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

Abstract

This application discloses a control method, device, cardiopulmonary sound detection ring, and storage medium for a cardiopulmonary sound detection device, relating to the field of wearable device technology. The disclosed control method for 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 includes: acquiring 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; updating a preset force transmission coefficient based on the inertial parameters to obtain a target force transmission coefficient; and calculating the pressure detection value of the cardiopulmonary sound detection device based on the target force transmission coefficient and the deformation. This ensures that the calculated pressure detection value corresponds to the actual deformation data, accurately determining the pressure value and thus improving the accuracy of cardiopulmonary sound detection.

Description

Technical Field

[0001] This application relates to the field of wearable device technology, and in particular to a control method, device, cardiopulmonary sound detection ring, and storage medium for a cardiopulmonary sound detection device. Background Technology

[0002] Human heart and lung sounds can be used to assess health status. When using smart ring-type products for heart and lung sound testing, users need to place the smart ring firmly against their chest wall and collect data by pressing. To ensure data stability, users of different body types need to use different pressure levels to guarantee data accuracy.

[0003] However, the pressure sensor inside the smart ring is extremely sensitive to the pressure position. Even if the pressure is the same, the sensor return value varies greatly under different pressure positions, making it difficult for users to judge whether the pressure is sufficient and reducing the accuracy of heart and lung sound detection.

[0004] The above content is only used to help understand the technical solution of this application and does not represent an admission that the above content is prior art. Summary of the Invention

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

[0006] To achieve the above objectives, this application proposes a control method for a cardiopulmonary sound detection device. 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 receiving cavity; and a PCB motherboard, a pressure-sensitive chip, and an inertial measurement unit disposed within the annular receiving 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.

[0007] In one embodiment, the inertial parameter includes 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 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.

[0008] In one embodiment, the step of determining the pressing area based on the angular deviation and obtaining the pressure deformation coefficient of the pressing area includes: 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.

[0009] In one embodiment, 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.

[0010] In one embodiment, 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.

[0011] In one embodiment, prior to the step of acquiring 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 acquired; 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, an instruction to adjust the wearing position is output.

[0012] Furthermore, to achieve the above objectives, this application also proposes a cardiopulmonary sound detection device, characterized in that the cardiopulmonary sound detection device comprises: 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.

[0013] In one embodiment, a force-conducting medium is provided between the PCB motherboard and the housing, the force-conducting medium being epoxy resin and a silicone pad; An output component is used to output the current pressure value of the cardiopulmonary sound detection device during cardiopulmonary sound detection; a detection module is used to detect cardiopulmonary sound data.

[0014] In addition, to achieve the above objectives, this application also proposes a cardiopulmonary sound detection ring, which includes: a memory, a processor, and a computer program stored in the memory and executable on the processor, the computer program being configured to implement the steps of the control method for the cardiopulmonary sound detection device as described above.

[0015] In addition, to achieve the above objectives, this application also proposes a storage medium, which is a computer-readable storage medium, on which a computer program is stored, and when the computer program is executed by a processor, it implements the steps of the control method for the cardiopulmonary sound detection device as described above.

[0016] One or more technical solutions proposed in this application have at least the following technical effects: By acquiring the PCB motherboard deformation detected by the pressure-sensitive chip and the inertial parameters detected by the inertial measurement unit when the pressure detection process is triggered, the preset force transmission coefficient is updated based on the inertial parameters to obtain the target force transmission coefficient. Finally, the pressure detection value is calculated based on the target force transmission coefficient and the deformation, ensuring that the calculated pressure detection value corresponds to the actual deformation data. This allows the user to calculate the pressure value that meets the requirements of the pressing position even if the pressing position deviates, effectively solving the problem of inaccurate judgment of pressure detection value, and thus improving the accuracy of heart and lung sound detection by pressing the smart ring. Attached Figure Description

[0017] The accompanying drawings, which are incorporated in and form part of this specification, illustrate embodiments consistent with this application and, together with the description, serve to explain the principles of this application.

[0018] To more clearly illustrate the technical solutions in the embodiments of this application or the prior art, the drawings used in the description of the embodiments or the prior art will be briefly introduced below. Obviously, for those skilled in the art, other drawings can be obtained based on these drawings without creative effort.

