Control method and device of heart and lung sound detection device, heart and lung sound detection ring and storage medium

Abstract

The invention discloses a cardiopulmonary sound detection device control method and device, a cardiopulmonary sound detection ring and a storage medium, relates to the technical field of wearable equipment, and discloses a cardiopulmonary sound detection device control method, the cardiopulmonary sound detection device comprises an outer shell and an inner shell, the outer shell and the inner shell are connected and enclose to form an annular accommodating cavity; the heart and lung sound detection device comprises an annular containing cavity, and a PCB mainboard, a pressure sensing chip and an inertial measurement unit which are arranged in the annular containing cavity, and the control method of the heart and lung sound detection device comprises the steps that when a pressure detection process is triggered, the deformation quantity, detected by the pressure sensing chip, of the PCB mainboard and inertial parameters detected by the inertial measurement unit are obtained; updating a preset force conduction coefficient based on the inertial parameter to obtain a target force conduction coefficient; and calculating a pressure detection value of the heart and lung sound detection device according to the target force conduction coefficient and the deformation quantity. The calculation result of the pressure detection value corresponds to the real deformation data, the pressure value is accurately judged, and the accuracy of heart and lung sound detection is improved.

Description

TECHNICAL FIELD

[0001] The present application relates to the technical field of wearable devices, and particularly relates to a control method and device of a heart-lung sound detection device, a heart-lung sound detection ring, and a storage medium. BACKGROUND

[0002] Human heart-lung sound data can be used to determine health status. When using a smart ring product to perform heart-lung sound testing, the user needs to press the smart ring against the chest wall to collect data. To meet the data stability requirement, users of different body types need to use different pressing forces to ensure data accuracy.

[0003] However, the pressure sensor inside the smart ring is extremely sensitive to the pressing position. Even if the pressing force is the same, the sensor return value differs greatly under different pressing positions, making it difficult for the user to determine whether the pressure meets the standard and reducing the accuracy of heart-lung sound detection.

[0004] The above content is only used to assist in understanding the technical solutions of the present application and does not represent an admission that the above content is prior art. SUMMARY

[0005] The main purpose of the present application is to provide a control method and device of a heart-lung sound detection device, a heart-lung sound detection ring, and a storage medium, aiming to solve the technical problem that the pressure detection value is difficult to determine when performing heart-lung sound detection based on a wearable device ring, resulting in low accuracy of heart-lung sound detection.

[0006] To achieve the above purpose, the present application provides a control method of a heart-lung sound detection device, the heart-lung sound detection device comprising a shell and an inner shell, the shell being connected with the inner shell and enclosing an annular accommodating cavity; and a PCB mainboard, a pressure sensing chip, and an inertial measurement unit arranged in the annular accommodating cavity, the control method of the heart-lung sound detection device comprising: obtaining a deformation amount of the PCB mainboard detected by the pressure sensing chip and an inertial parameter detected by the inertial measurement unit when a pressure detection process is triggered; updating a preset force transmission coefficient based on the inertial parameter to obtain a target force transmission coefficient; calculating a pressure detection value of the heart-lung sound detection device according to the target force transmission coefficient and the deformation amount.

[0007] In an embodiment, the inertial parameter comprises a detection angle, and the step of updating the preset force transmission coefficient based on the inertial parameter to obtain the target force transmission coefficient comprises: determining an angle deviation amount between the detection angle and a preset angle, and calculating an angle component of the angle deviation amount at the preset angle, the preset angle being an angle corresponding to the preset force transmission coefficient; determine a pressing area according to the angle deviation amount, and obtain a pressure deformation coefficient of the pressing area; calculate a product of the angle component, the pressure deformation coefficient, and the preset force conduction coefficient to obtain the target force conduction coefficient.

[0008] In an embodiment, the step of determining a pressing area according to the angle deviation amount, and obtaining a pressure deformation coefficient of the pressing area comprises: determining a pressing area according to the angle deviation amount; determining a deviation distance between the pressing area and an initial area, the initial area being an area corresponding to a preset angle; calculating the pressure deformation coefficient of the pressing area according to the deviation distance and a preset linear relationship between the deviation distance and the deformation coefficient.

[0009] In an embodiment, after the step of calculating the pressure detection value of the heart-lung sound detection device according to the target force conduction coefficient and the deformation amount, the control method of the heart-lung sound detection device further comprises: if the pressure detection value is in an abnormal interval, outputting prompt information of pressure value adjustment; if the pressure detection value meets a preset pressure value, triggering a heart-lung sound detection process.

[0010] In an embodiment, after the step of calculating the pressure detection value of the heart-lung sound detection device according to the target force conduction coefficient and the deformation amount, the control method of the heart-lung sound detection device further comprises: obtaining historical pressing data of a user, and constructing a pressing behavior model of the user according to the historical pressing data; determining associated pressure data of the inertia parameter in the pressing behavior model; if the pressure detection value is in a pressure floating interval corresponding to the pressure data, triggering a heart-lung sound detection process.

