CN117717334A

CN117717334A - Data acquisition method and electronic equipment

Info

Publication number: CN117717334A
Application number: CN202410173979.6A
Authority: CN
Inventors: 解智博; 谭银炯; 李辰龙; 贾兴旺
Original assignee: Honor Device Co Ltd
Current assignee: Honor Device Co Ltd
Priority date: 2024-02-07
Filing date: 2024-02-07
Publication date: 2024-03-19
Anticipated expiration: 2044-02-07
Also published as: CN117717334B

Abstract

The application provides a data acquisition method and electronic equipment, which relate to the technical field of electronic equipment, and the electronic equipment uses a PPG module to collect detection light signals in a noninvasive manner, so that calculation is performed based on characteristic parameters (the proportion between alternating current components and direct current components corresponding to the detection light signals) corresponding to the detection light signals, and the proportion of HbA1C of a user to total hemoglobin is determined. Compared with a mode of measuring HbA1C by means of a large-scale biochemical analyzer, the data acquisition method provided by the embodiment of the application does not need to collect blood for a user so as to bring wounds to the user, and can also acquire detection information for detecting HbA1C conveniently and rapidly, so that convenience is brought to the user for screening diabetes and/or for controlling diabetes for a long time based on a detection result of HbA 1C.

Description

Data acquisition method and electronic equipment

Technical Field

The embodiment of the application relates to the technical field of electronic equipment, in particular to a data acquisition method and electronic equipment.

Background

The level of glycosylated hemoglobin (HbA 1C) can accurately reflect the average blood glucose level of a human body, and the detection result of HbA1C is irrelevant to factors such as blood taking time, whether a user is empty or not, whether the user uses insulin or not, and the like, so HbA1C is an important index for screening diabetes and assisting in long-term control of diabetes.

Currently, hbA1C is detected mainly by intravenous blood sampling of a user and then analysis using a large-scale biochemical analyzer. On the one hand, since only larger hospitals are generally provided with biochemical analysis instruments, and the allocation situation of professional resources for detecting HbA1C by using the instruments is also not optimistic, the detection mode for detecting HbA1C by relying on large biochemical analysis instruments is very inconvenient, so that the requirements of detecting HbA1C of users in real time and carrying out daily monitoring on HbA1C of users are difficult to meet. On the other hand, the trauma necessary for venous blood collection of the user also causes additional pain to the user, brings the risk of infection of infectious diseases to the user and possibly causes physical nerve damage to the user.

Disclosure of Invention

The embodiment of the application provides a data acquisition method and electronic equipment, which are used for realizing noninvasive detection of HbA1C of a user so as to facilitate the user to carry out diabetes screening and/or long-term control of diabetes based on the detection result of HbA 1C.

In order to achieve the above purpose, the embodiments of the present application adopt the following technical solutions: the detection light signals are collected by the electronic equipment in a noninvasive mode through the PPG module, and accordingly calculation is conducted based on characteristic parameters corresponding to the detection light signals (the proportion between alternating current components and direct current components corresponding to the detection light signals) to determine the proportion of HbA1C of a user to total hemoglobin. Therefore, compared with a mode of measuring HbA1C by means of a large-scale biochemical analyzer, the data acquisition method provided by the embodiment of the application does not need to collect blood for a user so as to bring wounds to the user, and can be used for conveniently and rapidly acquiring detection information for detecting HbA1C, so that convenience is brought to the user for screening diabetes and/or for long-term control of diabetes based on a detection result of HbA 1C.

In a first aspect, the present application provides a data acquisition method applied to a first electronic device including a PPG module. And acquiring at least six detection light signals for a user through the PPG module by the first electronic equipment. Wherein each detection light signal comprises a light signal reflected from the user after the light is irradiated on the user, and the wavelengths of the light used for detecting different detection light signals are different from each other. The first electronic device obtains the characteristic parameters corresponding to each detected light signal (i.e., the ratio between the ac component and the dc component corresponding to each detected light signal), so as to calculate together based on the obtained six characteristic parameters, so as to obtain the ratio of HbA1C in the total hemoglobin among the multiple hemoglobin of the user.

In this application, utilize PPG module to gather the detection light signal to the user through first electronic equipment and carry out HbA 1C's detection, can realize atraumatic detection user's HbA1C, and can acquire user HbA1C in real time and account for total hemoglobin's proportion in order to be used for carrying out daily monitoring to user's HbA1C to detect HbA1C and carry out diabetes screening or carry out diabetes long-term control for the user and provide very big facility.

In addition, considering that a plurality of haemoglobin exists in blood of a user, the method and the device collect at least six detection light signals through the PPG module by using the first electronic equipment, so that the proportion between alternating current components and direct current components corresponding to each detection light signal is utilized to calculate the proportion occupied by HbA1C in the plurality of haemoglobin. Thus, the problem of inaccurate measurement results caused by mixing other hemoglobin with HbA1C to be actually detected, which is common in the related art, can be avoided. That is, the data acquisition method provided by the embodiment of the application can realize more accurate detection of the HbA1C level of the user, so that accuracy and effectiveness of HbA1C detection of the user are ensured.

In a possible implementation manner of the first aspect, after the first electronic device collects at least six detection optical signals for a user, photoelectric conversion is performed on the at least six detection optical signals to obtain corresponding electrical signals, and then the first electronic device amplifies and samples the electrical signals corresponding to each detection optical signal, so as to obtain PPG signals corresponding to the at least six detection optical signals. Then, the first electronic device calculates, for each PPG signal, a ratio between the AC component and the DC component according to the AC component and the DC component included in the PPG signal, so as to obtain characteristic parameters AC/DC corresponding to at least six detected light signals. Thus, the first electronic device can calculate based on the respective AC/DC signals corresponding to at least six detection signals, so as to obtain the proportion of HbA1C in the total hemoglobin in the multiple hemoglobin of the user.

In a possible implementation manner of the first aspect, after the first electronic device obtains at least six AC/DCs, the first electronic device first determines, using the at least six AC/DCs, a concentration ci of each of six haemoglobin of the user (ci is a concentration of the ith haemoglobin, i is any one of values 1 to 6). Then, the first electronic device divides the sum of the two HbA1C concentrations of the six kinds of hemoglobin by the sum of the total six kinds of hemoglobin to obtain a ratio between the sum of the two HbA1C concentrations and the sum of the six kinds of hemoglobin, wherein the ratio is a ratio of the two HbA1C concentrations of the user to the total hemoglobin.

In a possible implementation manner of the first aspect, the first electronic device records a process of acquiring the detection light signal once and calculating to obtain a proportion of HbA1C of the user to total hemoglobin by using AC/DC corresponding to the detection light signal as performing one HbA1C detection on the user. Therefore, the first electronic device can repeatedly acquire the detection light signals for a plurality of times through the PPG module to calculate for a plurality of times so as to obtain the proportion of HbA1C of the user to total hemoglobin. Further, the first electronic device also records the total number of times HbA1C is detected for the user. Then, under the condition that the total detection times are larger than or equal to a first preset times, the first electronic equipment further counts the first detection times that the calculated HbA1C of the user accounts for the total hemoglobin in the multi-time HbA1C detection of the user and is larger than or equal to a preset threshold value.

And under the condition that the first detection times are greater than or equal to the second preset times, the first electronic equipment pushes the first detection result to the user. But under the condition that the first detection times are larger than the third preset times, the first electronic equipment pushes the second detection result to the user.

The first preset times are larger than the second preset times, and the first preset times are also larger than the third preset times. In addition, the severity of the second detection result is greater than the severity of the first detection result.

In the application, the first electronic device detects HbA1C of a user for multiple times by using the PPG module, and based on the fact that HbA1C detected each time is the calculated ratio of HbA1C of the user to total hemoglobin, the HbA1C is compared with the size between preset thresholds, the number of times that the ratio of HbA1C to total hemoglobin is larger than or equal to the preset thresholds is counted, and finally a corresponding HbA1C detection result is pushed to the user according to the number of times. In this way, the accuracy and the validity of the result of detecting HbA1C of the user can be ensured by comprehensively determining the detection result output to the user by the ratio of HbA1C calculated in the plurality of times of detection to total hemoglobin.

In another possible implementation manner of the first aspect, the first electronic device may further perform synchronous statistics when recording a total number of times of HbA1C detection is performed on the user: the calculated ratio of HbA1C of the user to total hemoglobin is smaller than the second detection times of the minimum value of the preset threshold interval, the ratio of HbA1C of the user to total hemoglobin is in the third detection times of the preset threshold interval, and the ratio of HbA1C of the user to total hemoglobin is larger than the fourth detection times of the maximum value of the preset threshold interval.

Wherein the sum of the second detection times, the third detection times and the fourth detection times is equal to the total detection times.

And then, under the condition that the second detection times are larger than the third detection times and the second detection times are also larger than the fourth detection times, the first electronic equipment pushes the third detection result to the user. And when the third detection times are larger than the second detection times and the third detection times are also larger than the fourth detection times, the first electronic equipment pushes the fourth detection result to the user. And under the condition that the fourth detection times are larger than the second detection times and the fourth detection times are also larger than the third detection times, the first electronic equipment pushes a fifth detection result to the user.

Wherein the fourth test result corresponds to a greater severity than the third test result. The fifth test result corresponds to a greater severity than the fourth test result.

In a possible implementation manner of the first aspect, when the first electronic device collects at least six detection light signals to the user through the PPG module, the first electronic device may start to collect the at least six detection light signals to the user through the PPG module under the condition that the monitoring finds that the user does not have body movement according to the preset indication information.

In a possible implementation manner of the first aspect, the data acquisition method provided in the present application may also be implemented in a scenario in which the first electronic device performs data interaction with the second electronic device. After the first electronic device acquires at least six detection light signals for a user through the PPG module, the first electronic device sends PPG signals corresponding to the at least six detection light signals to the second electronic device. As such, the second electronic device, after receiving the at least six PPG signals, calculates a proportion of HbA1C of the user to total hemoglobin based on the AC/DC of each of the at least six PPG signals together. And after the second electronic device calculates the ratio of HbA1C of the user to total hemoglobin, the second electronic device sends the ratio of HbA1C of the user to total hemoglobin to the first electronic device, and the first electronic device can display the ratio of HbA1C of the user to total hemoglobin.

In the application, data interaction is performed through the first electronic device and the second electronic device, so that after the first electronic device collects a detection light signal by using the PPG module, a PPG signal corresponding to the detection light signal is sent to the second electronic device, and the proportion of HbA1C of a user to total hemoglobin is calculated by the second electronic device based on the proportion between an AC component and a DC component in the PPG signal. Therefore, the purpose of noninvasively detecting the HbA1C of the user and timely obtaining the detection result based on the data interaction between the first electronic device and the second electronic device can be achieved under the condition that the first electronic device does not have the data calculation capability or the data calculation capability of the first electronic device is insufficient.

In another possible implementation manner of the first aspect, in a scenario in which the first electronic device performs data interaction with the second electronic device, the data acquisition method provided in the present application may also be executed by the second electronic device. When the second electronic device executes the data acquisition method, at least six PPG signals from the first electronic device are received first, and then the second electronic device calculates the ratio of HbA1C of the user to total hemoglobin based on the ratio between the AC component and the DC component in the PPG signals. And, the second electronic device may also select to send the ratio of HbA1C to total hemoglobin to the first electronic device and/or display the ratio of HbA1C to total hemoglobin.

The first electronic device still collects at least six detection light signals for a user through the PPG module at the local end, and obtains PPG signals corresponding to the at least six detection light signals respectively so as to send the at least six PPG signals to the second electronic device.

In a second aspect, the present application provides an electronic device, comprising: the processor is electrically connected with the PPG module. The PPG module is used for collecting at least six detection light signals. The PPG module comprises a light emitter and a light receiver. The light receiver is used for collecting detection light signals reflected from the user after the light rays with each wavelength are irradiated on the user. In addition, the processor is used for acquiring the characteristic parameters corresponding to each detection light signal, and calculating based on at least six characteristic parameters so as to obtain the proportion of glycosylated hemoglobin HbA1C of the user to total hemoglobin.

The characteristic parameters corresponding to each detected light signal obtained by the processor are as follows: the ratio between the alternating current component and the direct current component corresponding to the optical signal is detected.

In this application, utilize PPG module to gather the detection light signal to the user through electronic equipment with noninvasive mode to detect HbA1C based on the characteristic function that the detection light signal corresponds, can realize noninvasive detection user's HbA1C, and can acquire user HbA1C in real time and account for total hemoglobin's proportion in order to be used for carrying out daily monitoring to user's HbA1C, thereby detect HbA1C and carry out diabetes screening or carry out diabetes long-term control for the user and provide very big facility.

In a possible implementation manner of the second aspect, the PPG module includes a plurality of light emitters. The plurality of light emitters are used for respectively emitting light signals to the user, the light emitting periods of the different light emitters are different from each other, and the wavelengths of the light rays emitted by the different light emitters to the user are also different from each other. The light receiver is configured to receive the detection light signal reflected from the user during the light emission period of each light emitter.

In another possible implementation manner of the second aspect, the PPG module includes a plurality of optical receivers. In this case, the optical transmitter is still used to transmit at least six wavelengths of optical signals to the user, and the plurality of optical receivers are used to receive the detected optical signals reflected back from the user, respectively.

Wherein the wavelengths of the detected optical signals received by the different optical receivers are different from each other.

