculating the user's blood pressure based on this oscillation wave signal. In other words, the pressure inside the airbag used for blood pressure measurement during the rest interval will be significantly greater than the pressure inside the airbag used for tactile feedback during the breathing training.

[0020] In another implementation, the wearable device also incorporates a photoplethysmography (PPG) sensor on its surface. During the first breathing exercise, the device can detect the airbag pressure and PPG signal based on the PPG sensor. Based on the measured airbag pressure and PPG signal, it determines the first physiological parameters, including heart rate variability (HRV) and blood pressure changes. In other words, the wearable device can simultaneously perform airbag pressure detection and PPG signal detection during breathing exercises, and calculate the first physiological parameters such as HRV and blood pressure changes based on the measured PPG signal within the airbag. This implementation eliminates the need for the airbag to exert a force on the user's blood vessels after inflation that could block blood flow. It simultaneously provides tactile feedback for breathing exercises and blood pressure measurement, achieving tactile feedback during the airbag inflation process and blood flow measurement.

[0021] In a second aspect, embodiments of this application provide an electronic device that may include a processor and a memory; wherein the memory is coupled to the processor and is used to store a computer program, which, when executed by the processor, causes the electronic device to perform the method described in the first aspect or any possible implementation thereof.

[0022] Thirdly, this application provides a computer-readable storage medium having a computer program stored thereon, which, when executed by a processor, implements the method described in the first aspect or any possible implementation of the first aspect.

[0023] Fourthly, this application provides a computer program product, including a computer program that, when executed by a processor, implements the method described in the first aspect or any possible implementation of the first aspect. Attached Figure Description

[0024] To more clearly illustrate the technical solutions in the embodiments of the present invention or the background art, the accompanying drawings used in the embodiments of the present invention or the background art will be described below.

[0025] Figures 1A-1C show guided animations of breathing exercises;

[0026] Figure 2 illustrates a wearable device provided in an embodiment of this application;

[0027] Figure 3 illustrates the overall flow of the breathing training method provided in the embodiments of this application;

[0028] Figure 4 illustrates an implementation flow of the breathing training method provided in an embodiment of this application;

[0029] Figure 5 illustrates an exemplary user interface for displaying a breathing training course provided in this embodiment;

[0030] Figure 6 illustrates, for example, the inflation slope of the air pump inflating the airbag;

[0031] Figure 7 illustrates, exemplarily, a user interface for demonstrating the effects of breathing training provided in an embodiment of this application;

[0032] Figure 8 illustrates an exemplary breathing training settings interface provided in an embodiment of this application;

[0033] Figure 9 illustrates an application flow of the breathing training method provided in an embodiment of this application;

[0034] Figure 10 shows a waveform comparison of the oscillation wave signal transmitted by the blood vessel when the airbag compresses the blood vessel with different pressures;

[0035] Figure 11 shows the relationship between the cross-sectional area of ​​a blood vessel and the transmural pressure of the blood vessel.

[0036] Figure 12 shows the waveform of the PPG signal acquired during blood pressure measurement under ideal conditions;

[0037] Figure 13 shows the waveform of the PPG signal acquired during the airbag inflation process;

[0038] Figure 14 illustrates the overall flow of the blood pressure measurement method provided in the embodiments of this application;

[0039] Figure 15 illustrates the principle of linear fitting to multiple data points;

[0040] Figure 16 shows a user interface 20 for displaying blood pressure measurement results provided in an embodiment of this application;

[0041] Figure 17 is a schematic diagram of the hardware structure of the electronic device 100 provided in the embodiment of this application. Detailed Implementation

[0042] The terminology used in the following embodiments of this application is for the purpose of describing particular embodiments only and is not intended to be a limitation of this application.

[0043] During breathing training, mastering correct breathing techniques helps users achieve better training results. Furthermore, breathing training apps typically offer multiple training modes, such as rapid breathing and deep, slow breathing, each requiring different breathing techniques. Therefore, guiding users to breathe correctly becomes crucial.

[0044] Figures 1A-1C illustrate a guided breathing training animation. Figures 1A, 1B, and 1C respectively show the screen guiding the user through exhalation, breath-holding, and inhalation. As shown in Figure 1A, when guiding the user to exhale, the Tai Chi symbol 11 in the screen gradually shrinks until the exhalation ends, and the remaining time for the exhalation is displayed, such as "5 seconds remaining." As shown in Figure 1B, when guiding the user to hold their breath, the size of the Tai Chi symbol 11 remains constant until the breath-hold ends, and the remaining time for the breath-hold is displayed, such as "5 seconds remaining." As shown in Figure 1C, when guiding the user to inhale, the Tai Chi symbol 11 gradually enlarges until the inhalation ends, and the remaining time for the inhalation is displayed, such as "5 seconds remaining."

[0045] However, the breathing training guidance shown in Figures 1A-1C is a visual guidance. Visual guidance requires users to keep their eyes on the screen to keep up with the correct breathing rhythm, which to some extent distracts users and prevents them from fully focusing on breathing itself, resulting in a poor user experience.

[0046] To address the aforementioned issues, this application provides a breathing training method that offers tactile feedback during breathing exercises, enabling users to master the correct breathing rhythm and focus on the breathing itself, thus providing an immersive breathing training experience. Furthermore, this application can also measure physiological parameters such as blood pressure during the breathing training process, providing feedback on the training effect.

[0047] In this embodiment, the tactile feedback is generated based on an airbag. Inflating and deflating the airbag changes the pressure within it, thereby producing tactile stimulation. The device providing tactile feedback can be a wearable device, with an airbag on its wearing surface. When a user wears the wearable device, the airbag comes into contact with the user's skin, allowing the user to feel the tactile stimulation provided by the airbag's inflation and deflation. Besides providing tactile feedback, the airbag on the wearable device can also be used for blood pressure measurement. Thus, this embodiment can combine tactile feedback and blood pressure measurement based on the airbag on the wearable device, saving design costs and avoiding additional hardware requirements.

[0048] For example, as shown in Figure 2, the wearable device can be a smartwatch or a smart bracelet. An airbag can be placed on the inner side of the strap (the wearing surface of the strap). This airbag can not only be used for blood pressure measurement but also provide tactile feedback for breathing training. This improves the user experience of breathing training while also enabling the sharing of hardware and design space between breathing training and blood pressure measurement. Figure 2 only exemplifies one design position of the airbag on the wearable device. In practical applications, the airbag can be placed in other positions on the wearable device, as long as it can provide tactile stimulation to the skin and meet the requirements for blood pressure measurement.

[0049] Figure 3 illustrates the overall flow of the breathing training method provided in the embodiments of this application. The details are as follows.

[0050] S11. Wearable devices can initiate the first breathing training.

[0051] First Breath Training can be a breathing training mode or course, offered by a fitness and wellness app or as a standalone breathing training app. Alternatively, First Breath Training can be a breathing training feature or service, integrated into a fitness and wellness app or implemented as a standalone breathing training app.

[0052] The first breathing training can be initiated manually by the user, such as when the user enters a sports and health application and starts the first breathing training. The first breathing training can also be triggered by internal device events, such as automatically starting the first breathing training at 8 PM every day, or automatically starting the first breathing training when the user's blood pressure exceeds a preset range.

[0053] The most important parameter in first-round breathing training is the breathing rhythm. The breathing rhythm can be user-defined or a system default. It can include the following parameters: the inhalation time, breath-holding time, and exhalation time for each cycle. If the user can inhale during the specified inhalation time, hold their breath during the specified breath-holding time, and exhale during the specified exhalation time—that is, breathe in accordance with the breathing rhythm—they will master the correct breathing technique and achieve better training results. One breath consists of one inhalation, one breath-holding, and one exhalation.

[0054] The first breathing training may also include one or more of the following parameters: training rounds, training duration, and target value of the first physiological parameter. The training rounds refer to the total number of breathing rounds included in the first breathing training, such as 100 breaths; the training duration refers to the total training time of the first breathing training, such as 30 minutes; the target value of the first physiological parameter refers to the training objective of the first breathing training on the first physiological parameter, which may include blood pressure, blood pressure changes, etc., for example, the target value is a reduction of blood pressure by 10 mmHg. These parameters may be user-defined or system defaults.

[0055] S12. The wearable device can control the inflation and deflation of the airbag on the wearable device according to the breathing rhythm of the first breathing training. The airbag can be placed on the wearing surface of the wearable device.

[0056] The specific implementation of controlling the inflation and deflation of the airbag on the wearable device according to the breathing rhythm of the first breathing training may include: controlling the airbag to inflate during the inhalation time of each round of breathing, controlling the pressure inside the airbag to remain constant during the breath-holding time of each round of breathing, and controlling the airbag to deflate during the exhalation time of each round of breathing.

[0057] The airbag inflation rate can be calculated by dividing the airbag's single inflation volume by the duration of a single inhalation during the first breathing exercise. The airbag's single inflation volume can be obtained by subtracting the minimum air pressure from the maximum air pressure, where the maximum and minimum air pressures are the air pressures at the end of a single inflation and deflation, respectively. These can be system defaults or adjusted according to the user's preference for haptic feedback intensity. For example, the air pressure at the end of deflation can be 0 mmHg, and the air pressure at the end of inflation can be 100 mmHg. Similarly, the airbag deflation rate can be calculated by dividing the airbag's single deflation volume by the duration of a single exhalation during the first breathing exercise. The single deflation volume can be equal to the single inhalation volume.

[0058] Because the airbag is positioned on the wearing surface of the wearable device, it comes into contact with the user's skin when the device is worn, allowing the user to feel the tactile stimulation provided by the inflation and deflation of the airbag. In this way, the user can follow the breathing rhythm expressed by this tactile feedback, focusing on breathing itself and obtaining an immersive breathing training experience.

[0059] While providing tactile feedback via airbags, the wearable device can also display a breathing guidance animation based on the breathing rhythm of the first breathing training session. This animation serves to cue the breathing rhythm. The breathing animation, along with the inflation and deflation of the airbags, provides comprehensive breathing training guidance to the user. In practice, the wearable device can also differentiate the guidance method based on whether it is being worn. For example, when worn, it provides tactile feedback via airbags to guide the user's breathing training, while when not worn, it provides visual feedback via breathing guidance animation to guide the user's breathing training.

[0060] Prior to S12, the wearable device can also detect that it is being worn. That is, the prerequisite for executing S12 can include that the wearable device is being worn. Specifically, the wearable device can determine whether it is being worn by detecting temperature changes through a temperature sensor located on the wearing surface. When being worn, this temperature change will occur within a predicted temperature range. The wearable device can also detect whether it is being worn using devices such as infrared sensors and capacitance detection modules; this embodiment does not limit this detection.

[0061] S13. The wearable device may also measure the user’s first physiological parameters, which may include blood pressure, by using an airbag that is inflated and deflated during the first breathing training.

[0062] As can be seen, in addition to providing tactile feedback, the airbag on the wearable device can also be used for blood pressure measurement. Thus, the embodiments of this application can combine tactile feedback for breathing training and blood pressure measurement based on the airbag on the wearable device, saving design costs and avoiding additional hardware requirements.

[0063] In one implementation, the wearable device can measure the user's blood pressure using traditional blood pressure measurement methods during rest intervals in breathing training. This involves controlling the inflation of a cuff to generate a sufficiently large force to compress the blood vessel, blocking blood flow, collecting the oscillation wave signal transmitted through the blocked blood vessel during this process without external force affecting the blocked blood flow, and calculating the user's blood pressure based on this oscillation wave signal. In other words, the pressure inside the cuff used for blood pressure measurement during rest intervals will be significantly greater than the pressure inside the cuff used for tactile feedback during breathing training.

[0064] In another implementation, the wearable device can simultaneously perform airbag pressure detection and photoplethysmography (PPG) signal detection during breathing training, and calculate primary physiological parameters such as heart rate variability (HRV) and blood pressure changes based on the measured PPG signal within the airbag. This implementation does not require the airbag to exert a force on the user's blood vessels strong enough to block blood flow after inflation. It can simultaneously provide tactile feedback for breathing training and blood pressure measurement based on the airbag, thus reusing the airbag inflation process for tactile feedback and the airbag inflation and deflation process for blood pressure measurement. Users can complete blood pressure measurement imperceptibly during breathing training, improving user comfort. This blood pressure measurement method will be described in detail in subsequent embodiments and will not be elaborated here.

[0065] The breathing training method provided in this application embodiment will be further described in detail below with reference to the flowchart shown in Figure 4.

[0066] S21. Wearable devices can initiate the first breathing training.

[0067] The implementation details of S21 can be found in the explanation of S11 in Figure 3, and will not be repeated here.

[0068] S22. The wearable device can be set to the breathing rhythm for the first breathing training.