[0011] In an embodiment, before the step of obtaining the deformation amount of the PCB mainboard detected by the pressure sensing chip and the inertia parameter detected by the inertia measurement unit when the pressure detection process is triggered, the control method of the heart-lung sound detection device further comprises: when a start instruction of the heart-lung sound detection device is detected, obtaining a current inertia parameter detected by the inertia measurement unit; calculating a confidence degree of wearing deviation of the heart-lung sound detection device according to the current inertia parameter and a historical inertia parameter; if the confidence degree is greater than a preset confidence degree, outputting a wearing position adjustment instruction.

[0012] In addition, to achieve the above object, the application further provides a heart-lung sound detection device, characterized in that the heart-lung sound detection device comprises: an outer shell and an inner shell, the outer shell being connected with the inner shell and enclosing an annular accommodating cavity; a PCB mainboard arranged in the annular accommodating cavity; a pressure-sensitive chip arranged between the PCB mainboard and the inner shell and used for detecting a deformation amount of the PCB mainboard; an inertial measurement unit arranged in the annular accommodating cavity and used for detecting an inertial parameter of the heart-lung sound detection device; a calculation module used for calculating a pressure value according to the deformation amount and the inertial parameter.

[0013] In an embodiment, a force transmission medium is arranged between the PCB mainboard and the outer shell, and the force transmission medium is epoxy resin and a silica gel pad; an output component used for outputting the pressure value of the heart-lung sound detection device in a heart-lung sound detection process; and a detection module used for detecting heart-lung sound data.

[0014] In addition, to achieve the above object, the application further provides a heart-lung sound detection ring, which comprises a memory, a processor and a computer program stored in the memory and executable on the processor, and the computer program is configured to implement the steps of the control method of the heart-lung sound detection device.

[0015] In addition, to achieve the above object, the application further provides a storage medium, which is a computer readable storage medium, and the storage medium stores a computer program, and the computer program is executed by a processor to implement the steps of the control method of the heart-lung sound detection device.

[0016] The one or more technical solutions provided by the application have at least the following technical effects: By acquiring the deformation amount of the PCB mainboard detected by the pressure-sensitive chip and the inertial parameter detected by the inertial measurement unit when the pressure detection process is triggered, then updating the preset force transmission coefficient based on the inertial parameter to obtain a target force transmission coefficient, and finally calculating the pressure detection value according to the target force transmission coefficient and the deformation amount, the calculation result of the pressure detection value is ensured to correspond to the real deformation data, so that the user can still calculate the pressure value meeting the requirement of the pressing position even if the pressing position deviates, effectively solving the problem that the pressure detection value is difficult to accurately judge, and further improving the accuracy when the heart-lung sound is detected by pressing the intelligent ring. BRIEF DESCRIPTION OF DRAWINGS

[0017] The accompanying drawings, which are incorporated into and form a part of the specification, illustrate preferred embodiments of the present application and, together with the description, serve to explain the principles of the application.

[0018] In order to more clearly illustrate the technical solutions in the embodiments of the present application or the prior art, the accompanying drawings needed to be used in the embodiments or prior art description will be briefly introduced. Obviously, for those skilled in the art, based on the drawings, other drawings can be obtained without creative labor.

[0019] Figure 1 The annular section schematic diagram of the heart and lung sound detection device of the present application; Figure 2 The structure schematic diagram between the outer shell and the inner shell of the heart and lung sound detection device of the present application; Figure 3 The flow schematic diagram of the first embodiment of the control method of the heart and lung sound detection device of the present application; Figure 4 The flow schematic diagram of the second embodiment of the control method of the heart and lung sound detection device of the present application; Figure 5 The force schematic diagram of the heart and lung sound detection ring provided by the second embodiment of the present application; Figure 6 The force surface schematic diagram of the heart and lung sound detection ring provided by the second embodiment of the present application; Figure 7 The force schematic diagram of the heart and lung sound detection ring provided by the second embodiment of the present application; Figure 6 The pressure change schematic diagram obtained after the pressure test of the force area of the heart and lung sound detection ring provided by the second embodiment of the present application.

[0020] Explanation of the reference signs: 1. Outer shell; 2. Pressure sensing chip; 3. Inertial sensor; 4. PCB mainboard; 5. PCB mainboard support.

[0021] 6. Force transmission medium.

[0022] The purpose implementation, functional characteristics and advantages of the present application will be further explained by combining with the embodiments and referring to the drawings. DETAILED DESCRIPTION

[0023] It should be understood that the specific embodiments described herein are only used to explain the technical solutions of the present application, and are not used to limit the present application.

[0024] The main solution of the embodiments of the present application is: obtaining the deformation amount of the PCB mainboard detected by the pressure sensing chip and the inertial parameter detected by the inertial measurement unit when the pressure detection process is triggered; The preset force conduction coefficient is updated based on the inertia parameter, and a target force conduction coefficient is obtained. According to the target force conduction coefficient and the deformation variable, a pressure detection value of the heart-lung sound detection device is calculated.