In this application, consider that there are multiple hemoglobin in user's blood to, this application utilizes PPG module to gather six at least detection light signals to the user through electronic equipment, thereby utilizes the proportion between the alternating current component that every detection light signal corresponds and the direct current component, calculates the proportion that HbA1C accounts for among the multiple hemoglobin altogether. Thus, the problem of inaccurate detection results of HbA1C can be avoided. That is, the electronic device provided by the application can realize more accurate detection of the HbA1C level of the user, thereby ensuring the accuracy and the effectiveness of HbA1C detection of the user.

In a possible implementation manner of the second aspect, a wavelength of light emitted by the PPG module to the user through the light emitter is greater than or equal to 500nm and less than or equal to 1100nm, and/or a wavelength of light emitted by the light emitter to the user is greater than or equal to 1600nm and less than or equal to 1850nm.

In this application, consider the light penetration ability and the absorption of water in the human body to light can both influence the validity of the detection light signal that gathers when stronger to this application, thereby this application is through the light emitter to the user light that the wavelength is greater than or equal to 500nm and less than or equal to 1100nm, and/or through the light emitter to the user light that the wavelength is greater than or equal to 1600nm and less than or equal to 1850nm, can avoid like this because the light penetration ability is not enough can't gather the condition of detection light signal, and avoid the absorption of water to light stronger and lead to detecting the condition that the light signal is weaker and thereby be difficult to accurate detection user HbA 1C.

In a possible implementation manner of the second aspect, the electronic device further includes: the connecting component is connected with the main body and is used for binding the main body on the skin of a user. In addition, the processor is located in the main body, and the PPG module is arranged on the main body, or the PPG module is arranged on the connecting component.

In this application, considering the different design needs of in-service use, the electronic equipment that this application provided can set up the PPG module in the main part, also can set up the PPG module on adapting unit. Therefore, the method and the device can meet the use requirements of different users for noninvasive HbA1C detection based on the electronic equipment, and therefore flexibility of noninvasive HbA1C detection of the users by using the electronic equipment is improved.

In a third aspect, the present application provides an electronic device, which is a first electronic device or a second electronic device; the electronic device has the functionality to implement the method described in the first aspect above. The functions can be realized by hardware, and can also be realized by executing corresponding software by hardware. The hardware or software includes one or more modules corresponding to the functions described above.

In a fourth aspect, the present application provides an electronic device, including: a processor and a memory; the memory is for storing computer program code comprising computer executable instructions which, when the electronic device is running, are executed by the processor to cause the electronic device to perform the method as described in the first aspect above.

In a fifth aspect, the present application provides an electronic device, including: a processor; the processor is configured to couple to the memory and to execute the method according to the first aspect described above according to the instructions in the memory after reading the instructions.

In a sixth aspect, the present application provides a computer readable storage medium having stored therein computer instructions which, when run on an electronic device, enable the electronic device to perform the method of the first aspect described above.

In a seventh aspect, the present application provides a computer program product comprising instructions which, when run on a computer, cause the computer to perform the method of the first aspect described above.

In an eighth aspect, there is provided an apparatus comprising a processor for supporting an electronic device to implement the functions referred to in the first aspect. In one possible design, the apparatus further includes a memory for storing program instructions and data necessary for the electronic device.

The technical effects caused by any one of the design manners of the third aspect to the eighth aspect may refer to the technical effects caused by different implementation manners of the first aspect, which are not repeated herein.

Drawings

Fig. 1 is a schematic view of a scenario in which light is emitted to a human blood vessel according to an embodiment of the present application;

FIG. 2 is a graph showing the change in absorption intensity of each of oxyhemoglobin and reduced hemoglobin for different wavelengths of light according to an embodiment of the present application;

fig. 3 is a schematic hardware structure of an electronic device according to an embodiment of the present application;

fig. 4 is a schematic structural diagram of a PPG module in an electronic device according to an embodiment of the present application;

fig. 5 is a schematic diagram of a position layout of an LED and a PD in a PPG module according to an embodiment of the present application;

fig. 6 is a schematic diagram of a position layout of an LED and a PD in another PPG module according to an embodiment of the present application;

FIG. 7 is a schematic view of a scene in which different skin tissues reflect light according to an embodiment of the present application;

FIG. 8 is a graph showing the change of the absorption intensity of water for light with different wavelengths according to an embodiment of the present application;

fig. 9 is a schematic diagram of a mobile phone integrated with a PPG module according to an embodiment of the present application;

fig. 10 is a schematic diagram of a smart earphone integrated with a PPG module according to an embodiment of the present application;

FIG. 11 is a schematic diagram of a finger-clamping HbA1C detecting instrument according to an embodiment of the present application;

fig. 12 is a schematic diagram of an intelligent bracelet integrated with a PPG module according to an embodiment of the present application;

Fig. 13 is a schematic diagram of another smart band integrated with PPG module according to an embodiment of the present application;

fig. 14 is a schematic diagram of another smart band integrated with a PPG module according to an embodiment of the present application;

FIG. 15 is a flowchart illustrating an implementation step of the data acquisition method according to the embodiment of the present application;

FIG. 16 is a graph showing the variation of the absorption amount of hemoglobin and plasma for light of different wavelengths according to the embodiment of the present application;

fig. 17 is a schematic diagram of a position layout of an LED and a PD in a PPG module according to another embodiment of the present application;

FIG. 18 is a schematic diagram of a scenario in which a user triggers an instruction to detect HbA1C based on a first electronic device according to an embodiment of the present application;

FIG. 19 is a schematic diagram of a scenario in which a user detects an instruction to HbA1C based on a handset trigger according to an embodiment of the present application;

fig. 20 is a schematic view of a scenario in which a first electronic device and a second electronic device according to an embodiment of the present application are communicatively connected;

FIG. 21 is a flowchart illustrating another implementation step of the data acquisition method according to the embodiment of the present application;

fig. 22 is a schematic diagram of another execution flow of the data acquisition method according to the embodiment of the present application.

Detailed Description

The technical solutions in the embodiments of the present application are described below with reference to the drawings in the embodiments of the present application. In the description of the embodiments of the present application, the terminology used in the embodiments below is for the purpose of describing particular embodiments only and is not intended to be limiting of the application. As used in the specification of this application and the appended claims, the singular forms "a," "an," "the," and "the" are intended to include, for example, "one or more" such forms of expression, unless the context clearly indicates to the contrary. It should also be understood that in the various embodiments herein below, "at least one", "one or more" means one or more than two (including two). The term "and/or" is used to describe an association relationship of associated objects, meaning that there may be three relationships; for example, a and/or B may represent: a alone, a and B together, and B alone, wherein A, B may be singular or plural. The character "/" generally indicates that the context-dependent object is an "or" relationship.

Reference in the specification to "one embodiment" or "some embodiments" or the like means that a particular feature, structure, or characteristic described in connection with the embodiment is included in one or more embodiments of the application. Thus, appearances of the phrases "in one embodiment," "in some embodiments," "in other embodiments," and the like in the specification are not necessarily all referring to the same embodiment, but mean "one or more but not all embodiments" unless expressly specified otherwise. The terms "comprising," "including," "having," and variations thereof mean "including but not limited to," unless expressly specified otherwise. The term "coupled" includes both direct and indirect connections, unless stated otherwise. The terms "first," "second," and the like are used for descriptive purposes only and are not to be construed as indicating or implying relative importance or implicitly indicating the number of technical features indicated.

In the embodiments of the present application, words such as "exemplary" or "such as" are used to mean serving as examples, illustrations, or descriptions. Any embodiment or design described herein as "exemplary" or "for example" should not be construed as preferred or advantageous over other embodiments or designs. Rather, the use of words such as "exemplary" or "such as" is intended to present related concepts in a concrete fashion.

Prior to the description of the embodiments of the present application, related technical terms related to the embodiments of the present application will be briefly described herein.

1. Diabetes mellitus.

Diabetes mellitus is a common metabolic endocrine disease characterized mainly by hyperglycemia.

Today, the clinical use of a measurement of a user's blood glucose is still being used to screen whether the user is diabetic. However, since the blood glucose measurement result is merely representative of the blood glucose level of the user at one time, the blood glucose measurement result can only prompt the physical condition of the user when the blood glucose test sample is collected, but cannot be used as an index for evaluating the control degree of diabetes of the user.

2. Glycosylated hemoglobin (HbA 1C).

HbA1C is a portion of hemoglobin that is bound to glucose in blood. When the concentration of glucose in blood is high, hbA1C content formed in the human body is also high. Since the HbA1C content of the blood remains relatively unchanged before the red blood cells die, the life of the red blood cells in the human body is generally longer. Thus HbA1C levels can reflect average blood glucose levels in humans over a longer period of time. Further, hbA1C levels are independent of factors such as blood withdrawal time, patient fasting, and insulin use. This determines that HbA1C levels are a good indicator for screening diabetes and aiding in long-term control of diabetes. In view of this, in recent years, detection of HbA1C has been receiving a great deal of clinical attention.

3. Photoplethysmography (photo plethysmo graphy, PPG).

When light passes through skin tissue and then is reflected to the detection structure, illumination is attenuated to a certain extent, and on the premise that the measurement part does not move greatly, the absorption of the light by muscles, bones, veins, other connecting tissues and the like of the measurement part is basically unchanged. However, arterial blood is different from muscles, bones, veins, other connective tissues, etc., and the absorption of light by arterial blood is naturally changed due to the flow of blood in the artery. It is because the absorption of light by arteries varies while the absorption of light by other tissues is substantially unchanged, so that when the detected light signal reflected to the light receiver is converted into an electrical signal, the resulting electrical signal is divided into a Direct Current (DC) component and an alternating current (alternating current, AC) component. The AC component is extracted for analysis and detection, so that the characteristic of arterial blood flow can be reflected. This technique of detecting the flow characteristics of blood based on converting the reflected detection light signal into an electrical signal and extracting the AC component in the electrical signal is called PPG. The electrical signal obtained by converting the detection light signal reflected to the light receiver is called PPG signal, and the PPG signal is obtained by performing photoelectric conversion on the detection light signal, amplifying the converted electrical signal, and then resampling.

4. PPG module.

The PPG module mainly comprises a light emitter and a light receiver (also called a light detector or a light detection structure and the like) and is used for acquiring a PPG signal containing an AC component for a user to use by electronic equipment integrating the PPG module for the photoplethysmography to extract the AC component from the PPG signal for analysis and detection, so as to determine the blood flow characteristics of the user.

At present, an electronic device integrated with a PPG module generally comprises a wearable device, a smart phone, a tablet computer, a notebook computer, a medical device, an intelligent household appliance and the like, so as to be used for detecting information such as pulse rhythm and amplitude of an artery of a user and obtaining physiological characteristics of the user such as heart rate and respiratory frequency. The wearable device can be specifically a wearable device capable of supporting human health monitoring such as an intelligent watch, an intelligent bracelet, a wireless earphone, intelligent glasses and the like or an intelligent eye shield and the like.

In the related art, when the electronic device detects the physiological characteristics of the human body through the PPG module, an Analog Front End (AFE) of the electronic device drives a light emitting diode (light emitting diode, LED) to emit light, and after the light is transmitted to the skin, a part of the light is absorbed by human tissues (including blood) in the skin, and another part of the light is scattered and reflected. Wherein the scattered and reflected light forms a detection light signal after exiting the skin, which is received by a photo-diode (PD) on the wearable device and converted into an electrical signal. After the AFE receives the electrical signal converted and output by the PD, the received electrical signal may be amplified and sampled to obtain the PPG signal.

5. The ratio between the alternating current component and the direct current component (AC/DC) in the PPG signal.

The PPG signal collected by the PPG module comprises a direct current component (DC) and an alternating current component (AC). Wherein the DC component represents the absorption of light by the skin, muscle, vein, bone, etc. tissues, which is substantially constant throughout the blood circulation. The AC component represents the absorption of light by the artery. Since the absorption of light by the artery varies with the pulse period, the intensity of light received by the PD also varies with the pulse period in a pulsating manner. Based on this principle, the ratio (AC/DC) between the alternating current component and the direct current component in the PPG signal can be calculated by the langbo-beer law.

For example, as shown in fig. 1, when the PPG module emits light with an incident light intensity I0 to the detection portion through the LED, the transmitted light intensity I received by the PD during vasoconstriction can be calculated by the following formula 1.

Equation 1.

Where ki is the light absorption coefficient of the substance i at the detection site, ci is the concentration of the substance i, L is the optical path length, and DC is the direct current component.

Further, since the optical path L increases by Δl at the time of the vascular pulsation, the transmitted light intensity I received by the PD can be calculated by the following formula 2.

Equation 2.

Equation 3 can be obtained by dividing equation 1 by equation 2 and taking the logarithm.

Equation 3.

In addition, since the optical path Δi increased when the blood vessel beats is much smaller than the transmitted light intensity I emitted by the light emitter, the conversion of equation 3 results in equation 4.

Equation 4.

Thus, the result calculated based on equation 4The ratio AC/DC between the AC component and the DC component in the PPG signal acquired by the PPG module through emitting light to the detection part by the LED can be expressed.

Because the AFE can drive the LED to emit different light rays (specifically, light rays with different wavelengths), the principle that the absorbance of a specific substance to different light rays is different can be utilized, and based on collecting the PPG signals of the detection light signals with multiple wavelengths, the relative proportion of multiple different substances can be further calculated, so that the measurement of certain physiological indexes of the user can be realized. For example, as shown in fig. 2, since the absorption intensities of two substances, that is, oxygenated hemoglobin and reduced hemoglobin, are different for different wavelengths of light, when measuring blood oxygen of a user, a PPG module may generally collect PPG signals of two detection light signals with different wavelengths (specifically, may be detection light signals with a wavelength of 660nm and a wavelength of 940 nm), so as to obtain AC/DC signals corresponding to the two PPG signals, and calculate the ratio of the oxygenated hemoglobin to the reduced hemoglobin by using the two sets of AC/DC signals, thereby calculating the saturation of the blood oxygen.