[0069] The breathing rhythm of the first breathing training session can be user-defined. For example, the wearable device can first display the breathing training course interface shown in Figure 5. This interface can display multiple breathing training courses (or breathing training modes) such as "Quick Relaxation," "Soothing Relaxation," and "Ultimate Relaxation." Different breathing training courses can have different default breathing rhythms (such as exhalation time, breath-holding time, inhalation time, etc.). Users can select one of these breathing training courses to open; the selected breathing training is the first breathing training session. When a user selects a breathing training session, the breathing rhythm of that training session is set. Of course, users can also make some modifications to the default breathing rhythm to adjust it, such as lengthening the exhalation time for deeper breathing.

[0070] The breathing rhythm for the first breathing training session can also be automatically set by the wearable device based on one or more factors such as historical breathing training results, the user's current blood pressure measurement, the user's current heart rate variability measurement, and breathing training preferences. For example, if the user's historical training results show that a slow inhale and slow exhale breathing rhythm is most effective, then the breathing rhythm for the first breathing training session can be set to a slow inhale and slow exhale breathing rhythm. Similarly, if the user's current blood pressure measurement is high and slow inhale and slow exhale are suitable for lowering blood pressure, then the breathing rhythm for the first breathing training session can be set to a slow inhale and slow exhale breathing rhythm. Furthermore, if the user prefers a fast inhale and fast exhale breathing rhythm, then the breathing rhythm for the first breathing training session can be set to a fast inhale and fast exhale breathing rhythm.

[0071] In practical applications, the breathing rhythm of the first breathing training can also be set based on other strategies, and this application embodiment does not limit this.

[0072] S23. Wearable devices can set the inflation and deflation rhythm of the air pump according to the breathing rhythm.

[0073] The wearable device can also be equipped with an air pump, which works in conjunction with the airbag to inflate and deflate it. After setting the breathing rhythm for the first breathing training via S22, the wearable device can then set the air pump's inflation / deflation rhythm and rate. Specifically, the air pump's inflation time can be the inhalation time within the breathing rhythm, and the air pump's deflation time can be the exhalation time within the breathing rhythm. The breath-holding time within the breathing rhythm is the time during which the air pump maintains a constant pressure within the airbag, that is, maintaining a constant air volume within the airbag without further inflation or deflation.

[0074] Wearable devices can also adjust the air pump's inflation and deflation rates based on breathing rhythm. The inflation rate per cycle is calculated by dividing the inflation volume by the inflation duration, and the deflation rate per cycle is calculated by dividing the deflation volume by the deflation duration. As mentioned earlier, the inflation volume per cycle equals the deflation volume per cycle; these can be system defaults or adjusted based on the user's preference for haptic feedback intensity. Typically, if a user prefers stronger haptic feedback, the inflation volume per cycle can be set relatively large.

[0075] The embodiments of this application do not restrict the execution order of S21, S22 and S23. They can be executed in parallel, or S22 and S23 can be executed before S21.

[0076] S24. During the first breathing training, the wearable device can control the air pump to slowly inflate the airbag during inhalation, keep the air pressure in the airbag constant during breath-holding, and slowly deflate the airbag during exhalation, so that the inflation and deflation rhythm is consistent with the breathing rhythm of the first breathing training.

[0077] During inhalation control, the wearable device can adjust the air pump's inflation rate by changing the duty cycle and operating voltage, ensuring the inflation rate matches the inhalation rate, which is the reciprocal of the inhalation duration. Similarly, during exhalation control, the wearable device can adjust the air pump's deflation rate by changing the duty cycle and operating voltage, ensuring the deflation rate matches the exhalation rate, which is the reciprocal of the exhalation duration.

[0078] Duty cycle refers to the proportion of time the air pump spends inflating the airbag within a single cycle. For example, if the duty cycle is 50%, the air pump spends half the time inflating the airbag within one cycle. In practical applications, the inflation rate of the air pump can be increased by increasing its duty cycle, and decreased by decreasing it. Operating voltage refers to the voltage applied to the air pump during operation. Increasing the operating voltage increases the pump's power, thus increasing the inflation rate; conversely, decreasing the operating voltage reduces the pump's power, thus decreasing the inflation rate.

[0079] The inflation rate of the air pump on the airbag can be expressed as the inflation slope shown in Figure 6, such as 4.5 mmHg / s.

[0080] Specifically, the inflation slope of the airbag can be calculated by the duration of a single inhalation and the maximum pressure difference (peak pressure) of the airbag. For example, if the airbag's internal pressure is 0 mmHg at the start of inflation, and the highest internal pressure is 100 mmHg when inflation is complete, and the duration of a single inhalation is 10 seconds, then the inflation slope of the airbag can be calculated as follows:

[0081] For airbags with a deflation valve, the air pump flow rate and the deflation valve can be controlled during deflation to ensure the deflation rate matches the exhalation rate. For airbags without a deflation valve, the air pump flow rate can be reduced during deflation to match the exhalation rate. For airbags with a shut-off valve, the valve is closed during breath-holding to maintain a constant internal pressure. For airbags without a shut-off valve, proportional-integral-derivative (PID) control of the air pump can maintain a constant internal pressure during breath-holding. In this way, the inflation and deflation rhythm of the airbag can be controlled to match the breathing rhythm of the first breathing training.

[0082] In wearable devices, the air pump can be connected to a processor, such as an application processor, to receive instructions from the processor and control the air pump to inflate and deflate the airbag according to those instructions. The instructions can carry the following information: timing information describing the inflation / deflation rhythm. In this way, the air pump can inflate and deflate the airbag according to this rhythm, ensuring the rhythm matches the breathing rhythm of the first breathing training. The instructions can also carry the inflation / deflation rate for each inflation / deflation. Thus, the air pump can inflate and deflate the airbag according to this rate.

[0083] S25. During the first breathing training, the wearable device can also perform airbag pressure detection and PPG signal detection.

[0084] Specifically, a pressure gauge can be installed inside the airbag. The wearable device can use this pressure gauge to measure the air pressure inside the airbag. Additionally, a PPG sensor can be installed on the wearing surface of the wearable device, such as the bottom of a smartwatch. The wearable device can use this PPG sensor to collect PPG signals. The bottom surface of the watch body is the side that contacts the user's skin and is opposite the display surface (the screen side) of the watch body.

[0085] S26. Wearable devices can calculate primary physiological parameters such as heart rate variability (HRV) changes and blood pressure changes based on the airbag pressure and PPG signal measured during the first breathing training.

[0086] In this embodiment, HRV can be calculated as follows: The heartbeat cycle is obtained using peak point identification technology, and the variability between instantaneous heartbeats is calculated, such as the standard deviation of sinus intervals (SDNN) and the standard deviation of instantaneous heartbeats, to characterize the magnitude of HRV. Besides SDNN, other indicators for measuring HRV include the root mean square of successive differences (rMSSD) of the R-wave time interval.

[0087] This application embodiment can simultaneously record the pressure difference signal and PPG signal within the airbag, and calculate the blood pressure value based on the waveform changes of the PPG signal during airbag inflation. Traditional blood pressure measurement methods require controlling the airbag inflation to generate a very large force compressing the blood vessels, blocking blood flow, and collecting the oscillation wave signal transmitted by the blood vessels during the process of blocking blood flow without external force affecting it, and then calculating the user's blood pressure based on this oscillation wave signal. However, in the blood pressure measurement method provided by this application embodiment, the pressure applied by the airbag to the user's blood vessels does not need to reach the pressure required to block blood flow, which can reduce the user's discomfort when measuring blood pressure; furthermore, this also makes it more feasible and more comfortable to perform blood pressure measurement while providing tactile feedback for breathing training through the airbag, because the force stimulation provided by the airbag when providing tactile feedback is not as great as the external force blocking blood flow. Users can unknowingly complete health monitoring processes such as blood pressure measurement while immersed in breathing training.

[0088] The following text will explain in detail how to estimate primary physiological parameters such as HRV and blood pressure changes based on airbag pressure and PPG signals, which will not be elaborated here.

[0089] S27. After determining the first physiological parameters such as HRV changes and blood pressure changes, the wearable device can determine whether the first physiological parameters have reached the training goal of the first breathing training. If yes, S28 can be executed; otherwise, it can return to execute S24-S265, that is, continue to guide the user to perform breathing training and monitor the user's physiological parameters such as HRV changes and blood pressure changes while providing tactile feedback.

[0090] The training objective for the first breath training can be set by the user or by the system default. For example, the user can set the training objective as a decrease in blood pressure of 10 mmHg. If, in S26, it is estimated that the blood pressure has decreased and the decrease reaches 10 mmHg, then it can be determined that the user's first physiological parameter has reached the objective of the first breath training; otherwise, it can be determined that the user's first physiological parameter has not yet reached the objective of the first breath training. This example is merely for explaining the embodiments of this application and should not be construed as limiting the scope. In practical applications, users can set training objectives according to their own needs.

[0091] S28. After achieving the training goal of the first breathing exercise, the wearable device can end the first breathing exercise and demonstrate the effect of the breathing exercise.

[0092] Specifically, wearable devices can present the training effect of the first breathing training based on the measurement value of the first physiological parameter. The training effect can include one or more of the following: the measurement value of the first physiological parameter (such as blood pressure, HRV), the change in the measurement value of the first physiological parameter, and the difference between the measurement value of the first physiological parameter and the target value of the first physiological parameter.

[0093] Figure 7 exemplarily illustrates a display interface for the effects of breathing training. As shown in Figure 7, the effects of breathing training can be presented comparatively, showing health conditions such as blood pressure and stress before and after the training. It can also display changes in blood pressure during the training process, allowing users to intuitively understand the benefits of breathing training for their health. Figure 7 is merely used to explain embodiments of this application and should not be construed as limiting the scope of the application. In practical applications, the effects of breathing training may also include HRV relaxation scores (i.e., HRV improvement), average blood pressure during the breathing training period, etc.

[0094] In addition to the user's first physiological parameter reaching the training goal of the first breathing training, the termination conditions of the first breathing training may also include: the number of training rounds reaching the required number of training rounds, and the training duration reaching the required training duration. In S27, the wearable device can also determine whether the first breathing training meets the termination conditions; if so, the first breathing training ends.

[0095] Users can set the end conditions for the first breathing training through the breathing training settings interface shown in Figure 8, such as the number of training rounds, training time, and training goals.

[0096] In this embodiment, the breathing rhythm and termination conditions of the first breathing training can be adaptively adjusted based on the training effect. Specifically, the wearable device can adjust one or more of the following training parameters of the first breathing training based on the deviation between the first physiological parameter and the training goal of the first breathing training: training rounds, training duration, training goal, and breathing rhythm. For example, if the user's blood pressure does not decrease by 10 mmHg during the first breathing training, i.e., the blood pressure reduction has not reached the training goal, one or more of the following adjustments can be performed: increasing the number of training rounds, increasing the training duration, lowering the training goal, and adjusting the breathing rhythm to deep inhalation and deep exhalation to help the user's blood pressure decrease to reach the training goal. These examples are merely for explaining the embodiments of this application and should not be construed as limiting the scope of the application.

[0097] The graphical user interfaces (GUIs) mentioned in this embodiment, such as the breathing guidance animation, breathing training course interface, breathing training settings interface, and breathing training effect display interface, can also be displayed on a large-screen device connected to the wearable device, such as a smartphone, tablet, or smart screen, to facilitate the display of more information to the user. There is communication between the wearable device and the large-screen device. Based on this communication, the GUI to be displayed, user settings (such as the user-selected breathing training course and user-set breathing rhythm), and the wearable device's detection data (such as airbag pressure and PPG signal) can be interacted with. The aforementioned steps for calculating physiological parameters such as blood pressure and HRV changes (e.g., step S26) can also be performed by the large-screen device. The wearable device can only provide tactile feedback through the airbag and collect PPG signals and airbag pressure during breathing training through the PPG sensor and airbag, transmitting them to the large-screen device, which then calculates physiological parameters such as blood pressure and HRV based on the PPG signals and airbag pressure. Taking the process shown in Figure 4 as an example, the wearable device can execute only S24-S25, while the large-screen device can execute S21-S23 and S26-S28. This application does not impose any restrictions on how wearable devices and large-screen devices should divide their functions to achieve the breathing training method provided in the embodiments of this application, and the appropriate choice can be made according to actual application needs.

[0098] Figure 9 illustrates an application flow of an embodiment of this application. In this flow, the user begins breathing training based on a pre-made breathing training course and completes the entire breathing training process according to the preset parameters of the course (such as breathing rhythm, training rounds, etc.), ultimately achieving the relaxation effect of breathing training.