[0025] In this embodiment, for the convenience of description, the following is described with the heart-lung sound detection device as the execution subject.

[0026] Human heart-lung sound data can be used to judge the health status. When using a smart ring type product to test heart-lung sound, the user needs to press the smart ring against the chest wall to collect data. In order to meet the data stability requirement, different users with different body shapes need to use different pressing forces to ensure the accuracy of the data.

[0027] However, the pressure sensor inside the smart ring is extremely sensitive to the pressing position. Even if the pressing force is the same, the sensor return value is quite different under different pressing positions, which makes it difficult for the user to judge whether the pressure meets the standard, and reduces the accuracy of heart-lung sound detection.

[0028] The present application provides a solution. By obtaining the PCB mainboard deformation variable detected by the pressure sensing chip and the inertia parameter detected by the inertia measurement unit when the pressure detection process is triggered, the real deformation information of the contact between the ring and the skin and the interference information when the pressing position of the ring deviates are captured at the same time. Then, the preset force conduction coefficient is updated based on the inertia parameter to obtain the target force conduction coefficient, so that the force conduction coefficient dynamically adapts to the force conduction characteristics when the pressing position deviates under different activity states of the hand. Finally, the pressure detection value is calculated according to the target force conduction coefficient and the deformation variable, so that the calculation result of the pressure detection value corresponds to the real deformation data. Even if the pressing position deviates, the user can still calculate the pressure value that meets the requirement of the pressing position, effectively solving the problem that the pressure detection value is difficult to accurately judge, and improving the accuracy of heart-lung sound detection by pressing the smart ring. The ring type wearable device can accurately calculate the pressing force even if the user wears it with deviation.

[0029] In order to better understand the technical scheme of the present application, the following will be described in detail in combination with the drawings and specific embodiments.

[0030] Please refer to Figure 1 and Figure 2 In the embodiment of the present application, the heart-lung sound detection device includes a shell 1 and an inner shell (not shown in the figure), the shell 1 is connected with the inner shell and forms an annular accommodating cavity. It can be understood that the annular accommodating cavity is the cavity between the shell 1 and the inner shell. The annular accommodating cavity is provided with a pressure sensing chip 2 and an inertia sensor 3. The internal structure of the annular accommodating cavity is as shown in Figure 2As shown, the heart-lung sound detection device further comprises a PCB mainboard 4, wherein the pressure-sensitive chip 2 is arranged between the PCB mainboard 4 and the inner shell, and the pressure-sensitive chip 2 can be a piezoelectric or capacitive pressure-sensitive chip. The PCB mainboard 4 and the outer shell 1 are further provided with a PCB mainboard support 5.

[0031] In this embodiment, the pressure-sensitive chip 2 is used to detect the deformation amount of the PCB mainboard 4, and the inertial measurement unit 3 is used to detect the inertial parameters of the heart-lung sound detection device. In addition, the heart-lung sound detection device is further provided with a calculation module (not shown in the figure) for calculating the pressure value according to the deformation amount and the inertial parameters.

[0032] Based on this, when the heart-lung sound detection device is a heart-lung sound detection ring, the wearer wears the ring and presses the ring on the chest wall position, the pressure-sensitive chip 2 detects the deformation amount of the PCB board 4 at this time, the inertial measurement unit obtains the inertial parameters that can be used to calculate the current position and wearing angle of the ring, and then calculates the actual pressing deviation position according to the inertial parameters, and finally calculates the pressure value based on the calculation module through the deformation amount and the pressing deviation position, and outputs the pressure value through the output component. In this way, the wearing angle and position of the ring are judged by combining the inertial measurement unit, so as to adjust the pressure value, improve the pressure detection accuracy, and further improve the accuracy of subsequent heart-lung sound detection based on the pressure value. In this way, the micro-deformation amount of the PCB mainboard 4 inside the ring is detected by one sensor, which can be converted into the pressing force applied outside the ring.

[0033] Please continue to refer to Figure 2 In the heart-lung sound detection device, the PCB mainboard 4 and the outer shell 1 are further provided with a force transmission medium 6. Optionally, the force transmission ring is preferably epoxy resin and silicone rubber pad, which is filled with epoxy resin and silicone rubber pad inside the ring, so as to improve the stability of the deformation of the PCB mainboard when the heart-lung sound detection device is pressed. Please continue to refer to Figure 2 After the pressing force is applied outside the ring, the force transmission path is: deformation of the outer shell 6 -> deformation of the epoxy resin and the silicone rubber pad, i.e. the force transmission medium 6 between the outer shell 6 and the PCB mainboard 4 -> deformation of the PCB mainboard 6 -> deformation detected by the pressure sensor. In this embodiment, the objects with different force transmission medium parameters inside the ring are fused, and the mechanical transmission is carried out according to the unified mechanical transmission medium parameters, so as to realize the linearization of the mechanical transmission and improve the accuracy of the pressure result when collecting pressure based on the heart-lung sound detection ring.