The implementation of the examples of the present application will be described in detail below with reference to the accompanying drawings.

First, referring to fig. 3, fig. 3 is a schematic structural diagram of an electronic device 100 according to an embodiment of the present application. As shown in fig. 3, the electronic device 100 may include a processor 110, an external memory interface 120, an internal memory 121, a universal serial bus (universal serial bus, USB) interface 130, a charge management module 111, a power management module 112, a battery 113, an antenna 1, an antenna 2, a mobile communication module 140, a wireless communication module 150, an audio module 170, a speaker 170A, a receiver 170B, a microphone 170C, an earphone interface 170D, a sensor module 180, keys 190, a motor 191, an indicator 192, a camera 193, a display 194, a user identification module (subscriber identification module, SIM) card interface 195, and the like.

It should be understood that the illustrated structure of the embodiment of the present invention does not constitute a specific limitation on the electronic device 100. In other embodiments of the present application, electronic device 100 may include more or fewer components than shown, or certain components may be combined, or certain components may be split, or different arrangements of components. The illustrated components may be implemented in hardware, software, or a combination of software and hardware.

The processor 110 may include one or more processing units, such as: the processor 110 may include an application processor (application processor, AP), a modem processor, a graphics processor (graphics processing unit, GPU), an image signal processor (image signal processor, ISP), a controller, a memory, a video codec, a digital signal processor (digital signal processor, DSP), a baseband processor, and/or a neural network processor (neural-network processing unit, NPU), etc. Wherein the different processing units may be separate devices or may be integrated in one or more processors. The controller may be a neural hub and a command center of the electronic device 100, among others. The controller can generate operation control signals according to the instruction operation codes and the time sequence signals to finish the control of instruction fetching and instruction execution.

A memory may also be provided in the processor 110 for storing instructions and data. In some embodiments, the memory in the processor 110 is a cache memory. The memory may hold instructions or data that the processor 110 has just used or recycled. If the processor 110 needs to reuse the instruction or data, it can be called directly from the memory. Repeated accesses are avoided and the latency of the processor 110 is reduced, thereby improving the efficiency of the system.

In some embodiments, the processor 110 may include one or more interfaces. The interfaces may include an integrated circuit (inter-integrated circuit, I2C) interface, an integrated circuit built-in audio (inter-integrated circuit sound, I2S) interface, a pulse code modulation (pulse code modulation, PCM) interface, a universal asynchronous receiver transmitter (universal asynchronous receiver/transmitter, UART) interface, a mobile industry processor interface (mobile industry processor interface, MIPI), a general-purpose input/output (GPIO) interface, a subscriber identity module (subscriber identity module, SIM) interface, and/or a universal serial bus (universal serial bus, USB) interface, among others.

It should be understood that the interfacing relationship between the modules illustrated in the embodiments of the present invention is only illustrative, and is not meant to limit the structure of the electronic device 100. In other embodiments of the present application, the electronic device 100 may also use different interfacing manners, or a combination of multiple interfacing manners in the foregoing embodiments.

The charge management module 111 is configured to receive a charge input from a charger. The charging management module 111 may also supply power to the electronic device through the power management module 112 while charging the battery 113. The wireless communication function of the electronic device 100 may be implemented by the antenna 1, the antenna 2, the mobile communication module 140, the wireless communication module 150, a modem processor, a baseband processor, and the like.

The antennas 1 and 2 are used for transmitting and receiving electromagnetic wave signals. Each antenna in the electronic device 100 may be used to cover a single or multiple communication bands. Different antennas may also be multiplexed to improve the utilization of the antennas. For example: the antenna 1 may be multiplexed into a diversity antenna of a wireless local area network. In other embodiments, the antenna may be used in conjunction with a tuning switch.

The mobile communication module 140 may provide a solution for wireless communication including 2G/3G/4G/5G/6G, etc. applied on the electronic device 100. The modem processor may include a modulator and a demodulator. The wireless communication module 150 may provide solutions for wireless communication including wireless local area network (wireless local area networks, WLAN) (e.g., wireless fidelity (wireless fidelity, wi-Fi) network), bluetooth (BT), global navigation satellite system (global navigation satellite system, GNSS), frequency modulation (frequency modulation, FM), near field wireless communication technology (near field communication, NFC), infrared technology (IR), etc., as applied to the electronic device 100.

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

A display screen (or screen) 194 is used to display images, video, etc. The display 194 includes a display panel. The display panel may include, but is not limited to, a liquid crystal display (liquid crystal display, LCD), an organic light-emitting diode (OLED), an active-matrix organic light emitting diode or active-matrix organic light-emitting diode (AMOLED), a flexible light-emitting diode (flex-emitting diode, FLED), a mini light-emitting diode (mini organic light-emitting diode, MINILED), a micro organic light-emitting diode (micro organic light-emitting diode, micro led), a quantum dot light-emitting diode (quantum dot light emitting diodes, QLED), and the like. In some embodiments, the electronic device 100 may include 1 or N display screens 194, N being a positive integer greater than 1.

The electronic device 100 may implement photographing functions through an ISP, a camera 193, a video codec, a GPU, a display screen 194, an application processor, and the like.

The external memory interface 120 may be used to connect an external memory card, such as a Micro SD card, to enable expansion of the memory capabilities of the electronic device 200.

The internal memory 121 may be used to store computer executable program code including instructions.

The processor 110 executes various functional applications of the electronic device 100 and data processing by executing instructions stored in the internal memory 121. The internal memory 121 may include a storage program area and a storage data area. The storage program area may store an application program (such as a sound playing function, an image playing function, etc.) required for at least one function of the operating system, etc. The storage data area may store data created during use of the electronic device 100 (e.g., audio data, phonebook, etc.), and so on. In addition, the internal memory 121 may include a high-speed random access memory, and may further include a nonvolatile memory such as at least one magnetic disk storage device, a flash memory device, a universal flash memory (universal flash storage, UFS), and the like.

The electronic device 100 may implement audio functions through an audio module 170, a speaker 170A, a receiver 170B, a microphone 170C, an earphone interface 170D, an application processor, and the like. Such as music playing, recording, etc.

The keys 190 include a power-on key, a volume key, etc. The indicator 192 may be an indicator light.

The sensor module 180 may include a fold angle detection sensor, a pressure sensor, a gyroscope sensor, a barometric sensor,

Magnetic sensor, acceleration sensor, distance sensor, proximity light sensor, fingerprint sensor, temperature sensor, touch sensor, ambient light sensor, bone conduction sensor, PPG module etc..

In one possible embodiment, in order to overcome the defect or problem of HbA1C detection that is currently dependent on a large-scale biochemical analyzer, the electronic device 100 provided in the embodiments of the present application collects at least six detection light signals through the PPG module. Then, the processor 110 obtains the characteristic parameters corresponding to each detected light signal (the ratio AC/DC between the AC component and the DC component in the PPG signal corresponding to the detected light signal), and calculates the characteristic parameters based on at least six characteristic parameters together, so as to obtain the ratio of HbA1C of the user to total hemoglobin.

As shown in fig. 4, the PPG module may include an optical emitter and an optical receiver. The light transmitter is used for transmitting at least six light rays, and the light receiver is used for collecting detection light signals reflected from a user after each light ray irradiates the user; the wavelengths of the different kinds of light emitted by the light emitters are different from each other.

When the electronic device 100 collects at least six detection light signals by using the PPG module, the PPG module emits light with at least 6 wavelengths to an HbA1C detection portion (such as a wrist, a finger, etc.) of the user through the light emitter. Meanwhile, the PPG module receives the light signals reflected after the light emitted by the light emitter is absorbed by the HbA1C detection part of the user through the light receiver, so that the light signals reflected by the dermis layer in the received light signals with each wavelength are used as detection light signals corresponding to the light with each wavelength.

After the PPG module collects at least six wavelength detection light signals, photoelectric conversion is performed on each wavelength detection light signal to obtain a corresponding electric signal, and the PPG module continues to amplify the electric signal corresponding to each wavelength detection light signal as a signal and samples the amplified electric signal, so as to obtain PPG signals corresponding to the at least six wavelength detection light signals. At least six PPG signals may be transmitted to the processor 110 through an electrical connection between the PPG module and the processor 110. Thus, the processor 110 obtains respective characteristic parameters (the ratio between the AC component and the DC component in each PPG signal, i.e. the AC/DC value) of at least six PPG signals, and calculates the ratio of HbA1C to total hemoglobin among the multiple hemoglobin of the user.

In a possible embodiment, the PPG module comprises a plurality of light emitters. At this time, the plurality of light emitters emit light signals to the user, respectively, and the light emission periods of the different light emitters are different from each other. Further, the light receiver receives the detection light signal reflected back from the user in the light emission period of each light emitter.

Illustratively, as shown in fig. 5, assuming that the PPG module is mainly composed of 6 Light Emitters (LEDs) of different wavelengths plus one light receiver (PD) of wide reception spectrum, the positional layout of the LEDs and PD may be: the 6 LEDs surround 1 PD. When the PPG module collects at least 6 detection light signals, the PPG module emits light in a time-sharing manner through the LEDs with 6 different wavelengths, so that the HbA1C detection part of a user is emitted with 6 different wavelengths in a time-sharing manner (the wavelength combination of the 6 different wavelengths can be 535nm, 560nm, 577nm, 593nm, 622nm and 636 nm).

When the PPG module emits light with the 1 st wavelength of 535nm at the first time based on the first LED, the PPG module receives light signals reflected by the cuticle, the epidermis layer, the dermis layer and the subcutaneous tissue of the detection part of HbA1C sequentially through the light with the 1 st wavelength of 535nm at the first time based on the PD, and the PPG module only determines the light signals reflected by the dermis layer as detection light signals with the 1 st wavelength of 535nm acquired at the first time. Then, when the PPG module emits light with the wavelength of 560nm at the second time based on the second LED, the PPG module receives light signals reflected by the stratum corneum, the epidermis, the dermis and the subcutaneous tissue of the HbA1C detection part sequentially at the second time based on PD, wherein the PPG module only determines the light signals reflected by the dermis as detection light signals with the wavelength of 560nm at the second time, wherein the detection light signals are collected at the first time. The process of collecting the detection light signals of the other various wavelengths by the PPG module is similar, and will not be described here again.

In a possible embodiment, the PPG module includes a plurality of light receivers, where the light emitter is still configured to emit light signals of at least six wavelengths to the user, and the plurality of light receivers are configured to respectively receive the detected light signals reflected back from the user. Wherein the wavelengths of the detected optical signals received by the different optical receivers are different from each other.

The number and location distribution of LEDs and PDs on the PPG module may also be as shown in fig. 6: at least 6 PDs surround 1 LED. That is, the number of PDs included in the PG module is plural at this time, and the number of LEDs included in the PPG module is only 1. Therefore, when the PPG module collects at least six detection light signals, the LED with a wide spectrum wavelength can still emit light rays with one wavelength in different time periods, so that among the PD with 6 narrow receiving spectrums, only the PD sensitive to the light rays with the wavelengths emitted by the LED in different time periods receives the light signals reflected by the stratum corneum, the epidermis, the dermis and the subcutaneous tissues in sequence, and the received light signals reflected by the dermis are used as detection light signals with one wavelength. Therefore, the PPG module can sequentially collect detection light signals corresponding to at least 6 wavelengths of light emitted by the LEDs in a time-sharing manner.

In another possible embodiment, when the PPG module adopts a combination mode of 1 LED with a broad spectrum wavelength and at least 6 PDs with narrow receiving spectrums, the PPG module collects at least 6 detection light signals, and can also emit 6 wavelengths of light at the same time by the LED with a broad spectrum wavelength. Since each PD of the 6 narrow receiving spectrums is sensitive to the optical signal of one wavelength only, the PD of the 6 narrow receiving spectrums can respectively receive the optical signal reflected by the stratum corneum, the epidermis, the dermis and the subcutaneous tissue of the sensitive one of the 6 wavelengths at the same time. And each of the 6 PDs uses the received light reflected by the dermis layer as a detection light signal received by itself. Thus, the first electronic device can collect 6 detection light signals at the same time.

In a possible embodiment, the wavelength of the light emitted by the PPG module to the HbA1C detection portion of the user by the light emitter for collecting the detection light signal is greater than or equal to 500nm and less than or equal to 1100nm, and/or the wavelength is greater than or equal to 1600nm and less than or equal to 1850nm.

In the embodiment of the present application, when the proportion of HbA1C of the user is measured and calculated, the ratio AC/DC between the AC component and the DC component in the PPG signal corresponding to each detected light signal acquired by the PPG module is needed to calculate and determine the proportion of one or more of 6 kinds of hemoglobin to the 6 kinds of total hemoglobin. However, since the PPG signal corresponding to the detected light signal is the PPG signal corresponding to the light signal reflected by the user's arterial blood after absorbing the light signal, as shown in fig. 7, at least the PPG module is required to transmit the light signal capable of penetrating the dermis layer (the skin is mainly divided into the stratum corneum, the epidermis layer, the dermis layer, the subcutaneous tissue, and the artery is mainly present in the dermis layer) to the HbA1C detection site (such as the wrist, the finger, etc.) of the user, so the dermis layer is the target area to be detected. Moreover, since the light with different wavelengths has different penetration capacities to the skin, and the light with a longer wavelength has a stronger penetration capacity to the skin in general, it is determined from the light penetration capacities shown by the research that the PPG module is required to emit at least the light signal with the wavelength of 500 nanometers (nm) or more in order to detect the information of the substances in the artery of the dermis layer (i.e., the above-mentioned various haemoglobins).