[0099] As shown in Figure 9:

[0100] S31. The user enters the breathing training application.

[0101] The breathing training function or service can also be integrated into sports and health applications or other types of applications instead of being implemented as a standalone application.

[0102] S32. Users select a suitable emotional relaxation course in the breathing training application, such as "deep relaxation".

[0103] The breathing training application can provide a user interface as shown in Figure 5 for displaying breathing training courses, where users can select the course they want to start.

[0104] The training parameters for the "Deep Relaxation" course can be preset, such as: 20 training rounds, 2 seconds for a single inhalation, 2 seconds for a single breath-hold, 4 seconds for a single exhalation, and training goals such as "blood pressure decreases by 10 mmHg and heart rate variability increases by 10%".

[0105] S33. The wearable device can initiate a "deep relaxation" breathing training, controlling the air pump to inflate and deflate the airbag based on pre-set training parameters, so that the inflation and deflation rhythm of the airbag is consistent with the breathing rhythm of the breathing training, in order to provide tactile feedback to guide the user in breathing training.

[0106] For instructions on how to ensure that the inflation and deflation rhythm of the airbag matches the breathing rhythm of this breathing exercise, please refer to the relevant content mentioned above, which will not be repeated here.

[0107] S34. When performing S33, the wearable device can detect the pressure inside the airbag through the pressure gauge inside the airbag and detect the PPG signal through the PPG sensor.

[0108] S35. Calculate one or more physiological parameters such as HRV, HRV change, blood pressure change, and blood pressure based on the measured airbag pressure and PPG signal.

[0109] Specifically, if the pressure inside the cuff and the PPG signal were measured during the first round of breathing training, the initial values ​​of HRV and blood pressure can be calculated based on them; if the pressure inside the cuff and the PPG signal were not measured during the first round of breathing training, the changes in HRV and blood pressure can be calculated based on them.

[0110] S36. Determine whether the changes in HRV and blood pressure have achieved the training objectives of the "deep relaxation" course. If so, the "deep relaxation" breathing training can be terminated, and the training effect can be demonstrated, such as showing the user changes in HRV and blood pressure. If not, continue to provide tactile feedback to guide the user in breathing training until the user's changes in HRV and blood pressure reach the training objectives, or one or more of the following termination conditions are met: the total number of training rounds reaches the number of training rounds for "deep relaxation," or the total training duration reaches the training duration for "deep relaxation."

[0111] Even if the user's HRV and blood pressure changes do not ultimately reach the training goals, the wearable device can still demonstrate the effects of the breathing training to the user.

[0112] Next, we will explain in detail how to measure blood pressure using the airbag and PPG sensor on the wearable device.

[0113] In current common blood pressure measurement algorithms, blood pressure is measured by utilizing changes in light absorption by skin tissue caused by blood flow. This requires the acquisition of photoplethysmography (PPG) signals using photoelectric sensors, and blood pressure is calculated using the PPG signals. However, this algorithm lacks a supporting principle, and its accuracy in blood pressure measurement needs to be verified. Another method uses the pressure pulse transmitted by blood vessels under external pressure to measure blood pressure. This method requires applying sufficient pressure to the user to block blood flow in the blood vessels, and uses the oscillation wave signal transmitted by the blood vessels during the blocking process without external force to calculate the user's blood pressure. However, the large pressure can easily cause discomfort to the user, resulting in a poor user experience during blood pressure measurement.

[0114] For example, Figure 10 shows a schematic diagram comparing the waveforms of the oscillation wave signals transmitted by the blood vessels when the airbag compresses the blood vessels with different pressures.

[0115] As shown in Figure 10, if the upper limit of the balloon pressure is 240 mmHg, the pressure time is approximately 60 seconds, and a complete oscillating wave waveform can be acquired. This oscillating wave waveform describes the pressure pulse transmitted through the blood vessel during the occlusion process without external force. If the upper limit of the balloon pressure is 190 mmHg, the pressure time is approximately 45 seconds, but the acquired oscillating wave waveform is only 60% of the complete oscillating wave waveform. If the upper limit of the balloon pressure is 140 mmHg, the pressure time is approximately 30 seconds, but the acquired oscillating wave waveform is only 50% of the complete oscillating wave waveform. If the upper limit of the balloon pressure is 100 mmHg, the pressure time is greater than 20 seconds, but the acquired oscillating wave waveform is only 30% of the complete oscillating wave waveform.

[0116] As can be seen from Figure 10, the higher the upper limit of the pressure applied by the airbag, the longer the airbag pressurizes. Furthermore, the pressure applied by the airbag needs to reach 240 mmHg in order to collect a complete oscillation waveform and realize the calculation of the user's blood pressure.

[0117] The blood pressure measurement method provided in this application embodiment may include: firstly initiating a first blood pressure measurement, acquiring a PPG signal collected when the airbag pressure value is less than a first value during the first blood pressure measurement, then initiating a second blood pressure measurement, acquiring a PPG signal collected when the airbag pressure value is less than the first value during the second blood pressure measurement, and then determining the user's blood pressure change value during the first and second blood pressure measurements based on the PPG signals and airbag pressure values ​​collected during the first and second blood pressure measurements.

[0118] Since there is a certain mathematical relationship between blood flow and blood pressure and the difference between the airbag pressure and the airbag pressure when the airbag pressure is less than the first value, this application embodiment realizes the use of this mathematical relationship to determine the user's blood pressure change value by using the PPG signal and airbag pressure collected during the blood pressure measurement process.

[0119] This application provides an algorithm for measuring blood pressure. The method utilizes the relationship between the user's blood pressure and the pressure difference applied by the airbag when the pressure applied by the airbag is less than a certain value, and the blood flow. The method calculates the user's blood pressure change trend by using the pressure applied by the airbag and the PPG signal, thus achieving accurate analysis of the user's blood pressure under the premise of theoretical support.

[0120] Furthermore, since the difference between the user's blood pressure and the pressure applied by the airbag has a mathematical relationship with blood flow, this first value is relatively small, typically less than 100 mmHg. This is smaller than the pressure applied when measuring blood pressure using pressure pulses transmitted by blood vessels under external pressure. In other words, in the blood pressure measurement method provided in this application embodiment, the pressure applied by the airbag does not need to reach the pressure required to block blood flow, reducing the user's discomfort when measuring blood pressure. This allows the electronic device to measure blood pressure even with a smaller pressure, while also shortening the blood pressure measurement time and expanding the application scenarios of the blood pressure measurement method provided in this application embodiment.

[0121] The following describes the algorithm derivation process of the blood pressure measurement method involved in the embodiments of this application.

[0122] Figure 11 is a schematic diagram showing the relationship between the cross-sectional area of ​​a blood vessel and the transmural pressure of the blood vessel.

[0123] Transvascular pressure is the difference between the pressure inside the blood vessel or the pressure inside the vessel wall and the external pressure. In the embodiments of this application, transvascular pressure can be expressed by the following formula 1: P = SBP - F Formula 1

[0124] Where P represents transvascular pressure, SBP represents blood pressure, and F represents external force, namely the pressure applied by the electronic device 100 through the airbag.

[0125] As can be seen from Formula 1, transvascular pressure can be equal to the difference between the user's blood pressure and the pressure applied by the electronic device 100 through the airbag.

[0126] As shown in Figure 11, generally speaking, the larger the cross-sectional area of ​​the blood vessel, the greater the transvascular pressure. Furthermore, as can be seen from line segment 1 in Figure 11, when the transvascular pressure reaches a certain range, the cross-sectional area of ​​the blood vessel and the transvascular pressure exhibit a linear relationship. Further, since the transvascular pressure is equal to the difference between the user's blood pressure and the pressure applied by the electronic device 100 through the airbag, assuming the user's blood pressure is constant, the transvascular pressure exhibits a linear relationship when it is within a large range (i.e., when the pressure applied by the electronic device 100 through the airbag is within a small range, such as when the pressure is less than a first value).

[0127] Therefore, the physical meaning of line segment 1 in Figure 11 can be expressed by the following formula 2: S = a1P + b1 (Formula 2)

[0128] Where S represents the cross-sectional area of ​​the blood vessel, P represents the transmural pressure of the blood vessel, and a1 and b1 are constants.

[0129] Furthermore, since the cross-section of a blood vessel is approximately circular, the cross-sectional area of ​​the blood vessel and its diameter are related by the following formula 3:

[0130] Where S represents the cross-sectional area of ​​the blood vessel and D represents the diameter of the blood vessel.

[0131] Substituting Formula 3 into Formula 2 yields:

[0132] Will Substituting into formula 4 yields:

[0133] Additionally, the Darcy-Wiesbach equation shown in Equation 6 can be used to describe the relationship between head loss (or pressure loss) caused by friction in a fixed-length pipe and the average flow velocity in the pipe:

[0134] Where h represents the head loss caused by friction, and f D Let L represent the Darcy friction factor, L represent the pipe length, D represent the pipe diameter, V represent the average velocity of the fluid, and g represent the gravitational acceleration.

[0135] In this embodiment of the application, if Formula 6 is applied to blood pressure measurement, h can refer to the resistance generated by friction in the blood vessel, L can refer to the length of the blood vessel involved in measuring blood pressure, D can refer to the diameter of the blood vessel, and V can refer to the blood flow velocity in the blood vessel.

[0136] Furthermore, in the embodiments of this application, h, f DL and g can all be considered constants; therefore, formula 6 can be further transformed into formula 7: D = a³V 2 Formula 7

[0137] Where a3 is a constant,

[0138] Since the flow rate of a fluid is equal to the cross-sectional area of ​​the fluid multiplied by the flow velocity, the blood flow rate Q and the blood flow velocity V have the following relationship, as shown in Formula 8:

[0139] Substituting formula 7 into formula 8 yields:

[0140] Where a4 is a constant.

[0141] Combining formulas 1, 5, and 9, we can obtain:

[0142] Furthermore, Formula 10 can be derived as follows: Q≈a4(a2(SBP-F)+b2)=a4a2SBP-a4a2F+a4b2 Formula 11

[0143] Where, let a4a2 = a, a4b2 = b, Formula 11 can be further derived as: Q≈a·SBP-a·F+b Formula 12

[0144] As can be seen from Formula 12, when the airbag pressure is less than the first value, the blood flow rate, blood pressure, and the difference between the airbag pressure are linearly related.

[0145] Assuming that during the process of electronic device 100 measuring user blood pressure by inflating an airbag, at time point T... 11 The blood flow rate is Q 11 The user's blood pressure is SBP1, and the pressure applied by the airbag is F. 11 Time point T 12 The blood flow rate is Q 12 The user's blood pressure is SBP1, and the pressure applied by the airbag is F. 12 Therefore, combining formula 12, we can obtain:

[0146] As can be seen from Formula 13, during the process of measuring the user's blood pressure by the electronic device 100 using airbag pressure, the user's blood pressure value SBP1 is equal to the vascular flow Q at the two time points during this blood pressure measurement. 11 Q 12 and airbag pressure value F 11 F 12The calculated intermediate value Subtract a constant

[0147] Furthermore, assuming that during another instance of electronic device 100 measuring a user's blood pressure via airbag inflation, at time point T... 21 The blood flow rate is Q 21 The user's blood pressure was SBP2, and the pressure applied by the airbag was F. 21 Time point T 22 The blood flow rate is Q 22 The user's blood pressure was SBP2, and the pressure applied by the airbag was F. 22 Therefore, similar to formula 13, we can obtain:

[0148] Therefore, by combining formulas 13 and 14, we can obtain:

[0149] As can be seen from Formula 15, as long as the vascular flow Q and the pressure value F applied by the airbag at the two time points during the two airbag pressurization measurements are known, the user's blood pressure change value (SBP1-SBP2) during these two airbag pressurization measurements can be calculated.

[0150] Furthermore, PPG signals characterize changes in light absorption by skin tissue caused by blood flow. Specifically, when the heart contracts, the blood volume in the capillaries increases, enhancing light absorption and thus reducing reflected light; conversely, during diastole, blood flow decreases, increasing reflected light.

[0151] Therefore, it can be considered that the blood flow Q is directly proportional to the PPG signal X, i.e., Q = KX (K is a constant). Therefore, Equation 15 can be further transformed into:

[0152] Among them, X 11 and X 12 For electronic device 100, during a single measurement of user blood pressure via airbag inflation, time point T... 11 and time point T 12 The acquired PPG signal value, X 21 and X 22 During another instance of measuring a user's blood pressure via airbag inflation, electronic device 100, at time point T... 21 and time point T 22 The collected PPG signal value.

[0153] As can be seen from Formula 16, as long as the PPG signal and cuff pressure are collected during a single blood pressure measurement, the median value can be calculated. By combining the PPG signal and cuff pressure collected during another blood pressure measurement, another intermediate value can be calculated. The difference between these two intermediate values ​​represents the change in the user's blood pressure during these two blood pressure measurements.