[0034] Further, the heart-lung sound detection device further comprises an output component (not shown in the figure) for outputting the current pressure value of the heart-lung sound detection device during heart-lung sound detection, and a detection module (not shown in the figure) for detecting heart-lung sound data.

[0035] It can be understood that when the heart-lung sound detection device detects heart-lung sound, the collection of heart-lung sound depends on the acoustic coupling of the device and the chest wall. If the pressure is insufficient, a gap or loose contact between the device and the chest wall is easy to occur, and the heart-lung sound is greatly attenuated due to air blockage and tissue elasticity scattering in the propagation process, resulting in extremely low signal-to-noise ratio of the collected signal. If the pressure is too large, the chest wall tissue such as muscle and fat will be deformed due to excessive compression, changing the propagation path and acoustic characteristics such as frequency response and amplitude of the heart-lung sound, resulting in signal distortion.

[0036] If the user makes a mistake in judging the pressure value due to the deviation of the pressing position, the heart-lung sound detection device will be frequently in an insufficient pressure state or an excessive pressure state, directly damaging the integrity of the heart-lung sound signal and causing the accuracy to decrease.

[0037] Based on this, the embodiment of the present application provides a control method of a heart-lung sound detection device. The embodiment takes a heart-lung sound detection ring as an example, and refers to Figure 3 , Figure 3 FIG. 1 is a flowchart of a first embodiment of the control method of the heart-lung sound detection device.

[0038] In the embodiment, the control method of the heart-lung sound detection device includes steps S10-S30: In step S10, the deformation amount of the PCB mainboard detected by the pressure-sensitive chip and the inertial parameter detected by the inertial measurement unit are acquired when the pressure detection process is triggered.

[0039] In the embodiment, the PCB mainboard will be slightly bent or deformed under the pressure. At this time, the deformation amount of the PCB mainboard can be collected by the pressure-sensitive chip 2. The inertial measurement unit (IMU) is a sensor module integrating an accelerometer and a gyroscope. Through the inertial parameters collected by the inertial measurement unit, it can be judged whether the space posture of the ring deviates from the preset wearing reference under the current pressing state. For example, when the ring is normally worn and pressed against the chest wall based on the ring, the pressing force is completely transmitted along the pressing axis, the Z acceleration is stable in the reference range, and there is no additional force component in the other two axes in space. At this time, if the ring is worn to the inside of the finger, for example, by 10°, the force will be decomposed into one axis when pressing. At this time, the acceleration of the pressing axis decreases due to the partial force deviation, and the acceleration data of the axis decomposed by the force is abnormal. Similarly, the principle of the deviation judgment process through the gyroscope data is similar, which will not be described herein. The inertial parameters usually include the acceleration parameters detected by the accelerometer and the angular velocity parameters detected by the gyroscope, and other inertial parameters that help to detect the deviation of the ring.

[0040] For example, when the ring is in contact with the user and the pressure changes, the PCB mainboard generates a bending deformation of 0.01-0.05 mm, the pressure-sensitive chip converts the deformation into a 0.5-2.5 V voltage signal, and the voltage signal is digitized and displayed through an analog-to-digital converter. At the same time, when the inertial sensor synchronous signal is triggered, the acceleration and angular velocity of the hand movement are read and the time stamp is recorded.

[0041] The present embodiment collects the deformation associated with the pressure and the inertia parameter associated with the interference factor to provide a data basis for subsequent pressure value detection.

[0042] In step S20, the preset force transmission coefficient is updated based on the inertia parameter to obtain a target force transmission coefficient.

[0043] In the present embodiment, the pressure size is equal to the force transmission coefficient multiplied by the signal value corresponding to the deformation. The preset force transmission coefficient is the force attenuation / amplification ratio of the pressure transmitted to the PCB mainboard when the ring is not deviated. The target force transmission coefficient is the force transmission coefficient corresponding to the deviation position.

[0044] As an optional implementation, when updating the preset force transmission coefficient, the current actual pressing position can be calculated based on the inertia parameter, and then a data table of different force transmission coefficients corresponding to different pressing positions stored in the database is queried based on the data table to update and cover the preset force transmission coefficient.

[0045] Optionally, the preset force transmission coefficient can also be updated based on the pressure deformation coefficient between the pressing position and the standard pressing position to obtain the target force transmission coefficient. For example, if the pressure deformation coefficient is 0.9 of the standard position, the target force transmission coefficient is 0.9 of the preset force transmission coefficient.

[0046] Optionally, the deviation angle between the current position and the standard pressing position can also be calculated, and the angle component of the deviation angle under the standard pressing position, i.e., cosθ / sinθ, is calculated, and then the result is multiplied by the preset force transmission coefficient to obtain the target force transmission coefficient.