In some examples, the absorption of light is strong because of the high content of water in the human body. And, as shown in fig. 8, water has a strong absorption capacity for light having a wavelength of 1100nm or more and 1600nm or less and light having a wavelength of 1850nm or more and 2050nm or less. Therefore, in consideration of the influence of water on light absorption, the PPG module cannot emit light having a wavelength region of 1100nm or more and 1600nm or less to the user through the light emitter, nor cannot generate light having a wavelength region of 1850nm or more and 2050nm or less to the user through the light emitter.

In view of the above, the electronic device needs to select light in a wavelength range of greater than or equal to 500nm and less than or equal to 1100nm for detecting HbA1C of the user, and of course, the electronic device may also select light with different wavelengths in a wavelength range of greater than or equal to 1600nm and less than or equal to 1850nm through the PPG module for detecting HbA1C of the user. That is, when the electronic device collects at least 6 detection light signals for the user through the PPG module, it preferably emits light with a wavelength range of greater than or equal to 500nm and less than or equal to 1100nm and/or greater than or equal to 1600nm and less than or equal to 1850nm to the HbA1C detection portion such as the wrist or finger of the user through the light emitter LED.

In a possible embodiment, the electronic device provided in the embodiment of the present application may be specifically an intelligent wearable device (such as a wearable device supporting human health monitoring, such as an intelligent watch, an intelligent bracelet, an intelligent earphone or an intelligent eye mask), a mobile phone, a tablet computer, a notebook computer, a medical device, an intelligent household appliance, or the like.

In this embodiment of the present application, as shown in fig. 9, in the case where the electronic device provided in this embodiment of the present application is specifically a mobile phone, the PPG module may be disposed on the back of the smart phone. The position layout of the optical transmitter and the optical receiver included in the PPG module may be as shown in fig. 5. At this time, when the electronic device collects at least six detection light signals for the user through the PPG module, the user can be prompted to attach the finger to the PPG module at the back of the mobile phone, and the user is prompted to keep still for at least about 1 minute, so that the LED emits at least six wavelength light signals, and the PD receives the light signals reflected by the dermis layer as detection light signals, so as to collect at least six detection light signals.

In this embodiment of the present application, as shown in fig. 10, in the case where the electronic device provided in this embodiment of the present application is specifically an intelligent earphone, the PPG module may be disposed at a position where the intelligent earphone is directly attached to the skin of the ear portion of the user when the user wears the intelligent earphone. At this time, when the electronic device collects at least six detection light signals for a user through the PPG module, the user can keep a static state, and light with one wavelength is emitted by the LED with a wide spectrum wavelength at each time in different time periods, so that the PD with a wide receiving spectrum receives the light signals reflected by the stratum corneum, the epidermis, the dermis and the subcutaneous tissues at each time, and uses the received light signals reflected by the dermis as detection light signals with one wavelength. Therefore, the PPG module can sequentially collect detection light signals corresponding to at least 6 wavelengths of light emitted by the LEDs in a time-sharing manner.

It should be noted that, in the embodiment of the present application, it is assumed that the wavelength combination of 6 light rays generated by the PPG module through the LED to the skin of the ear portion of the user is specifically 535nm, 560nm, 577nm, 593nm, 622nm, and 636nm. When the PPG module emits light with the wavelength of 535nm at the first time based on the LED, the PPG module receives light signals reflected by the light with the wavelength of 535nm at the first time through the stratum corneum, the epidermis, the dermis and the subcutaneous tissue of the HbA1C detection part based on the PD, and the PPG module only determines the light signals reflected by the dermis as detection light signals with the wavelength of 535nm, which are collected at the first time. And then, when the PPG module emits light with the wavelength of 560nm at the second time based on the LED, the PPG module receives light signals reflected by the stratum corneum, the epidermis, the dermis and the subcutaneous tissues of the HbA1C detection part sequentially through the light with the wavelength of 560nm at the second time based on the PD, and the PPG module only determines the light signals reflected by the dermis as detection light signals with the wavelength of 560nm, which are acquired at the first time. The process of collecting the detection light signals of the other various wavelengths by the PPG module is similar, and will not be described here again.

In this embodiment of the present application, as shown in fig. 11, in the case where the electronic device provided in the embodiment of the present application is specifically a finger-clip-type HbA1C detecting instrument, the PPG module may be disposed at a position where the inside of the instrument is attached to the finger pad portion of the finger of the user. When the electronic equipment collects at least six detection light signals for a user through the PPG module, the user can be prompted to stretch fingers into the instrument to keep fingers and the LED and the PD of the PPG module to be attached, and the user is prompted to keep static for at least about 1 minute, so that the light signals with at least six wavelengths are emitted by the LED, and the PD receives the light signals reflected by the dermis layer as the detection light signals, so that at least six detection light signals are collected.

In this embodiment of the present application, as shown in fig. 12 to 14, in the case where the electronic device provided in this embodiment of the present application is specifically an intelligent bracelet, the electronic device provided in this embodiment of the present application further includes: a main body and a connecting part. Wherein the processor may be located in the main body. The connecting part is connected with the main body and is mainly used for binding the main body on the skin of a user.

In one possible embodiment, as shown in fig. 12, the PPG module may be provided on the main body. Alternatively, in another possible embodiment, as shown in fig. 13, the PPG module may also be provided on the connection member.

In this embodiment, no matter the PPG module is disposed on the main body or on the connection component, the position layout of the light emitter and the light receiver included in the PPG module may be as shown in fig. 5. At this time, when the electronic device collects at least six detection light signals for the user through the PPG module, the user can be prompted to attach the LED and the PD on the PPG module to the skin of the wrist, and the user is prompted to keep still for at least about 1 minute, so that the LED emits at least six wavelength light signals, and the PD receives the light signals reflected by the dermis layer as the detection light signals, so as to collect at least six detection light signals.

In addition, in a possible embodiment, as shown in fig. 14, in the case where the electronic device provided in the embodiment of the present application is specifically a smart bracelet, the PPG module may also be disposed on a side surface of the main body that is not in contact with the skin of the user (in the case where the user wears the smart bracelet normally, the back surface of the main body is usually in contact with the skin at the wrist of the user). At this time, when the electronic device collects at least six detection light signals for the user through the PPG module, the user can be prompted to attach the finger to the PPG module on the side surface of the main body, and the user is prompted to keep still for at least about 1 minute, so that the LED emits at least six wavelength light signals, and the PD receives the light signals reflected by the dermis layer as the detection light signals, so as to collect at least six detection light signals.

It should be noted that, in this embodiment of the present application, in the case where the electronic device is an intelligent bracelet, if the PPG module includes a light emitter and a light receiver, which are disposed on a bottom surface of the intelligent bracelet body, where the Light Emitter (LED) and the light receiver (PD) are in contact with the skin of the user, the position office of the Light Emitter (LED) and the light receiver (PD) may be as shown in fig. 5: the PD is positioned at the center of the bottom surface of the main body, 6 LED single-wavelength light emitting devices are surrounded by the PD, and the gap between the PD and the LED devices is 2mm-10mm (preferably 3.5 mm). Further, preferred combinations of emission wavelengths of the 6 LEDs are 535nm, 560nm, 577nm, 593nm, 622nm, and 636nm, and respective distributions of the 6 LED devices may be arranged or interspersed in order of wavelength.

In addition, in the embodiment of the present application, the location office of the transmitter (LED) and the optical receiver (PD) may also be as shown in fig. 6: the LED is positioned in the center of the bottom surface of the main body, 6 PD devices are surrounded by the LED, and the gap between the PD and the LED devices is 2mm-10mm (preferably 3.5 mm). Further, among the 6 PDs, each PD device is sensitive to only a single wavelength LED light, the combination of sensitive wavelengths is preferably 535nm, 560nm, 577nm, 593nm, 622nm, and 636nm, and the distribution positions of the 6 PD devices may be arranged in order of sensitive wavelengths or alternately arranged.

It should be noted that, in the embodiment of the present application, the light emitter (LED light emitting device) included in the PPG module may be a device in which a plurality of light emitting wafers are packaged into one module, and the PD device may also be a device in which a plurality of sensitive units are packaged into one module, so that the number of LED devices and/or PD devices included in the PPG module may be correspondingly reduced.

In this embodiment of the present application, the light emitter included in the PPG module may be a laser device with a corresponding wavelength in addition to the LED device described above. The plurality of light receivers may be: a filter of corresponding wavelength is added above the wide wavelength PD device to realize a PD sensitive to single wavelength light.

In this embodiment of the present application, because reflection and absorption effects of different wavelengths are different, in order to achieve an optimal signal-to-noise ratio, gaps between each of multiple LEDs and a single PD in the PPG module, or gaps between each of multiple PDs and a single LED, are not required to be identical.

In this embodiment of the present application, the outline of the sensor for collecting the detection light signal, which is formed by the LED and the PD on the PPG module, may be a shape such as a circle, an ellipse, a rectangle, or the like. That is, the electronic device provided in the embodiment of the present application is not limited to the specific shape of the outline of the sensor composed of the LED and the PD included in the PPG module.

Next, based on the above description of the electronic device provided in the embodiment of the present application, the general concept of the data acquisition method of the present application is proposed.

As is clear from the description in the background art, the present day relies on a large biochemical analyzer to measure the HbA1C level of the user in a venous blood sampling manner, so that it is difficult to meet the requirement of real-time obtaining of the detection information of HbA1C to perform daily monitoring on the HbA1C of the user, and the user can suffer a certain wound due to venous blood sampling treatment on the user.

In view of this, the embodiment of the application provides a data acquisition method, which is applied to a first electronic device including a PPG module, and at least six detection optical signals are collected for a user through the PPG module through the first electronic device, wherein each detection optical signal in the six detection optical signals includes an optical signal reflected from the user after light irradiates the user, and wavelengths of light used for detecting different detection optical signals are different from each other. Then, the first electronic device acquires a characteristic parameter corresponding to each detection light signal (a characteristic parameter corresponding to each detection light signal, that is, a ratio between an alternating current component and a direct current component corresponding to each detection light signal). Finally, the first electronic device calculates a proportion of HbA1C in total hemoglobin among a plurality of hemoglobin of the user based on the six acquired characteristic parameters.

In the embodiment of the application, the first electronic device uses the PPG module to collect the detection light signal in a noninvasive manner, so that the calculation is performed based on the characteristic parameters corresponding to the detection light signal (the proportion between the alternating current component and the direct current component corresponding to the detection light signal) to determine the proportion of HbA1C of the user to total hemoglobin. Therefore, compared with a mode of measuring HbA1C by means of a large-scale biochemical analysis instrument, the data acquisition method provided by the embodiment of the application does not need to collect blood for a user so as to bring wounds to the user, and can be used for conveniently and rapidly acquiring detection information for detecting HbA 1C. That is, the data acquisition method provided by the embodiment of the application can realize noninvasive detection of HbA1C of a user, and can immediately acquire the proportion of HbA1C of the user to total hemoglobin for daily monitoring of HbA1C of the user, so that great convenience is provided for the user to detect HbA1C for diabetes screening or for long-term control of diabetes.

In addition, the data acquisition method provided by the embodiment of the application also considers that a plurality of haemoglobin exists in blood of a user, so that at least six detection light signals are acquired by using the PPG module through the first electronic device, and the proportion between the alternating current component and the direct current component corresponding to each detection light signal is utilized to calculate the proportion of HbA1C in the plurality of haemoglobin. Thus, the problem of inaccurate measurement results caused by mixing other hemoglobin with HbA1C to be actually detected, which is common in the related art, can be avoided. That is, the data acquisition method provided by the embodiment of the application can realize more accurate detection of the HbA1C level of the user, so that accuracy and effectiveness of HbA1C detection of the user are ensured.

Based on the overall overview of the data acquisition method provided in the embodiments of the present application, each specific embodiment of the data acquisition method provided in the embodiments of the present application is sequentially described below.

Referring to fig. 15, fig. 15 is a flow chart of a data acquisition method according to an embodiment of the present application in one possible embodiment. It should be understood that, although the execution order of some method steps is shown in fig. 15, the data acquisition method provided in the embodiment of the present application may of course be adopted different from the execution order of the method steps shown in the drawings based on different design requirements of practical applications. That is, the order of the steps of the method shown in fig. 15 is not limited to the logic sequence of execution of the data acquisition method provided in the embodiments of the present application, and any other reasonable variation based on the order of the steps of the method shown in fig. 15 should be included in the protection scope of the data acquisition method provided in the embodiments of the present application.

In one possible embodiment of the data acquisition method provided in the embodiments of the present application, when the data acquisition method is executed by a first electronic device including a PPG module, first, the first electronic device executes S1: and (3) collecting. That is, the first electronic device collects at least six detection light signals for the user through the PPG module. Each detection light signal collected by the first electronic device comprises a light signal reflected from the user after the light irradiates the user, and the wavelengths of the light used for detecting different detection light signals are different from each other. Then, the first electronic device performs S2: and (3) acquiring. That is, the first electronic device obtains, according to the ac component and the dc component in the PPG signal corresponding to each detection light signal, a characteristic parameter corresponding to each detection signal (the characteristic parameter is a ratio between the ac component and the dc component in the PPG signal corresponding to the detection light signal). Finally, the first electronic device performs S3: and (3) calculating. That is, the first electronic device calculates the HbA1C ratio of the total hemoglobin of the user by using the obtained characteristic parameters corresponding to the at least six detection signals.