[0019] Figure 1 This is a schematic diagram of the annular cross-section of the cardiopulmonary sound detection device of this application; Figure 2 This is a schematic diagram of the structure between the outer shell and the inner shell of the cardiopulmonary sound detection device of this application; Figure 3 This is a flowchart illustrating the first embodiment of the control method for the cardiopulmonary sound detection device of this application. Figure 4 This is a flowchart illustrating a second embodiment of the control method for the cardiopulmonary sound detection device of this application. Figure 5 A schematic diagram of the forces acting on the cardiopulmonary sound detection ring provided in the second embodiment of this application; Figure 6 A schematic diagram of the force-bearing surface of the cardiopulmonary sound detection ring provided in the second embodiment of this application; Figure 7 for Figure 6 A schematic diagram of pressure changes obtained after a pressure test was performed on the stressed area.

[0020] Explanation of icon numbers: 1. Outer shell; 2. Pressure-sensitive chip; 3. Inertial sensor; 4. PCB motherboard; 5. PCB motherboard support.

[0021] 6. Force transmission medium.

[0022] The purpose, features, and advantages of this application will be further explained in conjunction with the embodiments and with reference to the accompanying drawings. Detailed Implementation

[0023] It should be understood that the specific embodiments described herein are merely illustrative of the technical solutions of this application and are not intended to limit this application.

[0024] The main solution of this application embodiment is: to obtain 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 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 deformation.

[0025] In this embodiment, for ease of description, the following description uses the cardiopulmonary sound detection device as the main execution subject.

[0026] Human heart and lung sounds can be used to assess health status. When using smart ring-type products for heart and lung sound testing, users need to place the smart ring firmly against their chest wall and collect data by pressing. To ensure data stability, users of different body types need to use different pressure levels to guarantee data accuracy.

[0027] However, the pressure sensor inside the smart ring is extremely sensitive to the pressure position. Even if the pressure is the same, the sensor return value varies greatly under different pressure positions, making it difficult for users to judge whether the pressure is sufficient and reducing the accuracy of heart and lung sound detection.

[0028] This application provides a solution that simultaneously captures the actual deformation information of the ring in contact with the skin and the interference information when the ring's pressure position deviates, by acquiring the PCB motherboard deformation detected by the pressure-sensitive chip and the inertial parameters detected by the inertial measurement unit when the pressure detection process is triggered. Then, based on the inertial parameters, the preset force transmission coefficient is updated to obtain the target force transmission coefficient, so that the force transmission coefficient dynamically adapts to the force transmission characteristics when the pressing position deviates under different hand activity states. Finally, the pressure detection value is calculated based on the target force transmission coefficient and deformation, ensuring that the calculated pressure detection value corresponds to the actual deformation data. This allows the user to calculate the pressure value that meets the requirements of the pressing position even when the pressing position deviates, effectively solving the problem of inaccurate judgment of pressure detection value. This improves the accuracy of cardiopulmonary sound detection by pressing a smart ring, enabling wearable ring devices to accurately calculate the applied pressing pressure even when the user wears the ring incorrectly.

[0029] To better understand the technical solution of this application, a detailed description will be provided below in conjunction with the accompanying drawings and specific implementation methods.

[0030] Please refer to Figure 1 and Figure 2 In this embodiment, the cardiopulmonary sound detection device includes an outer shell 1 and an inner shell (not shown in the figure). The outer shell 1 and the inner shell are connected and enclose a ring-shaped receiving cavity; it can be understood that the ring-shaped receiving cavity is the cavity between the outer shell 1 and the inner shell. A pressure-sensitive chip 2 and an inertial sensor 3 are disposed inside the ring-shaped receiving cavity. The internal structure of the ring-shaped receiving cavity is as follows. Figure 2As shown, the cardiopulmonary sound detection device also includes a PCB motherboard 4, wherein a pressure-sensitive chip 2 is disposed between the PCB motherboard 4 and the inner shell. The pressure-sensitive chip 2 can be a piezoelectric or capacitive pressure-sensitive chip. A PCB motherboard support 5 is also disposed between the PCB motherboard 4 and the outer shell 1.

[0031] In this embodiment, the pressure-sensitive chip 2 is used to detect the deformation of the PCB motherboard 4, while the inertial measurement unit 3 is used to detect the inertial parameters of the cardiopulmonary sound detection device. Furthermore, the cardiopulmonary sound detection device is also equipped with a calculation module (not shown in the figure) for calculating pressure values ​​based on the deformation and the inertial parameters.