[0047] The above parameters are only used for explanation and illustration, and are not limited to the present application.

[0048] It can be understood that if there is no wearing deviation, the target force transmission coefficient is the preset force transmission coefficient.

[0049] In step S30, the pressure detection value of the heart-lung sound detection device is calculated according to the target force transmission coefficient and the deformation.

[0050] In the embodiment, the target force conduction coefficient is K, the deformation variable is x, and the heart-lung sound detection ring calculates the pressure detection value. First, the base pressure S is calculated through the deformation variable parameter, and then S is multiplied by the target force conduction coefficient K to obtain the pressure detection value that eliminates the wearing deviation of the ring. The way of calculating the pressure value through the deformation variable parameter is a prior art, and the present application will not be described here.

[0051] Further, if the pressure detection value is in the abnormal interval, it means that the current pressure value is too large or too small, and at this time, the prompt information of pressure value adjustment needs to be output to allow the user to adjust the actual pressing force based on the prompt information.

[0052] Optionally, when the pressure detection value meets the preset pressure value, the heart-lung sound detection process can be triggered, that is, the heart-lung sound detection is performed only under normal pressure to avoid reducing the accuracy of the detection result due to excessive or insufficient pressure.

[0053] The embodiment provides a control method of a heart-lung sound detection device. By collecting the deformation variable and the inertia parameter of the PCB mainboard, capturing the signal parameter under the pressure and the inertia parameter for judging whether the ring is worn, then calculating the angle component of the current position or the pressure deformation coefficient of the current position based on the inertia parameter, updating the force conduction coefficient through the angle component or the pressure deformation coefficient, and finally calculating the actual pressure value through the initial pressure value corresponding to the updated force conduction coefficient and the deformation variable parameter, the user can still calculate the pressure value meeting the requirements of the pressing position even if the pressing position deviates, and the accuracy of the subsequent heart-lung sound detection based on the pressure value is improved.

[0054] Based on the first embodiment of the present application, in the second embodiment of the present application, the same or similar contents as the above first embodiment can be referred to the above introduction, and will not be described hereinafter. On this basis, when updating the preset force conduction coefficient through the angle component, the angle component cosθ / sinθ is less than or equal to 1, that is, the target force conduction coefficient is less than or equal to the preset force conduction coefficient. However, the pressure deformation coefficient between the current pressing position and the standard pressing position cannot accurately reflect the component of the deviation position, so in the embodiment, the angle deviation amount and the pressure deformation coefficient can be combined for calculation to improve the accuracy and effectiveness of the calculation of the target force conduction coefficient.

[0055] Specifically, the inertia parameter includes a detection angle, please refer to Figure 4 , step S20 further includes steps S21-S23: Step S21, determining the angle deviation amount between the detection angle and the preset angle, and calculating the angle component of the angle deviation amount under the preset angle.

[0056] In the embodiment, the preset angle is an angle corresponding to a preset force transmission coefficient, and the preset angle is a fixed value, so that the angle deviation amount can be calculated directly based on the detected angle.

[0057] For example, the preset angle is θ0, the detected angle is θx, the angle deviation amount is θx-θ0, and the angle component is cos(θx-θ0).

[0058] In step S22, the pressing area is determined according to the angle deviation amount, and the pressure deformation coefficient of the pressing area is obtained.

[0059] Please continue to refer to Figure 2 Due to the internal device structure of the heart-lung sound detection ring, the force transmission medium 6 is usually in contact with the PCB mainboard at a certain position, so that when the pressure position is different, the force is transmitted to the force transmission medium 6, and then the effect of deforming the PCB mainboard 4 by the force transmission medium is also different. That is, the sensitivity of the force transmission medium 6 to the force is different at different pressure positions, and the pressure deformation coefficient of the position is also different.

[0060] Therefore, in the embodiment, when obtaining the pressure deformation coefficient of the pressing area, the pressing area is first determined according to the angle deviation amount, then the deviation distance between the pressing area and the initial area, which is the area corresponding to the preset angle, i.e., the standard pressing area, is determined, and finally the pressure deformation coefficient of the pressing area is calculated according to the deviation distance and the preset linear relationship between the deviation distance and the deformation coefficient. The preset linear relationship between the deviation distance and the deformation coefficient is an approximately linear curve fitted after calibration of multiple points before the product is shipped, and the specific obtaining process is not limited by the present application.

[0061] In step S23, the product of the angle component, the pressure deformation coefficient, and the preset force transmission coefficient is calculated to obtain the target force transmission coefficient.

[0062] For example, the target force transmission coefficient kx=cos(θx-θ0)*F(x)*k0, wherein k0 is the preset force transmission coefficient, and F(x) is the pressure deformation coefficient.

