Wearable device, blood pressure measuring method and related device

Abstract

The invention discloses wearable equipment, a blood pressure measuring method and a related device, and belongs to the field of data processing. The method comprises the following steps: acquiring a pressure data set acquired by at least one sensor array, and determining an effective pressure sensing unit from absolute pressure sensing units included in the at least one sensor array based on the pressure data set acquired by the at least one sensor array, determining arterial pressure data corresponding to at least one arterial blood vessel on the basis of pressure data collected by the effective pressure sensing units in the at least one sensor array, and determining the blood pressure of the user on the basis of the arterial pressure data corresponding to the at least one arterial blood vessel. As the arterial pressure data can represent the pressure actually borne by the corresponding arterial blood vessel in the blood pressure measurement process, the accuracy of the blood pressure result determined based on the arterial pressure data corresponding to the arterial blood vessel is high.

Description

Technical Field

[0001] This application relates to the field of data processing, and particularly to a wearable device, a blood pressure measurement method and related devices. Background Art

[0002] Blood pressure is an important indicator for health monitoring and can reflect the health status of the human body. Human blood pressure refers to the lateral pressure exerted by the pulsating blood flow in the blood vessels on the blood vessel wall, that is, the pressure perpendicular to the blood vessel wall. Among them, the peak value of the pressure is the systolic blood pressure, also known as high blood pressure, and the valley value of the pressure is the diastolic blood pressure, also known as low blood pressure. Currently, the human blood pressure is usually measured by an upper arm type or wrist blood pressure monitor. Taking the upper arm blood pressure monitor as an example, the user wears the cuff at the position level with the heart, then inflates and pressurizes the airbag in the cuff to exceed the systolic blood pressure to block the blood flow in the upper arm, and then gradually deflates and decompresses to collect the pressure data inside the airbag during the deflation process. This pressure data can represent the actual pressure borne by the arterial blood vessels during the pressurization process. This pressure data includes the pulse wave signal (also known as dynamic pressure) of the arterial blood vessels and the corresponding external pressurization signal (also known as static pressure), and then the blood pressure of the user is determined based on this dynamic pressure and static pressure.

[0003] Among them, the width of the airbag has a decisive impact on the accuracy of blood pressure measurement. For a wrist blood pressure monitor, the width of the airbag must reach at least 60 millimeters to ensure that the collected pressure data accurately represents the actual pressure borne by the arterial blood vessels during the pressurization process, so as to ensure the accuracy of the measurement data. However, with the progress and development of technology, more and more wearable devices are equipped with blood pressure measurement functions. And due to the pursuit of portability and compactness of wearable devices, the width of the wearable strap of the wearable device is usually relatively narrow (usually about 30 millimeters), which results in a relatively narrow width of the airbag inside the wearable strap (also known as a narrow airbag). When inflating this narrow airbag, the cross-section of the narrow airbag is close to a circle, resulting in compression loss, making the collected pressure data higher than the actual pressure borne by the arterial blood vessels, leading to a higher calculated blood pressure. That is to say, when measuring blood pressure through a narrow airbag, the gas pressure inside the narrow airbag cannot accurately represent the actual pressure borne by the arterial blood vessels during the pressurization process, resulting in inaccurate blood pressure measurement results finally. Summary of the Invention

[0004] This application provides a wearable device, a blood pressure measurement method and related devices, which can solve the problem of inaccurate blood pressure measurement results in the related art. The technical solutions are as follows:

[0005] In a first aspect, a wearable device is provided. The wearable device includes a wearing strip, an inflation assembly, at least one sensor array, and a processor. The inflation assembly includes an air pump and an airbag. The airbag is located inside the wearing strip and is distributed along the length direction of the wearing strip. The air pump is configured to inflate and pressurize the airbag and then deflate and decompress it during the process of the user measuring blood pressure. The at least one sensor array is located on a side of the airbag away from the wearing strip. When the user wears the wearable device, the at least one sensor array corresponds to the position of at least one artery of the user. The sensor array includes a plurality of absolute pressure sensing units. The size of the absolute pressure sensing unit in a first direction is not greater than the diameter of the corresponding artery. The first direction is perpendicular to the flow direction of the corresponding artery. The sensor array is configured to collect the pressure borne by the corresponding artery during the process of the user measuring blood pressure. The processor is configured to determine the blood pressure of the user based on the pressure data set collected by the at least one sensor array.

[0006] Since the sensor array includes a plurality of absolute pressure sensing units, the pressure measured by the absolute pressure sensing unit is relative to the vacuum pressure. Therefore, the pressure measured by the absolute pressure sensing unit is not affected by the change of atmospheric pressure and can accurately reflect the real pressure situation. Since the at least one sensor array is located on a side of the airbag away from the wearing strip, in this case, when the user wears the wearable device, the sensor array can contact the user's skin and collect the pressure data at the contact position. The pressure data is relative to the vacuum pressure. Compared with the method of collecting the pressure data inside the airbag, the pressure data collected in this application can accurately represent the actual pressure borne by the corresponding contact position, thus ensuring the accuracy of the finally determined blood pressure of the user.

[0007] Optionally, the column direction of the sensor array is the same as the flow direction of the corresponding artery. The plurality of absolute pressure sensing units are arranged in an M-row and N-column manner, and the distance between two adjacent absolute pressure sensing units in the same row is not greater than the diameter of the corresponding artery. M is an integer greater than or equal to 1, and N is an integer greater than 1.

[0008] For any arterial blood vessel corresponding to a sensor array, since the absolute pressure sensing unit directly above the arterial blood vessel has the smallest distance from the arterial blood vessel, the signal intensity of the pulse wave directly above the arterial blood vessel is the largest, and the signal intensity of the pulse wave gradually attenuates from directly above the arterial blood vessel to both sides. If the size of the absolute pressure sensing unit in the first direction is larger than the diameter of the corresponding arterial blood vessel, it will result in a small difference in the pressure data collected by the absolute pressure sensing units in the sensor array, making it difficult to determine the arterial pressure data corresponding to the arterial blood vessel based on the pressure data collected by the absolute pressure sensing unit. In this application, however, the size of the absolute pressure sensing unit in the first direction is not larger than the diameter of the corresponding arterial blood vessel, which can make the fidelity of the signal details of the pressure data set collected by the sensor array relatively high, facilitating the determination of the arterial pressure data corresponding to the arterial blood vessel and making the finally determined blood pressure more accurate.

[0009] Optionally, the absolute pressure sensing units in adjacent rows among the multiple absolute pressure sensing units are arranged staggeredly.

[0010] For any arterial blood vessel corresponding to a sensor array, the absolute pressure sensing unit directly above the arterial blood vessel collects the pulse wave with the largest signal intensity. However, there is usually a certain distance between two adjacent absolute pressure sensing units in the same row, and the row direction of the sensor array is perpendicular to the flow direction of the corresponding arterial blood vessel. Therefore, the arterial blood vessel may be located within the distance between two adjacent absolute pressure sensing units in a certain row of the sensor array. In this case, these two adjacent absolute pressure sensing units cannot be directly above the blood vessel, and thus cannot collect the pulse wave signal with the optimal signal intensity. However, since the absolute pressure sensing units in adjacent rows among the multiple absolute pressure sensing units included in the sensor array are arranged staggeredly, in this way, it can effectively ensure that the sensor array can collect the pulse wave signal with the optimal signal intensity, thereby ensuring the accuracy of the finally determined user blood pressure.

[0011] Optionally, the at least one sensor array includes a first array and / or a second array. The first array corresponds to the radial artery blood vessel, and the second array corresponds to the ulnar artery blood vessel.

[0012] Optionally, the size of the sensor array in the first direction is more than three times the diameter of the corresponding arterial blood vessel.

[0013] Since the absolute pressure sensing units in adjacent rows among the multiple absolute pressure sensing units included in the sensor array may be staggeredly arranged, or the number of absolute pressure sensing units included in each row of the sensor array is different and / or the spacing between adjacent absolute pressure sensing units in the same row is different. In this case, the sensor array is not a regular rectangle, that is, the sensor array has multiple dimensions in the first direction. At this time, it can be understood that the minimum dimension among the multiple dimensions of the sensor array in the first direction is greater than three times the diameter of the corresponding arterial blood vessel when the dimension of the sensor array in the first direction is greater than three times the diameter of the corresponding arterial blood vessel.

[0014] Optionally, the wearable device further includes a memory for storing a computer program for executing the blood pressure measurement method provided in the following second aspect. The processor is configured to execute the computer program stored in the memory to implement the blood pressure measurement method described in the following second aspect.

[0015] Optionally, the wearable device may further include a communication bus for establishing a connection between the processor and the memory.

[0016] In a second aspect, there is provided a blood pressure measurement method using the wearable device described in the first aspect above. The method includes: acquiring pressure data sets respectively collected by the at least one sensor array, where the pressure data sets are collected by the multiple absolute pressure sensing units included in the corresponding sensor array during the process of inflating and pressurizing or deflating and decompressing the airbag; determining effective pressure sensing units from the absolute pressure sensing units included in the at least one sensor array based on the pressure data sets collected by the at least one sensor array, where the pressure data collected by the effective pressure sensing units can effectively characterize the pulsation condition of the user's arterial blood vessels; determining arterial pressure data corresponding to the at least one arterial blood vessel respectively based on the pressure data collected by the effective pressure sensing units in the at least one sensor array, where the arterial pressure data characterizes the pressure actually borne by the corresponding arterial blood vessel during the blood pressure measurement process; and determining the user's blood pressure based on the arterial pressure data corresponding to the at least one arterial blood vessel.

[0017] Considering that the size of the arterial blood vessel is relatively small compared to the size of the sensor array, in this application, an absolute pressure sensing unit (also referred to as an effective pressure sensing unit) that can effectively characterize the pulsation of the user's arterial blood vessel is determined from the multiple absolute pressure sensing units included in the sensor array. Then, based on the pressure data collected by the effective pressure sensing unit, the arterial pressure data corresponding to the arterial blood vessel is determined, thereby ensuring the accuracy of the finally determined arterial pressure data. Also, since the arterial pressure data can characterize the actual pressure borne by the corresponding arterial blood vessel during blood pressure measurement, the accuracy of the blood pressure result determined based on the arterial pressure data corresponding to the arterial blood vessel is relatively high. In addition, in the case of determining the arterial pressure data corresponding to at least two arterial blood vessels, this application can also determine the user's blood pressure based on the arterial pressure data corresponding to the at least two arterial blood vessels, thereby further improving the accuracy of blood pressure measurement.

[0018] During the process of the user measuring blood pressure, the airbag in the wearable device can be inflated and pressurized at a target rate and then deflated and depressurized, or inflated and pressurized and then deflated and depressurized at a target rate, or inflated and pressurized at a target rate and then deflated and depressurized at a target rate again. That is to say, there is at least one process in which the pressure changes at a target rate during the processes of inflation and pressurization and deflation and depressurization of the airbag in the wearable device, and the at least one sensor array can collect a pressure data set during the process in which the airbag pressure changes at a target rate.

[0019] Among them, the target rate is set in advance. The upper limit of the value range of the target rate is related to the sampling frequency of the sensor array and the user's heart rate. The higher the sampling frequency of the sensor array and / or the higher the user's heart rate, the higher the upper limit of the value range of the target rate. In other words, the sampling frequency of the sensor array and the user's heart rate are proportional to the upper limit of the value range of the target rate.

[0020] Optionally, the above pressure data set includes multiple groups of pressure data collected by the multiple absolute pressure sensing units included in the corresponding sensor array, and each group of pressure data includes pressure data at multiple moments.

[0021] In other words, for any sensor array, the pressure data set collected by the sensor array includes multiple groups of pressure data. The multiple groups of pressure data correspond one-to-one to the multiple absolute pressure sensing units included in the sensor array, and each group of pressure data is the pressure data respectively collected by the corresponding absolute pressure sensing unit at multiple moments.

[0022] Optionally, the wearable device determines multiple groups of candidate pressure sensing units from the absolute pressure sensing units included in the first sensor array based on the first pressure data set, and determines the effective pressure sensing unit in the first sensor array from the multiple groups of candidate pressure sensing units.

[0023] Among them, the above first pressure data set is the pressure data set collected by the first sensor array, and the first sensor array is any one of at least one sensor array included in the wearable device. The multiple groups of candidate pressure sensing units correspond to multiple first moments one by one. The positions of the candidate pressure sensing units in the same group are continuous, and the difference between the pressure data collected at the corresponding first moment is within the pressure fluctuation range. The first moment is one of the multiple moments, and the first artery is the artery corresponding to the first sensor array.

[0024] Optionally, the wearable device stores the coordinates of each absolute pressure sensing unit in the first sensor array. In this case, the continuity of the positions of the candidate pressure sensing units in the same group means that the abscissas and / or ordinates of the candidate pressure sensing units in the same group are continuous. In addition, if the difference between the pressure data collected by the candidate pressure sensing units in the same group at the same moment is within the pressure fluctuation range, it indicates that the difference in the pressure data collected by the candidate pressure sensing units in the same group is relatively small.

[0025] In practical applications, the pressure at the position where the airbag contacts the skin is much greater than the pressure at the position where the airbag does not contact the skin, and the difference in the pressure data at the position where the airbag contacts the skin is relatively small. Therefore, if the positions of the candidate pressure sensing units in the same group are continuous and the difference in the pressure data collected is relatively small, it indicates that the group of candidate pressure sensing units may be located at the position where the airbag contacts the skin. In this case, the pressure data collected by the group of candidate pressure sensing units is valid, so as to ensure the accuracy and reliability of the subsequent determined user blood pressure.

[0026] Optionally, the implementation process of determining the effective pressure sensing units in the first sensor array from the multiple groups of candidate pressure sensing units includes: determining at least one first sensing unit from the multiple groups of candidate pressure sensing units, and based on the first pressure data set, determining at least one second sensing unit from the absolute pressure sensing units included in the first sensor array. The positions of the at least one second sensing unit are continuous, and the intersection of the at least one first sensing unit and the at least one second sensing unit is used as the effective pressure sensing units in the first sensor array.