[0154] In other words, in the blood pressure measurement method provided in this application embodiment, in addition to compressing blood vessels with an airbag, the electronic device 100 also needs to collect the PPG signal reflected by the blood vessels under external pressure through a photoelectric sensor, so that the electronic device 100 can use the airbag pressure and PPG signal to calculate the user's blood pressure.

[0155] Figure 12 illustrates, for example, the waveform of the PPG signal acquired by the electronic device 100 during blood pressure measurement under ideal conditions.

[0156] Since the heartbeat is actually the repeated contraction and relaxation of the heart, when the heart contracts, it pumps blood out of the heart, gradually increasing the blood flow in the blood vessels. This increased blood volume in the blood vessels leads to increased light absorption, resulting in a smaller PPG amplitude. Conversely, when the heart relaxes, blood flows back into the heart from the blood vessels, reducing the blood flow in the blood vessels. This decrease in blood volume reduces light absorption, further decreasing the PPG amplitude. Therefore, as can be seen from Figure 12(a) or (b), the waveform of the PPG signal exhibits a fluctuating trend that changes with the user's heartbeat.

[0157] Furthermore, when the electronic device 100 compresses the blood vessel with an airbag, the greater the pressure applied by the external force, the less blood can flow through the cross-sectional area of ​​the blood vessel, resulting in a gradual decrease in the amplitude of blood flow fluctuations with each heartbeat. Therefore, as can be seen from Figure 12(a) or (b), the pressure applied by the airbag gradually increases over time, causing the amplitude of the PPG signal peaks and troughs to gradually decrease over time. A single peak or trough in the PPG signal can be considered as one heartbeat.

[0158] Furthermore, assuming that Figure 12(a) and (b) represent PPG signals measured with the same pressure applied by the airbag, the blood pressure value corresponding to user (a) in Figure 12 is lower than that corresponding to user (b). This is because if the user's blood pressure is lower, the blood vessels are more easily compressed under the influence of external force, and the peak or trough value of the waveform changes more rapidly as the external force gradually increases. Conversely, if the user's blood pressure is higher, the blood vessels are less easily compressed under the influence of external force, and the peak or trough value of the waveform changes more slowly as the external force gradually increases.

[0159] Therefore, as can be seen from Figure 12(a), when the user's blood pressure is low, if the external force applied to the blood vessel gradually increases, the amplitude of the PPG signal fluctuation decreases more rapidly. As can be seen from Figure 12(b), when the user's blood pressure is high, if the external force applied to the blood vessel gradually increases, the amplitude of the PPG signal fluctuation decreases more slowly.

[0160] Taking the PPG signals obtained from two blood pressure measurements as shown in Figure 12 as an example, since systolic blood pressure refers to the blood pressure at which the arterial blood pressure reaches its highest value when the heart contracts, the peak value of the PPG signal can be used to calculate the user's systolic blood pressure (high pressure). Correspondingly, since diastolic blood pressure refers to the blood pressure at which the arterial blood pressure reaches its lowest value when the heart relaxes, the trough value of the PPG signal can be used to calculate the user's diastolic blood pressure (low pressure).

[0161] So, assuming that in the waveform shown in Figure 12(a), time point T a11 The corresponding PPG signal value is X a11 The pressure applied by the airbag is F a11 Time point T a12 The corresponding PPG signal value is X a12 The pressure applied by the airbag is F a12 Assuming that in the waveform shown in Figure 12(b), time point T a21 The corresponding PPG signal is X a21 The pressure applied by the airbag is F a21 Time point T a22 The corresponding PPG signal value is X a22 The pressure applied by the airbag is F a22 Therefore, using Formula 16, the change in systolic blood pressure between two blood pressure measurements can be calculated.

[0162] Furthermore, assuming that in the waveform shown in Figure 12(a), time point T b11 The corresponding PPG signal value is X b11 The pressure applied by the airbag is F b11 Time point T b12 The corresponding PPG signal value is X b12 The pressure applied by the airbag is F b12 Assuming that in the waveform shown in Figure 12(b), time point T b21 The corresponding PPG signal is X b21 The pressure applied by the airbag is F b21 Time point T b22 The corresponding PPG signal value is X b22 The pressure applied by the airbag is F b22Therefore, using Formula 16, the change in diastolic blood pressure between two blood pressure measurements can be calculated.

[0163] Figure 12 shows the PPG signal collected during the gradual increase of airbag pressure when measuring blood pressure. In addition to using the data collected during the airbag pressurization process to calculate the blood pressure change value, the electronic device 100 can also use the data collected during the airbag depressurization process to calculate the blood pressure change value. In this case, the waveform of the PPG signal collected during the airbag depressurization process is opposite to the waveform shown in Figure 12. Specifically, the amplitude of the peak and trough fluctuations of the PPG signal gradually increases over time.

[0164] In other words, as can be seen from Formula 16, if the PPG signal value X and the pressure value F applied by the airbag at the two time points during the two blood pressure measurements are known, the user's blood pressure change during these two blood pressure measurements can be calculated, including the user's systolic blood pressure change and diastolic blood pressure change.

[0165] In addition, Formula 16 can also be transformed into:

[0166] As can be seen from Formula 17, if the PPG signal value X and the pressure value F applied by the airbag at the two time points during two blood pressure measurements are known, and the user's blood pressure value during one of the blood pressure measurements (hereinafter referred to as the calibration blood pressure value), then the user's blood pressure value during the other blood pressure measurement (hereinafter referred to as the measured blood pressure value) can be calculated.

[0167] The calibrated blood pressure value can be obtained using existing known blood pressure measurement methods.

[0168] For example, during one of the blood pressure measurements, the electronic device 100 can use an external calibration device to measure the user's calibrated blood pressure value. This external calibration device can be a device capable of measuring the user's actual blood pressure value, such as an arm-type blood pressure monitor.

[0169] For example, if the electronic device 100 can measure the user's blood pressure using existing known blood pressure measurement methods, then the electronic device 100 can simultaneously measure blood pressure using the blood pressure measurement method provided in the embodiments of this application, obtain the PPG signal and airbag pressure value collected when the airbag pressure value is less than a first value (e.g., 100 mmHg), and measure the user's calibrated blood pressure value using existing known blood pressure measurement methods.

[0170] Furthermore, if existing known blood pressure measurement methods utilize the pressure pulse transmitted through a blood vessel under external pressure to measure blood pressure, then during one blood pressure measurement, the maximum pressure value of the air bladder in the electronic device 100 can be greater than or equal to the pressure required to block blood flow. Thus, the electronic device 100 can calculate the PPG signal acquired when the air bladder pressure value is less than a first value using the air bladder pressure value. The calibrated blood pressure value SBP1 for the user during this blood pressure measurement is calculated using the complete oscillation wave signal reflected by the blood vessel during the process of vascular occlusion without external pressure. Then, it is combined with the PPG signal and the airbag pressure value collected during another blood pressure measurement when the airbag pressure is lower than the first value to calculate... Finally, the user's measured blood pressure value SBP2 during another blood pressure measurement can be calculated using the above formula 17.

[0171] Taking the PPG signals obtained from the two blood pressure measurements shown in Figure 12 as an example, if the electronic device 100 also measures the user's systolic blood pressure (high pressure value) as SBP through an external calibration device during the blood pressure measurement process corresponding to (a) in Figure 4. a1 The diastolic blood pressure (low pressure) is SBP. b1 Therefore, using Formula 17, we can calculate the user's systolic blood pressure (high pressure value) during the blood pressure measurement process corresponding to Figure 4(b). The user's diastolic blood pressure (systolic blood pressure) should be:

[0172] In other words, as can be seen from Formula 17, if the user's blood pressure change during two blood pressure measurements and the user's actual blood pressure value during one of the blood pressure measurements are calculated, then the user's blood pressure value during the other blood pressure measurement can be calculated.

[0173] Additionally, it should be noted that the waveform diagram shown in Figure 12 depicts the fluctuation of the PPG signal under ideal conditions, i.e., the peak values ​​of the PPG signal are all on a straight line (e.g., as shown in Figure 12(a) from X). a11 To X a12 On the dashed line), the trough values ​​are all on a straight line (for example, as shown in Figure 12(a) from X). b11 To X b12 The PPG signal is measured on the dashed line, but due to various factors, the acquisition of the PPG signal is not stable enough, so that in the actual waveform of the PPG signal, some peak values ​​are not on a straight line, or some trough values ​​are not on a straight line.

[0174] Therefore, in order to achieve more accurate blood pressure measurement, after the PPG signal is actually acquired, the waveform corresponding to the PPG signal can be linearly fitted, and the value on the fitted straight line can be selected to calculate the systolic blood pressure change or systolic blood pressure value, or the diastolic blood pressure change or diastolic blood pressure value.

[0175] For example, linear fitting of the waveform corresponding to the PPG signal can be achieved using any of the following methods:

[0176] 1) Select a fixed number of heartbeats or a specified range of heartbeats, and use a sliding window to perform linear fitting in the rising or falling segment of the waveform, and select the line with the best fitting effect as the final fitting result.

[0177] For example, the fixed number of heartbeats can be 3, 5, etc., and the specified range of heartbeats can be (2,6). This application embodiment does not limit this.

[0178] One heartbeat corresponds to one peak or one trough on the PPG waveform. Therefore, selecting a fixed number of heartbeats is equivalent to selecting a specified number of peaks or troughs, and selecting a specified range of heartbeats is equivalent to selecting a certain number of peaks or troughs within a certain range, and performing linear fitting within the specified range of the PPG waveform.

[0179] The line with the best fit can be the line with the most peaks or troughs, or the line whose peaks or troughs are closest to the line.

[0180] The rising segment of the waveform refers to the curve segment in the PPG waveform where multiple consecutive peak values ​​gradually increase, while the falling segment refers to the curve segment in the PPG waveform where multiple consecutive peak values ​​gradually decrease.

[0181] Specifically, if the electronic device 100 collects the PPG signal during the airbag inflation process, linear fitting can be performed using a sliding window method on the waveform's descending segment. Conversely, if the electronic device 100 collects the PPG signal during the airbag depressurization process, linear fitting can be performed on the waveform's ascending segment. In other words, if the electronic device 100 uses data collected during airbag inflation to calculate blood pressure, linear fitting can be performed on the waveform's descending segment; if the electronic device 100 uses data collected during airbag depressurization to calculate blood pressure, linear fitting can be performed on the waveform's ascending segment.

[0182] 2) Under a fixed pressure difference or within a specified pressure difference range, linear fitting is performed in the rising or falling segment of the waveform using a sliding window, and the straight line with the best fitting effect is selected as the final fitting result.

[0183] The pressure difference can refer to the difference in pressure applied by the airbag at two different time points during blood pressure measurement.

[0184] For example, the fixed pressure difference value may refer to 20 mmHg, and the specified pressure difference value range may refer to (10 mmHg, 50 mmHg). This application embodiment does not limit this.

[0185] Since the pressure applied by the airbag varies at different time points in the waveform corresponding to the PPG signal, selecting a fixed pressure difference or a specified pressure difference range is equivalent to performing linear fitting on the PPG waveform within a certain range.

[0186] For details regarding the fitting effect, as well as the description of the rising and falling segments of the waveform, please refer to the relevant description in Method 1 above, which will not be repeated here.

[0187] In addition to using heart rate and pressure difference as reference factors, other reference factors, such as time, PPG signal difference, etc., can be used to select the fitting range of PPG waveform. This application does not limit this.

[0188] Figure 13 is a waveform diagram of the PPG signal collected by the electronic device 100 provided in this embodiment of the application during the airbag inflation process. The principle of linear fitting of the PPG waveform is described below with reference to Figure 13.

[0189] As shown in Figure 13, the PPG waveform fluctuates up and down over time. After time point T1, the peak of the PPG waveform gradually decreases. Therefore, the PPG waveform after time point T1 belongs to the declining segment of the waveform.

[0190] In chronological order, the peaks of the falling segment of the waveform are numbered sequentially as follows: 1, 2, 3, 4, 5, 6...

[0191] Assuming a fixed heart rate of 4 beats per minute is used to linearly fit the PPG waveform, we can first perform linear fitting on peaks 1, 2, 3, and 4 to determine line 1. Then, we can perform linear fitting on peaks 2, 3, 4, and 5 to determine line 2. Next, we can perform linear fitting on peaks 3, 4, 5, and 6 to determine line 3, and so on... Then, we select the line with the best fit from these multiple lines 1, 2, 3... as the final fitting result. If line 2 is the best-fitting line, we can select the PPG signal value and time on line 2, as well as the pressure value applied by the airbag at that time, to calculate the blood pressure change or blood pressure value.