In the embodiment of the present application, since a plurality of hemoglobin (e.g., oxyhemoglobin, reduced hemoglobin, carbon monoxide hemoglobin, methemoglobin) are included in the blood of the user, it is naturally necessary to take various hemoglobin into consideration in order to precisely measure the HbA1C ratio of the glycosylated hemoglobin when measuring HbA1C for the user. However, since the proportion of HbA1C to total hemoglobin itself is low (most cases < 10%), and the concentrations of carbon monoxide hemoglobin and methemoglobin are also low in a normal scene, the portions of carbon monoxide hemoglobin and methemoglobin in HbA1C can be ignored. Therefore, when measuring the HbA1C ratio among various hemoglobin of a user, there can be mainly considered 6 kinds of oxy-glycosylated hemoglobin, reduced-glycosylated hemoglobin, oxy-non-glycosylated hemoglobin, reduced-non-glycosylated hemoglobin, carbon monoxide hemoglobin, and methemoglobin.

Therefore, when the first electronic device measures and calculates the proportion of HbA1C of the user, at least the relative proportion of the 6 types of hemoglobin needs to be measured, that is, the PPG module needs to be controlled to collect at least 6 detection light signals for the user, so that the ratio AC/DC between the alternating current component and the direct current component in the PPG signal corresponding to each detection light signal is utilized to calculate and determine the proportion of one or more types of hemoglobin in the 6 types of hemoglobin to the 6 types of total hemoglobin.

In addition, in combination with the electronic device provided in the foregoing embodiment of the present application, when the detection light signal is collected by the PPG module for the user, regarding the selection of the wavelength of the light emitted by the light emitter in the PPG module to the user, the first electronic device may select the light to be used for detecting the HbA1C of the user through the PPG module in the wavelength range greater than or equal to 500nm and less than or equal to 1100nm, and may also select the light with different wavelengths through the PPG module in the wavelength range greater than or equal to 1600nm and less than or equal to 1850nm to detect the HbA 1C. That is, when the first electronic device collects at least 6 detection light signals for the user through the PPG module, the wavelength range of the light emitted to the HbA1C detection portion such as the wrist or finger of the user is preferably 500nm or more and 1100nm or less, and/or 1600nm or more and 1850nm or less.

In addition, since the absorption of light by other tissues of the human body (such as skin, muscle, vein, bone, etc.) remains substantially constant, it will only appear as a DC portion in the PPG signal, and since other substances in the artery with a small content will itself absorb little light, the absorption of light in the wavelength range of 500nm or more and 1100nm or less by water, and the absorption of light in the wavelength range of 1600nm or more and 1850nm or less will be small, and will not have a substantial effect on the AC portion. In this way, the first electronic device selects light rays to emit to the detection part of the HbA1C of the user through the PPG module within a wavelength range of greater than or equal to 500nm and less than or equal to 1100nm and/or greater than or equal to 1600nm and less than or equal to 1850nm, and collects an optical signal reflected by the detection part of the HbA1C of the user as a detection optical signal, and performs photoelectric conversion, amplification and sampling processing on the collected detection optical signal to obtain a corresponding PPG signal, so that only the 6 kinds of hemoglobin can be equivalently considered to contribute to an AC part in the PPG signal. As shown in fig. 16, methemoglobin, oxyhemoglobin, carboxyhemoglobin, and deoxyhemoglobin (wherein oxyhemoglobin may be specifically any one of oxyglycosylated hemoglobin and oxynon-glycosylated hemoglobin, carboxyhemoglobin may be specifically carbon monoxide hemoglobin, and deoxyhemoglobin may be specifically any one of reductive glycosylated hemoglobin and reductive non-glycosylated hemoglobin) each have a high absorption of light rays having a wavelength of 500nm or more and 1100nm or less, and particularly have a significantly higher absorption of light rays having a wavelength of about 600nm than that of light rays having a wavelength of about 1200 nm. Whereas the wavelengths of light with higher absorption by plasma are mainly concentrated in the range of greater than or equal to 1400nm and less than or equal to 1600 nm. Thus, the first electronic device may consider that only 6 kinds of hemoglobin, which is oxy-glycosylated hemoglobin, reduced-glycosylated hemoglobin, oxy-non-glycosylated hemoglobin, reduced-non-glycosylated hemoglobin, carbon monoxide hemoglobin, and methemoglobin, causes the AC component in the PPG signals corresponding to each of the at least six detection light signals to change after at least six detection light signals are acquired by selecting light having a wavelength range of 500nm or more and 1100nm or less and/or selecting light having a wavelength range of 1600nm or more and 1850nm or less.

For example, the first electronic device collects 6 detection light signals for the user through the PPG module. As shown in fig. 5, it is assumed that the PPG module integrated by the first electronic device is mainly composed of 6 LEDs with different wavelengths and a PD with a wide receiving spectrum, where the position layout of the LEDs and the PD may be: the 6 LEDs surround 1 PD. When the first electronic device collects the detection light signals through the PPG module, the PPG module is used for controlling the AFE to drive the LEDs with 6 different wavelengths to emit light in a time-sharing mode so as to realize the time-sharing emission of the light with 6 different wavelengths to the HbA1C detection part of the user (the wavelength of the light is in a wavelength range of more than or equal to 500nm and less than or equal to 1100nm and/or the wavelength of the light is in a wavelength range of more than or equal to 1600nm and less than or equal to 1850 nm). When the AFE drives 1 LED to emit light, the PD of the PPG module receives light signals reflected by the stratum corneum, the epidermis, the dermis and the subcutaneous tissues of the HbA1C detection part sequentially from light rays with one wavelength emitted by the LED. The PD determines only the received optical signal reflected by the dermis layer as the detection optical signal. Therefore, after the AFE sequentially drives the 6 LEDs to emit light and receives the reflected light signals through the PD in the time period of each LED to emit light, the light signals reflected by the dermis layer are determined to be detection light signals, and the PPG module can sequentially acquire 6 detection light signals.

After the first electronic device acquires detection light signals with one wavelength through the PPG module, the detection light signals are further subjected to photoelectric conversion to obtain electric signals, and then the electric signals are amplified and sampled to obtain PPG signals corresponding to the detection signals with one wavelength. The first electronic device can sequentially acquire PPD signals corresponding to 6 detection optical signals in sequence through the circulation.

Or, the first electronic device may further perform photoelectric conversion on each detection optical signal one by one to obtain an electrical signal after a total of 6 detection optical signals are acquired by the PPG module, and then amplify and sample each electrical signal respectively, so as to obtain PPG signals corresponding to the detection signals with a total of 6 wavelengths at a time.

In this embodiment of the present application, the PPG module may determine the wavelength of the detected optical signal collected each time based on the correspondence (generally, the same) between the time when the PD receives the detected optical signal and the time when the LED emits the detected optical signal. For example, when the first electronic device emits light of the first wavelength at the first time based on the LED through the PPG module, the first electronic device receives a detection light signal of the first wavelength at the first time based on the PD through the PPG module. When the PPG module emits light with a second wavelength at a second time based on the LED, the PPG module receives a detection light signal with the second wavelength at the second time based on the PD. The process of determining the wavelengths of the collected other various detection light signals by the first electronic device through the PPG module is similar, and will not be described in detail here.

In another possible embodiment, the first electronic device may further collect a number of detected light signals greater than 6 through the PPG module, and calculate, based on a ratio between an ac component and a dc component corresponding to each detected light signal, a ratio of HbA1C of the user to total hemoglobin.

The first electronic device collects detection light signals of 9 wavelengths for a user through the PPG module. Preferably, the wavelength combination of the light rays for detection of the 9 wavelength detection optical signals may be 535nm, 560nm, 577nm, 593nm, 622nm, 636nm, 660nm, 940nm, and 970nm. In the case where the PPG module integrated by the first electronic device mainly consists of 9 LEDs of different wavelengths plus 1 PD of wide reception spectrum, the position layout of the LEDs and the PD may be as shown in fig. 17: 9 LEDs surround 1 PD. When the first electronic equipment collects detection light signals through the PPG module, the PPG module is used for controlling the AFE to drive the 9 LEDs with different wavelengths to emit light in a time-sharing mode, so that the 9 light signals with different wavelengths are emitted to the HbA1C detection part of the user in a time-sharing mode. That is, the AFE drives the LED of the 1 st wavelength to emit light at the 1 st time, and then drives the LED of the 2 nd wavelength to emit light at the 2 nd time after the 1 st time, and so on until the AFE drives the LED of the 9 th wavelength to emit light at the 9 th time.

When the AFE drives 9 LEDs with different wavelengths to emit light in a time-sharing mode, the PD of the PPG module also receives the light signals with one wavelength emitted by each LED successively. That is, the PD receives the light signals reflected by the stratum corneum, epidermis, dermis, and subcutaneous tissue of the HbA1C detection site sequentially from the light of the 1 st wavelength at time 1, and receives the light signals reflected by the stratum corneum, epidermis, dermis, and subcutaneous tissue of the HbA1C detection site sequentially from the light of the 2 nd wavelength at time 2 after time 1. By analogy, the PD can receive optical signals of 9 wavelengths in total. And then, the PD takes the optical signals reflected by the dermis layer in the optical signals with each wavelength as detection optical signals, so that the first electronic equipment acquires 9 kinds of detection optical signals through the PPG module.

It should be noted that, in the embodiment of the present application, when the first electronic device controls the PPG module to collect PPG signals with 6 wavelengths for a user, any combination with 6 wavelengths may be selected preferentially from the above-mentioned combinations with 9 specific wavelengths 535nm, 560nm, 577nm, 593nm, 622nm, 636nm, 660nm, 940nm and 970 nm. Of course, the first electronic device may also arbitrarily select other 6 wavelength combinations among the aforementioned wavelength ranges 500nm-1100nm and/or 1600nm-1850 nm.

It should be noted that, in the embodiment of the present application, the first electronic device includes, but is not limited to, an intelligent wearable device (such as a smart watch, a smart bracelet, or a smart eye mask, etc., a wearable device supporting human health monitoring), a mobile phone, a tablet computer, a notebook computer, a medical device, a smart home appliance, etc. When the first electronic device collects at least six detection light signals for a user through the PPG module, an LED and a PD on the PPG module are required to be slightly and tightly attached to HbA1C detection parts such as arms and wrists of the user, and the user is prompted to keep the body still for at least about 1 minute, so that the light signals with various wavelengths are emitted by the AFE driving LED, and the PD receives the light signals reflected by the dermis layer as detection light signals, so that at least six detection light signals are collected.

It should be noted that, in the embodiment of the present application, when the AFE drives the LEDs with different wavelengths to emit light in a time-sharing manner, because the blood of the user is flowing, the time interval of the AFE driving the LEDs to emit light with the 1 st wavelength is short enough to ensure that the object of receiving the reflected light signal by the PD to collect the multiple detected light signals is nearly the same blood from the 1 st LED driven by the AFE to the last 1 st LED driven by the AFE to emit light with the last 1 st wavelength. For example, the interval between the time-sharing emission of light with different wavelengths by the AFE driving different LEDs may be set to 30 microseconds (us), where the interval between the 1 st wavelength light and the last 1 st wavelength light is short enough, so that the detected light signal with the 1 st wavelength acquired is guaranteed to be approximately the same as the time phase of the detected light signal with the last 1 st wavelength corresponding to blood.

Furthermore, in the embodiments of the present application, considering that the penetration depths of light of different wavelengths are different, the blood flows from the deep layer of the skin to the shallow layer of the skin, and this flow process requires a short time, it is still possible to cause the phases of arterial blood detected simultaneously by light of different wavelengths to be different. For example, the difference in the phases of arterial blood detected simultaneously by green light and infrared light can reach tens to one hundred milliseconds, which time difference greatly affects the result. Therefore, in the calculation, the data of the absorption amounts I of the light with different wavelengths used by the PPG module should have corresponding time differences. Illustratively, in the case of the combination of 9 wavelengths, specifically 535nm, 560nm, 577nm, 593nm, 622nm, 636nm, 660nm, 940nm, and 970nm described above, if the time for the PPG module to use the PPG signal detected by light of 970nm is t0, the time for the PPG module to use the PPG signal detected by light of 940nm should be t0+t1, and the time for the PPG module d to use the PPG signal detected by light of 660nm should be t0+t2. Similarly, the time for the PPG module to detect the PPG signal using 535nm light should be t0+t8. Where t1 to t8 are fixed, typically on the order of 1ms-10ms.

In one possible embodiment, the placement of LEDs on the PPG module with PDs may employ a combination of 1 wide spectrum wavelength LED and multiple narrow receive spectrum PDs (at least 6) in addition to the multiple LEDs surrounding 1 PD as shown in fig. 5 or 17. At this time, the position layout of 1 LED and a plurality of PDs may be as shown in fig. 6: at least 6 PDs surround 1 LED. Therefore, when the first electronic device collects the detection light signals through the PPG module, the AFE can still drive the LEDs with wide spectrum wavelengths to emit light rays with one wavelength at a time, so that only the PD sensitive to the light rays with the wavelength emitted by the current LEDs in the 6 PDs with narrow receiving spectrums receives the light signals reflected by the stratum corneum, the epidermis, the dermis and the subcutaneous tissues in sequence, and the received light signals reflected by the dermis are used as detection light signals with one wavelength. Therefore, the PPG module can sequentially acquire detection light signals corresponding to at least 6 wavelengths of light emitted by the current LED in a time-sharing manner.