[0027] Based on the dynamic pressure collected by each absolute pressure sensing unit in the first sensor array, determine the maximum peak-to-peak value corresponding to each absolute pressure sensing unit in the first sensor array to obtain multiple maximum peak-to-peak values. Based on the multiple maximum peak-to-peak values, determine at least one second candidate sensing unit. The positions of the at least one second candidate sensing unit are continuous, and the difference between the corresponding maximum peak-to-peak values is within the peak-to-peak value fluctuation range. Based on the at least one second candidate sensing unit, determine at least one second sensing unit.

[0028] For any arterial blood vessel corresponding to a sensor array, the signal intensity of the pulse wave directly above the arterial blood vessel is the greatest, and the signal intensity of the pulse wave gradually attenuates from directly above the arterial blood vessel to both sides. Therefore, if the positions of at least one second candidate sensing unit are continuous and the corresponding maximum peak-to-peak differences are small, it indicates that the at least one second candidate sensing unit may be located around the arterial blood vessel. In this case, the pressure data collected by the at least one second candidate sensing unit is valid, or rather, the data collected by this group of candidate pressure sensing units is pressure data that can characterize the pulsation of the arterial blood vessel. Only in this way can the accuracy and reliability of the subsequent determined user blood pressure be ensured.

[0029] In addition, since the first sensing unit is located at the position where the airbag contacts the skin, and the second sensing unit is located around the arterial blood vessel, and the effective pressure sensing units in the first sensor array are the intersection of the at least one first sensing unit and the at least one second sensing unit, therefore, the effective pressure sensing unit is an absolute pressure sensing unit located at the position where the airbag contacts the skin and around the arterial blood vessel. In this case, the arterial pressure data determined based on the pressure data collected by the effective pressure sensing unit in the subsequent steps is accurate and valid, thereby further ensuring the accuracy and reliability of the subsequent determined user blood pressure.

[0030] Optionally, based on the pressure data collected by the effective pressure sensing units in the second sensor array, determine the arterial pressure data corresponding to the second arterial blood vessel. The second sensor array is any one of the at least one sensor array, and the second arterial blood vessel is the arterial blood vessel corresponding to the second sensor array.

[0031] There are various implementation manners for determining the arterial pressure data corresponding to the second arterial blood vessel based on the pressure data collected by the effective pressure sensing units in the second sensor array. Next, two of the implementation manners will be introduced.

[0032] For the first implementation manner, the pressure data is the pressure data collected by the effective pressure sensing units at multiple moments respectively, and the arterial pressure data is the arterial pressure data corresponding to multiple moments respectively. In this case, for any one of the multiple moments, take the average value or the maximum value of the pressure data collected by the effective pressure sensing unit at this moment as the arterial pressure data corresponding to this moment. In the same way, the arterial pressure data corresponding to multiple times can be obtained.

[0033] For the second implementation manner, determine the pressure data collected by one effective pressure sensing unit in the second sensor array as the arterial pressure data corresponding to the second arterial blood vessel.

[0034] Optionally, based on the pressure data collected by the effective pressure sensing units in the second sensor array, determine the maximum peak-to-peak value corresponding to each effective pressure sensing unit to obtain at least one maximum peak-to-peak value, and use the pressure data collected by the effective pressure sensing unit corresponding to the largest maximum peak-to-peak value among the at least one maximum peak-to-peak value as the arterial pressure data corresponding to the second arterial blood vessel.

[0035] In practical applications, before determining the arterial pressure data corresponding to the at least one arterial blood vessel based on the pressure data collected by the effective pressure sensing units in the at least one sensor array, the wearable device may further determine the tissue attenuation coefficient corresponding to at least one effective pressure sensing unit in the target sensor array. The tissue attenuation coefficient indicates the attenuation of the pulse wave of the target arterial blood vessel by the human tissue. The target arterial blood vessel is the arterial blood vessel corresponding to the target sensor array, and the target sensor array is any one of the at least one sensor array. Based on the tissue attenuation coefficient corresponding to the at least one effective pressure sensing unit, correct the pressure data collected by the at least one effective pressure sensing unit.

[0036] That is to say, this application takes into account the attenuation of the pulse wave of the target arterial blood vessel by the human tissue, and corrects the pressure data collected by the effective pressure sensing unit by calculating the tissue attenuation coefficient, so that the corrected pressure data collected by the effective pressure sensing unit can accurately reflect the pulsation of the arterial blood vessel, thereby ensuring the accuracy and reliability of the finally determined user blood pressure.

[0037] Determine the distance between the at least one effective pressure sensing unit and the target arterial blood vessel, determine the unit attenuation coefficient, where the unit attenuation coefficient refers to the attenuation of the pulse wave of the target arterial blood vessel by the human tissue with a unit thickness, and based on the unit attenuation coefficient and the distance between the at least one effective pressure sensing unit and the target arterial blood vessel, determine the tissue attenuation coefficient corresponding to the at least one effective pressure sensing unit respectively.

[0038] Optionally, determine the distance between the first effective pressure sensing unit and the target arterial blood vessel, determine the unit attenuation coefficient, where the first effective pressure sensing unit is any one of the at least one effective pressure sensing unit, and use the value obtained by multiplying the unit attenuation coefficient by the distance between the first effective pressure sensing unit and the target arterial blood vessel as the tissue attenuation coefficient corresponding to the first effective pressure sensing unit. Processing each first effective pressure sensing unit in the at least one first effective pressure sensing unit in the same way can determine the tissue attenuation coefficient corresponding to the at least one effective pressure sensing unit respectively.

[0039] Based on the pressure data collected by the effective pressure sensing units in the target sensor array, determine the primary pressure sensing unit and the secondary pressure sensing unit in the effective sensing units of the target sensor array. The primary pressure sensing unit is the absolute pressure sensing unit with the maximum signal intensity among the effective sensing units of the target sensor array, and the signal intensity of the secondary pressure sensing unit is less than that of the primary pressure sensing unit. Based on the primary pressure sensing unit and the secondary pressure sensing unit in the effective sensing units, determine the distance between the first effective pressure sensing unit and the target arterial vessel, and determine the unit attenuation coefficient.

[0040] Based on the pressure data collected by the effective pressure sensing units in the target sensor array, determine the maximum peak-to-peak value corresponding to each effective pressure sensing unit to obtain at least one maximum peak-to-peak value. The effective pressure sensing unit corresponding to the largest maximum peak-to-peak value among the at least one maximum peak-to-peak values is used as the primary pressure sensing unit. The effective pressure sensing unit corresponding to the maximum peak-to-peak value that is not equal to the largest maximum peak-to-peak value and the difference is greater than the maximum peak-to-peak value difference threshold among the at least one maximum peak-to-peak values is used as the secondary pressure sensing unit.

[0041] When the first effective pressure sensing unit is the primary pressure sensing unit, the method for determining the distance between the first effective pressure sensing unit and the target arterial vessel and determining the unit attenuation coefficient is different from when the first effective pressure sensing unit is the secondary pressure sensing unit. The following will be introduced separately.

[0042] When the first effective pressure sensing unit is the primary pressure sensing unit, based on the pressure data collected by the first effective pressure sensing unit, the pressure data collected by the target secondary pressure sensing unit, and the distance between the first effective pressure sensing unit and the target secondary pressure sensing unit in the first direction, determine the distance between the first effective pressure sensing unit and the target arterial vessel, and the distance between the target secondary pressure sensing unit and the target arterial vessel. The target secondary pressure sensing unit is any secondary pressure sensing unit in the target sensor array. Based on the pressure data collected by the first effective pressure sensing unit, the pressure data collected by the target secondary pressure sensing unit, the distance between the first effective pressure sensing unit and the target arterial vessel, and the distance between the target secondary pressure sensing unit and the target arterial vessel, determine the unit attenuation coefficient.

[0043] When the first effective pressure sensing unit is a secondary pressure sensing unit, based on the pressure data collected by the first effective pressure sensing unit, the pressure data collected by the primary pressure sensing unit, and the distance between the first effective pressure sensing unit and the primary pressure sensing unit in the first direction, determine the distance between the first effective pressure sensing unit and the target arterial blood vessel, and the distance between the primary pressure sensing unit and the target arterial blood vessel. Based on the pressure data collected by the first effective pressure sensing unit, the pressure data collected by the primary pressure sensing unit, the distance between the first effective pressure sensing unit and the target arterial blood vessel, and the distance between the primary pressure sensing unit and the target arterial blood vessel, determine the unit attenuation coefficient.

[0044] For any one of the at least one effective pressure sensing units, subtract the tissue attenuation coefficient corresponding to the effective pressure sensing unit from the pressure data of the effective pressure sensing unit among multiple absolute pressures to obtain multiple corrected static pressures, add the tissue attenuation coefficient corresponding to the effective pressure sensing unit to the pressure data of the effective pressure sensing unit among multiple dynamic pressures to obtain multiple corrected dynamic pressures, and use the multiple corrected static pressures and the multiple corrected dynamic pressures as the first pressure data of the effective pressure sensing unit to achieve the correction of the pressure data collected by the effective pressure sensing unit. Process each of the at least one effective pressure sensing units in the same manner to achieve the correction of the pressure data collected by each of the at least one effective pressure sensing units.

[0045] For the pressure applied by the airbag (i.e., the static pressure), the pressure applied by the airbag first reaches the absolute pressure sensing unit and then passes through the attenuation of human tissue to reach the target arterial blood vessel. The static pressure borne by the target arterial blood vessel is smaller than the static pressure collected by the absolute pressure sensing unit. Therefore, subtracting the tissue attenuation coefficient corresponding to the effective pressure sensing unit from each of the multiple static pressures can achieve the correction of the static pressure.

[0046] For the pulse wave generated by the target arterial blood vessel, the pulse wave passes through the attenuation of human tissue after being emitted from the target arterial blood vessel to reach the absolute pressure sensing unit. The dynamic pressure generated by the target arterial blood vessel is larger than the dynamic pressure collected by the absolute pressure sensing unit. Therefore, adding the tissue attenuation coefficient corresponding to the effective pressure sensing unit to each of the multiple dynamic pressures can achieve the correction of the dynamic pressure.

[0047] When the number of the at least one arterial blood vessel is one, the wearable device can directly determine the user's blood pressure based on the arterial pressure data corresponding to the arterial blood vessel according to relevant algorithms.

[0048] When the number of the at least one arterial vessel is at least two, that is, the at least one arterial vessel includes at least two arterial vessels, in this case, there are various ways to determine the user's blood pressure for the arterial pressure data corresponding to the at least two arterial vessels. Next, two of the implementation ways will be introduced.

[0049] The first implementation way: The arterial pressure data includes static pressures corresponding to multiple moments and dynamic pressures corresponding to each static pressure. The static pressure represents the pressure applied by the airbag, and the dynamic pressure represents the pulsation condition of the corresponding arterial vessel under the compression of the static pressure. The at least two arterial vessels respectively correspond to different weights. In this case, among the dynamic pressures of the arterial pressure data respectively corresponding to the at least two arterial vessels, the dynamic pressures corresponding to the same moment are multiplied by their respective corresponding weights and then added together to obtain multiple superimposed dynamic pressures. Among the static pressures of the arterial pressure data respectively corresponding to the at least two arterial vessels, the static pressures corresponding to the same moment are multiplied by their respective corresponding weights and then added together to obtain multiple superimposed static pressures. The multiple superimposed dynamic pressures and the multiple superimposed static pressures are used as the superimposed arterial pressure data. Based on the superimposed arterial pressure data, the user's blood pressure is determined according to the relevant algorithm.

[0050] The second implementation way: The arterial pressure data includes multiple static pressures and dynamic pressures corresponding to each static pressure. The static pressure represents the pressure applied by the airbag, and the dynamic pressure represents the pulsation condition of the corresponding arterial vessel under the compression of the static pressure. In this case, the wearable device can superimpose the dynamic pressures in the arterial pressure data respectively corresponding to the at least two arterial vessels according to the static pressures in the arterial pressure data respectively corresponding to the at least two arterial vessels to obtain the superimposed arterial pressure data. Based on the superimposed arterial pressure data, the user's blood pressure is determined according to the relevant algorithm.

[0051] When the at least two arterial vessels are the ulnar artery and the radial artery, due to reasons such as the different depths of the ulnar artery and the radial artery in human tissues, the irregularity of the human wrist bones, and the influence of the user's wearing method, the pulse wave signal in the airbag obtained by the superposition of the pulse pulsations of the ulnar artery and the radial artery in the time domain cannot accurately represent the pulsation condition of the user's arterial vessels during the pressurization process, with a large error, which will further result in poor accuracy of the blood pressure result. This application can superimpose the arterial pressure data respectively corresponding to the at least two arterial vessels in the static pressure dimension, thus fundamentally avoiding the problem of large errors in the pulse wave signal caused by simple superposition in the time domain, and further improving the accuracy of blood pressure measurement.

[0052] In a third aspect, a blood pressure measurement device is provided, which is included in the wearable device described in the first aspect above. The blood pressure measurement device has the function of implementing the behavior of the blood pressure measurement method in the second aspect above. The blood pressure measurement device includes at least one module, and the at least one module is used to implement the blood pressure measurement method provided in the second aspect above.

[0053] In a fourth aspect, a computer-readable storage medium is provided. Instructions are stored in the storage medium. When the instructions run on a computer, the computer is caused to execute the steps of the blood pressure measurement method described in the second aspect above.

[0054] In a fifth aspect, a computer program product including instructions is provided. When the instructions run on a computer, the computer is caused to execute the steps of the blood pressure measurement method described in the first aspect above. Or rather, a computer program is provided. When the computer program runs on a computer, the computer is caused to execute the steps of the blood pressure measurement method described in the second aspect above.