[0192] Figure 13 only illustrates the principle of linear fitting of the PPG waveform when determining the systolic blood pressure change or systolic blood pressure value. The principle of linear fitting of the PPG waveform for determining the diastolic blood pressure change or diastolic blood pressure value is similar, except that the trough value of the PPG signal is selected when linearly fitting the PPG waveform. Furthermore, the PPG waveform shown in Figure 13 is merely illustrative and does not constitute a limitation on the embodiments of this application.

[0193] Figure 14 illustrates the blood pressure measurement method provided in an embodiment of this application. Further details are provided below.

[0194] S101. Electronic device 100 initiates the first blood pressure measurement. During the first blood pressure measurement, a first pressure is applied to the airbag, including a pressure less than a first value. During the application of the first pressure, a first PPG signal is acquired when the applied pressure is less than the first value.

[0195] Among them, electronic device 100 can be wearable devices such as watches, bracelets, and rings, or devices such as wrist blood pressure monitors and arm blood pressure monitors.

[0196] For example, the electronic device 100 may include a pressurization module and a PPG signal detection module.

[0197] During blood pressure measurement, the pressurization module applies pressure to the user's skin and compresses subcutaneous blood vessels when the user wears the electronic device 100. The PPG signal detection module can collect PPG signals when the pressurization module compresses the subcutaneous blood vessels.

[0198] For example, the pressurization module may include a motor and an airbag. The electronic device 100 can apply pressure to the airbag through the motor to compress subcutaneous blood vessels. The PPG signal detection module may include a photoelectric sensor. The electronic device 100 can emit light to the skin through the photoelectric sensor and collect PPG signals using the light reflected back from the blood vessels.

[0199] In addition, the electronic device 100 can collect the pressure value applied to the airbag by the electronic device 100 during the blood pressure measurement process through a pressure sensor.

[0200] For detailed descriptions of the pressurization module, PPG signal detection module, and pressure sensor, please refer to the relevant content of pressurization module 193, photoelectric sensor 180B, and pressure sensor 180C in Figure 2 above, which will not be repeated here.

[0201] For example, the electronic device 100 can initiate blood pressure measurement in any one or more of the following ways:

[0202] 1) Electronic device periodically starts blood pressure measurement.

[0203] In this case, the electronic device 100 can activate blood pressure measurement at regular intervals to periodically monitor the user's blood pressure.

[0204] Furthermore, during the periodic blood pressure measurement process of the electronic device 100, if the electronic device 100 detects that the user is in a state where measurement is not possible, such as during exercise, just before starting a blood pressure measurement, the electronic device 100 can automatically skip the blood pressure measurement or delay the blood pressure measurement.

[0205] 2) Electronic device 100 initiates blood pressure measurement based on user operation.

[0206] In this situation, the electronic device 100 can respond to the user's action of initiating blood pressure measurement by starting the measurement itself. This increases the user's autonomy when measuring blood pressure, allowing the user to decide whether to activate the measurement based on their own needs.

[0207] 3) Electronic device 100 starts blood pressure measurement when preset conditions are met.

[0208] The preset conditions can refer to a specified time, a specified physical condition, etc. For example, the electronic device 100 can start blood pressure measurement at 12:00 noon, or it can start blood pressure measurement when it detects that the user is in a static state. This application embodiment does not limit the preset conditions.

[0209] The electronic device 100 can also initiate blood pressure measurement in other ways, and this application embodiment does not limit this.

[0210] The first value is less than the pressure required to block blood flow. For example, this first value could be 100 mmHg, and can be preset by the developer. Since the user's blood flow and the difference between the user's blood pressure and the airbag pressure are linearly related when the pressure applied by the airbag is less than the first value, the electronic device 100 can utilize this linear relationship to analyze the user's blood pressure using the PPG signal acquired when the airbag pressure is less than the first value and the airbag pressure itself.

[0211] This first value can be determined based on the range of values ​​of transvascular pressure when there is a linear relationship between the cross-sectional area of ​​the blood vessel and the transvascular pressure. This first value should be less than the maximum external pressure corresponding to the range of values ​​of transvascular pressure when the user's blood pressure is constant.

[0212] During the first blood pressure measurement, the electronic device 100 applies a first pressure to the cuff, which may include pressures less than a first value, and the following two situations are possible:

[0213] 1) During the first blood pressure measurement, the maximum pressure applied to the airbag was less than the first value.

[0214] In this scenario, the pressure applied to the cuff by the electronic device 100 during the first blood pressure measurement will not exceed the pressure required to block blood flow. In other words, the pressure applied by the electronic device 100 during the initial blood pressure measurement is relatively low; this blood pressure measurement mode can be considered a low-pressure inflator mode. This reduces user discomfort during blood pressure measurement, achieving a virtually imperceptible measurement experience.

[0215] In some implementations, the electronic device 100 can provide a blood pressure trend tracking function. After the electronic device 100 activates this function, it can periodically start blood pressure measurement in a low-pressure inflation mode and use the PPG signal and cuff pressure collected during multiple blood pressure measurements to analyze the user's blood pressure change trend.

[0216] 2) During the first blood pressure measurement, the maximum pressure applied to the airbag was greater than the first value.

[0217] During the first blood pressure measurement, the maximum pressure applied to the airbag can be greater than or equal to the pressure required to block blood flow.

[0218] In this scenario, the electronic device 100 can not only acquire the PPG signal when the cuff pressure is below a first value during the first blood pressure measurement, but also obtain the complete oscillation waveform of the blood vessel during the process of occlusion without external pressure. Thus, the electronic device 100 can use this complete oscillation waveform to calculate the user's blood pressure value during the first blood pressure measurement.

[0219] In addition, the first PPG signal collected by the electronic device 100 can be data collected during the airbag inflation process, or it can be data collected during the airbag depressurization process.

[0220] In other words, the electronic device 100 can analyze the user's blood pressure using data collected during the airbag inflation process, and it can also analyze the user's blood pressure using data collected during the airbag depressurization process.

[0221] For example, taking the use of data collected during the airbag inflation process by the electronic device 100 to analyze the user's blood pressure, the electronic device 100 can adopt any of the following inflation strategies during airbag inflation:

[0222] 1) Pressurize by increasing pressure at a constant speed.

[0223] 2) Pressurize by first increasing the pressure to a certain value at a relatively fast speed, and then increasing the pressure at a slower speed.

[0224] Other boost strategies may also be used in the electronic device 100, and this application embodiment does not limit them.

[0225] In addition, if the electronic device 100 uses the data collected during the airbag decompression process to analyze the user's blood pressure, its decompression strategy is similar to its blood pressure increase strategy. For example, it may use a method of decreasing the pressure at a constant speed, or it may use a method of decreasing the pressure at a slower speed to a certain value and then decreasing the pressure at a faster speed.

[0226] Because the electronic device 100 inflates the cuff to a certain value and then deflates it during blood pressure measurement, if the first blood pressure measurement is performed in low-pressure inflation mode, the electronic device 100 can stop inflating the cuff under any of the following conditions during the inflation process:

[0227] 1) After the electronic device 100 increases the airbag pressure to the upper pressure limit, it stops increasing the pressure.

[0228] For example, if the first blood pressure measurement is performed in a low-pressure boost mode, the upper limit of the pressure is a first value, such as 100 mmHg.

[0229] 2) When the waveform of the acquired PPG signal shows a significant drop, the electronic device 100 can stop boosting the voltage after the user's heart rate reaches a preset number.

[0230] A significant drop in the waveform of a PPG signal can refer to a continuous decrease in multiple (e.g., 3) peak values ​​of the PPG signal, or further, a difference between two adjacent peak values ​​exceeding a threshold.

[0231] The electronic device 100 can determine the user's heart rate based on the number of peaks appearing in the waveform of the PPG signal.

[0232] For example, the preset number of times can be 3. This application embodiment does not limit the preset number of times.

[0233] Alternatively, in mode 2, the electronic device 100 can also set a pressure upper limit. That is, the electronic device 100 can first increase the pressure of the airbag according to the pressure upper limit. If the conditions of mode 2 are met, that is, after the waveform of the acquired PPG signal shows a significant drop and a PPG signal containing a preset number of heartbeats has been acquired, the pressurization can be stopped directly without reaching the pressure upper limit.

[0234] 3) Electronic device 100 can stop pressurizing after the airbag pressurization time reaches the preset duration.

[0235] The preset duration can be 5 seconds, but this application embodiment does not limit it.

[0236] The electronic device 100 can also stop pressurizing when other conditions are met, and this application embodiment does not limit this.

[0237] S102. Electronic device 100 acquires the user's blood pressure value at the time of the first blood pressure measurement.

[0238] The user's blood pressure value during the first blood pressure measurement can be obtained using existing known blood pressure measurement methods, such as oscillometric method and mercury sphygmomanometer method.

[0239] In addition, the user's blood pressure value at the time of the first blood pressure measurement can be obtained by electronic device 100 or by other devices.

[0240] If the user's blood pressure value during the first blood pressure measurement is obtained by another device, the other device can send the blood pressure value to the electronic device 100, or the user can manually input the blood pressure value into the electronic device 100 so that the electronic device 100 can obtain the blood pressure value.

[0241] If the user's blood pressure value during the first blood pressure measurement is obtained by the electronic device 100, the maximum pressure applied to the cuff during the first blood pressure measurement can be greater than or equal to the pressure required to block blood flow. In this way, the electronic device 100 can use the oscillating waveform signal collected during the first blood pressure measurement, when the blood vessel is not compressed by external force to block blood flow, to determine the user's blood pressure value during the first blood pressure measurement.

[0242] It is understood that the embodiments of this application do not limit the method by which the electronic device 100 obtains the user's blood pressure value during the first blood pressure measurement. Furthermore, step S102 can be an optional step; that is, the electronic device 100 does not need to obtain the user's blood pressure value during the first blood pressure measurement.

[0243] S103. Electronic device 100 initiates a second blood pressure measurement. During the second blood pressure measurement, a second pressure is applied to the airbag, including a pressure less than the first value. During the application of the second pressure, a second PPG signal is acquired when the applied pressure is less than the first value.

[0244] Similar to the first blood pressure measurement, during the second blood pressure measurement, the pressure applied to the air bladder by the electronic device 100 can fall into one of the following two categories:

[0245] 1) During the second blood pressure measurement, the maximum pressure applied to the airbag was less than the first value.

[0246] In other words, the second blood pressure measurement initiated by the electronic device 100 can be performed in a low-pressure pressurization mode.

[0247] 2) During the second blood pressure measurement, the maximum pressure applied to the airbag was greater than the first value.

[0248] In this way, the electronic device 100 can collect PPG signals even when the pressure applied by the airbag is less than the first value.

[0249] In addition, the second PPG signal collected by the electronic device 100 can be data collected during the airbag inflation process, or it can be data collected during the airbag depressurization process.

[0250] For details regarding the second blood pressure measurement process, including the method of initiating the measurement, the airbag inflation strategy, and the method of stopping inflation, please refer to the relevant content in step S101 above, which will not be repeated here.

[0251] It should be understood that step S103 can be executed before or after step S101, and the embodiments of this application do not limit this.

[0252] S104. The electronic device 100 determines the user's blood pressure change during the first and second blood pressure measurements based on the first PPG signal, the second PPG signal, the first pressure, and the second pressure.

[0253] The electronic device 100 can determine the user's blood pressure change during the first and second blood pressure measurements based on the relationship between the first PPG signal, the second PPG signal, the first pressure, the second pressure, and the blood flow when the airbag pressure is less than the first value, and the difference between blood pressure and airbag pressure.

[0254] Among them, when the airbag pressure is less than the first value, the relationship between blood flow and blood pressure and the difference between airbag pressure can be found in the above formula 12.

[0255] It can be seen that when the airbag pressure is less than the first value, the blood flow, blood pressure and the difference between the airbag pressure are linearly related.

[0256] Specifically, the electronic device 100 can determine a first intermediate value based on the airbag pressure and PPG signal at two time points during the first blood pressure measurement, and determine a second intermediate value based on the airbag pressure and PPG signal at two time points during the second blood pressure measurement. The difference between the first intermediate value and the second intermediate value is determined as the user's blood pressure change value during the first and second blood pressure measurements.

[0257] For example, the first pressure may include: pressure applied at a first time point and pressure applied at a second time point. The electronic device 100 may determine a first intermediate value based on the pressure applied at the first time point, the pressure applied at the second time point, the PPG signal corresponding to the first time point, and the PPG signal corresponding to the second time point, wherein the PPG signal corresponding to the first time point and the PPG signal corresponding to the second time point are determined according to the first PPG signal.