[0063] For the purpose of understanding the implementation process of the control method of the heart-lung sound detection device obtained by combining the above-mentioned first embodiment, please refer to Figure 5 , Figure 5 is a schematic diagram of force on different areas of the ring, including P1, P2, and P3, and Figure 6 is a top view of the force area of the ring shown in Figure 5 , Figure 6 P1, P2, and P3 in Figure 5 correspond to the areas in

[0064] Please refer to Figure 7 When the force is applied at the P2 position, the corresponding force transmission coefficient is k0, and the corresponding angle is θ0. When the same force is tested at the P1 and P3 positions, the force transmission coefficients are k1 and k2, respectively, and the corresponding deviation angles are θ1 and θ2, respectively. Wherein, F is the pressure size, and S is the corresponding value of the deformation variable. It can be seen that the force transmission coefficients at different positions are significantly different. k1 at the P1 position is greater than k0, indicating that the position sensor has higher sensitivity to force, and the corresponding pressure is greater under the same deformation variable. k2 at the P3 position is less than k0, indicating that it has lower sensitivity to force, and the corresponding pressure is smaller under the same deformation variable.

[0065] It can be understood that this difference is due to the different structures or stress characteristics of each position, resulting in changes in the efficiency of force transmission during transmission, ultimately making the pressure performance at different positions different in force due to the deviation of k even based on the same F=k×S relationship. Therefore, the present embodiment needs to calculate the pressure deformation coefficient of the pressing area according to the deviation distance and the preset linear relationship between the deviation distance and the deformation coefficient.

[0066] The present embodiment provides a control method of a heart and lung sound detection device. When calculating the force transmission coefficient of the deviation pressing position, the angle component is calculated by the deviation angle, and the pressure deformation coefficient of the pressing area is calculated by the deviation distance, the preset linear relationship between the deviation distance and the deformation coefficient. Finally, the product of the angle component, the pressure deformation coefficient and the preset force transmission coefficient is calculated, so as to combine the component of the force actually needed to be pressed by the deviation pressing position, and the sensitivity to force based on the position, to calculate the target force transmission coefficient conforming to the deviation pressing position, solve the problem of inaccurate pressure measurement at different pressing positions due to the sensitivity of the sensor, and improve the accuracy of pressure detection at the deviation pressing position.

[0067] Based on the first embodiment of the present application, in the third embodiment of the present application, the same or similar contents as the above first embodiment can be referred to the above introduction, and will not be repeated hereinafter. On this basis, the corresponding pressing behavior model under different inertia parameters can also be constructed by long-term collection of user wearing posture habits, pressing force habits and other parameters, and the pressure that should be detected under the current inertia parameter is calculated based on the data of the pressing behavior model, so as to judge whether the user presses with accurate force when the pressing position deviates.

[0068] Therefore, after step S30, the historical pressing data of the user can be acquired, and a pressing behavior model of the user is constructed according to the historical pressing data, and then the inertia parameter exists in the pressure data associated in the pressing behavior model, for example, when the user presses at a position with a deviation angle of 10°, the detected pressure parameter is usually 10-15 Pa, at this time, it is needed to judge whether the detected pressure value at the same deviation angle is in the interval. Therefore, if the pressure detection value is in the pressure floating interval corresponding to the pressure data, it indicates that the current pressure data is normal, triggering the heart-lung detection process, or recording the current time stamp, so as to collect the data at the current time stamp as the heart-lung sound detection data.

[0069] Based on the first embodiment of the present application, in the fourth embodiment of the present application, the same or similar contents as the above first embodiment can be referred to the above introduction, and will not be described in detail. On this basis, in addition to accurately judging the deviation position in the detection process, the probability of the ring pressing deviation under the current parameter can also be judged before pressing. Therefore, before step S10, when the start instruction of the heart-lung sound detection device is detected, the current inertia parameter detected by the inertia measurement unit at the current time can be acquired, and then the confidence degree of the heart-lung sound detection device wearing deviation is calculated according to the current inertia parameter and the historical inertia parameter, for example, in the current inertia parameter, the acceleration is X and the angular velocity is Y, and in the historical inertia data, the acceleration is [X-1, X+1] and the angular velocity is [Y-1, Y+1], there are a total of 10 groups of data, and the number of times of updating the force transmission coefficient is 4 times, at this time, it can be judged that the confidence degree of the wearing deviation is about 40%, and finally if the confidence degree is greater than the preset confidence degree, the pressing position prompt information is directly outputted, so that the user adjusts the wearing position of the ring or adjusts the pressing position.

[0070] The present application provides a heart-lung sound detection ring, which comprises at least one processor and a memory connected with the at least one processor; wherein the memory stores instructions executable by the at least one processor, and the instructions are executed by the at least one processor to enable the at least one processor to perform the control method of the heart-lung sound detection device in the first embodiment.

[0071] The heart-lung sound detection ring provided by the present application adopts the control method of the heart-lung sound detection device in the above embodiments, which can solve the technical problem that the pressure detection value is difficult to judge when detecting heart-lung sound based on a wearable device ring, resulting in low accuracy of heart-lung sound detection. Compared with the prior art, the heart-lung sound detection ring provided by the present application has the same beneficial effects as the control method of the heart-lung sound detection device provided by the above embodiments, and other technical features in the heart-lung sound detection ring are the same as the features disclosed in the previous embodiment method, which will not be described here.