[0055] The technical effects obtained in the third, fourth, and fifth aspects above are similar to the technical effects obtained by the corresponding technical means in the first and second aspects, and will not be elaborated here. Description of the Drawings

[0056] Figure 1 is a schematic diagram of a pressure distribution provided by an embodiment of the present application;

[0057] Figure 2 is a schematic diagram of a wrist blood pressure monitor provided by an embodiment of the present application;

[0058] Figure 3 is a schematic diagram of a wearable device provided by an embodiment of the present application;

[0059] Figure 4 is a schematic diagram of a sensor array provided by an embodiment of the present application;

[0060] Figure 5 is a schematic diagram of another sensor array provided by an embodiment of the present application;

[0061] Figure 6 is a schematic diagram of a sensor array a provided by an embodiment of the present application;

[0062] Figure 7 is a schematic diagram of another sensor array a provided by an embodiment of the present application;

[0063] Figure 8 is a schematic diagram of an absolute pressure sensing unit provided by an embodiment of the present application;

[0064] Figure 9It is a schematic diagram of another absolute pressure sensing unit provided by an embodiment of the present application;

[0065] Figure 10 It is a schematic diagram of an arrangement mode of a sensor array provided by an embodiment of the present application;

[0066] Figure 11 It is a schematic diagram of the distance between two adjacent absolute pressure sensing units provided by an embodiment of the present application;

[0067] Figure 12 It is a schematic diagram of another arrangement mode of a sensor array provided by an embodiment of the present application;

[0068] Figure 13 It is a schematic diagram of the flow direction of an arterial blood vessel provided by an embodiment of the present application;

[0069] Figure 14 It is a schematic diagram of a first array and a second array provided by an embodiment of the present application;

[0070] Figure 15 It is a schematic diagram of the structure of another wearable device provided by an embodiment of the present application;

[0071] Figure 16 It is a flowchart of a blood pressure measurement method provided by an embodiment of the present application;

[0072] Figure 17 It is a schematic diagram of a first pressure data provided by an embodiment of the present application;

[0073] Figure 18 It is a schematic diagram of a pulse wave signal of an arterial blood vessel provided by an embodiment of the present application;

[0074] Figure 19 It is a schematic diagram of a main pressure sensing unit and a secondary pressure sensing unit provided by an embodiment of the present application;

[0075] Figure 20 It is a schematic diagram of superimposed arterial pressure data provided by an embodiment of the present application;

[0076] Figure 21 It is a schematic diagram of the structure of a blood pressure measurement device provided by an embodiment of the present application. Detailed implementation manners

[0077] To make the objectives, technical solutions, and advantages of the embodiments of the present application clearer, the following will further describe the embodiments of the present application in detail with reference to the accompanying drawings.

[0078] For the convenience of understanding, before explaining the blood pressure measurement method provided by the embodiments of the present application in detail, the application scenarios involved in the embodiments of the present application will be introduced first.

[0079] Human blood pressure refers to the lateral pressure exerted by the pulsating blood flow in the blood vessels on the vessel wall, that is, the pressure perpendicular to the vessel wall. Among them, the peak value of the pressure is the systolic blood pressure, also known as the high pressure, and the trough value of the pressure is the diastolic blood pressure, also known as the low pressure. Blood pressure is an important indicator for health monitoring and can be used to evaluate the health status of the human body and the changes in the condition of critically ill patients. For example, the level of blood pressure can reflect whether multiple indicators such as heart function, blood flow, blood volume, and vasomotor function are normal. When the blood pressure shows abnormal increase or decrease, it indicates that the above indicators may be abnormal. A sudden decrease in blood pressure may be caused by insufficient blood volume, abnormal vasodilation, or severe impairment of heart function. In addition, if the blood pressure remains at a high or low level for a long time, it may also cause relatively large damage to blood vessels and multiple organs throughout the body. Therefore, it is very important to measure blood pressure regularly, which can detect chronic diseases such as hypertension early, take timely measures for intervention to avoid the deterioration of the condition, and at the same time can also detect the situation of low blood pressure in time to prevent accidents. For patients with hypertension, regular blood pressure measurement also helps doctors adjust the treatment plan according to the measurement results, so as to achieve better treatment effects.

[0080] Currently, human blood pressure is usually measured by an upper-arm or wrist blood pressure monitor. Taking the upper-arm blood pressure monitor as an example, the user wears the cuff at a position level with the heart, then inflates and pressurizes the airbag in the cuff to exceed the systolic blood pressure to block the blood flow in the upper arm, and then gradually deflates and decompresses to collect the pressure data inside the airbag during the deflation process. This pressure data can represent the actual pressure borne by the arterial blood vessels during the pressurization process. This pressure data includes the pulse wave signal of the artery (also known as the dynamic pressure) and the corresponding external pressurization signal (also known as the static pressure), and then the blood pressure of the user is determined based on this dynamic pressure and static pressure.

[0081] Among them, the width of the airbag has a decisive impact on the accuracy of blood pressure measurement. For a wrist blood pressure monitor, the width of the airbag must reach at least the standard width (60 mm) to ensure that the collected pressure data accurately represents the actual pressure borne by the arterial blood vessels during the pressurization process, thus ensuring the accuracy of the measurement data. However, with the progress and development of technology, more and more wearable devices are equipped with blood pressure measurement functions. And due to the pursuit of portability and compactness of wearable devices, the width of the wearable strap is usually relatively narrow (usually about 30 mm), which leads to a relatively narrow width of the airbag inside the wearable strap (also known as a narrow airbag / narrow-width airbag). When inflating this narrow airbag, the cross-section of the narrow airbag is close to a circle, resulting in compression loss, making the collected pressure data higher than the actual pressure borne by the arterial blood vessels. And, please refer to Figure 1 , from Figure 1It is not difficult to see that the pressure distribution at the position where the narrow airbag contacts the skin is not uniform compared with that of the standard-width airbag. In this case, the pressure at the position where the narrow airbag contacts the skin is quite different from the gas pressure inside the airbag, resulting in a relatively high blood pressure calculated finally. That is to say, when measuring blood pressure with the narrow airbag, the gas pressure inside the narrow airbag cannot accurately represent the actual pressure borne by the arterial blood vessels during the pressurization process, thus leading to inaccurate blood pressure measurement results finally.

[0082] Moreover, please refer to Figure 2 , for a wrist blood pressure monitor, the pulse wave signal included in the pressure data inside the airbag collected by the wrist blood pressure monitor is actually the combined action of the pulse beats of the ulnar artery and the radial artery on the airbag. For the convenience of description, the pulse wave signal included in the pressure data inside the airbag will be referred to as the pulse wave signal inside the airbag hereinafter. That is to say, please refer to Figure 2 , the pulse wave signal inside the airbag is actually the superposition of the pulse wave signal of the ulnar artery and the pulse wave signal of the radial artery in the time domain. Under ideal conditions, the waveforms of the pulse wave signal of the ulnar artery and the pulse wave signal of the radial artery should be close, and the mean arterial pressure (MAP) corresponding to the ulnar artery and the radial artery respectively should also be close to the mean arterial pressure of the user. However, due to the different depths of the ulnar artery and the radial artery in human tissues, the irregularity of the wrist bones of the human body, and the influence of the user's wearing method, etc., the pressures exerted by the narrow airbag on the ulnar artery and the radial artery at the same moment are different. In this case, the pulse wave signal inside the airbag obtained by the superposition of the pulse beats of the ulnar artery and the radial artery in the time domain cannot accurately represent the pulsation condition of the user's arterial blood vessels during the pressurization process, with a large error. This problem will further result in poor accuracy of the blood pressure result.

[0083] Based on the above problems, an embodiment of the present application provides a wearable device. The wearable device includes a wearable strip, an inflation component, at least one sensor array, and a processor. The inflation component includes an air pump and an airbag. Since the sensor array includes a plurality of absolute pressure sensing units, and the pressure measured by the absolute pressure sensing unit is relative to the vacuum pressure, therefore, the pressure measured by the absolute pressure sensing unit is not affected by the change of atmospheric pressure and can accurately reflect the real pressure situation. Since the at least one sensor array is located on the side of the airbag away from the wearable strip, in this case, when the user wears the wearable device, the sensor array can contact the user's skin and collect the pressure data at the contact position. The pressure data is relative to the vacuum pressure. Compared with the method of collecting the pressure data inside the airbag, the pressure data collected in the embodiment of the present application can accurately represent the actual pressure borne by the corresponding contact position, thus ensuring the accuracy of the finally determined user blood pressure. And, since the embodiment of the present application takes into account that the size of the artery is relatively small compared to the size of the sensor array, therefore, the embodiment of the present application can determine, from the plurality of absolute pressure sensing units included in the sensor array, the absolute pressure sensing unit (also called the effective pressure sensing unit) that can effectively represent the pulsation of the user's artery, and then based on the pressure data collected by the effective pressure sensing unit, determine the artery pressure data corresponding to the artery, thus ensuring the accuracy of the finally determined artery pressure data. Also, since the artery pressure data can represent the actual pressure borne by the corresponding artery during blood pressure measurement, the accuracy of the blood pressure result determined based on the artery pressure data corresponding to the artery is relatively high. In addition, in the case of determining the artery pressure data corresponding to at least two arteries, the embodiment of the present application can also determine the user's blood pressure based on the artery pressure data corresponding to the at least two arteries, thereby further improving the accuracy of blood pressure measurement.

[0084] Please refer to Figure 3 , Figure 3 FIG. is a schematic diagram of a wearable device provided by an embodiment of the present application. The wearable device includes a wearable strip 01, an air pump included in the inflation component ( Figure 3 not shown in the figure) and an airbag 02, at least one sensor array 03 ( Figure 3 the at least one sensor array is schematically represented by two sensor arrays in the figure) and a processor ( Figure 3 not shown in the figure).

[0085] The airbag 02 is located on the inner side of the wearable strip 01, and the airbag 02 is distributed along the length direction of the wearable strip 01. The air pump is used to inflate and pressurize the airbag 02 and then deflate and decompress it during the process of the user measuring blood pressure. The at least one sensor array 03 is located on the side of the airbag 02 away from the wearable strip 01. When the user wears the wearable device, the at least one sensor array corresponds to the position of at least one arterial blood vessel of the user.

[0086] Exemplarily, please refer to Figure 4 , if the at least one sensor array includes sensor array 03a and sensor array 03b, sensor array 03a and sensor array 03b are located on the side of the airbag 02 away from the wearable strip 01, and, please refer to Figure 5 , when the user wears the wearable device, the sensor array 03a corresponds to the position of the arterial blood vessel 1 of the user, and the sensor array 03b corresponds to the position of the arterial blood vessel 2 of the user.

[0087] It should be noted that in the case where the wearable strip 01 and the airbag 02 are two independent components, the airbag 02 is located on the inner side of the wearable strip 01. Of course, in actual applications, the wearable strip 01 and the airbag 02 can also be an integral body, the airbag 02 is located inside the wearable strip, and when the user wears the wearable device, the at least one sensor array 03 is located on the side of the wearable strip 01 that can contact the user's skin.

[0088] In some embodiments, for any one sensor array 03 in the at least one sensor array 03, the sensor array 03 includes a plurality of absolute pressure sensing units, the size of the absolute pressure sensing unit in the first direction is not greater than the diameter of the corresponding arterial blood vessel, and the first direction is perpendicular to the flow direction of the corresponding arterial blood vessel. The sensor array 03 is used to collect the pressure borne by the corresponding arterial blood vessel during the process of the user measuring blood pressure, and the processor is used to determine the user's blood pressure based on the pressure data set collected by the at least one sensor array 03.

[0089] Exemplarily, please refer to Figure 6 , if the at least one sensor array 03 includes sensor array a, the sensor array a includes a plurality of absolute pressure sensing units ( Figure 6 schematically represented by 7 absolute pressure sensing units to represent the plurality of absolute pressure sensing units), please refer to Figure 6 and Figure 7 , the size of the absolute pressure sensing unit in the first direction is not greater than the diameter of the corresponding arterial blood vessel, and the first direction is perpendicular to the flow direction of the corresponding arterial blood vessel. The sensor array a is used to collect the pressure borne by the corresponding arterial blood vessel during the process of the user measuring blood pressure.

[0090] In practical applications, for any arterial blood vessel corresponding to a sensor array, since the absolute pressure sensing unit directly above the arterial blood vessel has the smallest distance from the arterial blood vessel, the signal intensity of the pulse wave directly above the arterial blood vessel is the largest, and the signal intensity of the pulse wave gradually attenuates from directly above the arterial blood vessel to both sides. Please refer to Figure 8 , if the size of the absolute pressure sensing unit in the first direction is greater than the diameter of the corresponding arterial blood vessel, it will result in a small difference in the pressure data collected by the absolute pressure sensing units in the sensor array, making it difficult to determine the arterial pressure data corresponding to the arterial blood vessel based on the pressure data collected by the absolute pressure sensing unit. In the embodiments of the present application, please refer to Figure 9 , the size of the absolute pressure sensing unit in the first direction is not greater than the diameter of the corresponding arterial blood vessel, which can make the fidelity of the signal details of the pressure data set collected by the sensor array relatively high, facilitating the determination of the arterial pressure data corresponding to the arterial blood vessel and making the finally determined blood pressure more accurate.

[0091] In practical applications, the diameter of the standard arterial blood vessel in the human body is approximately 2 millimeters to 3 millimeters. In this case, the diameter of the above-mentioned arterial blood vessel can be any value between 2 millimeters and 3 millimeters. For example, the diameter of the arterial blood vessel can be 3 millimeters. Moreover, in different situations, it can be adjusted according to different requirements, and the embodiments of the present application do not limit this.

[0092] In some embodiments, for any sensor array 03, the column direction of the sensor array 03 is the same as the flow direction of the corresponding arterial blood vessel. The multiple absolute pressure sensing units are arranged in an M-row and N-column manner, and the distance between two adjacent absolute pressure sensing units in the same row is not greater than the diameter of the corresponding arterial blood vessel. M is an integer greater than or equal to 1, and N is an integer greater than 1.

[0093] It should be noted that the arrangement of the multiple absolute pressure sensing units included in the sensor array 03 is related to the width of the airbag of the wearable device, the position and diameter of the arterial blood vessel, and the size of the absolute pressure sensing unit. Those skilled in the art can adjust the arrangement of the multiple absolute pressure sensing units according to actual needs. For example, when the size of the absolute pressure sensing unit is 1 millimeter and the diameter of the arterial blood vessel is 3 millimeters, the multiple absolute pressure sensing units can be arranged in a 1-row and 24-column manner, or in a 4-row and 9-column manner, or in a 4-row and 6-column manner. The embodiments of the present application do not limit this.

[0094] Exemplarily, please refer to Figure 10, if the at least one sensor array 03 includes sensor array a, the column direction of the sensor array a is the same as the flow direction of the corresponding arterial blood vessel, and the seven absolute pressure sensing units of the sensor array a are arranged in a 1-row and 7-column manner. Please refer to Figure 11 , the distance between two adjacent absolute pressure sensing units in the same row in the sensor array a is not greater than the diameter of the corresponding arterial blood vessel.