[0258] Combining with Formula 16 above,

[0259] Among them, X 11 X represents the PPG signal corresponding to the first time point. 12 F represents the PPG signal corresponding to the second time point. 11 F represents the pressure applied at the first point in time. 12 This indicates the pressure applied at the second point in time.

[0260] Similarly, the second pressure may include: the pressure applied at a third time point and the pressure applied at a fourth time point. The electronic device 100 may determine the second intermediate value based on the pressure applied at the third time point, the pressure applied at the fourth time point, the PPG signal corresponding to the third time point, and the PPG signal corresponding to the fourth time point, wherein the PPG signal corresponding to the third time point and the PPG signal corresponding to the fourth time point are determined according to the second PPG signal.

[0261] Combining with Formula 16 above,

[0262] Among them, X 21 X represents the PPG signal corresponding to the third time point. 22 F represents the PPG signal corresponding to the fourth time point. 21 F represents the pressure applied at the third time point. 22 This indicates the pressure applied at the fourth time point.

[0263] The difference between the first intermediate value and the second intermediate value can represent the change in blood pressure from the second blood pressure measurement to the first blood pressure measurement; the difference between the second intermediate value and the first intermediate value can represent the change in blood pressure from the first blood pressure measurement to the second blood pressure measurement.

[0264] The first and second time points can refer to any two time points during the first blood pressure measurement, and the third and fourth time points can refer to any two time points during the second blood pressure measurement.

[0265] Among them, the PPG signals corresponding to the first and second time points, as well as the PPG signals corresponding to the third and fourth time points, fall into the following two categories:

[0266] Scenario 1: The PPG signal corresponding to the first time point can refer to the PPG signal of the first PPG signal at the first time point, and the PPG signal corresponding to the second time point can refer to the PPG signal of the first PPG signal at the second time point. Similarly, the PPG signal corresponding to the third time point can refer to the PPG signal of the second PPG signal at the third time point, and the PPG signal corresponding to the fourth time point can refer to the PPG signal of the second PPG signal at the fourth time point.

[0267] In other words, the electronic device 100 can directly use the values ​​on the collected PPG signal to calculate the user's blood pressure change value using the above formula 16.

[0268] This reduces the computational load on electronic devices by 100%.

[0269] Case 2: The PPG signals at the first and second time points are obtained by linearly fitting the first PPG signal, and the PPG signals at the third and fourth time points are obtained by linearly fitting the second PPG signal.

[0270] Specifically, the electronic device 100 can perform linear fitting on the first PPG signal to obtain a first straight line. The PPG signal corresponding to the first time point can refer to the value of the first straight line at the first time point, and the PPG signal corresponding to the second time point can refer to the value of the first straight line at the second time point. Similarly, the electronic device 100 can perform linear fitting on the second PPG signal to obtain a second straight line. The PPG signal corresponding to the third time point can refer to the value of the second straight line at the third time point, and the PPG signal corresponding to the fourth time point can refer to the value of the second straight line at the fourth time point.

[0271] In other words, after the electronic device 100 acquires the PPG signal during the blood pressure measurement process, it can first perform linear fitting processing on the PPG signal and use the processed PPG signal value to calculate the user's blood pressure change value.

[0272] This can improve the accuracy of blood pressure change calculations.

[0273] Furthermore, since a user's blood pressure includes systolic and diastolic pressure, the user's blood pressure variation can include the following two types:

[0274] 1) Change in systolic blood pressure

[0275] If the user's blood pressure change value includes the systolic blood pressure change value, when the electronic device 100 determines the user's blood pressure change value from the first blood pressure measurement to the second blood pressure measurement based on the first PPG signal, the second PPG signal, the first pressure, and the second pressure, the first PPG signal can specifically refer to the peak value in the first PPG signal, and the second PPG signal can specifically refer to the peak value in the second PPG signal.

[0276] Based on the above situation 1, the PPG signal corresponding to the first time point can refer to the peak value of the first PPG signal at the first time point, the PPG signal corresponding to the second time point can refer to the peak value of the first PPG signal at the second time point, similarly, the PPG signal corresponding to the third time point can refer to the peak value of the second PPG signal at the third time point, and the PPG signal corresponding to the fourth time point can refer to the peak value of the second PPG signal at the fourth time point.

[0277] Based on scenario 2 above, the PPG signals at the first and second time points are obtained by linearly fitting multiple peak values ​​from the first PPG signal. Specifically, the first straight line is the straight line obtained by linearly fitting multiple peak values ​​from the first PPG signal. Similarly, the PPG signals at the third and fourth time points are obtained by linearly fitting multiple peak values ​​from the second PPG signal. Specifically, the second straight line is the straight line obtained by linearly fitting multiple peak values ​​from the second PPG signal.

[0278] 2) Changes in diastolic blood pressure

[0279] If the user's blood pressure change value includes the diastolic blood pressure change value, then when the electronic device 100 determines the user's blood pressure change value from the first blood pressure measurement to the second blood pressure measurement based on the first PPG signal, the second PPG signal, the first pressure, and the second pressure, the first PPG signal can specifically refer to the trough value in the first PPG signal, and the second PPG signal can specifically refer to the trough value in the second PPG signal.

[0280] Based on the above situation 1, the PPG signal corresponding to the first time point can refer to the trough value of the first PPG signal at the first time point, the PPG signal corresponding to the second time point can refer to the trough value of the first PPG signal at the second time point, similarly, the PPG signal corresponding to the third time point can refer to the trough value of the second PPG signal at the third time point, and the PPG signal corresponding to the fourth time point can refer to the trough value of the second PPG signal at the fourth time point.

[0281] Based on scenario 2 above, the PPG signals at the first and second time points are obtained by linearly fitting multiple trough values ​​in the first PPG signal. Specifically, the first straight line is the straight line obtained by linearly fitting multiple trough values ​​in the first PPG signal. Similarly, the PPG signals at the third and fourth time points are obtained by linearly fitting multiple trough values ​​in the second PPG signal. Specifically, the second straight line is the straight line obtained by linearly fitting multiple trough values ​​in the second PPG signal.

[0282] For a detailed description of linear fitting of the PPG signal, please refer to Figure 5 above and its related content, which will not be repeated here.

[0283] In some implementations, the first pressure and / or the second pressure does not exceed a first value, which is less than the pressure required to block the blood vessel. That is, the electronic device 100, using a low-pressure pressurization mode for blood pressure measurement, can calculate the user's blood pressure changes over a period of time. This not only reduces user discomfort during blood pressure measurement but also allows for accurate calculation of the user's blood pressure changes.

[0284] In some implementations, the electronic device 100 can continue to perform multiple blood pressure measurements, using the PPG signal acquired during the blood pressure measurement when the cuff pressure is lower than the first value and the cuff pressure value to calculate a third intermediate value, a fourth intermediate value, and so on. These multiple intermediate values ​​are then used to analyze the user's blood pressure over a period of time. For example, the average real variability (ARV) can be calculated using the following formula 18:

[0285] Here, ARV represents mean dynamic variability, used to reflect the stability and fluctuation of blood pressure over a period of time, N represents the number of blood pressure measurements, and BP... k This represents the intermediate value obtained from the k-th blood pressure measurement, such as the first intermediate value, the second intermediate value, the third intermediate value, the fourth intermediate value, and so on.

[0286] Furthermore, the intermediate value obtained from the k-th blood pressure measurement is determined based on the PPG signal and airbag pressure collected during the k-th blood pressure measurement when the airbag pressure is lower than the first value. See the calculation formulas for the first and second intermediate values ​​above for details.

[0287] In some implementations, after the electronic device 100 calculates the user's blood pressure change value, the electronic device 100 can display the blood pressure change value so that the user can understand their blood pressure changes over a period of time.

[0288] Furthermore, if the electronic device 100 performs multiple blood pressure measurements, it can calculate the change in the user's blood pressure between any two measurements. The electronic device 100 can then display a curve plotted from these multiple blood pressure changes, allowing the user to understand the trend of their blood pressure changes over a period of time.

[0289] S105. Electronic device 100 determines the user's blood pressure value during the second blood pressure measurement based on the changes in blood pressure during the first and second blood pressure measurements and the user's blood pressure value during the first blood pressure measurement.

[0290] As can be seen from Formula 17, the user's blood pressure value during the second blood pressure measurement is equal to the user's blood pressure value during the first blood pressure measurement, minus the change in blood pressure between the first and second blood pressure measurements. This is because the change in the user's blood pressure directly reflects the trend of blood pressure change between the two measurements. If the user's accurate blood pressure value during one measurement is known, the user's blood pressure value during the other measurement can be calculated.

[0291] The blood pressure values ​​measured during the second blood pressure measurement include the following two types:

[0292] 1) Systolic blood pressure value

[0293] The systolic blood pressure value of a user during the second blood pressure measurement is equal to the systolic blood pressure value of the user during the first blood pressure measurement, minus the change in systolic blood pressure between the first and second blood pressure measurements.

[0294] 2) Diastolic blood pressure value

[0295] The diastolic blood pressure value of a user during the second blood pressure measurement is equal to the diastolic blood pressure value of the user during the first blood pressure measurement, minus the change in diastolic blood pressure between the first and second blood pressure measurements.

[0296] In some implementations, the electronic device 100 can perform multiple blood pressure measurements, so that the electronic device 100 can obtain the blood pressure change value between any two blood pressure measurements. As long as the electronic device 100 knows the user's blood pressure value at any one of these multiple blood pressure measurements, it can calculate the user's blood pressure value at any of the other blood pressure measurements.

[0297] Furthermore, as can be seen from Formula 16, the difference between the intermediate values ​​calculated by the electronic device 100 from the PPG signals and airbag pressure values ​​collected during the two blood pressure measurements can only be considered as an approximation of the blood pressure difference between the user during these two blood pressure measurements.

[0298] If the electronic device 100 acquires the user's blood pressure values ​​during N (N≥2) blood pressure measurements, as well as the PPG signal and airbag pressure collected during these N blood pressure measurements when the airbag pressure is less than a first value, then the electronic device 100 can use this data to find a more accurate mathematical relationship between the difference between the intermediate value calculated using the airbag pressure and PPG signal collected during the blood pressure measurement process and the user's actual blood pressure difference. Then, it can use this mathematical relationship to calculate the user's accurate blood pressure value for any given blood pressure measurement, thereby improving the accuracy of blood pressure calculation.

[0299] Specifically, Formula 17 can be transformed into the following Formula 19:

[0300] SBP1 represents the user's blood pressure value during the first blood pressure measurement, and SBP2 represents the user's blood pressure value during the second blood pressure measurement. Indicates the first intermediate value. The second intermediate value is represented by α, which is a coefficient determined based on the user's blood pressure values ​​during N blood pressure measurements, and the PPG signal and airbag pressure collected during these N blood pressure measurements when the airbag pressure is less than the first value.

[0301] α can be calculated using the following steps:

[0302] Step 1: Based on the PPG signal and airbag pressure collected during N blood pressure measurements when the airbag pressure is less than the first value, electronic device 100 calculates M intermediate values ​​S1, S2, S3…S… N .

[0303] The calculation method for any of the intermediate values ​​can be found in the descriptions of the first and second intermediate values ​​above, and will not be repeated here.

[0304] Step 2: Electronic device 100 can generate N-1 sets of blood pressure data. The i-th set of blood pressure data includes: the blood pressure change value ΔS from the i-th and K-th blood pressure measurements. i,K And the user's blood pressure value (SBP) at the i-th blood pressure measurement. i . i, K=1,2,3,...N, and K≠i.

[0305] Among them, the blood pressure change ΔS during the i-th and K-th blood pressure measurements i,K =S i -S K .

[0306] Assuming K is 2, then these N-1 sets of blood pressure data include: (ΔS 1,2 ,SBP1),(ΔS 3,2,SBP3),……(ΔS N,2 SBP N ).

[0307] Step 3: Electronic device 100 can use ΔS i,K and SBP i Using the coordinate axis as the coordinate axis, plot these N sets of data as N-1 data points on the coordinate axis, and find the straight line that fits these N-1 data points by linear fitting, where the slope of the straight line is α.

[0308] Figure 15 illustrates the principle of linear fitting for multiple data points.

[0309] As can be seen from Figure 15, the slope of the straight line obtained after linear fitting of multiple data points is the coefficient α required in Formula 19.

[0310] After the electronic device 100 calculates the coefficient α required by Formula 19, the difference between the intermediate values ​​calculated during any two known blood pressure measurements is taken. Given the user's calibrated blood pressure value SBP1 during one of the blood pressure measurements, the electronic device 100 can use formula 19 to calculate the user's measured blood pressure value SBP2 during the other blood pressure measurement process. Furthermore, compared to formula 17, the measured blood pressure value calculated by formula 19 is more accurate, thus improving the accuracy of blood pressure measurement.