[0032] Based on this, when the heart and lung sound detection device uses a ring for heart and lung sound detection, the wearer presses the ring against their chest wall. The pressure-sensitive chip 2 detects the deformation of the PCB board 4 at this time. The inertial measurement unit acquires inertial parameters that can be used to calculate the current position and angle of the ring. Then, based on the inertial parameters, the actual pressing deviation position is calculated. Finally, based on the calculation module, the pressure value is calculated using the deformation and pressing deviation position, and this pressure value is output through the output component. By combining this with the inertial measurement unit to determine the ring's wearing angle and position, the pressure value can be adjusted to improve the accuracy of pressure detection, thereby improving the accuracy of subsequent heart and lung sound detection based on the pressure value. Thus, by detecting the minute deformation of the PCB board 4 inside the ring with a single sensor, the magnitude of the pressing pressure applied to the outside of the ring can be converted into the actual pressure.

[0033] Please continue to refer to Figure 2 In the cardiopulmonary sound detection device, a force-conducting medium 6 is also provided between the PCB motherboard 4 and the outer casing 1. Optionally, the force-conducting ring is preferably made of epoxy resin and silicone pad. By injecting epoxy resin and silicone pad into the cardiopulmonary sound detection device, the stability of the PCB motherboard deformation when the device is pressed is improved. Please continue to refer to Figure 2 After applying pressure to the outside of the ring, the force transmission path is as follows: deformation of the outer shell 1 -> deformation of the epoxy resin between the outer shell 1 and the PCB motherboard 4, and deformation of the silicone pad (force transmission medium 6) -> deformation of the PCB motherboard 4 -> deformation detected by the pressure sensor. This embodiment achieves linearization of force transmission by fusing objects with different force transmission medium parameters inside the ring and transmitting force according to a unified force transmission medium parameter, thereby improving the accuracy of pressure results when collecting pressure based on a heart and lung sound detection ring.

[0034] Furthermore, the cardiopulmonary sound detection device also includes an output component (not shown in the figure) for outputting the current pressure value of the cardiopulmonary sound detection device during cardiopulmonary sound detection, and a detection module (not shown in the figure) for detecting cardiopulmonary sound data.

[0035] Understandably, when a cardiopulmonary sound detection device performs cardiopulmonary sound detection, the acquisition of cardiopulmonary sounds relies on the acoustic coupling between the device and the chest wall. If the pressure is insufficient, gaps or loose contact may occur between the device and the chest wall, causing the cardiopulmonary sounds to be significantly attenuated during propagation due to air obstruction and tissue elastic scattering, resulting in an extremely low signal-to-noise ratio. If the pressure is too high, chest wall tissues such as muscles and fat may deform due to excessive compression, altering the propagation path and acoustic characteristics of the cardiopulmonary sounds, such as frequency response and amplitude, thus distorting the signal.

[0036] If the user misjudges the pressure value due to incorrect pressing position, the heart and lung sound detection device will frequently be in a state of insufficient or excessive pressure, which will directly damage the integrity of the heart and lung sound signal and lead to a decrease in accuracy.

[0037] Based on this, this application provides a control method for a cardiopulmonary sound detection device. This embodiment uses a cardiopulmonary sound detection ring for illustration. Figure 3 , Figure 3 This is a flowchart illustrating the first embodiment of the control method for the cardiopulmonary sound detection device of this application.

[0038] In this embodiment, the control method of the heart and lung sound detection device includes steps S10 to S30: Step S10: When the pressure detection process is triggered, obtain the deformation of the PCB motherboard detected by the pressure-sensitive chip and the inertial parameters detected by the inertial measurement unit.

[0039] In this embodiment, the PCB motherboard undergoes slight bending or deformation under pressure. The deformation of the PCB motherboard can be collected by the pressure-sensitive chip 2. The inertial measurement unit (IMU), as a sensor module integrating an accelerometer and gyroscope, can determine whether the ring's spatial posture deviates from a preset wearing reference under the current pressing state by collecting inertial parameters. For example, when wearing the ring normally and pressing against the chest wall with the ring, the pressing force is transmitted entirely along the pressing axis, the Z-acceleration is stable within the reference range, and there are no additional force components on the other two axes in space. If the ring is worn off-center, such as tilted 10° towards the inside of the finger, the pressing force will be decomposed onto one axis. The acceleration of the pressing axis decreases due to the partial force deflection, and abnormal acceleration data appears on the axis where the force is decomposed. Similarly, the process of determining deviation using gyroscope data is similar in principle and will not be elaborated upon here. The inertial parameters typically include the acceleration parameters detected by the accelerometer, the angular velocity parameters detected by the gyroscope, and other inertial parameters that help detect ring deviation.