[0072] It should be understood that various parts of the present application can be realized in hardware, software, firmware, or a combination thereof. In the description of the above-described embodiments, specific features, structures, materials or characteristics can be combined in any one or more embodiments or examples in a suitable manner.

[0073] The above description is merely illustrative of the application and is not intended to limit the scope of the application. Any variations and modifications that can be made by those skilled in the art within the spirit and scope of the application are intended to be included in the scope of the application. Therefore, the scope of the application should be determined by the scope of the claims.

[0074] The present application provides a computer readable storage medium having stored thereon computer readable program instructions (i.e., a computer program) for performing the control method of the heart-lung sound detection device in the above-described embodiments.

[0075] The computer readable storage medium provided by the present application may, for example, be a U disk, but is not limited to an electrical, magnetic, optical, electromagnetic, infrared, or semiconductor system, system, or device, or any combination thereof. More specific examples of computer readable storage media can include, but are not limited to, an electrical connection having one or more conductive wires, a portable computer diskette, a hard disk, a random access memory, a read-only memory, an erasable programmable read-only memory (EPROM or flash memory), an optical fiber, a portable compact disk read-only memory (CD-ROM), an optical storage device, a magnetic storage device, or any suitable combination of the above. In the present embodiment, the computer readable storage medium can be any tangible medium that contains or stores a program that can be used by or in conjunction with an instruction execution system, system, or device. The program code contained on the computer readable storage medium can be transmitted in any suitable medium, including but not limited to electrical wire, optical cable, radio frequency (RF), etc., or any suitable combination thereof.

[0076] The above-described computer readable storage medium can be included in the heart-lung sound detection ring; or can exist separately and not be assembled into the heart-lung sound detection ring.

[0077] The above-described computer readable storage medium carries one or more programs, which, when executed by the heart-lung sound detection ring, cause the heart-lung sound detection ring to: obtain the deformation amount of the PCB mainboard detected by the pressure sensing chip and the inertial parameter detected by the inertial measurement unit when the pressure detection process is triggered; Update the preset force transmission coefficient based on the inertial parameter to obtain a target force transmission coefficient; Calculate a pressure detection value of the heart-lung sound detection device according to the target force transmission coefficient and the deformation variable.

[0078] Computer program code for carrying out operations of the present application can be written in any combination of one or more programming languages, including an object oriented programming language such as Java, Smalltalk, C++ or the like and conventional procedural programming languages, such as the "C" programming language or similar programming languages. The program code can execute entirely on the user's computer, partly on the user's computer, as a stand-alone software package, partly on the user's computer and partly on a remote computer or entirely on the remote computer or server. In the latter scenario, the remote computer can be connected to the user's computer through any type of network, including a local area network (LAN) or a wide area network (WAN), or the connection can be made to an external computer (for example, through the Internet using an Internet Service Provider).

[0079] The flow diagrams and the block diagrams in the drawings are illustrations of architectures, functionalities, and operations of possible implementations of systems, methods, and computer program products according to various embodiments of present application. In this regard, each block in the flow diagrams or block diagrams can represent a module, a procedure, or a part of code, which comprises one or more executable instructions for implementing the specified logical functions. It should also be noted that in some alternative implementations, the functions noted in the blocks can occur in a different order than that noted in the figures. For example, two blocks noted in succession can in fact be executed substantially concurrently or in the opposite order, depending on the functionality involved. It is also noted that each block and combination of blocks in the block diagrams or flow diagrams can be implemented by dedicated hardware-based systems which perform the specified functions or operations, or by a combination of dedicated hardware and computer instructions.

[0080] The modules involved in the embodiments of the present application can be implemented in the manner of software or hardware. Among them, the name of the module does not constitute a limitation to the unit itself in some cases.

[0081] The readable storage medium provided by the application is a computer readable storage medium, which stores computer readable program instructions (i.e. computer programs) for executing the control method of the above-mentioned heart-lung sound detection device, and can solve the technical problem that the pressure detection value is difficult to judge when detecting heart-lung sound based on a wearable device ring, resulting in low accuracy of heart-lung sound detection. Compared with the prior art, the beneficial effects of the computer readable storage medium provided by the application are the same as those of the control method of the heart-lung sound detection device provided by the above-mentioned embodiments, and will not be repeated here.

[0082] The above-mentioned is only part of the embodiments of the application, and does not limit the patent scope of the application. Any equivalent structural transformation, direct / indirect application in other related technical fields based on the technical concept of the application, and the contents of the specification and drawings are included in the patent protection scope of the application.