[0311] Furthermore, it can be understood that after the electronic device 100 calculates the coefficient α, the electronic device 100 can also use the coefficient α to calculate a more accurate blood pressure change value for the user between two blood pressure measurements. In other words, the change in blood pressure during the first and second blood pressure measurements can also be equal to the difference between the first and second intermediate values ​​multiplied by a coefficient α.

[0312] In some embodiments, after the electronic device 100 performs multiple blood pressure measurements, the electronic device 100 may display the user's calibrated blood pressure value and the measured blood pressure value calculated using the blood pressure measurement method provided in the embodiments of this application.

[0313] Figure 16 illustrates an exemplary user interface 20 for displaying blood pressure measurement results. As shown in Figure 16, the user interface 20 may include a blood pressure diagram 301, which can be used to display calibrated blood pressure values ​​and measured blood pressure values ​​obtained by the electronic device 100 when measuring blood pressure at different times. Both the calibrated blood pressure value and the measured blood pressure value may include two blood pressure values: systolic blood pressure value and diastolic blood pressure value.

[0314] In the user interface 20, the calibrated blood pressure value and the measured blood pressure value can be marked with different labels on the blood pressure diagram 301. Since the measured blood pressure value is an approximate calculation, the display area of ​​the label corresponding to the measured blood pressure value can be larger than the display area of ​​the label corresponding to the standard blood pressure value.

[0315] In this way, users can understand their blood pressure levels at different times, enabling them to manage and control their blood pressure health in a timely manner.

[0316] Furthermore, when measuring blood pressure using an airbag inflator, it is generally necessary to keep the measurement site aligned with the heart to ensure the accuracy of the measurement results. The measurement site can refer to the area where the user wears the electronic device 100. For example, if the electronic device 100 is a watch worn on the user's wrist, then the electronic device 100 needs to keep the user's wrist as level as possible with the heart when measuring blood pressure.

[0317] In some implementations, the electronic device 100 may display a prompt message before initiating blood pressure measurement, reminding the user to keep the measurement site aligned with the heart.

[0318] In other embodiments, if the electronic device 100 cannot ensure that the user's detection site is aligned with the heart during actual blood pressure measurement, the electronic device 100 may perform the following operations:

[0319] 1) The electronic device 100 can distinguish and display the measurement results of the user's detection site that is not level with the heart from the other measurement results, so that the user can distinguish between accurate and inaccurate measurement results.

[0320] 2) Electronic device 100 can only calculate the blood pressure change during the blood pressure measurement process, without calculating the user's blood pressure value.

[0321] 3) The electronic device 100 can compensate for the blood pressure measurement results based on the positional difference between the user's detection site and the heart.

[0322] Among them, the electronic device 100 can track the position of the user's detection site in real time based on sensors such as accelerometer and gyroscope. When the electronic device 100 measures blood pressure, it compensates for the blood pressure value calculated by the electronic device 100 based on the position difference or height difference between the user's detection site and the heart.

[0323] As can be seen from steps S101-S105, the electronic device 100 can use a low-pressure pressurization mode to measure blood pressure and monitor the user's blood pressure change trend, or further combine the user's blood pressure values ​​from one or more blood pressure measurements to deduce the user's blood pressure values ​​from other blood pressure measurements.

[0324] Because the pressure applied by the electronic device 100 is relatively small in the low-pressure pressurization mode, it causes less interference to the user. Therefore, the blood pressure measurement method provided in this application embodiment can be applied to blood pressure measurement during breathing training. It does not require the airbag to exert a force on the user's blood vessels that is strong enough to block blood flow after inflation. It can simultaneously provide tactile feedback for breathing training and blood pressure measurement based on the airbag, realizing the reuse of the airbag inflation process for tactile feedback and the airbag inflation and deflation process for blood pressure measurement. In this way, the user can complete blood pressure measurement imperceptibly during breathing training, improving the comfort of using the device.

[0325] Figure 17 shows a schematic diagram of the hardware structure of the electronic device 100.

[0326] Electronic device 100 may be a mobile phone, tablet computer, desktop computer, laptop computer, handheld computer, notebook computer, ultra-mobile personal computer (UMPC), netbook, as well as cellular phone, personal digital assistant (PDA), augmented reality (AR) device, virtual reality (VR) device, artificial intelligence (AI) device, wearable device, in-vehicle device, smart home device and / or smart city device. The embodiments of this application do not impose any special restrictions on the specific type of electronic device.

[0327] In this embodiment of the application, electronic device 100 may refer to a watch, bracelet, wrist blood pressure monitor, arm blood pressure monitor, or ring, etc.

[0328] Electronic device 100 may include a processor 110, internal memory 121, charging management module 140, power management module 141, battery 142, sensor module 180, pressurization module 193, and display screen 194, etc. Optionally, electronic device 100 may also include one or more of the following: wireless communication module 160, audio module 170, buttons 190, motor 191, indicator 192, etc. The audio module 170 may include one or more of the following: speaker 170A, receiver 170B, and microphone 170C. The sensor module 180 may include touch sensor 180A, photoelectric sensor 180B, pressure sensor 180C, etc.

[0329] Processor 110 may include one or more processing units, such as application processor (AP), modem processor, graphics processing unit (GPU), image signal processor (ISP), controller, video codec, digital signal processor (DSP), baseband processor, and / or neural network processing unit (NPU). These different processing units may be independent devices or integrated into one or more processors.

[0330] The processor 110 can control the pressure applied to the airbag and collect PPG signals during blood pressure measurement, and calculate the user's blood pressure change during the two blood pressure measurements based on the PPG signals and airbag pressure collected during the two blood pressure measurements.

[0331] The controller can generate operation control signals based on the instruction opcode and timing signals to complete the control of instruction fetching and execution.

[0332] The processor 110 may also include a memory for storing instructions and data. In some embodiments, the memory in the processor 110 is a cache memory. This memory can store instructions or data that the processor 110 has just used or that are used repeatedly. If the processor 110 needs to use the instruction or data again, it can retrieve it directly from the memory. This avoids repeated accesses, reduces the waiting time of the processor 110, and thus improves the efficiency of the system.

[0333] The processor 110 may include one or more interfaces. These interfaces may include an inter-integrated circuit (I2C) interface, an inter-integrated circuit sound (I2S) interface, a pulse code modulation (PCM) interface, a universal asynchronous receiver / transmitter (UART) interface, a mobile industry processor interface (MIPI), a general-purpose input / output (GPIO) interface, a subscriber identity module (SIM) interface, and / or a universal serial bus (USB) interface, etc.

[0334] The charging management module 140 receives charging input from a charger. The charger can be a wireless charger or a wired charger. In some wired charging embodiments, the charging management module 140 can receive charging input from a wired charger. In some wireless charging embodiments, the charging management module 140 can receive wireless charging input through the wireless charging coil of the electronic device 100. While charging the battery 142, the charging management module 140 can also supply power to the electronic device through the power management module 141.

[0335] The power management module 141 connects the battery 142, the charging management module 140, and the processor 110. The power management module 141 receives input from the battery 142 and / or the charging management module 140, providing power to the processor 110, internal memory 121, display screen 194, and wireless communication module 160, etc. The power management module 141 can also monitor parameters such as battery capacity, battery cycle count, and battery health status (leakage current, impedance). In some other embodiments, the power management module 141 may also be located within the processor 110. In other embodiments, the power management module 141 and the charging management module 140 may be located in the same device.

[0336] The wireless communication module 160 can provide solutions for wireless communication applied to the electronic device 100, including wireless local area networks (WLANs) (such as wireless fidelity (Wi-Fi) networks), Bluetooth (BT), global navigation satellite system (GNSS), frequency modulation (FM), near field communication (NFC), infrared (IR), NearLink, and intrabody communication (IBC). For example, when two electronic devices communicate using an IBC solution, both devices have at least one electrode that contacts the skin, through which they send and receive information via the human body. The wireless communication module 160 can be one or more devices integrating at least one communication processing module.

[0337] Electronic device 100 implements display functions through a GPU, a display screen 194, and an application processor. The GPU is a microprocessor for image processing, connected to the display screen 194 and the application processor. The GPU is used to perform mathematical and geometric calculations and for graphics rendering. Processor 110 may include one or more GPUs, which execute program instructions to generate or modify display information.

[0338] Display screen 194 is used to display images, videos, etc. Display screen 194 includes a display panel. The display panel can be a liquid crystal display (LCD), or it can be manufactured using organic light-emitting diodes (OLEDs), active-matrix organic light-emitting diodes (AMOLEDs), flexible light-emitting diodes (FLEDs), minimized LEDs, microLEDs, micro-OLEDs, quantum dot light-emitting diodes (QLEDs), etc. In some embodiments, electronic device 100 may include one or N displays 194, where N is a positive integer greater than 1.

[0339] The display screen 194 can be used to display the blood pressure change value calculated by the electronic device 100 or the user's blood pressure value, as well as the user interface related to blood pressure, etc.

[0340] Internal memory 121 may include one or more random access memory (RAM) and one or more non-volatile memory (NVM). The RAM can be directly read and written by the processor 110 and can be used to store executable programs (e.g., machine instructions) of the operating system or other running programs, as well as user and application data. The NVM can also store executable programs and user and application data, and can be pre-loaded into the RAM for direct read and write operations by the processor 110.

[0341] The internal memory 121 can be used to store the pressure value applied during the blood pressure measurement process of the electronic device 100, the acquired PPG signal, and the user's blood pressure change value calculated based on the pressure value and PPG signal, etc.

[0342] Electronic device 100 can implement audio functions, such as music playback and recording, through audio module 170, speaker 170A, receiver 170B, microphone 170C, and application processor.

[0343] The audio module 170 is used to convert digital audio information into analog audio signals for output, and also to convert analog audio input into digital audio signals. The audio module 170 can also be used for encoding and decoding audio signals. In some embodiments, the audio module 170 may be located in the processor 110, or some functional modules of the audio module 170 may be located in the processor 110.

[0344] The speaker 170A, also known as a "loudspeaker," is used to convert audio electrical signals into sound signals. The electronic device 100 can listen to music or make hands-free calls through the speaker 170A.

[0345] The receiver 170B, also known as the "earpiece," is used to convert audio electrical signals into sound signals. When the electronic device 100 answers a telephone call or voice message, the receiver 170B can be brought close to the ear to listen to the voice.

[0346] Microphone 170C, also known as a "microphone" or "voice transducer," is used to convert sound signals into electrical signals. When making a phone call or sending a voice message, the user can speak by bringing their mouth close to microphone 170C, inputting the sound signal into microphone 170C. Electronic device 100 may have at least one microphone 170C. In some embodiments, electronic device 100 may have two microphones 170C, which, in addition to collecting sound signals, can also perform noise reduction. In other embodiments, electronic device 100 may also have three, four, or more microphones 170C, which can collect sound signals, reduce noise, identify the sound source, and perform directional recording, etc.

[0347] Touch sensor 180A, also known as a "touch device," can be disposed on display screen 194. The touch sensor 180A and display screen 194 together form a touchscreen, also known as a "touchscreen." Touch sensor 180A is used to detect touch operations applied to or near it. The touch sensor can transmit the detected touch operation to the application processor to determine the type of touch event. Visual output related to the touch operation can be provided through display screen 194. In other embodiments, touch sensor 180A may also be disposed on the surface of electronic device 100, in a different location than display screen 194.

[0348] The photoelectric sensor 180B is used to monitor cardiovascular vital signs. The photoelectric sensor 180B consists of at least one pair of light-emitting diodes (LEDs) and a photodetector. The LEDs act as a light source to illuminate the skin, and the photodetector detects the transmitted or reflected light after absorption by blood and tissue during penetration, converting it into an electrical signal to obtain a PPG signal. Since the intensity of the transmitted or reflected light varies with arterial pulsation, the PPG signal also follows the arterial pulsation, i.e., the rhythmic fluctuations of the user's heartbeat. This PPG signal can be used to calculate parameters such as the user's heart rate, blood oxygen saturation, and blood pressure.

[0349] Pressure sensor 180C is used to sense pressure signals and can convert the pressure signals into electrical signals. In some embodiments, pressure sensor 180C may be disposed on display screen 194. There are many types of pressure sensors 180C, such as resistive pressure sensors, inductive pressure sensors, and capacitive pressure sensors. A capacitive pressure sensor may include at least two parallel plates with conductive material. When a force is applied to pressure sensor 180C, the capacitance between the electrodes changes. Electronic device 100 determines the intensity of the pressure based on the change in capacitance.