[0095] Optionally, for any sensor array 03, among the multiple absolute pressure sensing units included in the sensor array 03, the absolute pressure sensing units in adjacent rows are arranged staggeredly.

[0096] Exemplarily, if the at least one sensor array 03 includes sensor array b, please refer to Figure 12 , among the multiple absolute pressure sensing units included in the sensor array b, the absolute pressure sensing units in adjacent rows are arranged staggeredly.

[0097] Based on the above description, for the arterial blood vessel corresponding to any sensor array 03, the intensity of the pulse wave signal collected by the absolute pressure sensing unit located directly above the arterial blood vessel is the largest. However, there is usually a certain distance between two adjacent absolute pressure sensing units in the same row, and the row direction of the sensor array 03 is perpendicular to the flow direction of the corresponding arterial blood vessel. Therefore, please refer to Figure 13 , the arterial blood vessel may be located within the distance between two adjacent absolute pressure sensing units in the X-th row of the sensor array 03. In this case, the two adjacent absolute pressure sensing units cannot be located directly above the blood vessel, and thus cannot collect the pulse wave signal with the optimal signal intensity. However, since the absolute pressure sensing units in adjacent rows among the multiple absolute pressure sensing units included in the sensor array 03 are arranged staggeredly, there is an absolute pressure sensing unit located directly above the arterial blood vessel in the row above and / or below the X-th row. In this way, it can be effectively ensured that the sensor array 03 can collect the pulse wave signal with the optimal signal intensity, thereby ensuring the accuracy of the finally determined user blood pressure.

[0098] In some embodiments, please refer to Figure 14 , the at least one sensor array 03 includes a first array and / or a second array, the first array corresponds to the radial artery blood vessel, and the second array corresponds to the ulnar artery blood vessel.

[0099] Optionally, for any sensor array 03, the size of the sensor array 03 in the first direction is greater than three times the diameter of the corresponding arterial blood vessel. In other words, the sensor array 03 includes at least three absolute pressure sensing units in the first direction.

[0100] It should be noted that, since the absolute pressure sensing units in adjacent rows among the multiple absolute pressure sensing units included in the sensor array may be staggeredly arranged, or the number of absolute pressure sensing units included in each row of the sensor array is different and / or the spacing between adjacent absolute pressure sensing units in the same row is different, in this case, the sensor array is not a regular rectangle, that is, the sensor array has multiple dimensions in the first direction. At this time, the fact that the dimension of the sensor array 03 in the first direction is greater than three times the diameter of the corresponding arterial blood vessel can be understood as that the smallest dimension among the multiple dimensions of the sensor array in the first direction is greater than three times the diameter of the corresponding arterial blood vessel.

[0101] In some embodiments, the above wearable device can obtain the pressure data sets respectively collected by the at least one sensor array 03, and then, based on the pressure data sets collected by the at least one sensor array 03, determine the effective pressure sensing units from the absolute pressure sensing units included in the at least one sensor array 03. Based on the pressure data collected by the effective pressure sensing units in the at least one sensor array 03, determine the arterial pressure data corresponding to the at least one arterial blood vessel respectively, and based on the arterial pressure data corresponding to the at least one arterial blood vessel, determine the blood pressure of the user.

[0102] It should be noted that, in the case where the wearable device includes at least two sensor arrays, the arrangement manners of the at least two sensor arrays, the number of absolute pressure sensing units in the sensor array, and the spacing of the absolute pressure sensing units may be the same or different, and the embodiments of the present application do not make any limitation thereto.

[0103] The wearable device provided by the embodiments of the present application can be worn on any part of the user where blood pressure measurement can be performed, such as the wrist, leg, upper arm, etc., and the embodiments of the present application do not make any limitation thereto. In the case where the wearable device is worn on the user's wrist for blood pressure measurement, the wearable device can be an electronic device capable of performing blood pressure measurement, such as a watch, a bracelet, a wrist electronic blood pressure monitor, etc. At this time, the wearable strip can also be called a wristband, and the embodiments of the present application do not make any limitation thereto.

[0104] Those skilled in the art should understand that the above wearable device is only an example, and other existing or future wearable devices that can be applied to the embodiments of the present application should also be included within the protection scope of the embodiments of the present application and are hereby incorporated herein by reference.

[0105] It should be noted that the application scenarios and wearable devices described in the embodiments of the present application are for more clearly illustrating the technical solutions of the embodiments of the present application, and do not constitute a limitation on the technical solutions provided by the embodiments of the present application. Those of ordinary skill in the art can know that with the evolution of technology and the emergence of new application scenarios, the technical solutions provided by the embodiments of the present application are also applicable to similar technical problems.

[0106] Please refer to Figure 15 , Figure 15 , which is a schematic structural diagram of another wearable device shown according to the embodiments of the present application. This wearable device may be the above-mentioned wearable device. The wearable device includes at least one processor 1501, a communication bus 1502, a memory 1503, and at least one communication interface 1504.

[0107] The processor 1501 may be a general-purpose central processing unit (CPU), a network processor (NP), a microprocessor, or may be one or more integrated circuits for implementing the solution of the present application. For example, an application-specific integrated circuit (ASIC), a programmable logic device (PLD), or a combination thereof. The above PLD may be a complex programmable logic device (CPLD), a field-programmable gate array (FPGA), a generic array logic (GAL), or any combination thereof.

[0108] The communication bus 1502 is used to transmit information between the above components. The communication bus 1502 may be divided into an address bus, a data bus, a control bus, etc. For the sake of simplicity of representation, only a thick line is shown in the figure, but it does not mean that there is only one bus or one type of bus.

[0109] The memory 1503 can be a read-only memory (ROM), a random access memory (RAM), an electrically erasable programmable read-only memory (EEPROM), an optical disc (including a compact disc read-only memory (CD-ROM), a compressed optical disc, a laser disc, a digital versatile disc, a Blu-ray disc, etc.), a magnetic disk storage medium, or other magnetic storage devices, or any other medium that can be used to carry or store the desired program code in the form of instructions or data structures and can be accessed by a computer, but is not limited thereto. The memory 1503 can exist independently and be connected to the processor 1501 through the communication bus 1502. The memory 1503 can also be integrated with the processor 1501.

[0110] In some embodiments, the wearable device may further include at least one communication interface 1504. The communication interface 1504 uses any transceiver-like device for communicating with other devices or communication networks. The communication interface 1504 includes a wired communication interface and may also include a wireless communication interface. Among them, the wired communication interface can be, for example, an Ethernet interface. The Ethernet interface can be an optical interface, an electrical interface, or a combination thereof. The wireless communication interface can be a wireless local area networks (WLAN) interface, a cellular network communication interface, or a combination thereof, etc.

[0111] As an embodiment, the wearable device can include multiple processors, such as Figure 15 the processor 1501 and the processor 1505 shown in. Each of these processors can be a single-core processor or a multi-core processor. Here, the processor can refer to one or more devices, circuits, and / or processing cores for processing data (such as computer program instructions).

[0112] In a specific implementation, as an embodiment, the wearable device may further include an output device 1506 and an input device 1507. The output device 1506 communicates with the processor 1501 and can display information in various ways. For example, the output device 1506 may be a liquid crystal display (LCD), a light emitting diode (LED) display device, a cathode ray tube (CRT) display device, or a projector, etc. The input device 1507 communicates with the processor 1501 and can receive user input in various ways. For example, the input device 1507 may be a touch screen device or a sensing device, etc.

[0113] In some embodiments, the memory 1503 is used to store the program code 1510 for executing the solution of this application, and the processor 1501 can execute the program code 1510 stored in the memory 1503. The program code 1510 may include one or more software modules, and the wearable device can implement the blood pressure measurement method provided in the embodiments below Figure 16 through the processor 1501 and the program code 1510 in the memory 1503.

[0114] Figure 16 is a flowchart of a blood pressure measurement method provided by an embodiment of this application. This method is applied to the above-mentioned wearable device. Please refer to Figure 16 and the method includes the following steps.

[0115] Step 1601: Obtain pressure data sets respectively collected by at least one sensor array included in the wearable device. The pressure data sets are collected by a plurality of absolute pressure sensing units included in the corresponding sensor array during the process of inflating and pressurizing or deflating and depressurizing the airbag.

[0116] During the process of the user measuring blood pressure, the airbag in the wearable device can inflate and pressurize at a target rate and then deflate and depressurize, or inflate and pressurize and then deflate and depressurize at a target rate, or inflate and pressurize at a target rate and then deflate and depressurize at a target rate again. That is to say, there is at least one process in which the pressure changes at a target rate during the processes of inflating and pressurizing and deflating and depressurizing the airbag in the wearable device, and the at least one sensor array can collect the pressure data set during the process in which the airbag pressure changes at a target rate.

[0117] Wherein, the target rate is set in advance. The upper limit of the value range of the target rate is related to the sampling frequency of the sensor array and the user's heart rate. The higher the sampling frequency of the sensor array, and / or the higher the user's heart rate, the higher the upper limit of the value range of the target rate. In other words, the sampling frequency of the sensor array and the user's heart rate are directly proportional to the upper limit of the value range of the target rate.

[0118] Step 1602: Based on the pressure data set collected by at least one sensor array, determine effective pressure sensing units from the absolute pressure sensing units included in the at least one sensor array. The pressure data collected by the effective pressure sensing units can effectively characterize the pulsation of the user's arterial blood vessels.

[0119] In some embodiments, the above-mentioned pressure data set includes multiple groups of pressure data collected by multiple absolute pressure sensing units included in the corresponding sensor array, and each group of pressure data includes pressure data at multiple moments.

[0120] In other words, for any one sensor array, the pressure data set collected by the sensor array includes multiple groups of pressure data, and the multiple groups of pressure data correspond one-to-one with the multiple absolute pressure sensing units included in the sensor array. Each group of pressure data is the pressure data respectively collected by the corresponding absolute pressure sensing unit at multiple moments.

[0121] In a possible implementation, the wearable device determines multiple groups of candidate pressure sensing units from the absolute pressure sensing units included in the first sensor array based on the first pressure data set, and determines the effective pressure sensing units in the first sensor array from the multiple groups of candidate pressure sensing units.

[0122] Wherein, the above-mentioned first pressure data set is the pressure data set collected by the first sensor array, and the first sensor array is any one of the at least one sensor array included in the wearable device. The multiple groups of candidate pressure sensing units correspond one-to-one with multiple first moments. The positions of the candidate pressure sensing units in the same group are continuous, and the difference between the pressure data collected at the corresponding first moment is within the pressure fluctuation range. The first moment is one of the multiple moments, and the first arterial blood vessel is the arterial blood vessel corresponding to the first sensor array.

[0123] In some embodiments, the wearable device stores the coordinates of each absolute pressure sensing unit in the first sensor array. In this case, the continuity of the positions of the candidate pressure sensing units in the same group means that the abscissas and / or ordinates of the candidate pressure sensing units in the same group are continuous. In addition, if the difference between the pressure data collected by the candidate pressure sensing units in the same group at the same moment is within the pressure fluctuation range, it indicates that the pressure data collected by the candidate pressure sensing units in the same group have small differences.

[0124] It should be noted that the pressure fluctuation range is set in advance. For example, the pressure fluctuation range can be set from -5 mmHg to 5 mmHg, and in different situations, it can also be adjusted according to different requirements.

[0125] In practical applications, the pressure at the position where the airbag contacts the skin is much greater than the pressure at the position where the airbag does not contact the skin. Moreover, the difference in pressure data at the position where the airbag contacts the skin is relatively small. Therefore, if the positions of a group of candidate pressure sensing units are continuous and the difference in the collected pressure data is small, it indicates that this group of candidate pressure sensing units may be located at the position where the airbag contacts the skin. In this case, the pressure data collected by this group of candidate pressure sensing units is valid. Only in this way can the accuracy and reliability of the subsequent determined user blood pressure be ensured.

[0126] The implementation process of determining multiple groups of candidate pressure sensing units from the absolute pressure sensing units included in the first sensor array based on the first pressure dataset includes: determining multiple first moments from multiple moments. For any one of the multiple first moments, based on multiple first pressure data and the positions of the multiple absolute pressure sensing units included in the first sensor array, a group of candidate pressure sensing units corresponding to the first moment is determined from the absolute pressure sensing units included in the first sensor array. The multiple first pressure data correspond one-to-one to the multiple absolute pressure sensing units included in the first sensor array, and the first pressure data is the pressure data collected by the corresponding absolute pressure sensing unit at the first moment. Processing each of the multiple first moments in the same way can determine the candidate pressure sensing units corresponding to the multiple first moments respectively.

[0127] It should be noted that the pressure data collected by the absolute pressure sensing unit at the first moment includes static pressure and dynamic pressure. The static pressure represents the pressure exerted by the airbag at the first moment, and the dynamic pressure represents the pulsation of the corresponding arterial blood vessel under the compression of the static pressure. In this case, the first pressure data can also be the static pressure collected by the corresponding absolute pressure sensing unit at the first moment. In other words, the pressure data (original pressure data) collected by the absolute pressure sensing unit at the first moment consists of the static pressure and dynamic pressure at the first moment. In this case, the first pressure data can be the original pressure data collected at the first moment or the static pressure at the first moment. The embodiments of the present application do not make any limitations in this regard.

[0128] Since the first pressure data set may be collected during the inflation and pressurization process of the airbag or during the deflation and depressurization process of the airbag, if the first pressure data set is collected during the inflation and pressurization process of the airbag, at least one pressure data with the pressure data being the reference pressure value can be determined from the first pressure data set, the earliest moment among the moments corresponding to the at least one pressure data is used as the first starting moment, and the moments among the multiple moments that are later than the first starting moment are used as the multiple first moments. If the first pressure data set is collected during the deflation and depressurization process of the airbag, at least one pressure data with the pressure data being the reference pressure value can be determined from the first pressure data set, the latest moment among the moments corresponding to the at least one pressure data is used as the first starting moment, and the moments among the multiple moments that are earlier than the first starting moment are used as the multiple first moments. Of course, in practical applications, the multiple first moments can also be determined from the multiple moments in other ways. For example, some or all of the multiple moments can be directly used as the multiple first moments, and the embodiments of the present application do not limit this.