In another possible embodiment, when the PPG module adopts a combination mode of 1 LED with a wide spectrum wavelength and at least 6 PD with a narrow receiving spectrum, the first electronic device controls the PPG module to collect at least 6 detection light signals, and the AFE can drive the LED with a wide spectrum wavelength to emit light with 6 wavelengths at one time. Since each PD of the 6 narrow receiving spectrums is sensitive to the optical signal of one wavelength only, the PD of the 6 narrow receiving spectrums can respectively receive the optical signal reflected by the stratum corneum, the epidermis, the dermis and the subcutaneous tissue of the sensitive one of the 6 wavelengths at the same time. And each of the 6 PDs uses the received light reflected by the dermis layer as a detection light signal received by itself. Thus, the first electronic device can collect 6 detection light signals at the same time.

In a possible embodiment, when the first electronic device collects at least six detection optical signals to the user through the PPG module, the first electronic device may further automatically trigger an instruction and start to collect the at least six detection optical signals to the user through the PPG module in response to the instruction when the activity level of the user is monitored to be lower than a preset activity level threshold in a process of continuously monitoring the activity level of the user. Or, the first electronic device may further start to collect the above-mentioned at least six detection light signals to the user through the PPG module based on the timing information set by the user, in a case that the time of day reaches the measurement time set by the user.

In another possible embodiment, when the first electronic device collects at least six detection optical signals to the user through the PPG module, the first electronic device may start to collect the at least six detection optical signals to the user through the PPG module according to the preset indication information when the user finds that the user does not have body movement in the process of continuously monitoring the user.

It should be noted that, in the embodiment of the present application, the preset indication information may specifically be an instruction for controlling the first electronic device to respond to the acquisition and detection of the optical signal. The instruction may be triggered manually by the user or automatically by the first electronic device. In addition, the situation that the user does not have body movement may specifically be that the user keeps the body in a static state, or the situation that the user does not have body movement may at least also keep the position (such as an arm, a wrist, or a head, etc.) where the skin in close contact with the LEDs and the PD of the PPG module is located, unchanged in spatial position.

As illustrated in fig. 18, the first electronic device may specifically start to collect at least six detection light signals through the PPG module when it is monitored that the user keeps his body stationary by responding to an instruction triggered by the user clicking an instruction control provided by the first electronic device. Alternatively, as shown in fig. 19, the first electronic device may specifically further start to collect at least six detection light signals through the PPG module in response to an instruction sent by another electronic device (for example, triggered by a user clicking an instruction displayed on a display interface of the smartphone by a piece), when it is monitored that the user is sleeping and thus keeps the body in a stationary state (or a state in which the user remains sitting and no movement of an arm or a wrist occurs).

In a possible embodiment, after at least six detection optical signals are acquired by the PPG module for a user, the first electronic device performs photoelectric conversion on the at least six detection optical signals to obtain corresponding electrical signals, and then performs processing of amplifying and sampling on the electrical signals obtained by conversion, so as to obtain PPG signals corresponding to the at least six detection optical signals. Then, under the condition that the first electronic equipment has data calculation capability, the first electronic equipment calculates the proportion between the AC component and the DC component according to the AC component and the DC component contained in the PPG signals aiming at each PPG signal, so that at least six characteristic parameters corresponding to the detection light signals are obtained. After that, the first electronic device can calculate together based on the characteristic parameters AC/DC corresponding to each of the at least 6 detection signals, so as to obtain the proportion of HbA1C in the total hemoglobin in the multiple hemoglobin of the user.

For example, after the first electronic device collects 6 detection optical signals with wavelength combinations of 535nm, 560nm, 577nm, 593nm, 622nm and 636nm through the PPG module, the first electronic device performs photoelectric conversion on the 1 st detection optical signal to obtain an electrical signal corresponding to the 1 st detection optical signal, and then the first electronic device amplifies and samples the electrical signal to obtain a PPG signal corresponding to the 1 st detection optical signal. The first electronic device obtains PPG signals corresponding to the other 5 wavelength detection light signals respectively by adopting the same manner as obtaining the PPG signals corresponding to the 1 st detection light signal for the detection light signals of the other 5 wavelengths.

As described above, the first electronic device selects light to emit to the detection portion of HbA1C of the user through the PPG module in a wavelength range greater than or equal to 500nm and less than or equal to 1100nm, and/or greater than or equal to 1600nm and less than or equal to 1850nm, and collects the light signal reflected by the detection portion of HbA1C of the user as the detection light signal, and performs photoelectric conversion, amplification and sampling processing on the detection light signal to obtain a corresponding PPG signal, which can equivalently be considered that only 6 kinds of hemoglobin, that is, oxy-glycosylated hemoglobin, reduced-glycosylated hemoglobin, oxy-non-glycosylated hemoglobin, reduced-non-glycosylated hemoglobin, carbon monoxide hemoglobin and methemoglobin, will contribute to the AC portion in the PPG signal, and the absorption of light by other tissues of the human body (such as skin, muscle, vein, bone, etc.) will remain substantially constant, and will only appear as the DC portion in the PPG signal. So that each of the 6 PPG signals obtained by the first electronic device comprises an AC component and a DC component.

In this way, the first electronic device may calculate, for each PPG signal, the ratio between the AC component and the DC component in each PPG signal, using the AC component divided by the DC component. Thus, the first electronic device obtains the characteristic parameter AC/DC corresponding to each detected light signal.

In a possible embodiment, after the first electronic device obtains the characteristic parameters AC/DC corresponding to the at least six detected light signals, the first electronic device further calculates the proportion of HbA1C of the user to total hemoglobin based on the at least six characteristic parameters together, which may be referred to as the following procedure: the first electronic device first determines the respective concentrations ci of the six haemoglobin types of the user by using the obtained at least six characteristic parameters AC/DC (ci is the concentration of the ith haemoglobin type, i is any one of the values 1 to 6). Then, the first electronic device uses the sum of the concentrations of two kinds of HbA1C among the six kinds of hemoglobin divided by the sum of the concentrations of the total six kinds of hemoglobin to obtain a ratio between the sum of the concentrations of the two kinds of HbA1C and the sum of the concentrations of the six kinds of hemoglobin, and uses the calculated ratio as a ratio of the two kinds of HbA1C of the user to the total hemoglobin.

For example, the first electronic device collects the 9 detection light signals with wavelengths λ1 to λ9 through the PPG module, so that the proportion of HbA1C of the user to total hemoglobin is calculated together based on the characteristic parameters AC/DC corresponding to the 9 detection light signals. The first electronic device may calculate, for the PPG signal corresponding to the detected optical signal of each wavelength, an AC/DC value according to langerhans' law using the AC component and the DC component included in the PPG signal (i.e., the value of the optical signal of each wavelengthDenoted by R, r=ac/DC = -j =>）。

Meanwhile, since the first electronic device performs the collection of the detection light signal by selecting the light signal in the wavelength range of more than or equal to 500nm and less than or equal to 1100nm and/or more than or equal to 1600nm and less than or equal to 1850nm through the PPG module, the first electronic device absorbs light based on the 6 kinds of hemoglobin which are approximately equivalent to only oxy-glycosylated hemoglobin, reduced-glycosylated hemoglobin, oxy-non-glycosylated hemoglobin, reduced-non-glycosylated hemoglobin, carbon monoxide hemoglobin, methemoglobin in the wavelength range, the first electronic device performs the collection of the detection light signal based on the detection light signal in the wavelength range of more than or equal to 1600nm and less than or equal to 1850nm1 to->9, the AC/DC value of the PPG signal corresponding to the detected light signal may be listed as the following combination of equations:

For wavelength1：/>；

For wavelength2：/>；

For wavelength3：/>；

For the followingWavelength of4：/>；

For wavelength5：/>；

For wavelength6：/>；

For wavelength7：/>；

For wavelength8：/>；

For wavelength9：/>。

Where kij is the absorption coefficient of the ith hemoglobin for the light at the jth wavelength (known), and ci is the concentration of the ith hemoglobin.

Since R1 to R9 can be calculated by the AC/DC values of the PPG signals of various wavelengths measured by the PPG module, the first electronic device is assumed to set c1 as oxyhemoglobin-glycosylated red bloodThe concentration of protein, c2 is the concentration of reduced-glycosylated hemoglobin, c3 is the concentration of oxy-non-glycosylated hemoglobin, c4 is the concentration of reduced-non-glycosylated hemoglobin, c5 is the concentration of carbon monoxide hemoglobin, and c6 is the concentration of methemoglobin. The first electronic device can derive the ratio of the two HbA1C (C1 and C2) of the user to the total hemoglobin as. Thus, the first electronic device can calculate the ratio of HbA1c to total hemoglobin by solving the above 9 equations into a multiple one-time equation.

In this embodiment of the present application, the first electronic device may calculate HbA1c% by solving the above 9 equations by a multiple one-time equation, and may calculate the ratio of HbA1c to total hemoglobin by a machine learning model using the absorption coefficients of R1 to R9 and 6 kinds of hemoglobin for each wavelength optical signal.

In a possible embodiment, as shown in fig. 20, the data acquisition method provided in the embodiment of the present application may further calculate a proportion of HbA1C of the user to total hemoglobin through a second electronic device communicatively connected to the first electronic device. That is, when the data acquisition method provided in the embodiment of the present application is executed by the first electronic device including the PPG module, the first electronic device first collects at least six detection light signals for the user through the PPG module, where each detection light signal in the at least six detection light signals includes a light signal reflected from the user after the light irradiates the user, and wavelengths of light used for detecting different detection light signals are different from each other. Then, the first electronic device acquires PPG signals corresponding to the at least six detection light signals respectively, and sends the at least six PPG signals to the second electronic device through communication connection between the first electronic device and the second electronic device. Therefore, after receiving at least six PPG signals, the second electronic device obtains the characteristic parameters (the ratio between the ac component and the dc component in each PPG signal) corresponding to each PPG signal, and calculates the ratio of HbA1C to total hemoglobin in multiple hemoglobin of the user based on the obtained at least six characteristic parameters. Finally, the second electronic device sends the calculated HbA1C proportion of the total hemoglobin to the first electronic device, so that the first electronic device can obtain the HbA1C proportion of the user.

In the embodiment of the application, if the first electronic device integrates the PPG module but does not have the data computing capability, the first electronic device and the second electronic device with the data computing capability can be introduced to perform communication matching, so that the noninvasive HbA1C detection of the user is realized, and the proportion of the HbA1C of the user to the total hemoglobin is obtained in real time. In addition, under the condition, the first electronic equipment can still acquire the proportion information of HbA1C of the user to total hemoglobin, so that the acquired proportion information is displayed for the user, and the user can conveniently screen diabetes or carry out daily monitoring control on diabetes based on the proportion information of HbA 1C.

In a possible embodiment, as shown in fig. 21, when the data acquisition method provided in the embodiment of the present application is implemented in a scenario where the first electronic device and the second electronic device perform data interaction, when the data acquisition method provided in the embodiment of the present application is executed by the first electronic device including the PPG module, if the first electronic device itself does not have data computing capability or has limited data computing capability, in the case that the first electronic device has data transceiving capability, the first electronic device first executes step S4: and acquiring at least six detection light signals through the PPG module. Wherein each detection light signal comprises a light signal reflected from the user after the light irradiates the user, and the wavelengths of the light used for detecting different detection light signals are different from each other.

After that, the first electronic device obtains PPG signals corresponding to at least six detection light signals, and based on the communication connection with the second electronic device, performs step S5 towards the second device: and sending PPG signals corresponding to the at least six detection light signals respectively, so that the second electronic equipment with data computing capability or more sufficient data computing capability receives the at least six PPG signals.

The second electronic device, after receiving at least six PPG signals, locally for each PPG signal, uses an AC component divided by a DC component in the PPG signal to obtain an AC/DC of the resulting PPG signal. Then further execute step S6: the HbA1C ratio of the user to total hemoglobin is calculated based on the AC/DC of each of the at least six PPG signals. After calculating the proportion of HbA1C of the user to total hemoglobin, the second electronic device further performs step S7 for the first electronic device: transmitting the ratio of HbA1C of the user to total hemoglobin, so that the first electronic device receives the ratio of HbA1C of the user to total hemoglobin, and immediately executing step S8: the HbA1C of the user is shown to be the proportion of total hemoglobin.

It should be noted that, in the embodiment of the present application, the process that the first electronic device collects at least six detection optical signals through the PPG module is consistent with the process that the first electronic device collects at least six detection optical signals through the PPG module in the foregoing embodiments, and no further description is given here.

In addition, in the embodiment of the present application, the process of obtaining PPG corresponding to each of at least six detection optical signals by the first electronic device is also consistent with the process of performing photoelectric conversion, amplification and sampling on the detection optical signals by the first electronic device in the foregoing embodiments to obtain PPG signals corresponding to the detection optical signals, which is not described herein again.

Furthermore, in the embodiment of the present application, the process that the second electronic device obtains the AC/DC of each of the at least six PPG signals, and calculates the proportion of HbA1C of the user to the total hemoglobin based on the at least six AC/DC is identical to the process that the first electronic device obtains the characteristic parameters of the at least six detection light signals (the proportion between the AC component and the DC component in the PPG signal corresponding to each of the at least six detection light signals, that is, the AC/DC value) in the foregoing embodiment, so that the proportion of HbA1C of the user to the total hemoglobin based on the at least six AC/DC is calculated together, which is not repeated herein.

It should be noted that, in the embodiment of the present application, the second electronic device may be a terminal device with data interaction and data calculation capabilities, such as a smart phone, a tablet, a computer, and a cloud server.