[0350] In some embodiments, pressure sensor 180C can detect the pressure of the airbag during inflation or deflation of the airbag in electronic device 100. Additionally, photoelectric sensor 180B can acquire PPG signals during airbag inflation or deflation.

[0351] Buttons 190 include a power button, volume buttons, etc. Buttons 190 can be mechanical buttons or touch-sensitive buttons. Electronic device 100 can receive button input and generate key signal inputs related to user settings and function control of electronic device 100.

[0352] Motor 191 can generate vibration alerts. Motor 191 can be used for incoming call vibration alerts or for touch vibration feedback. For example, different vibration feedback effects can be corresponding to touch operations applied to different applications (such as taking photos, playing audio, etc.). Motor 191 can also correspond to different vibration feedback effects for touch operations applied to different areas of the display screen 194. Different application scenarios (such as time reminders, receiving messages, alarm clocks, games, etc.) can also correspond to different vibration feedback effects. The touch vibration feedback effect can also be customized.

[0353] Indicator 192 can be an indicator light, used to indicate charging status, power changes, or to indicate messages, missed calls, notifications, etc.

[0354] The pressurization module 193 can be used to apply pressure to the user's skin during blood pressure measurement, compressing the subcutaneous arterial blood flow, so that the electronic device 100 can acquire the PPG signal collected by the photoelectric sensor 180B during the process of the pressurization module 193 applying pressure to the user's skin. The PPG signal reflects the blood flow of the user's subcutaneous blood vessels under external pressure.

[0355] For example, the pressurization module 193 may include an airbag and a motor. The pressurization module 193 can inflate and deflate the airbag via the motor to apply pressure to the user's skin. In a specific example, if the electronic device 100 is a wearable device such as a watch or bracelet, the airbag may be located on the cuff of the electronic device 100.

[0356] Besides inflating the airbag, pressure on blood vessels can also be achieved by contracting the watchband. In this case, the pressure module 193 may include a retractable watchband and a motor, among other components. This application embodiment does not limit the components included in the pressure module 193 for applying pressure to the user.

[0357] The sensor module 180 of the electronic device 100 may further include one or more of the following sensors: accelerometer, barometric pressure sensor, temperature sensor, gyroscope sensor, etc. Among them:

[0358] An accelerometer can detect the magnitude of acceleration of an electronic device 100 in various directions (typically three axes). When the electronic device 100 is stationary, it can detect the magnitude and direction of gravity. It can also be used to identify the posture of the electronic device and is applied to applications such as screen orientation switching and pedometers.

[0359] A barometric pressure sensor can be used to measure air pressure, and in some embodiments, it can also be used to measure water pressure.

[0360] Temperature sensors can be used to measure a user's body temperature or the temperature of the user's environment.

[0361] A gyroscope sensor can be used to determine the motion attitude of an electronic device 100. In some embodiments, the angular velocity of the electronic device 100 about three axes (i.e., the x, y, and z axes) can be determined by the gyroscope sensor.

[0362] The structure illustrated in Figure 17 does not constitute a specific limitation on the electronic device 100. In other embodiments, the electronic device 100 may include more or fewer components than illustrated, or combine some components, or split some components, or have different component arrangements. The illustrated components may be implemented in hardware, software, or a combination of software and hardware.

[0363] Each step in the above method embodiments can be completed by integrated logic circuits in the processor or by instructions in software form. The method steps disclosed in the embodiments of this application can be directly manifested as being executed by a hardware processor, or being executed by a combination of hardware and software modules in the processor.

[0364] This application also provides an electronic device, which may include a memory and a processor. The memory may be used to store a computer program; the processor may be used to invoke the computer program in the memory, causing the electronic device to execute the method performed by the electronic device 100 in any of the above embodiments.

[0365] This application also provides a chip system including at least one processor for implementing the functions involved in the method performed by the electronic device 100 in any of the above embodiments.

[0366] In one possible design, the chip system also includes a memory for storing program instructions and data, which may be located within or outside the processor.

[0367] The chip system can consist of chips or include chips and other discrete components.

[0368] The chip system can contain one or more processors. These processors can be implemented in hardware or software. When implemented in hardware, the processor can be a logic circuit, an integrated circuit, etc. When implemented in software, the processor can be a general-purpose processor, implemented by reading software code stored in memory.

[0369] The chip system may contain one or more memories. These memories may be integrated with the processor or separated from it; this application does not limit this. For example, the memory may be a non-transient processor, such as a read-only memory (ROM), which may be integrated with the processor on the same chip or disposed on different chips. This application does not specifically limit the type of memory or the arrangement of the memory and processor.

[0370] For example, the chip system may be a field programmable gate array (FPGA), an application specific integrated circuit (ASIC), a system on chip (SoC), a central processor unit (CPU), a network processor (NP), a digital signal processor (DSP), a micro controller unit (MCU), a programmable logic device (PLD), or other integrated chips.

[0371] This application also provides a computer program product, the computer program product comprising: a computer program (also referred to as code or instructions), which, when the computer program is run, causes a computer to execute any of the methods executed by the electronic device 100 in any of the above embodiments.

[0372] This application also provides a computer-readable storage medium storing a computer program (also referred to as code or instructions). When the computer program is run, it causes the computer to perform any of the methods executed by the electronic device 100 in any of the above embodiments.

[0373] It should be understood that the processor in the embodiments of this application can be an integrated circuit chip with signal processing capabilities. In implementation, each step of the above method embodiments can be completed by the integrated logic circuits in the processor's hardware or by instructions in software form. The processor can be a general-purpose processor, a digital signal processor (DSP), an application-specific integrated circuit (ASIC), a field-programmable gate array (FPGA), or other programmable logic devices, discrete gate or transistor logic devices, or discrete hardware components. It can implement or execute the methods, steps, and logic block diagrams disclosed in the embodiments of this application. The general-purpose processor can be a microprocessor or any conventional processor. The steps of the methods disclosed in the embodiments of this application can be directly embodied in the execution of a hardware decoding processor, or executed by a combination of hardware and software modules in the decoding processor. The software modules can be located in random access memory, flash memory, read-only memory, programmable read-only memory, electrically erasable programmable memory, registers, or other mature storage media in the art. The storage medium is located in memory, and the processor reads the information in the memory and, in conjunction with its hardware, completes the steps of the above method.

[0374] Additionally, this application also provides an apparatus. Specifically, the apparatus may be a component or module, and may include one or more processors and a memory connected together. The memory stores a computer program. When the computer program is executed by one or more processors, the apparatus performs the methods described in the above-described method embodiments.

[0375] The apparatus, computer-readable storage medium, computer program product, or chip provided in the embodiments of this application are all used to execute the corresponding methods provided above. Therefore, the beneficial effects they can achieve can be referred to the beneficial effects of the corresponding methods provided above, and will not be repeated here.

[0376] The various embodiments of this application can be combined arbitrarily to achieve different technical effects.

[0377] In the above embodiments, implementation can be achieved, in whole or in part, through software, hardware, firmware, or any combination thereof. When implemented in software, it can be implemented, in whole or in part, as a computer program product. The computer program product includes one or more computer instructions. When the computer program instructions are loaded and executed on a computer, all or part of the processes or functions described in this application are generated. The computer can be a general-purpose computer, a special-purpose computer, a computer network, or other programmable device. The computer instructions can be stored in a computer-readable storage medium or transmitted from one computer-readable storage medium to another. For example, the computer instructions can be transmitted from one website, computer, server, or data center to another website, computer, server, or data center via wired (e.g., coaxial cable, fiber optic, digital subscriber line) or wireless (e.g., infrared, wireless, microwave, etc.) means. The computer-readable storage medium can be any available medium accessible to a computer or a data storage device such as a server or data center that integrates one or more available media. The available medium can be a magnetic medium (e.g., floppy disk, hard disk, magnetic tape), an optical medium (e.g., DVD), or a semiconductor medium (e.g., solid-state disk (SSD)).

[0378] Those skilled in the art will understand that all or part of the processes in the methods of the above embodiments can be implemented by a computer program instructing related hardware. This program can be stored in a computer-readable storage medium, and when executed, it can include the processes described in the above method embodiments. The aforementioned storage medium includes various media capable of storing program code, such as ROM or random access memory (RAM), magnetic disks, or optical disks.

[0379] In summary, the above description is merely an embodiment of the technical solution of the present invention and is not intended to limit the scope of protection of the present invention. Any modifications, equivalent substitutions, improvements, etc., made according to the disclosure of the present invention should be included within the scope of protection of the present invention.

Claims

1. A method of respiratory training, characterized by, The method includes: The wearable device initiates the first breathing exercise; The wearable device controls the inflation and deflation of the airbag on the wearable device according to the breathing rhythm of the first breathing training; the airbag is disposed on the wearing surface of the wearable device, and a pressure gauge is provided inside the airbag; The wearable device also uses the airbag inflated and deflated during the first breathing training to measure the user's first physiological parameter, which includes blood pressure.

2. The method of claim 1, wherein, Before the wearable device controls the airbag on the wearable device to inflate and deflate according to the breathing rhythm of the first breathing training, the method further includes: the wearable device detecting that the wearable device is in a wearing state.

3. The method of claim 2, wherein, The method further includes: after the wearable device starts the first breathing training, the wearable device also displays a breathing guidance animation according to the breathing rhythm of the first breathing training, the breathing guidance animation being used to prompt the breathing rhythm.

4. The method of any one of claims 1-3, wherein, Before the wearable device initiates the first breathing exercise, the method further includes: the wearable device displaying a first user interface, the first user interface displaying one or more breathing exercises, and detecting that the user selects the first breathing exercise from the one or more breathing exercises.

5. The method of any one of claims 1-4, wherein, Before the wearable device controls the airbag on the wearable device to inflate and deflate according to the breathing rhythm of the first breathing training, the method further includes: the wearable device acquiring the breathing rhythm of the first breathing training, the breathing rhythm including the following parameters: inhalation time, breath-holding time, and exhalation time for each round of breathing; The wearable device controls the inflation and deflation of the airbag on the wearable device according to the breathing rhythm of the first breathing training, including: the wearable device controls the airbag to inflate during the inhalation time, controls the pressure inside the airbag to remain constant during the breath-holding time, and controls the airbag to deflate during the exhalation time.

6. The method of any one of claims 1-5, wherein, Also includes: The wearable device determines whether the first breathing training meets the termination condition. If it does, the first breathing training ends. The termination conditions include one or more of the following: the number of training rounds reaches the number of training rounds of the first breathing training, the training duration reaches the training duration of the first breathing training, and the measured value of the first physiological parameter reaches the target value of the first physiological parameter in the first breathing training.

7. The method of claim 6, wherein, Also includes: During the first breathing training, the wearable device adjusts one or more of the following training parameters of the first breathing training according to the deviation between the first physiological parameter and the training target of the first breathing training: the number of training rounds, the training duration, the target value of the first physiological parameter, and the breathing rhythm of the first breathing training.

8. The method of any one of claims 1-7, wherein, After measuring the user's first physiological parameter, the method further includes: the wearable device presenting the training effect of the first breathing training based on the measured value of the first physiological parameter, wherein the training effect includes one or more of the following: the measured value of the first physiological parameter, the change in the measured value of the first physiological parameter, and the difference between the measured value of the first physiological parameter and the target value of the first physiological parameter.

9. The method of any one of claims 1-8, wherein, The wearable device also uses the inflated and deflated airbag during the first breathing training to measure the user's first physiological parameter. Specifically, during the rest interval in the first breathing training, the airbag is first inflated until the pressure inside the airbag is greater than a first pressure value, and then the airbag is deflated. The first physiological parameter is measured using the inflated and deflated airbag during the rest interval. The first pressure value is greater than a second pressure value, where the second pressure value is the maximum pressure value of the airbag when the airbag is inflated and deflated according to the breathing rhythm of the first breathing training.

10. The method of any one of claims 1-9, wherein, The wearable device is also equipped with a photovolume change mapping (PPG) sensor on its wearing surface. During the first breathing training, the wearable device detects the airbag pressure and the PPG signal based on the PPG sensor, and determines the first physiological parameter based on the measured airbag pressure and the PPG signal. The first physiological parameter includes: heart rate variability (HRV) change and blood pressure change.

11. An electronic device comprising a memory, a processor, and a computer program stored in the memory, characterized in that, The processor executes the computer program to implement the steps of the method according to any one of claims 1-10.

12. A computer readable storage medium having stored thereon computer programs / instructions, characterized in that, When the computer program / instructions are executed by the processor, they implement the steps of the method described in any one of claims 1-10.

13. A computer program product comprising computer programs / instructions, characterized in that, When the computer program / instructions are executed by the processor, they implement the steps of the method according to any one of claims 1-10.

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