[0040] For example, when the ring comes into contact with the user and the pressure changes, the PCB motherboard generates a bending deformation of 0.01 to 0.05 mm. The pressure-sensitive chip converts the deformation into a voltage signal of 0.5 to 2.5 V, which is then digitally displayed via an analog-to-digital converter. Simultaneously, when the inertial sensor synchronization signal is triggered, the acceleration and angular velocity of the hand movement are read, and a timestamp is recorded.

[0041] This embodiment provides a data foundation for subsequent pressure value detection by collecting pressure-related deformation and inertial parameters related to interference factors.

[0042] Step S20: Update the preset force transmission coefficient based on the inertial parameters to obtain the target force transmission coefficient.

[0043] In this embodiment, the pressure magnitude 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 transmitted to the PCB motherboard when the ring is worn without shifting. The target force transmission coefficient is the force transmission coefficient corresponding to the shifted position.

[0044] As an optional implementation, when updating the preset force transmission coefficient, the current actual pressing position can be calculated using inertial parameters. Then, a data table of different force transmission coefficients corresponding to different pressing positions is stored in the database. Based on this data table, the current force transmission coefficient is queried and the preset force transmission coefficient is updated and overwritten.

[0045] Optionally, the preset force transmission coefficient can 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, then 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 angular component of the deviation angle under the standard pressing position, i.e., cosθ / sinθ, can be calculated. Then, the result is multiplied by a preset force transmission coefficient to obtain the target force transmission coefficient.

[0047] The parameters mentioned above are for illustrative purposes only and are not intended to limit this application.

[0048] Understandably, if there is no wearing deviation, the target force transmission coefficient is the preset force transmission coefficient.

[0049] Step S30: Calculate the pressure detection value of the cardiopulmonary sound detection device based on the target force transmission coefficient and deformation.

[0050] In this embodiment, the target force transmission coefficient is K, and the deformation is x. When calculating the pressure detection value of the cardiopulmonary sound detection ring, the base pressure S is first calculated using the deformation parameter. Then, S is multiplied by the target force transmission coefficient K to obtain the pressure detection value after eliminating ring wearing deviation. The method of calculating the pressure value using the deformation parameter is prior art and will not be elaborated upon in this application.

[0051] Furthermore, if the pressure detection value is in an abnormal range, it indicates that the current pressure value is too high or too low. In this case, a prompt message for pressure adjustment needs to be output so that the user can adjust the actual pressing pressure based on the prompt message.

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

[0053] This embodiment provides a control method for a cardiopulmonary sound detection device. By collecting the deformation and inertial parameters of the PCB motherboard, capturing the signal parameters under pressure, and determining whether the ring is worn off-center, the method then calculates the angular component or the pressure deformation coefficient of the current position based on the inertial parameters. The force transmission coefficient is updated using the angular component or the pressure deformation coefficient. Finally, the actual pressure value is calculated using the updated force transmission coefficient and the initial pressure value corresponding to the deformation parameters. This allows the user to calculate the pressure value that meets the requirements of the pressing position even if the pressing position deviates, thereby improving the accuracy of subsequent cardiopulmonary sound detection based on the pressure value.

[0054] Based on the first embodiment of this application, in the second embodiment of this application, the same or similar content as the first embodiment can be referred to the above description, and will not be repeated hereafter. On this basis, when updating the preset force transmission coefficient through the angle component, the angle component cosθ / sinθ is less than or equal to 1, that is, the target force transmission coefficient is less than or equal to the preset force transmission coefficient. However, the pressure deformation coefficient between the current pressing position and the standard pressing position usually cannot accurately reflect the component of the deviation position. Therefore, in this embodiment, the angle deviation and the pressure deformation coefficient can be combined for calculation, thereby improving the accuracy and effectiveness of the target force transmission coefficient calculation.

[0055] Specifically, the inertial parameters include the detection angle; please refer to [reference needed]. Figure 4 Step S20 also includes steps S21 to S23: Step S21: Determine the angle deviation between the detection angle and the preset angle, and calculate the angle component of the angle deviation at the preset angle.

[0056] In this embodiment, the preset angle is the angle corresponding to the preset force transmission coefficient. Since the preset angle is a fixed value, the angle deviation between the two can be directly calculated based on the detection angle.