[0129] In practical applications, when the pressure exerted by the airbag on the arterial blood vessel is too small or too large, the absolute pressure sensing unit cannot clearly collect the pulse wave data of the arterial blood vessel. Therefore, the reference pressure value is the pressure value at which the absolute pressure sensing unit can clearly collect the pulse wave data of the arterial blood vessel. The reference pressure value is set by technicians based on experience. For example, the reference pressure value can be set to 80 mmHg, and in different situations, it can also be adjusted according to different requirements.

[0130] Since the reference pressure value is the pressure value at which the absolute pressure sensing unit can clearly collect the pulse wave data of the arterial blood vessel, if the pressure data collected by the absolute pressure sensing unit in the first sensor array reaches the reference pressure value, it indicates that the absolute pressure sensing unit closer to the arterial blood vessel in the first sensor array can collect the pulse wave signal. In this case, the accuracy of the determined candidate pressure sensing unit can be ensured.

[0131] Optionally, the implementation process of determining a set of candidate pressure sensing units corresponding to the first moment from the absolute pressure sensing units included in the first sensor array based on multiple first pressure data and the positions of the multiple absolute pressure sensing units included in the first sensor array includes: determining at least one set of first pressure sensing units from the absolute pressure sensing units included in the first sensor array based on the multiple first pressure data and the positions of the multiple absolute pressure sensing units included in the first sensor array, where the positions of the first pressure sensing units in the same set are continuous and the difference between the first pressure data collected is within the pressure fluctuation range; and selecting a set of pressure sensing units from the at least one set of first pressure sensing units as a set of candidate pressure sensing units corresponding to the first moment based on the first pressure data of the at least one set of first pressure sensing units.

[0132] In a possible implementation manner, based on the first pressure data of each set of first pressure sensing units, determine the first average value corresponding to each set of first pressure sensing units respectively to obtain at least one first average value, where the first average value is the average value of the first pressure data of the corresponding set of first pressure sensing units; take the set of first pressure sensing units corresponding to the largest first average value among the at least one first average value as the target pressure sensing unit set; in the target pressure sensing unit set, delete the first pressure sensing units whose first pressure data is less than the first pressure threshold, and use the target pressure sensing unit set after the deletion process as a set of candidate pressure sensing units corresponding to the first moment, where the first pressure threshold is the product of the first average value corresponding to the target pressure sensing unit set and the pressure ratio.

[0133] Among them, the pressure ratio is set in advance. For example, the pressure ratio can be set to 75%. Moreover, in different situations, it can also be adjusted according to different requirements.

[0134] Exemplarily, if there are 48 absolute pressure sensing units in the first sensor array, the 48 absolute pressure sensing units are arranged in a 24-row and 2-column manner, and the 48 are respectively the absolute pressure sensing units 1-24 corresponding to the first column and the absolute pressure sensing units 1-24 corresponding to the second column. Taking the absolute pressure sensing units 1-24 corresponding to the first column as an example, please refer to Figure 17 , Figure 17 as the first pressure data collected by 24 absolute pressure sensing units at moment A among multiple first moments, Figure 17 where the abscissa is the absolute pressure sensing units 1-24 and the ordinate is the first pressure data. It can be easily seen from Figure 17 that the first pressure data of the absolute pressure sensing units 5-16 is greater than the first pressure threshold. Therefore, the absolute pressure sensing units 5-16 are a set of candidate pressure sensing units corresponding to moment a.

[0135] In some embodiments, the process of determining the effective pressure sensing units in the first sensor array from the multiple sets of candidate pressure sensing units includes: determining at least one first sensing unit from the multiple sets of candidate pressure sensing units, determining at least one second sensing unit from the absolute pressure sensing units included in the first sensor array based on the first pressure dataset, where the positions of the at least one second sensing unit are continuous, and taking the intersection of the at least one first sensing unit and the at least one second sensing unit as the effective pressure sensing units in the first sensor array.

[0136] It should be noted that the continuity of the positions of the at least one second sensing unit means that the abscissas and / or ordinates of the at least one second sensing unit are continuous.

[0137] Optionally, each candidate pressure sensing unit in the multiple sets of candidate pressure sensing units, or the intersection of the multiple sets of candidate pressure sensing units, can be taken as the at least one first sensing unit. Of course, in practical applications, the at least one first sensing unit can also be determined by other means, and the embodiments of the present application do not limit this.

[0138] In some embodiments, the first pressure dataset includes the pressure data collected by each absolute pressure sensing unit in the first sensor array, and the pressure data includes static pressure and the dynamic pressure corresponding to the static pressure. The static pressure represents the pressure applied by the airbag, and the dynamic pressure represents the pulsation of the corresponding arterial blood vessel under the compression of the static pressure. In this case, based on the dynamic pressure collected by each absolute pressure sensing unit in the first sensor array, the maximum peak-to-peak value corresponding to each absolute pressure sensing unit in the first sensor array is determined to obtain a plurality of maximum peak-to-peak values. Based on the plurality of maximum peak-to-peak values, at least one second candidate sensing unit is determined, where the positions of the at least one second candidate sensing unit are continuous and the difference between the corresponding maximum peak-to-peak values is within the peak-to-peak fluctuation range. Based on the at least one second candidate sensing unit, at least one second sensing unit is determined.

[0139] Among them, the peak-to-peak fluctuation range is set in advance and can also be adjusted according to different requirements in different situations.

[0140] For any absolute pressure sensing unit in the first sensor array, a plurality of peak-to-peak values of the dynamic pressure of the absolute pressure sensing unit are determined, and the plurality of peak-to-peak values correspond one by one to the plurality of arterial pulsation cycles included in the dynamic pressure. The largest peak-to-peak value among the plurality of peak-to-peak values is taken as the corresponding maximum peak-to-peak value of the absolute pressure sensing unit.

[0141] It should be noted that the dynamic pressure collected by the effective pressure sensing unit is actually the pulse wave signal of the arterial blood vessel. Please refer to Figure 18 ,Figure 18 It is a schematic diagram of a pulse wave signal of an arterial blood vessel. The pulse wave signal includes multiple arterial pulsation cycles. The peak-to-peak value in the dynamic pressure is the difference between the maximum dynamic pressure and the minimum dynamic pressure in one arterial pulsation cycle.

[0142] In some embodiments, the at least one second candidate sensing unit can be directly determined as the at least one second sensing unit. In other embodiments, for the at least one second candidate sensing unit, the second candidate sensing unit with a maximum peak-to-peak value less than the maximum peak-to-peak value threshold can also be deleted. The at least one second candidate sensing unit after the deletion process is used as the at least one second candidate sensing unit. The maximum peak-to-peak value threshold is the product of the average value of the maximum peak-to-peak values corresponding to the at least one second candidate sensing unit and the peak-to-peak ratio.

[0143] Among them, the peak-to-peak ratio is set in advance. For example, the peak-to-peak ratio can be set to 75%. Moreover, in different situations, it can also be adjusted according to different requirements.

[0144] Based on the above description, for the arterial blood vessel corresponding to any one sensor array, the signal intensity of the pulse wave directly above the arterial blood vessel is the largest, and the signal intensity of the pulse wave gradually attenuates from directly above the arterial blood vessel to both sides. Therefore, if the positions of the at least one second candidate sensing unit are continuous and the corresponding maximum peak-to-peak differences are small, it indicates that the at least one second candidate sensing unit may be located around the arterial blood vessel. In this case, the pressure data collected by the at least one second candidate sensing unit is valid, or in other words, the data collected by this group of candidate pressure sensing units is the pressure data that can characterize the pulsation of the arterial blood vessel. Only in this way can the accuracy and reliability of the subsequent determined user blood pressure be ensured.

[0145] In addition, since the first sensing unit is located at the position where the airbag contacts the skin, and the second sensing unit is located around the arterial blood vessel, and the effective pressure sensing units in the first sensor array are the intersection of the at least one first sensing unit and the at least one second sensing unit, therefore, the effective pressure sensing units are the absolute pressure sensing units located at the position where the airbag contacts the skin and around the arterial blood vessel. In this case, the arterial pressure data determined based on the pressure data collected by the effective pressure sensing units in the subsequent steps is accurate and valid, thereby further ensuring the accuracy and reliability of the subsequent determined user blood pressure.

[0146] In summary, the embodiments of the present application can determine the absolute pressure sensing units located at the positions where the airbag contacts the skin based on the pressure data collected by the first sensor array, and can also determine the absolute pressure sensing units located around the arterial blood vessels based on the dynamic pressure collected by the first sensor array, thereby determining the effective pressure sensing units located at the positions where the airbag contacts the skin and around the arterial blood vessels. Of course, in practical applications, if the number of rows of the first sensor array is small, it may not be necessary to determine the absolute pressure sensing units located at the positions where the airbag contacts the skin in the first sensor array. Instead, only based on the dynamic pressure collected by the first sensor array, determine the absolute pressure sensing units located around the arterial blood vessels, and use the absolute pressure sensing units located around the arterial blood vessels as the effective pressure sensing units.

[0147] If the number of rows of the first sensor array is small, it means that the width of the first sensor array should be less than the width of the airbag in the wearable device. In this case, it can be considered that all the absolute pressure sensing units in the first sensor array are located at the positions where the airbag contacts the skin. Therefore, it is possible to directly determine the absolute pressure sensing units located around the arterial blood vessels based on the dynamic pressure collected by the first sensor array, and use the absolute pressure sensing units around the arterial blood vessels as the effective pressure sensing units.

[0148] Step 1603: Based on the pressure data collected by the effective pressure sensing units in at least one sensor array, determine the arterial pressure data corresponding to each of the at least one arterial blood vessel, where the arterial pressure data represents the pressure actually borne by the corresponding arterial blood vessel during blood pressure measurement.

[0149] Based on the pressure data collected by the effective pressure sensing units in the second sensor array, determine the arterial pressure data corresponding to the second arterial blood vessel, where the second sensor array is any one of the at least one sensor array, and the second arterial blood vessel is the arterial blood vessel corresponding to the second sensor array.

[0150] There are various implementation manners for determining the arterial pressure data corresponding to the second arterial blood vessel based on the pressure data collected by the effective pressure sensing units in the second sensor array. Next, two of the implementation manners will be introduced.

[0151] In the first implementation manner, the pressure data are the pressure data collected by the effective pressure sensing units at multiple moments respectively, and the arterial pressure data are the arterial pressure data corresponding to the multiple moments respectively. In this case, for any one of the multiple moments, take the average value or the maximum value of the pressure data collected by the effective pressure sensing unit at this moment as the arterial pressure data corresponding to this moment. In the same way, the arterial pressure data corresponding to multiple times can be obtained.

[0152] In the second implementation manner, the pressure data collected by one effective pressure sensing unit in the second sensor array is determined as the arterial pressure data corresponding to the second arterial blood vessel.

[0153] Optionally, based on the pressure data collected by the effective pressure sensing units in the second sensor array, the maximum peak-to-peak value corresponding to each effective pressure sensing unit is determined to obtain at least one maximum peak-to-peak value, and the pressure data collected by the effective pressure sensing unit corresponding to the largest maximum peak-to-peak value among the at least one maximum peak-to-peak value is used as the arterial pressure data corresponding to the second arterial blood vessel.

[0154] Optionally, the pressure data is the pressure data collected by the effective pressure sensing unit at multiple moments respectively, and the pressure data includes a static pressure and a dynamic pressure corresponding to the static pressure. The static pressure represents the pressure applied by the airbag, and the dynamic pressure represents the pulsation condition of the corresponding arterial blood vessel under the compression of the static pressure. In other words, the pressure data includes a plurality of static pressures and a plurality of dynamic pressures, and the plurality of static pressures, the plurality of dynamic pressures correspond one-to-one to the plurality of moments.

[0155] In this case, the implementation process of determining the maximum peak-to-peak value corresponding to each effective pressure sensing unit based on the pressure data collected by the effective pressure sensing units in the second sensor array includes: for any effective pressure sensing unit in the second sensor array, determining a plurality of peak-to-peak values of the dynamic pressure of the effective pressure sensing unit, and the plurality of peak-to-peak values correspond one-to-one to the plurality of arterial pulsation cycles included in the dynamic pressure, and taking the largest peak-to-peak value among the plurality of peak-to-peak values as the maximum peak-to-peak value corresponding to the effective pressure sensing unit. The effective pressure sensing units in the second sensor array are processed in the same manner to determine the maximum peak-to-peak value corresponding to each effective pressure sensing unit. Of course, in practical applications, the maximum peak-to-peak value corresponding to each effective pressure sensing unit can also be determined by other means, and the embodiments of the present application do not limit this.

[0156] Based on the above description, the wearable device can use the pressure data collected by the effective pressure sensing unit with the largest MAP among the effective pressure sensing units as the arterial pressure data corresponding to the second arterial blood vessel. Of course, in practical applications, the pressure data collected by any effective pressure sensing unit in the second sensor array can also be determined as the arterial pressure data corresponding to the second arterial blood vessel.

[0157] In practical applications, before determining the arterial pressure data corresponding to the at least one arterial blood vessel based on the pressure data collected by the effective pressure sensing units in at least one sensor array, the wearable device may further determine the tissue attenuation coefficient corresponding to at least one effective pressure sensing unit in the target sensor array. The tissue attenuation coefficient indicates the attenuation of the pulse wave of the target arterial blood vessel by the human tissue. The target arterial blood vessel is the arterial blood vessel corresponding to the target sensor array, and the target sensor array is any one of the at least one sensor array. Based on the tissue attenuation coefficient corresponding to the at least one effective pressure sensing unit, the pressure data collected by the at least one effective pressure sensing unit is corrected.

[0158] That is to say, the embodiment of the present application takes into account the attenuation of the pulse wave of the target arterial blood vessel by the human tissue, and corrects the pressure data collected by the effective pressure sensing unit by calculating the tissue attenuation coefficient, so that the corrected pressure data collected by the effective pressure sensing unit can accurately reflect the pulsation of the arterial blood vessel, thereby ensuring the accuracy and reliability of the finally determined user blood pressure.