In another possible embodiment, the data acquisition method provided in the embodiment of the present application may also be directly applied to a second electronic device that is in communication connection with the first electronic device, so that, when the first electronic device does not have the data calculation capability, the second electronic device and the first electronic device perform communication coordination to calculate and obtain the proportion of HbA1C of the user to total hemoglobin. That is, when the data acquisition method provided by the embodiment of the application is executed by the second electronic device, the second electronic device directly receives at least six PPG signals sent by the first electronic device. The at least six PPG signals are obtained by the first electronic device through processing of photoelectric conversion, electric signal amplification and sampling of at least six detection light signals after the at least six detection light signals are acquired by the PPG module for a user. And, among at least six detection optical signals collected by the first electronic device, each detection optical signal includes an optical signal reflected from the user after the light is irradiated on the user, and wavelengths of light used for detecting different detection optical signals are different from each other. The first electronic device sends the collected six detection light signals to the second electronic device through communication connection with the second electronic device. After six PPG signals are received, the second electronic device obtains a characteristic parameter (a proportion between an alternating current component and a direct current component in each PPG signal) corresponding to each PPG signal, and calculates a proportion of HbA1C in total hemoglobin among multiple hemoglobin of a user based on the six obtained characteristic parameters. And, the second electronic device also presents to the user the proportion of HbA1C to total hemoglobin. Or the second electronic device returns the calculated proportion of HbA1C of the user to the total hemoglobin to the first electronic device so that the first electronic device can display the proportion of HbA1C of the user to the total hemoglobin. Alternatively, the second electronic device may return the ratio of HbA1C of the user to total hemoglobin to the first electronic device, and display the ratio of HbA1C of the user to total hemoglobin.

Referring to fig. 22, in a possible embodiment, in a scenario where the first electronic device and the second electronic device perform data interaction, the data acquisition method provided in the embodiment of the present application may also be executed by the second electronic device.

That is, the second electronic device first receives at least six PPG signals transmitted by the first electronic device. The first electronic device collects at least six detection light signals in advance through a PPG module of the first electronic device, each detection light signal comprises a light signal reflected from a user after the light irradiates the user, and wavelengths of light used for detecting different detection light signals are different from each other. And then, the first electronic device acquires the PPG signals corresponding to the at least six detection light signals respectively, and sends the PPG signals corresponding to the at least six detection light signals respectively to the second electronic device.

The second electronic device obtains, after receiving at least six PPG signals, a corresponding characteristic parameter of each PPG signal, i.e. a ratio AC/DC between an AC component and a DC component in the PPG signal. And the second electronic device performs calculation based on at least six characteristic parameters AC/DC together, thereby obtaining the proportion of HbA1C of the user to total hemoglobin.

And finally, the second electronic device returns the calculated HbA1C proportion of the user to the first electronic device so that the first electronic device can display the HbA1C proportion of the user to the total hemoglobin.

It should be noted that, in the embodiment of the present application, the process that the first electronic device collects at least six detection optical signals through the PPG module in advance is consistent with the process that the first electronic device collects at least six detection optical signals through the PPG module in the foregoing embodiments, and no further description is given here.

In addition, in the embodiment of the present application, before the first electronic device sends the PPG signals corresponding to the six detection light signals to the second electronic device, a process of obtaining the PPG corresponding to each of the at least six detection light signals is also consistent with a process of performing photoelectric conversion, amplification and sampling on the detection light signals by the first electronic device in the foregoing embodiments to obtain PPG signals corresponding to the detection light signals, which is not described herein again.

Furthermore, in the embodiment of the present application, the process that the second electronic device obtains the AC/DC values of the characteristic parameters of each of the at least six PPG signals, and calculates the proportion of HbA1C of the user to the total hemoglobin based on the at least six AC/DC values is also consistent with the process that the first electronic device obtains the characteristic parameters of the at least six detection light signals (the proportion between the AC component and the DC component in the PPG signal corresponding to each of the at least six detection light signals, that is, the AC/DC values), so that the proportion of HbA1C of the user to the total hemoglobin is calculated based on the at least six AC/DC values.

In a possible embodiment, after calculating the proportion of HbA1c of the user to the total hemoglobin, the electronic device may compare the proportion of HbA1c to the total hemoglobin with a preset threshold, so as to push, to the user, a detection result of HbA1c corresponding to the currently calculated proportion of HbA1c to the total hemoglobin according to the comparison result.

In the embodiment of the present application, the electronic device may be the first electronic device described above. For example, in the scenario that the first electronic device performs the data acquisition method provided in the embodiments of the present application separately, after calculating the proportion of HbA1c of the user to total hemoglobin, the first electronic device pushes, to the user, an HbA1c detection result corresponding to the currently calculated proportion of HbA1c to total hemoglobin according to a comparison result of the proportion of HbA1c to total hemoglobin and a preset threshold. Or under the scene that the first electronic device and the second electronic device perform data interaction, the electronic device is the first electronic device or the second electronic device. The electronic device may be the first electronic device or the second electronic device. For example, after the second electronic device calculates the proportion of HbA1c in total hemoglobin of the user and sends the proportion of HbA1c in total hemoglobin to the first electronic device, the first electronic device may push, to the user, a detected HbA1c result corresponding to the currently calculated proportion of HbA1c in total hemoglobin according to a comparison result between the proportion of HbA1c in total hemoglobin and a preset threshold. And after the second electronic device calculates the proportion of HbA1c to total hemoglobin, the second electronic device can push a HbA1c detection result corresponding to the currently calculated proportion of HbA1c to total hemoglobin to a user according to a comparison result of the proportion of HbA1c to total hemoglobin and a preset threshold value.

It should be noted that, in the embodiment of the present application, the preset threshold may be a threshold 6.4 corresponding to confirming that the user has suffered from diabetes. After the electronic device calculates the proportion of HbA1C of the user to total hemoglobin, if the proportion of HbA1C to total hemoglobin is greater than or equal to 6.4, the electronic device confirms that the detection result of HbA1C corresponding to the proportion of HbA1C to total hemoglobin calculated currently is: the user may suffer from diabetes, suggest to reduce sugar intake and go to hospital for examination immediately, etc. The electronic device pushes the HbA1C detection result to the user. Otherwise, if the ratio of HbA1C to total hemoglobin is less than 6.4, the first electronic device confirms that the HbA1C detection result corresponding to the ratio of HbA1C to total hemoglobin obtained by current calculation is: user HbA1C levels were normal. The electronic device also pushes the HbA1C detection result to the user.

It should be noted that, in the embodiment of the present application, the preset threshold may also be other values, for example, 6.3, 6.2, 6.1, 6.5, 6.6, etc., which are not limited herein.

In a possible embodiment, after the ratio of HbA1C of the user to the total hemoglobin is calculated by the electronic device, the data acquisition method provided in the embodiment of the present application may further collect at least six detection light signals at a time, calculate the ratio of HbA1C of the user to the total hemoglobin together by using the characteristic parameters AC/DC corresponding to the at least six detection light signals, and record the process as performing one HbA1C detection on the user. Thus, the electronic device can also record the total detection times of HbA1C detection on the user for a plurality of times, and count the detection times that the ratio of HbA1C to total hemoglobin calculated by HbA1C detection on the user exceeds a preset threshold value, so as to push HbA1C detection results with different severity degrees to the user based on the two times.

Next, taking the first electronic device as an example, the electronic device will be described in detail based on the total detection times and the detection times that the proportion of HbA1C to total hemoglobin exceeds a preset threshold, and the HbA1C detection results corresponding to different severity are pushed to the user.

In a possible embodiment, the first electronic device repeatedly collects the detection light signal through the PPG module multiple times, so as to calculate multiple times to obtain the proportion of HbA1C of the user to total hemoglobin. In addition, the first electronic device records and obtains the total detection times of HbA1C detection of the user in the process of calculating the ratio of HbA1C to total hemoglobin for a plurality of times.

Then, when the first electronic device records that the total detection times of HbA1C detection of the user is greater than or equal to a first preset times (for example, 15 times, 12 times, 20 times or other times), the first electronic device further counts the first detection times of the calculated ratio of HbA1C of the user to total hemoglobin in the current multi-time HbA1C detection of the user, which is greater than or equal to a preset threshold (for example, a value of 6.2, 6.3, 6.4, 6.5 or 6.6, etc.). And, if the counted first detection times are greater than or equal to the second preset times (for example, 3 times, 4 times, 5 times, 6 times or 7 times), the first electronic device determines to push the first detection result indicating that the user may have diabetes to the user. Alternatively, in the case where the counted first number of detections is greater than a third preset number of times (e.g., 8 times, 9 times, 10 times, or another number of times greater than 7), the first electronic device determines to push a second detection result to the user indicating that the user is confirmed to have diabetes.

It should be noted that, in the embodiment of the present application, the first preset times are greater than the second preset times, and the first preset times are also greater than the third preset times. Further, the first detection result indicates that the user may have diabetes only, and the second detection result indicates that the user is confirmed to have diabetes, i.e., the severity corresponding to the second detection result is greater than the severity corresponding to the first detection result. In this way, the first electronic device detects HbA1C of the user for multiple times by using the PPG module, and based on the calculated ratio of HbA1C of the user to total hemoglobin of HbA1C detected by each time and the comparison of the calculated ratio of HbA1C to total hemoglobin with the preset threshold, the times that the ratio of HbA1C to total hemoglobin is greater than or equal to the preset threshold are counted, and finally HbA1C detection results corresponding to different severity degrees are pushed to the user according to the times. Thereby, accuracy and validity of the result of HbA1C detection of the user can be ensured.

It should be noted that, in this embodiment of the present application, the first electronic device may further set an effective value (such as other specific values of 4.0, 4.2, 4.5, etc.) about the proportion of HbA1C to total hemoglobin, so that in the process of recording the total detection times of detecting HbA1C by the user by the first electronic device in a certain detection, if the proportion of HbA1C calculated by the first electronic device to total hemoglobin by the user is smaller than the effective value, the first electronic device does not count the HbA1C detected by the user into the total detection times, and the proportion of HbA1C calculated by the user to total hemoglobin is discarded, so as not to be used as a reference for finally determining to output the detection result to the user. Therefore, when the first electronic device combines the HbA1C detection for a plurality of times to combine the total detection times and the first detection times, and determines to push the HbA1C detection result to the user, the calculation result which is obviously lower than the effective value is prevented from providing error reference for determining the HbA1C detection result, so that the accuracy of the HbA1C detection result pushed to the user is effectively improved.

In this embodiment of the present application, the preset threshold, the first preset times, the second preset times, and the third preset times may be experience values added in advance by a developer or a user of the electronic device. It should be appreciated that the above-described preset thresholds, first preset times, second preset times and third preset times may of course be other values than those listed herein, based on different design needs of the actual application. That is, the data acquisition method provided in the embodiment of the present application is not limited to specific values of the preset threshold, the first preset times, the second preset times, and the third preset times.

In this embodiment of the present application, when the first electronic device records the total number of times of HbA1C detection performed on the user, the following data may also be counted: calculating the ratio of HbA1C of the user to total hemoglobin, wherein the calculated second detection times are smaller than the minimum value of the preset threshold interval, the calculated third detection times are when the ratio of HbA1C of the user to total hemoglobin is in the preset threshold interval, and the calculated ratio of HbA1C of the user to total hemoglobin is larger than the fourth detection times of the maximum value of the preset threshold interval. Wherein the sum of the second detection times, the third detection times and the fourth detection times is equal to the total detection times.

In this embodiment, the preset threshold interval may be an experience value added in advance by a developer or a user of the electronic device. For example, the preset threshold interval may be: (4.9, 9.1), (5.1,6.2), (5.3, 6.2), (5.5, 6.3), (5.7, 6.4) or (5.7, 6.6) and the like. It should be appreciated that the specific size of the predetermined threshold interval may of course be other values than those listed herein, based on the different design needs of the actual application. That is, the data acquisition method provided in the embodiment of the present application is not limited to a specific value range of the preset threshold interval.

Taking the example of confirming that the HbA1C level of the user is 5.7 as the pre-diabetes corresponding threshold value and confirming that the user has 6.4 as the diabetes corresponding threshold value, the first electronic device frames the threshold value intervals of 5.7 and 6.4, and the first electronic device can determine that the detection result of HbA1C detection of the user is normal when the calculated ratio of HbA1C of the user to total hemoglobin is smaller than the minimum value of 5.7 of the threshold value interval (5.7,6.4). When the calculated proportion of HbA1C of the user to total hemoglobin is in the threshold interval (5.7,6.4), the first electronic device can determine that the detection result of HbA1C detection of the user is that the HbA1C level of the user is in the pre-diabetes. Or when the calculated proportion of HbA1C of the user to the total hemoglobin is larger than the maximum value of the threshold interval (5.7,6.4), the first electronic device determines that the detection result of HbA1C of the user is: the user may have diabetes and recommend to go to the hospital for an immediate examination.

In addition, in the embodiment of the present application, the first electronic device calculates the second detection times, the third detection times and the fourth detection times, so as to actually determine, according to a voting result of a certain detection result in the multiple HbA1C detections performed on the user, to push the HbA1C detection result corresponding to different severity degrees such as "normal", "pre-diabetes" or "having diabetes" to the user according to a majority rule.

That is, in the embodiment of the present application, when the second detection number counted by the first electronic device is greater than the third detection number and the second detection number is also greater than the fourth detection number, the first electronic device determines to push to the user a third detection result indicating that HbA1C detection is normal for the user. For example, the total number of detections recorded by the first electronic device is 15 times, the second number of detections counted by the first electronic device is 8 times, the third number of detections is 4 times, and the fourth number of detections is only 3 times, where the second number of detections is greater than the third number of detections and the second number of detections is greater than the fourth number of detections, then the first electronic device determines that the current result of performing HbA1C detection on the user 15 times is: hbA1C level is normal, thereby pushing a third detection result indicating that HbA1C level is normal to the user.