Claims

1. A control method for a cardiopulmonary sound detection device, characterized in that, The cardiopulmonary sound detection device includes an outer shell and an inner shell, the outer shell and the inner shell being connected and enclosing an annular cavity; and a PCB motherboard, a pressure-sensitive chip, and an inertial measurement unit disposed within the annular cavity. The control method for the cardiopulmonary sound detection device includes: When the pressure detection process is triggered, the pressure-sensitive chip detects the deformation of the PCB motherboard, and the inertial measurement unit detects the inertial parameters. The target force transmission coefficient is obtained by updating the preset force transmission coefficient based on the inertial parameters. The pressure detection value of the cardiopulmonary sound detection device is calculated based on the target force transmission coefficient and the deformation.

2. The control method for the cardiopulmonary sound detection device as described in claim 1, characterized in that, The inertial parameters include the detection angle, and the step of updating the preset force transmission coefficient based on the inertial parameters to obtain the target force transmission coefficient includes: Determine the angular deviation between the detection angle and the preset angle, and calculate the angular component of the angular deviation at the preset angle, where the preset angle is the angle corresponding to the preset force transmission coefficient; The pressing area is determined based on the angular deviation, and the pressure deformation coefficient of the pressing area is obtained. The target force transmission coefficient is obtained by calculating the product of the angular component, the pressure deformation coefficient, and the preset force transmission coefficient.

3. The control method for the cardiopulmonary sound detection device as described in claim 2, characterized in that, The steps of determining the pressing area based on the angular deviation and obtaining the pressure deformation coefficient of the pressing area include: The pressing area is determined based on the angular deviation. Determine the deviation distance between the pressing area and the initial area, wherein the initial area is the area corresponding to a preset angle; The pressure deformation coefficient of the pressing area is calculated based on the deviation distance and the preset linear relationship between the deviation distance and the deformation coefficient.

4. The control method for the cardiopulmonary sound detection device as described in claim 1, characterized in that, After the step of calculating the pressure detection value of the cardiopulmonary sound detection device based on the target force transmission coefficient and the deformation, the control method of the cardiopulmonary sound detection device further includes: If the pressure detection value is in an abnormal range, a prompt message for adjusting the pressure value will be output. If the pressure detection value meets the preset pressure value, the heart and lung sound detection process is triggered.

5. The control method for the cardiopulmonary sound detection device as described in claim 1, characterized in that, After the step of calculating the pressure detection value of the cardiopulmonary sound detection device based on the target force transmission coefficient and the deformation, the control method of the cardiopulmonary sound detection device further includes: Obtain the user's historical press data, and construct the user's press behavior model based on the historical press data; Determine the pressure data associated with the inertial parameters in the pressing behavior model; If the pressure detection value is within the pressure fluctuation range corresponding to the pressure data, the heart and lung sound detection process is triggered.

6. The control method for the cardiopulmonary sound detection device as described in claim 1, characterized in that, Before the step of obtaining the deformation of the PCB motherboard detected by the pressure-sensitive chip and the inertial parameters detected by the inertial measurement unit when the pressure detection process is triggered, the control method of the cardiopulmonary sound detection device further includes: When the activation command of the cardiopulmonary sound detection device is detected, the current inertial parameters detected by the inertial measurement unit are obtained; Based on the current inertial parameters and historical inertial parameters, calculate the confidence level of the wearing deviation of the cardiopulmonary sound detection device; If the confidence level is greater than the preset confidence level, output a pressing position prompt message.

7. A heart and lung sound detection device, characterized in that, The cardiopulmonary sound detection device includes: An outer shell and an inner shell, wherein the outer shell and the inner shell are connected and enclose a ring-shaped receiving cavity; The PCB motherboard is disposed within the annular receiving cavity; A pressure-sensitive chip is disposed between the PCB motherboard and the inner shell to detect the deformation of the PCB motherboard; An inertial measurement unit is disposed within the annular cavity and is used to detect the inertial parameters of the cardiopulmonary sound detection device; The calculation module is used to calculate the pressure value based on the deformation and the inertial parameters.

8. The cardiopulmonary sound detection device as described in claim 7, characterized in that, A force-conducting medium is provided between the PCB motherboard and the housing, and the force-conducting medium is epoxy resin and silicone pad; An output component is used to output the current pressure value of the cardiopulmonary sound detection device during cardiopulmonary sound detection; The detection module is used to detect heart and lung sound data.

9. A ring for detecting heart and lung sounds, characterized in that, The cardiopulmonary sound detection ring includes: a memory, a processor, a computer program stored in the memory and executable on the processor, and a cardiopulmonary sound detection device as claimed in any one of claims 7-8, wherein the computer program is configured to implement the steps of the control method for the cardiopulmonary sound detection device as claimed in any one of claims 1 to 6.

10. A storage medium, characterized in that, The storage medium is a computer-readable storage medium, and a computer program is stored on the storage medium. When the computer program is executed by a processor, it implements the steps of the control method of the cardiopulmonary sound detection device as described in any one of claims 1 to 6.

Images