[0159] In some embodiments, the implementation process of determining the tissue attenuation coefficient corresponding to at least one effective pressure sensing unit in the target sensor array includes: determining the distance between the at least one effective pressure sensing unit and the target arterial blood vessel, determining the unit attenuation coefficient, where the unit attenuation coefficient refers to the attenuation of the pulse wave of the target arterial blood vessel by the human tissue with a unit thickness, and based on the unit attenuation coefficient and the distance between the at least one effective pressure sensing unit and the target arterial blood vessel, determining the tissue attenuation coefficient corresponding to each of the at least one effective pressure sensing unit.

[0160] Optionally, determine the distance between the first effective pressure sensing unit and the target arterial blood vessel, determine the unit attenuation coefficient, where the first effective pressure sensing unit is any one of the at least one effective pressure sensing unit, and based on the value obtained by multiplying the unit attenuation coefficient by the distance between the first effective pressure sensing unit and the target arterial blood vessel, use it as the tissue attenuation coefficient corresponding to the first effective pressure sensing unit. Processing each of the at least one first effective pressure sensing units in the same way can determine the tissue attenuation coefficient corresponding to each of the at least one effective pressure sensing unit.

[0161] In some embodiments, based on the pressure data collected by the effective pressure sensing units in the target sensor array, the primary pressure sensing unit and the secondary pressure sensing unit in the effective sensing units of the target sensor array are determined. The primary pressure sensing unit is the absolute pressure sensing unit with the maximum signal intensity among the effective sensing units of the target sensor array, and the signal intensity of the secondary pressure sensing unit is less than that of the primary pressure sensing unit. Based on the primary pressure sensing unit and the secondary pressure sensing unit in the effective sensing units, the distance between the first effective pressure sensing unit and the target artery is determined, and the unit attenuation coefficient is determined.

[0162] Optionally, based on the pressure data collected by the effective pressure sensing units in the target sensor array, the maximum peak-to-peak value corresponding to each effective pressure sensing unit is determined to obtain at least one maximum peak-to-peak value. The effective pressure sensing unit corresponding to the largest maximum peak-to-peak value among the at least one maximum peak-to-peak values is used as the primary pressure sensing unit. The effective pressure sensing unit corresponding to the maximum peak-to-peak value that is not equal to the largest maximum peak-to-peak value among the at least one maximum peak-to-peak values and the difference is greater than the maximum peak-to-peak value difference threshold is used as the secondary pressure sensing unit.

[0163] Of course, in practical applications, the primary pressure sensing unit and the secondary pressure sensing unit can also be determined by other means. For example, the effective pressure sensing unit with the largest average value of the pressure data collected by the effective pressure sensing units in the target sensor array is used as the primary pressure sensing unit. For another example, the effective pressure sensing units in the target sensor array except the primary pressure sensing unit are used as the secondary pressure sensing units. The embodiments of the present application do not limit this.

[0164] Among them, the maximum peak-to-peak value difference threshold is set in advance. For example, the maximum peak-to-peak value difference threshold can be set to 2, and in different situations, it can also be adjusted according to requirements.

[0165] It should be noted that the implementation method of determining the maximum peak-to-peak value corresponding to each effective pressure sensing unit based on the pressure data collected by the effective pressure sensing units in the target sensor array is similar to the implementation method of determining the maximum peak-to-peak value corresponding to each effective pressure sensing unit based on the pressure data collected by the effective pressure sensing units in the second sensor array above. For detailed content, please refer to the relevant content above, and it will not be elaborated here.

[0166] In practical applications, the airbag included in the wearable device is a narrow airbag. The wearable device also includes a barometric pressure sensor for collecting the gas pressure inside the airbag. In this case, after determining the main pressure sensing unit in the effective sensing unit, the mean arterial pressure (MAP) corresponding to the main pressure sensing unit can be determined based on the pressure data collected by the main pressure sensing unit. Based on the pressure data collected by the barometric pressure sensor and according to relevant algorithms, the MAP corresponding to the barometric pressure sensor can be determined. If the MAP corresponding to the main pressure sensing unit is greater than or equal to the MAP corresponding to the barometric pressure sensor, the above step 1601 is returned, that is, the blood pressure of the user is measured again. If the MAP corresponding to the main pressure sensing unit is less than the MAP corresponding to the barometric pressure sensor, the above step of determining the secondary pressure sensing unit is continued.

[0167] Based on the above description, when the narrow airbag is inflated, the pressure data collected by the barometric pressure sensor is higher than the pressure actually borne by the arterial blood vessel. Therefore, under normal circumstances, the MAP corresponding to the main pressure sensing unit should be less than the MAP corresponding to the barometric pressure sensor. If the MAP corresponding to the main pressure sensing unit is greater than or equal to the MAP corresponding to the barometric pressure sensor, it indicates that the measurement result of the wearable device is incorrect and needs to be measured again.

[0168] In some embodiments, the pressure data collected by the main pressure sensing unit is the pressure data collected by the main pressure sensing unit at multiple moments respectively. The pressure data includes static pressure and the dynamic pressure corresponding to the static pressure. In this case, the static pressure corresponding to the first dynamic pressure in the dynamic pressure of the main pressure sensing unit is used as the MAP corresponding to the main pressure sensing unit, and the first dynamic pressure is the dynamic pressure corresponding to the maximum peak-to-peak value in the dynamic pressure of the main pressure sensing unit.

[0169] Based on the above description, the peak-to-peak value in the dynamic pressure is the difference between the maximum dynamic pressure and the minimum dynamic pressure in an arterial pulsation cycle. Therefore, the dynamic pressure corresponding to the above maximum peak-to-peak value is any one of the maximum dynamic pressure and the minimum dynamic pressure corresponding to the maximum peak-to-peak value in the corresponding arterial pulsation cycle, or the maximum dynamic pressure among the two dynamic pressures, or the minimum dynamic pressure among the two dynamic pressures, or the average value of the maximum peak-to-peak value in the corresponding arterial pulsation cycle, or the dynamic pressure corresponding to the midpoint of the time of the corresponding arterial pulsation cycle, and so on. Of course, in practical applications, the dynamic pressure corresponding to the maximum peak-to-peak value can also be determined by other means, and the embodiments of the present application do not limit this.

[0170] When the first effective pressure sensing unit is the main pressure sensing unit, the method for determining the distance between the first effective pressure sensing unit and the target arterial blood vessel and the method for determining the unit attenuation coefficient are different from those when the first effective pressure sensing unit is the secondary pressure sensing unit, and will be introduced separately below.

[0171] When the first effective pressure sensing unit is the main pressure sensing unit, based on the pressure data collected by the first effective pressure sensing unit, the pressure data collected by the target secondary pressure sensing unit, and the distance between the first effective pressure sensing unit and the target secondary pressure sensing unit in the first direction, determine the distance between the first effective pressure sensing unit and the target arterial blood vessel, and the distance between the target secondary pressure sensing unit and the target arterial blood vessel. The target secondary pressure sensing unit is any secondary pressure sensing unit in the target sensor array. Based on the pressure data collected by the first effective pressure sensing unit, the pressure data collected by the target secondary pressure sensing unit, the distance between the first effective pressure sensing unit and the target arterial blood vessel, and the distance between the target secondary pressure sensing unit and the target arterial blood vessel, determine the unit attenuation coefficient.

[0172] In some embodiments, the distances between any two absolute pressure sensing units in the target sensor array in the first direction are stored in the wearable device. If the first effective pressure sensing unit is the main pressure sensing unit, the wearable device can, based on the ratio of the MAP corresponding to the target secondary pressure sensing unit to the MAP corresponding to the first effective pressure sensing unit, and the distance between the first effective pressure sensing unit and the target secondary pressure sensing unit in the first direction, use relevant formulas such as trigonometric functions to determine the distance between the first effective pressure sensing unit and the target arterial blood vessel, and the distance between the target secondary pressure sensing unit and the target arterial blood vessel.

[0173] It should be noted that the method for determining the MAP corresponding to the target secondary pressure sensing unit is similar to the method for determining the MAP corresponding to the main pressure sensing unit described above. For detailed content, please refer to the relevant content in the above text and will not be elaborated here.

[0174] Based on the above description, since the pulse wave signal intensity collected by the absolute pressure sensing unit located directly above the arterial blood vessel is the largest, and the main pressure sensing unit is the absolute pressure sensing unit with the largest signal intensity among the effective sensing units of the target sensor array, please refer to Figure 19, the main pressure sensing unit can be regarded as the absolute pressure sensing unit directly above the target artery in the target sensor array. The distance between the main pressure sensing unit and the target artery is Distance 1. The secondary pressure sensing unit is the absolute pressure sensing unit farther from the target artery, and the distance between the secondary pressure sensing unit and the target artery is Distance 2. The ratio of the MAP corresponding to the secondary pressure sensing unit to the MAP corresponding to the main pressure sensing unit can represent the ratio between Distance 1 and Distance 2. Therefore, based on the ratio of the MAP corresponding to the secondary pressure sensing unit to the MAP corresponding to the main pressure sensing unit, and the distance between the main pressure sensing unit and the secondary pressure sensing unit in the first direction (i.e., Figure 19 Distance 3 in

[0175] According to relevant formulas such as trigonometric functions, Distance 1 and Distance 3 can be determined.

[0176] In some other embodiments, if the first effective pressure sensing unit is the main pressure sensing unit, the wearable device can also determine the distance between the first effective pressure sensing unit and the target artery, and the distance between the target secondary pressure sensing unit and the target artery according to relevant formulas such as trigonometric functions based on the ratio of the MAP corresponding to the target secondary pressure sensing unit to the MAP corresponding to the first effective pressure sensing unit, the ratio of the maximum peak-to-peak value corresponding to the target secondary pressure sensing unit to the maximum peak-to-peak value corresponding to the first effective pressure sensing unit, and the distance between the first effective pressure sensing unit and the target secondary pressure sensing unit in the first direction. Of course, in practical applications, the distance between the first effective pressure sensing unit and the target artery, and the distance between the target secondary pressure sensing unit and the target artery can also be determined by other means, and the embodiments of the present application do not limit this.

[0177] Optionally, the user may input at least one of their gender, height data, and weight data into the wearable device, and then the wearable device can obtain the user's basic information.

[0178] The implementation process of determining the unit attenuation coefficient based on the pressure data collected by the first effective pressure sensing unit, the pressure data collected by the target secondary pressure sensing unit, the distance between the first effective pressure sensing unit and the target artery, and the distance between the target secondary pressure sensing unit and the target artery includes: dividing the MAP difference by the distance difference to obtain the unit attenuation coefficient. The MAP difference is the difference between the MAP of the first effective pressure sensing unit and the MAP of the target secondary pressure sensing unit. The distance difference is the difference between the first distance and the second distance. The first distance is the distance between the first effective pressure sensing unit and the target artery, and the second distance is the distance between the target secondary pressure sensing unit and the target artery.

[0179] When the first effective pressure sensing unit is a secondary pressure sensing unit, based on the pressure data collected by the first effective pressure sensing unit, the pressure data collected by the primary pressure sensing unit, and the distance between the first effective pressure sensing unit and the primary pressure sensing unit in the first direction, determine the distance between the first effective pressure sensing unit and the target artery, and the distance between the primary pressure sensing unit and the target artery. Based on the pressure data collected by the first effective pressure sensing unit, the pressure data collected by the primary pressure sensing unit, the distance between the first effective pressure sensing unit and the target artery, and the distance between the primary pressure sensing unit and the target artery, determine the unit attenuation coefficient.

[0180] The implementation method of determining the distance between the first effective pressure sensing unit and the target artery, and the distance between the primary pressure sensing unit and the target artery based on the pressure data collected by the first effective pressure sensing unit, the pressure data collected by the primary pressure sensing unit, and the distance between the first effective pressure sensing unit and the primary pressure sensing unit in the first direction is similar to the implementation method in the above text for determining the distance between the first effective pressure sensing unit and the target artery, and the distance between the target secondary pressure sensing unit and the target artery based on the pressure data collected by the first effective pressure sensing unit, the pressure data collected by the target secondary pressure sensing unit, and the distance between the first effective pressure sensing unit and the target secondary pressure sensing unit in the first direction. For detailed content, please refer to the relevant content in the above text, and it will not be elaborated here.

[0181] Based on the pressure data collected by the first effective pressure sensing unit, the pressure data collected by the main pressure sensing unit, the distance between the first effective pressure sensing unit and the target arterial blood vessel, and the distance between the main pressure sensing unit and the target arterial blood vessel, the implementation manner of determining the unit attenuation coefficient is similar to the implementation manner of determining the unit attenuation coefficient based on the pressure data collected by the first effective pressure sensing unit, the pressure data collected by the target secondary pressure sensing unit, the distance between the first effective pressure sensing unit and the target arterial blood vessel, and the distance between the target secondary pressure sensing unit and the target arterial blood vessel as described above. For the detailed content, please refer to the relevant content in the above text and will not be elaborated here.

[0182] In some embodiments, the pressure data includes a plurality of static pressures and dynamic pressures respectively corresponding to each static pressure. In this case, the implementation process of correcting the pressure data collected by at least one effective pressure sensing unit based on the tissue attenuation coefficient corresponding to the at least one effective pressure sensing unit includes: for any one of the at least one effective pressure sensing units, subtracting the tissue attenuation coefficient corresponding to the effective pressure sensing unit from the pressure data of the effective pressure sensing unit among the plurality of absolute pressures respectively to obtain a plurality of corrected static pressures, adding the tissue attenuation coefficient corresponding to the effective pressure sensing unit to the pressure data of the effective pressure sensing unit among the plurality of dynamic pressures respectively to obtain a plurality of corrected dynamic pressures, and taking the plurality of corrected static pressures and the plurality of corrected dynamic pressures as the first pressure data of the effective pressure sensing unit to implement the correction of the pressure data collected by the effective pressure sensing unit. Each of the at least one effective pressure sensing units is processed in the same manner to implement the correction of the pressure data collected by each of the at least one effective pressure sensing units.

[0183] For the pressure applied by the airbag (i.e., the static pressure), the pressure applied by the airbag first reaches the absolute pressure sensing unit and then can reach the target arterial blood vessel only after the attenuation of the human tissue. The static pressure borne by the target arterial blood vessel is smaller than the static pressure collected by the absolute pressure sensing unit. Therefore, subtracting the tissue attenuation coefficient corresponding to the effective pressure sensing unit from the plurality of static pressures respectively can implement the correction of the static pressure.