Or when the third detection times counted by the first electronic device are larger than the second detection times and the third detection times are also larger than the fourth detection times, the first electronic device determines to push a fourth detection result indicating that the HbA1C level of the user is in the pre-diabetes state to the user. In this case, since the third detection result is the same as the first detection result, the user is normal, and thus the severity corresponding to the fourth detection result is greater than the severity corresponding to the third detection result. For example, the total detection times recorded by the first electronic device is 15 times, the second detection times counted by the first electronic device is 4 times, the third detection times are 8 times, the fourth detection times are 3 times, the third detection times are larger than the second detection times and the third detection times are also larger than the fourth detection times, and then the first electronic device determines that the current 15 HbA1C detection results of the user are that the HbA1C level of the user is in the pre-diabetes stage, so that the fourth detection result indicating that the user may be in the pre-diabetes stage is pushed to the user, and the recent opinion removal detection or sugar intake reduction is suggested.

Or, if the fourth detection times counted by the first electronic device are greater than the second detection times and the fourth detection times are also greater than the third detection times, the first electronic device determines to push a fifth detection result indicating that the user has diabetes to the user. Wherein the fourth test result indicates that the user is pre-diabetes, such that the fifth test result corresponds to a greater severity than the fourth test result. For example, the total detection times recorded by the first electronic device is 15 times, the second detection times counted by the first electronic device is 3 times, the third detection times are 4 times, the fourth detection times are 8 times, the fourth detection times are greater than the second detection times and the fourth detection times are also greater than the third detection times, the first electronic device determines that the user has diabetes as a result of performing HbA1C detection on the user for 15 times, and pushes a fifth detection result to the user, wherein the fifth detection result indicates that the user may have diabetes, and the user is suggested to go to the hospital for examination immediately.

In the embodiment of the application, the first electronic device detects HbA1C of the user for a plurality of times, and determines to finally push a detection result representing normal, pre-diabetes or diabetes of the user to the user according to the ratio of HbA1C of the user to total hemoglobin calculated in the process of detecting HbA1C of each time, so that the purpose of flexibly and accurately screening diabetes or controlling diabetes for a long term based on detecting HbA1C of the user is achieved.

It should be noted that, in the embodiment of the present application, the second electronic device specifically adopts the same manner as the first electronic device, so as to implement pushing of the detection result to the user based on the total detection times and the detection times when the proportion of HbA1C to total hemoglobin exceeds the preset threshold. And will not be described in detail here.

In some embodiments, an electronic device is provided in the embodiments of the present application, where the electronic device may be the first electronic device or the second electronic device in the foregoing embodiments. The electronic device also has a function of implementing the data acquisition method described in each of the above embodiments. The functions can be realized by hardware, and can also be realized by executing corresponding software by hardware. The hardware or software includes one or more modules corresponding to the functions described above.

In some embodiments, embodiments of the present application provide an electronic device, including: a processor and a memory; the memory is used for storing computer program code, the computer program code comprising computer executable instructions which, when the electronic device is running, cause the electronic device to perform the data acquisition method as described in the various embodiments above.

In some embodiments, embodiments of the present application provide an electronic device, including: a processor; the processor is configured to couple to the memory and execute the data acquisition method according to the above embodiments according to the instructions after reading the instructions in the memory.

In some embodiments, embodiments of the present application provide a computer-readable storage medium comprising computer instructions that, when executed on an electronic device, cause the electronic device to perform a wallpaper display method as described above.

In some embodiments, embodiments of the present application provide a computer program product that, when run on an electronic device, causes the electronic device to perform the data acquisition method as described in the various embodiments above.

In some embodiments, embodiments of the present application provide a computer program product containing instructions that, when run on a computer, enable the computer to perform the data acquisition method described in the various embodiments above.

In some embodiments, an apparatus is provided in an embodiment of the present application, where the apparatus includes a processor configured to support an electronic device to implement the functions of the data acquisition method described in the foregoing embodiments. In one possible design, the apparatus further includes a memory for storing program instructions and data necessary for the electronic device.

It will be apparent to those skilled in the art from this description that, for convenience and brevity of description, only the above-described division of the functional modules is illustrated, and in practical application, the above-described functional allocation may be performed by different functional modules according to needs, i.e. the internal structure of the apparatus is divided into different functional modules to perform all or part of the functions described above.

In the several embodiments provided in this application, it should be understood that the disclosed apparatus and method may be implemented in other ways. For example, the apparatus embodiments described above are merely illustrative, e.g., the division of the modules or units is merely a logical functional division, and there may be additional divisions when actually implemented, e.g., multiple units or components may be combined or integrated into another apparatus, or some features may be omitted, or not performed. Alternatively, the coupling or direct coupling or communication connection shown or discussed with each other may be an indirect coupling or communication connection via some interfaces, devices or units, which may be in electrical, mechanical or other form. The units described as separate parts may or may not be physically separate, and the parts displayed as units may be one physical unit or a plurality of physical units, may be located in one place, or may be distributed in a plurality of different places. Some or all of the units may be selected according to actual needs to achieve the purpose of the solution of this embodiment.

In addition, each functional unit in each embodiment of the present application may be integrated in one processing unit, or each unit may exist alone physically, or two or more units may be integrated in one unit. The integrated units 22 may be implemented in hardware or in software functional units. The integrated units, if implemented in the form of software functional units and sold or used as stand-alone products, may be stored in a readable storage medium. Based on such understanding, the technical solution of the embodiments of the present application may be essentially or a part contributing to the prior art or all or part of the technical solution may be embodied in the form of a software product stored in a storage medium, including several instructions for causing a device (may be a single-chip microcomputer, a chip or the like) or a processor (processor) to perform all or part of the steps of the methods described in the embodiments of the present application. And the aforementioned storage medium includes: a U-disk, a removable hard disk, a Read Only Memory (ROM), a random access memory (random access memory, RAM), a magnetic disk, or an optical disk, or other various media capable of storing program codes.

The foregoing is merely a specific embodiment of the present application, but the scope of the present application is not limited thereto, and any changes or substitutions within the technical scope of the present disclosure should be covered in the scope of the present application. Therefore, the protection scope of the present application shall be subject to the protection scope of the claims.

Claims

1. The data acquisition method is characterized by being applied to first electronic equipment, wherein the first electronic equipment comprises a photoplethysmography (PPG) module; the method comprises the following steps:

the first electronic device collects at least six detection light signals through the PPG module; each detection light signal comprises a light signal reflected from a user after the light irradiates the user, and the wavelengths of the light used for detecting different detection light signals are different from each other;

the first electronic equipment acquires characteristic parameters corresponding to each detection light signal; the characteristic parameter is the proportion between the alternating current component and the direct current component corresponding to the detection light signal;

and the first electronic equipment calculates and obtains the proportion of the glycosylated hemoglobin HbA1C of the user to the total hemoglobin based on at least six characteristic parameters.

2. The method of claim 1, wherein the first electronic device obtaining the characteristic parameter corresponding to each detected optical signal comprises:

the first electronic device performs photoelectric conversion on each detection light signal to obtain a PPG signal corresponding to each detection light signal; each of the PPG signals includes an ac component and a dc component;

the first electronic device calculates a ratio between the alternating current component and the direct current component for each PPG signal to obtain a characteristic parameter corresponding to each detection light signal.

3. The method of claim 1, wherein the first electronic device calculates a ratio of glycosylated hemoglobin HbA1C of the user to total hemoglobin based on at least six of the characteristic parameters, comprising:

the first electronic device determines respective concentrations of six haemoglobins of the user based on at least six of the characteristic parameters;

the first electronic device calculates a ratio of a sum of the concentrations of two HbA1C of the six kinds of hemoglobin to the sum of the concentrations of the six kinds of hemoglobin to obtain a ratio of the two HbA1C of the user to total hemoglobin.

4. The method according to claim 1, wherein after the first electronic device calculates a ratio of glycosylated hemoglobin HbA1C of the user to total hemoglobin based on at least six of the characteristic parameters, the method further comprises:

the first electronic equipment records the total detection times of HbA1C detection of the user; calculating the proportion of HbA1C to total hemoglobin by using the detection light signal, wherein HbA1C is detected once for the user;

under the condition that the total detection times are larger than or equal to a first preset times, the first electronic equipment counts the first detection times that the proportion of HbA1C in the multiple times of HbA1C detection is larger than or equal to a preset threshold value;

when the first detection times are greater than or equal to second preset times, the first electronic equipment pushes a first detection result to the user; the first preset times are larger than the second preset times; or,

when the first detection times are greater than or equal to a third preset times, the first electronic equipment pushes a second detection result to the user; the first preset times are larger than the third preset times, and the third preset times are larger than the second preset times; the severity degree corresponding to the second detection result is greater than the severity degree corresponding to the first detection result.

5. The method of claim 1, wherein after the first electronic device records a total number of detections of HbA1C for the user, the method further comprises:

the first electronic equipment records the total detection times of HbA1C detection of the user;

counting a second detection frequency of a minimum value of which the proportion of HbA1C to total hemoglobin is smaller than a preset threshold value interval, a third detection frequency of which the proportion of HbA1C to total hemoglobin is in the preset threshold value interval and a fourth detection frequency of which the proportion of HbA1C to total hemoglobin is larger than the maximum value of the preset threshold value interval by the first electronic device; the sum of the second detection times, the third detection times and the fourth detection times is equal to the total detection times;

when the second detection times are larger than the third detection times and the second detection times are larger than the fourth detection times, the first electronic equipment pushes a third detection result to the user;

when the third detection times are larger than the second detection times and the third detection times are larger than the fourth detection times, the first electronic equipment pushes a fourth detection result to the user; the severity degree corresponding to the fourth detection result is greater than the severity degree corresponding to the third detection result;

When the fourth detection times are larger than the second detection times and the fourth detection times are larger than the third detection times, the first electronic device pushes a fifth detection result to the user; the severity degree corresponding to the fifth detection result is greater than the severity degree corresponding to the fourth detection result.

6. The method according to any one of claims 1 to 5, wherein the first electronic device collects at least six detection light signals through the PPG module, comprising:

and the first electronic equipment acquires at least six detection light signals for the user through the PPG module under the condition that the user does not have body movement according to preset indication information.

7. The data acquisition method is characterized by being applied to first electronic equipment, wherein the first electronic equipment comprises a PPG module, and the first electronic equipment is in communication connection with second electronic equipment; the method comprises the following steps:

The first electronic device sends PPG signals corresponding to the at least six detection light signals to the second electronic device;

the first electronic device displays the HbA1C proportion of the total hemoglobin of the user returned by the second electronic device.

8. The data acquisition method is characterized by being applied to second electronic equipment, wherein the second electronic equipment is in communication connection with first electronic equipment, and the first electronic equipment comprises a PPG module; the method comprises the following steps:

the second electronic device receives at least six PPG signals sent by the first electronic device; the wavelengths of the detection optical signals corresponding to the at least six PPG signals are different from each other;

the second electronic equipment acquires characteristic parameters corresponding to each PPG signal; the characteristic parameter is the proportion between alternating current component and direct current component in the PPG signal;

and the second electronic equipment calculates the ratio of HbA1C of the user to total hemoglobin based on at least six characteristic parameters, and returns the ratio of HbA1C of the user to total hemoglobin to the first electronic equipment.

9. An electronic device, the electronic device comprising:

The PPG module is used for collecting at least six detection light signals; the PPG module comprises a light emitter and a light receiver; the light transmitter is used for transmitting at least six light rays, and the light receiver is used for collecting detection light signals reflected from a user after each light ray irradiates the user; the wavelengths of the different light rays are different from each other;

the processor is electrically connected with the PPG module;

the processor is used for acquiring characteristic parameters corresponding to each detection light signal and calculating and obtaining the proportion of glycosylated hemoglobin HbA1C of the user to total hemoglobin based on at least six characteristic parameters; the characteristic parameter is the proportion between the alternating current component and the direct current component corresponding to the detection light signal.

10. The electronic device of claim 9, wherein the number of light emitters is a plurality;

a plurality of the optical transmitters respectively transmit optical signals to users; the light emission periods of the different light emitters are different from each other;

the light receiver receives a detection light signal reflected back from the user during a light emission period of each of the light emitters.

11. The electronic device of claim 9, wherein the number of optical receivers is a plurality;

The optical transmitter is used for transmitting optical signals with at least six wavelengths to the user;

the plurality of light receivers respectively receive detection light signals reflected back from the user; the wavelengths of the detection optical signals received by different optical receivers are different from each other.

12. The electronic device according to any one of claims 9 to 11, characterized in that a wavelength of light of the detection light signal is detected to be greater than or equal to 500nm and less than or equal to 1100nm, and/or the wavelength is greater than or equal to 1600nm and less than or equal to 1850nm.

13. The electronic device of any one of claims 9 to 11, wherein the electronic device further comprises:

a body within which the processor is located;

a connecting member connected to the main body for binding the main body to the skin of the user;

the PPG module is arranged on the main body, or the PPG module is arranged on the connecting component.

14. An electronic device is characterized in that the electronic device is a first electronic device or a second electronic device; the electronic device includes: a processor and a memory, the processor coupled with the memory; the memory is used for storing computer program codes; the computer program code comprising computer instructions which, when executed by the processor, cause the electronic device to perform the method of any of claims 1-8.

15. A computer readable storage medium comprising computer instructions which, when run on an electronic device, cause the electronic device to perform the method of any of claims 1-8.

16. A computer program product comprising computer instructions which, when run on an electronic device, cause the electronic device to perform the method of any of claims 1-8.