[0184] For the pulse wave generated by the target arterial blood vessel, the pulse wave can reach the absolute pressure sensing unit only after the attenuation of the human tissue after being emitted from the target arterial blood vessel. The dynamic pressure generated by the target arterial blood vessel is larger than the dynamic pressure collected by the absolute pressure sensing unit. Therefore, adding the tissue attenuation coefficient corresponding to the effective pressure sensing unit to the plurality of dynamic pressures respectively can implement the correction of the dynamic pressure.

[0185] Step 1604: Determine the user's blood pressure based on the arterial pressure data corresponding to the at least one arterial blood vessel.

[0186] When the number of arterial blood vessels is different, the implementation of determining the user's blood pressure based on the arterial pressure data corresponding to the at least one arterial blood vessel is different. The following will introduce them separately.

[0187] When the number of the at least one arterial blood vessel is one, the wearable device can directly determine the user's blood pressure based on the arterial pressure data corresponding to the arterial blood vessel according to relevant algorithms.

[0188] When the number of the at least one arterial blood vessel is at least two, that is, the at least one arterial blood vessel includes at least two arterial blood vessels. In this case, there are multiple implementations of determining the user's blood pressure for the arterial pressure data corresponding to the at least two arterial blood vessels. The following will introduce two of the implementations.

[0189] The first implementation: The arterial pressure data includes static pressures corresponding to multiple moments and dynamic pressures corresponding to each static pressure. The static pressure represents the pressure applied by the airbag, and the dynamic pressure represents the pulsation of the corresponding arterial blood vessel under the compression of the static pressure. The at least two arterial blood vessels respectively correspond to different weights. In this case, add the dynamic pressures corresponding to the same moment in the arterial pressure data corresponding to the at least two arterial blood vessels after multiplying them by their respective corresponding weights to obtain multiple superimposed dynamic pressures. Add the static pressures corresponding to the same moment in the arterial pressure data corresponding to the at least two arterial blood vessels after multiplying them by their respective corresponding weights to obtain multiple superimposed static pressures. Use the multiple superimposed dynamic pressures and the multiple superimposed static pressures as the superimposed arterial pressure data, and determine the user's blood pressure based on the superimposed arterial pressure data according to relevant algorithms.

[0190] Exemplarily, if the number of arterial blood vessels is 2, the two arterial blood vessels are arterial blood vessel 1 and arterial blood vessel 2 respectively. The weight corresponding to arterial blood vessel 1 is weight 1, and the weight corresponding to arterial blood vessel 2 is weight 2. The arterial pressure data corresponding to arterial blood vessel 1 and arterial blood vessel 2 both include static pressures corresponding to 2 moments and dynamic pressures corresponding to each static pressure. The 2 moments are moment 1 and moment 2 respectively. Taking moment 1 as an example, the static pressure corresponding to arterial blood vessel 1 at moment 1 is static pressure 11, the dynamic pressure corresponding to moment 1 is dynamic pressure 11, the static pressure corresponding to arterial blood vessel 2 at moment 1 is static pressure 21, and the dynamic pressure corresponding to moment 1 is dynamic pressure 21.

[0191] In this case, multiply the static pressure 11 by weight 1, multiply the static pressure 21 by weight 2, add the weighted static pressure 11 and the weighted static pressure 12 to obtain the superimposed static pressure corresponding to time 1. Multiply the dynamic pressure 11 by weight 1, multiply the dynamic pressure 21 by weight 2, add the weighted dynamic pressure 11 and the weighted dynamic pressure 12 to obtain the superimposed dynamic pressure corresponding to time 1.

[0192] In a second implementation manner, the arterial pressure data includes a plurality of static pressures and the dynamic pressure corresponding to each static pressure. The static pressure represents the pressure applied by the airbag, and the dynamic pressure represents the pulsation condition of the corresponding arterial blood vessel under the compression of the static pressure. In this case, in some embodiments, the wearable device may superimpose the dynamic pressures in the arterial pressure data corresponding to at least two arterial blood vessels according to the static pressures in the arterial pressure data corresponding to the at least two arterial blood vessels respectively, to obtain the superimposed arterial pressure data, and determine the user's blood pressure according to a related algorithm based on the superimposed arterial pressure data.

[0193] Optionally, the at least two arterial blood vessels respectively correspond to different weights. In this case, in the dynamic pressures of the arterial pressure data corresponding to the at least two arterial blood vessels respectively, the dynamic pressures corresponding to the same static pressure are multiplied by their respective corresponding weights and then added together to obtain a plurality of superimposed dynamic pressures. The plurality of superimposed dynamic pressures and the static pressures corresponding to the plurality of superimposed dynamic pressures respectively are used as the superimposed arterial pressure data.

[0194] It should be noted that the sum of the weights corresponding to the at least two arterial blood vessels is 1.

[0195] Exemplarily, if the number of arterial blood vessels is 2, the two arterial blood vessels are arterial blood vessel 1 and arterial blood vessel 2 respectively, the weight corresponding to arterial blood vessel 1 is weight 1, and the weight corresponding to arterial blood vessel 2 is weight 2; the arterial pressure data corresponding to arterial blood vessel 1 includes static pressure 11 and the dynamic pressure 11 corresponding to the static pressure 11, and the arterial pressure data corresponding to arterial blood vessel 2 includes static pressure 21 and the dynamic pressure 21 corresponding to the static pressure 21.

[0196] If the static pressure 11 is equal to the static pressure 21, multiply the dynamic pressure 11 by weight 1, multiply the dynamic pressure 21 by weight 2, add the weighted dynamic pressure 11 and the weighted dynamic pressure 12 to obtain the superimposed dynamic pressure corresponding to the static pressure 11 (or the static pressure 21).

[0197] In the case where the at least two arterial blood vessels are the ulnar artery and the radial artery, based on the above description, due to the different depths of the ulnar artery and the radial artery in human tissues, the irregularity of the human wrist bones, and the influence of the user's wearing method, etc., the pulse wave signal in the airbag obtained by the superposition of the pulse beats of the ulnar artery and the radial artery in the time domain cannot accurately represent the pulsation of the user's arterial blood vessels during the pressurization process, with a large error, which will further result in poor accuracy of the blood pressure result. Please refer to Figure 20 , the embodiment of the present application can superimpose the arterial pressure data corresponding to the at least two arterial blood vessels in the static pressure dimension, thus fundamentally avoiding the problem of large errors in the pulse wave signal caused by simple superposition in the time domain, and further improving the accuracy of blood pressure measurement.

[0198] Since the sensor array includes a plurality of absolute pressure sensing units, the pressure measured by the absolute pressure sensing unit is relative to the vacuum pressure. Therefore, the pressure measured by the absolute pressure sensing unit is not affected by the change of atmospheric pressure and can accurately reflect the real pressure situation. Since the at least one sensor array is located on the side of the airbag away from the wearing strip, in this case, when the user wears the wearable device, the sensor array can contact the user's skin and collect the pressure data at the contact position. The pressure data is relative to the vacuum pressure. Compared with the method of collecting the pressure data inside the airbag, the pressure data collected by the embodiment of the present application can accurately represent the actual pressure borne by the corresponding contact position, thus ensuring the accuracy of the finally determined user blood pressure. And, since the embodiment of the present application takes into account that the size of the arterial blood vessel is relatively small compared to the size of the sensor array, the embodiment of the present application can determine the absolute pressure sensing unit (also called the effective pressure sensing unit) that can effectively represent the pulsation of the user's arterial blood vessel from the plurality of absolute pressure sensing units included in the sensor array, and then based on the pressure data collected by the effective pressure sensing unit, determine the arterial pressure data corresponding to the arterial blood vessel, thus ensuring the accuracy of the finally determined arterial pressure data. Also, since the arterial pressure data can represent the actual pressure borne by the corresponding arterial blood vessel during blood pressure measurement, the accuracy of the blood pressure result determined based on the arterial pressure data corresponding to the arterial blood vessel is relatively high. In addition, in the case of determining the arterial pressure data corresponding to at least two arterial blood vessels, the embodiment of the present application can also determine the user's blood pressure based on the arterial pressure data corresponding to the at least two arterial blood vessels, thus further improving the accuracy of blood pressure measurement.

[0199] When the absolute pressure sensing units in adjacent rows among the multiple absolute pressure sensing units included in the sensor array are staggered, it can effectively ensure that the sensor array can collect the optimal pulse wave signal in terms of signal strength, thereby ensuring the accuracy of the finally determined user blood pressure. In the embodiments of the present application, considering the attenuation of the pulse wave of the target artery by the human tissue, the pressure data collected by the effective pressure sensing unit is corrected by calculating the tissue attenuation coefficient, so that the pressure data collected by the corrected effective pressure sensing unit can accurately reflect the pulsation of the artery, thereby ensuring the accuracy and reliability of the finally determined user blood pressure.

[0200] Figure 21 FIG. 4 is a schematic structural diagram of a blood pressure measurement device provided by an embodiment of the present application. The blood pressure measurement device can be implemented as part or all of the above wearable device by software, hardware or a combination of both. The device includes: an acquisition module 2101, a first determination module 2102, a second determination module 2103, and a third determination module 2104.

[0201] The acquisition module 2101 is configured to acquire pressure data sets respectively collected by at least one sensor array. The pressure data sets are collected by a plurality of absolute pressure sensing units included in the corresponding sensor array during the process of inflating and pressurizing or deflating and decompressing the airbag. For the detailed implementation process, refer to the corresponding content in the above respective embodiments, and details are not described herein again.

[0202] The first determination module 2102 is configured to determine effective pressure sensing units from the absolute pressure sensing units included in the at least one sensor array based on the pressure data sets collected by the at least one sensor array. The pressure data collected by the effective pressure sensing units can effectively characterize the pulsation of the user's artery. For the detailed implementation process, refer to the corresponding content in the above respective embodiments, and details are not described herein again.

[0203] The second determination module 2103 is configured to determine arterial pressure data corresponding to at least one artery based on the pressure data collected by the effective pressure sensing units in the at least one sensor array. The arterial pressure data characterizes the actual pressure borne by the corresponding artery during the blood pressure measurement process. For the detailed implementation process, refer to the corresponding content in the above respective embodiments, and details are not described herein again.

[0204] The third determination module 2104 is configured to determine the user's blood pressure based on the arterial pressure data corresponding to at least one artery. For the detailed implementation process, refer to the corresponding content in the above respective embodiments, and details are not described herein again.

[0205] Optionally, the pressure data set includes multiple groups of pressure data collected by a plurality of absolute pressure sensing units, and each group of pressure data includes pressure data at multiple moments;

[0206] The first determination module 2102 is specifically configured to:

[0207] Based on the first pressure data set, determine multiple groups of candidate pressure sensing units from the absolute pressure sensing units included in the first sensor array;

[0208] Wherein, the first pressure data set is the pressure data set collected by the first sensor array, the first sensor array is any one of at least one sensor array, the multiple groups of candidate pressure sensing units correspond to multiple first moments one by one, the positions of the candidate pressure sensing units in the same group are continuous and the difference between the pressure data collected at the corresponding first moment is within the pressure fluctuation range, the first moment is one moment among multiple moments, and the first arterial blood vessel is the arterial blood vessel corresponding to the first sensor array;

[0209] Determine the effective pressure sensing units in the first sensor array from the multiple groups of candidate pressure sensing units.

[0210] Optionally, the device further includes:

[0211] A fourth determination module, configured to determine the tissue attenuation coefficient corresponding to at least one effective pressure sensing unit in the target sensor array, where the tissue attenuation coefficient indicates the attenuation of the pulse wave of the target arterial blood vessel by the human tissue, the target arterial blood vessel is the arterial blood vessel corresponding to the target sensor array, and the target sensor array is any one of at least one sensor array;

[0212] A correction module, configured to correct the pressure data collected by at least one effective pressure sensing unit based on the tissue attenuation coefficient corresponding to at least one effective pressure sensing unit.

[0213] Optionally, the fourth determination module is specifically configured to:

[0214] Determine the distance between at least one effective pressure sensing unit and the target arterial blood vessel;

[0215] Determine the unit attenuation coefficient, where the unit attenuation coefficient refers to the attenuation of the pulse wave of the target arterial blood vessel by the human tissue with a unit thickness;

[0216] Based on the unit attenuation coefficient and the distance between at least one effective pressure sensing unit and the target arterial blood vessel, determine the tissue attenuation coefficient corresponding to at least one effective pressure sensing unit respectively.

[0217] Optionally, the arterial pressure data includes multiple static pressures and the dynamic pressure corresponding to each static pressure, at least one arterial blood vessel includes at least two arterial blood vessels, the static pressure represents the pressure applied by the airbag, and the dynamic pressure represents the pulsation of the corresponding arterial blood vessel under the compression of the static pressure;

[0218] The third determination module 2104 is specifically configured to:

[0219] Superimpose the dynamic pressure in the arterial pressure data respectively corresponding to at least two arterial blood vessels according to the static pressure in the arterial pressure data respectively corresponding to the at least two arterial blood vessels, so as to obtain the superimposed arterial pressure data;

[0220] Determine the blood pressure of the user based on the superimposed arterial pressure data.

[0221] In the embodiment of the present application, since the sensor array includes a plurality of absolute pressure sensing units, and the pressure measured by the absolute pressure sensing unit is relative to the vacuum pressure, therefore, the pressure measured by the absolute pressure sensing unit is not affected by the change of the atmospheric pressure and can accurately reflect the real pressure situation. Since the at least one sensor array is located on the side of the airbag away from the wearable strip, in this case, when the user wears the wearable device, the sensor array can contact the user's skin and collect the pressure data at the contact position, and the pressure data is relative to the vacuum pressure. Compared with the method of collecting the pressure data inside the airbag, the pressure data collected in the embodiment of the present application can accurately represent the actual pressure borne by the corresponding contact position, so as to ensure the accuracy of the finally determined blood pressure of the user. Moreover, since the embodiment of the present application takes into account that the size of the arterial blood vessel is relatively small compared with the size of the sensor array, therefore, the embodiment of the present application can determine, from the plurality of absolute pressure sensing units included in the sensor array, the absolute pressure sensing unit (also called the effective pressure sensing unit) that can effectively represent the pulsation condition of the user's arterial blood vessel, and then determine the arterial pressure data respectively corresponding to the arterial blood vessel based on the pressure data collected by the effective pressure sensing unit, so as to ensure the accuracy of the finally determined arterial pressure data. Also, since the arterial pressure data can represent the actual pressure borne by the corresponding arterial blood vessel during blood pressure measurement, the accuracy of the blood pressure result determined based on the arterial pressure data corresponding to the arterial blood vessel is relatively high. In addition, in the case of determining the arterial pressure data corresponding to at least two arterial blood vessels, the embodiment of the present application can also determine the blood pressure of the user based on the arterial pressure data corresponding to the at least two arterial blood vessels, so as to further improve the accuracy of blood pressure measurement.

[0222] It should be noted that: when the blood pressure measurement device provided in the above embodiment performs blood pressure measurement, only the above-mentioned division of each functional module is used for illustration. In practical applications, the above functions can be allocated to different functional modules according to needs, that is, the internal structure of the device is divided into different functional modules to complete all or part of the functions described above. In addition, the blood pressure measurement device provided in the above embodiment and the embodiment of the blood pressure measurement method belong to the same concept, and the specific implementation process is detailed in the method embodiment, which will not be elaborated here.

[0223] An embodiment of the present application also provides a computer-readable storage medium, in which instructions are stored. When the instructions run on a computer, the computer is caused to execute the steps of the blood pressure measurement method described in the above embodiment, or execute the steps of the blood pressure measurement method described in the above embodiment.

[0224] An embodiment of the present application also provides a computer program product containing instructions. When the instructions run on a computer, the computer is caused to execute the steps of the blood pressure measurement method described in the above embodiment. Or rather, a computer program is provided. When the computer program runs on a computer, the computer is caused to execute the steps of the blood pressure measurement method described in the above embodiment.

[0225] In the above embodiment, it can be implemented in whole or in part by software, hardware, firmware, or any combination thereof. When implemented using software, it can be implemented in whole or in part in the form of a computer program product. The computer program product includes one or more computer instructions. When the computer instructions are loaded and executed on a computer, the processes or functions described in the embodiments of the present application are generated in whole or in part. The computer can be a general-purpose computer, a special-purpose computer, a computer network, or other programmable devices. The computer instructions can be stored in a computer-readable storage medium, or transmitted from one computer-readable storage medium to another computer-readable storage medium. For example, the computer instructions can be transmitted from a website, computer, server, or data center to another website, computer, server, or data center in a wired manner (such as coaxial cable, optical fiber, digital subscriber line (DSL)) or a wireless manner (such as infrared, wireless, microwave, etc.). The computer-readable storage medium can be any available medium that can be accessed by a computer, or a data storage device such as a server or data center that includes one or more integrated available media. The available medium can be a magnetic medium (such as a floppy disk, hard disk, magnetic tape), an optical medium (such as a digital versatile disc (DVD)), or a semiconductor medium (such as a solid state disk (SSD)), etc. It should be noted that the computer-readable storage medium mentioned in the embodiments of the present application can be a non-volatile storage medium, in other words, it can be a non-transitory storage medium.

[0226] It should be understood that the "multiple" mentioned herein refers to two or more. In the description of the embodiments of the present application, unless otherwise specified, " / " means "or". For example, A / B can mean A or B; the "and / or" herein is merely a description of the association relationship of associated objects, indicating that there can be three relationships. For example, A and / or B can mean: A exists alone, A and B exist simultaneously, and B exists alone. In addition, for the convenience of clearly describing the technical solutions of the embodiments of the present application, in the embodiments of the present application, terms such as "first" and "second" are used to distinguish identical or similar items with basically the same functions and roles. Those skilled in the art can understand that terms such as "first" and "second" do not limit the quantity and execution order, and terms such as "first" and "second" do not necessarily mean different.

[0227] It should be noted that the information (including but not limited to user device information, user personal information, etc.), data (including but not limited to data for analysis, stored data, displayed data, etc.) and signals involved in the embodiments of the present application are all authorized by the user or fully authorized by all parties, and the collection, use and processing of relevant data need to comply with the relevant laws, regulations and standards of relevant countries and regions. For example, the pressure data sets respectively collected by at least one sensor array involved in the embodiments of the present application are all obtained under full authorization.

[0228] The above are the embodiments provided by the present application, which are not intended to limit the present application. Any modifications, equivalent replacements, improvements, etc. made within the spirit and principle of the present application shall be included in the protection scope of the present application.

Claims

1. A wearable device, characterized in that, the wearable device includes a wearable strip, an inflation component, at least one sensor array and a processor, and the inflation component includes an air pump and an airbag; the airbag is located inside the wearable strip, and the airbag is distributed along the length direction of the wearable strip, and the air pump is used to inflate and pressurize the airbag and then deflate and decompress it during the process of the user measuring blood pressure; the at least one sensor array is located on the side of the airbag away from the wearable strip, and when the user wears the wearable device, the at least one sensor array corresponds to the position of at least one arterial blood vessel of the user; the sensor array includes a plurality of absolute pressure sensing units, and the size of the absolute pressure sensing unit in the first direction is not greater than the diameter of the corresponding arterial blood vessel, and the first direction is perpendicular to the flow direction of the corresponding arterial blood vessel; the sensor array is used to collect the pressure borne by the corresponding arterial blood vessel during the process of the user measuring blood pressure, and the processor is used to determine the blood pressure of the user based on the pressure data set collected by the at least one sensor array.

2. The wearable device according to claim 1, characterized in that, the column direction of the sensor array is the same as the flow direction of the corresponding arterial blood vessel, the plurality of absolute pressure sensing units are arranged in an M-row and N-column manner, and the distance between two adjacent absolute pressure sensing units in the same row is not greater than the diameter of the corresponding arterial blood vessel, M is an integer greater than or equal to 1, and N is an integer greater than 1.

3. The wearable device according to claim 2, characterized in that, the absolute pressure sensing units in adjacent two rows among the plurality of absolute pressure sensing units are arranged staggeredly.

4. The wearable device according to claim 1, characterized in that, the at least one sensor array includes a first array and / or a second array, the first array corresponds to the radial artery blood vessel, and the second array corresponds to the ulnar artery blood vessel.

5. The wearable device according to claim 1, characterized in that, the size of the sensor array in the first direction is more than three times the diameter of the corresponding arterial blood vessel.

6. A blood pressure measurement method using the wearable device according to any one of claims 1-5, characterized in that, the method includes: obtaining the pressure data sets respectively collected by the at least one sensor array, where the pressure data sets are collected by a plurality of absolute pressure sensing units included in the corresponding sensor array during the process of inflating and pressurizing or deflating and decompressing the airbag; determining effective pressure sensing units from the absolute pressure sensing units included in the at least one sensor array based on the pressure data sets collected by the at least one sensor array, and the pressure data collected by the effective pressure sensing units can effectively characterize the pulsation condition of the arterial blood vessels of the user; determining the arterial pressure data corresponding to the at least one arterial blood vessel respectively based on the pressure data collected by the effective pressure sensing units in the at least one sensor array, and the arterial pressure data characterizes the actual pressure borne by the corresponding arterial blood vessel during the blood pressure measurement process; Determine the blood pressure of the user based on the arterial pressure data corresponding to the at least one arterial blood vessel.

7. The method according to claim 6, wherein, the pressure data set includes multiple sets of pressure data collected by the multiple absolute pressure sensing units, and each set of pressure data includes pressure data at multiple moments; the determining of the effective pressure sensing units from the absolute pressure sensing units included in the at least one sensor array based on the pressure data set collected by the at least one sensor array includes: determining multiple sets of candidate pressure sensing units from the absolute pressure sensing units included in the first sensor array based on the first pressure data set; wherein, the first pressure data set is the pressure data set collected by the first sensor array, the first sensor array is any one of the at least one sensor array, the multiple sets of candidate pressure sensing units correspond one-to-one to multiple first moments, the positions of the candidate pressure sensing units in the same set are continuous and the difference between the pressure data collected at the corresponding first moments is within the pressure fluctuation range, the first moment is one of the multiple moments, and the first arterial blood vessel is the arterial blood vessel corresponding to the first sensor array; determining the effective pressure sensing units in the first sensor array from the multiple sets of candidate pressure sensing units.

8. The method according to claim 6, wherein, before determining the arterial pressure data corresponding to the at least one arterial blood vessel based on the pressure data collected by the effective pressure sensing units in the at least one sensor array, the method further includes: determining the tissue attenuation coefficient corresponding to at least one effective pressure sensing unit in the target sensor array, the tissue attenuation coefficient indicating the attenuation of the pulse wave of the target arterial blood vessel by the human tissue, the target arterial blood vessel being the arterial blood vessel corresponding to the target sensor array, and the target sensor array being any one of the at least one sensor array; correcting the pressure data collected by the at least one effective pressure sensing unit based on the tissue attenuation coefficient corresponding to the at least one effective pressure sensing unit.

9. The method according to claim 8, wherein, the determining of the tissue attenuation coefficient corresponding to at least one effective pressure sensing unit in the target sensor array includes: determining the distance between the at least one effective pressure sensing unit and the target arterial blood vessel; determining the unit attenuation coefficient, the unit attenuation coefficient referring to the attenuation of the pulse wave of the target arterial blood vessel by the human tissue with a unit thickness; determining the tissue attenuation coefficient corresponding to each of the at least one effective pressure sensing unit based on the unit attenuation coefficient and the distance between the at least one effective pressure sensing unit and the target arterial blood vessel.

10. The method according to claim 6, wherein, The arterial pressure data includes a plurality of static pressures and the dynamic pressures corresponding to each static pressure. The at least one arterial blood vessel includes at least two arterial blood vessels. The static pressure represents the pressure applied by the airbag, and the dynamic pressure represents the pulsation condition of the corresponding arterial blood vessel under the compression of the static pressure; Determining the blood pressure of the user based on the arterial pressure data corresponding to the at least one arterial blood vessel respectively includes: Superposing the dynamic pressures in the arterial pressure data corresponding to the at least two arterial blood vessels respectively according to the static pressures in the arterial pressure data corresponding to the at least two arterial blood vessels respectively, to obtain the superposed arterial pressure data; Determining the blood pressure of the user based on the superposed arterial pressure data.

11. A blood pressure measuring device characterized in that it is included in the wearable device according to any one of claims 1-5, and the device includes: an acquisition module, configured to acquire the pressure data sets respectively collected by the at least one sensor array, where the pressure data sets are collected by a plurality of absolute pressure sensing units included in the corresponding sensor array during the process of inflating and pressurizing or deflating and decompressing the airbag; a first determination module, configured to determine effective pressure sensing units from the absolute pressure sensing units included in the at least one sensor array based on the pressure data sets collected by the at least one sensor array, where the pressure data collected by the effective pressure sensing units can effectively represent the pulsation condition of the arterial blood vessels of the user; a second determination module, configured to determine the arterial pressure data corresponding to the at least one arterial blood vessel respectively based on the pressure data collected by the effective pressure sensing units in the at least one sensor array, where the arterial pressure data represents the pressure actually borne by the corresponding arterial blood vessel during the blood pressure measurement process; a third determination module, configured to determine the blood pressure of the user based on the arterial pressure data corresponding to the at least one arterial blood vessel.

12. The device according to claim 11 characterized in that the pressure data sets include multiple groups of pressure data collected by the multiple absolute pressure sensing units, and each group of pressure data includes pressure data at multiple moments; The first determination module is specifically configured to: determine multiple groups of candidate pressure sensing units from the absolute pressure sensing units included in the first sensor array based on the first pressure data set; wherein, the first pressure data set is the pressure data set collected by the first sensor array, the first sensor array is any one of the at least one sensor array, the multiple groups of candidate pressure sensing units correspond one by one to multiple first moments, the positions of the candidate pressure sensing units in the same group are continuous and the difference between the pressure data collected at the corresponding first moment is within the pressure fluctuation range, the first moment is one of the multiple moments, and the first arterial blood vessel is the arterial blood vessel corresponding to the first sensor array; determine the effective pressure sensing units in the first sensor array from the multiple groups of candidate pressure sensing units.

13. The device according to claim 11 characterized in that the device further includes: A fourth determination module, configured to determine the tissue attenuation coefficient corresponding to at least one effective pressure sensing unit in the target sensor array, where the tissue attenuation coefficient indicates the attenuation of the pulse wave of the target artery blood vessel by the human tissue, the target artery blood vessel is the artery blood vessel corresponding to the target sensor array, and the target sensor array is any one of the at least one sensor array; A correction module, configured to correct the pressure data collected by the at least one effective pressure sensing unit based on the tissue attenuation coefficient corresponding to the at least one effective pressure sensing unit.

14. The device according to claim 13, wherein, the fourth determination module is specifically configured to: determine the distance between the at least one effective pressure sensing unit and the target artery blood vessel; determine the unit attenuation coefficient, where the unit attenuation coefficient refers to the attenuation of the pulse wave of the target artery blood vessel by the human tissue with a unit thickness; based on the unit attenuation coefficient and the distance between the at least one effective pressure sensing unit and the target artery blood vessel, determine the tissue attenuation coefficient corresponding to each of the at least one effective pressure sensing unit.

15. The device according to claim 11, wherein, the arterial pressure data includes a plurality of static pressures and the dynamic pressure corresponding to each static pressure, the at least one artery blood vessel includes at least two artery blood vessels, the static pressure represents the pressure applied by the airbag, and the dynamic pressure represents the pulsation condition of the corresponding artery blood vessel under the compression of the static pressure; the third determination module is specifically configured to: superimpose the dynamic pressures in the arterial pressure data corresponding to the at least two artery blood vessels according to the static pressures in the arterial pressure data corresponding to the at least two artery blood vessels respectively, to obtain the superimposed arterial pressure data; based on the superimposed arterial pressure data, determine the blood pressure of the user.

16. A computer-readable storage medium, wherein, instructions are stored in the storage medium, and when the instructions run on the computer, the computer is caused to execute the steps of the method according to any one of claims 6-10.

17. A computer program, wherein, the computer program includes instructions, and when the instructions run on the computer, the computer is caused to execute the steps of the method according to any one of claims 6-10.

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