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

[0058] Step S22: Determine the pressing area based on the angular deviation and obtain the pressure deformation coefficient of the pressing area.

[0059] Please continue to refer to Figure 2 Due to the limitations of the internal structure of the cardiopulmonary sound detection ring, the force transmission medium 6 is usually in contact with the PCB motherboard at a certain position. Therefore, the force transmitted to the force transmission medium 6, and the resulting deformation of the PCB motherboard 4 caused by the force transmission medium, will vary depending on the pressure position. That is, the sensitivity of the force transmission medium 6 to force varies at different pressure positions, and the pressure deformation coefficient at that position will also vary.

[0060] Therefore, in this embodiment, when obtaining the pressure deformation coefficient of the pressing area, the pressing area is first determined based on the angular deviation. Then, the deviation distance between the pressing area and the initial area is determined. The initial area is the area corresponding to the preset angle, i.e., the standard pressing area. Finally, 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. The preset linear relationship between the deviation distance and the deformation coefficient is an approximately linear curve fitted after calibration at multiple points before the product leaves the factory. The specific acquisition process is not limited in this application.

[0061] Step S23: Calculate the product of the angle component, the pressure deformation coefficient, and the preset force transmission coefficient to obtain the target force transmission coefficient.

[0062] For example, the target force transmission coefficient kx = cos(θx-θ0)*F(x)*k0, where K0 is the preset force transmission coefficient and F(x) is the pressure deformation coefficient.

[0063] For example, to help understand the implementation flow of the control method for the cardiopulmonary sound detection device obtained in combination with the first embodiment described above, please refer to... Figure 5 , Figure 5 This is a diagram illustrating the forces acting on different areas of the ring, including P1, P2, and P3. Figure 6 That is Figure 5 The top view of the stress area of ​​the ring shown. Figure 6 P1, P2, P3 and Figure 5 The corresponding regions are shown in the diagram. Among them, P2 is the standard pressure region.

[0064] Please refer to Figure 7 When a force is applied at position P2, the corresponding force transmission coefficient is k0, and the corresponding angle is θ0. When the same force is applied at positions P1 and P3, the force transmission coefficients are k1 and k2, respectively, and the corresponding deviation angles are θ1 and θ2, respectively. Here, F represents the pressure magnitude, and S represents the deformation value. It can be seen that there are significant differences in the force transmission coefficients at different positions. At position P1, k1 is greater than k0, indicating that the sensor is more sensitive to force at this position, and the corresponding pressure is greater for the same deformation. At position P3, k2 is less than k0, indicating that its sensitivity to force is lower, and the corresponding pressure is smaller for the same deformation.

[0065] Understandably, this difference stems from variations in the structure or stress characteristics of different locations, leading to changes in the efficiency of force transmission. Ultimately, even based on the same relationship F=k×S, the pressure performance at different locations will exhibit significant differences in force due to deviations in k. Therefore, this embodiment requires calculating the pressure deformation coefficient of the pressing area based on the deviation distance and the preset linear relationship between the deviation distance and the deformation coefficient.

[0066] This embodiment provides a control method for a cardiopulmonary sound detection device. When calculating the force transmission coefficient at the deviation pressing position, the angular component is calculated through the deviation angle, and the pressure deformation coefficient of the pressing area is calculated through the deviation distance and the preset linear relationship between the deviation distance and the deformation coefficient. Finally, the product of the angular component, the pressure deformation coefficient, and the preset force transmission coefficient is calculated. This, combined with the component of the actual force required at the deviation pressing position and the sensitivity of the position to force, calculates the target force transmission coefficient that matches the deviation pressing position. This solves the problem of inaccurate pressure measurement at different pressing positions due to sensor sensitivity, and improves the accuracy of pressure detection at the deviation pressing position.

[0067] Based on the first embodiment of this application, in the third embodiment of this application, the same or similar content as the first embodiment can be referred to the above description, and will not be repeated hereafter. On this basis, a pressing behavior model corresponding to different inertial parameters can be constructed by collecting parameters such as user wearing posture habits and pressing pressure habits over a long period of time, and the pressure that should be detected under the current inertial parameters can be calculated based on the data of the pressing behavior model, so as to determine whether the user presses with accurate force when the pressing position deviates.

[0068] Therefore, after step S30, the user's historical compression data can be acquired, and a compression behavior model of the user can be constructed based on the historical compression data. Then, it is determined whether the inertial parameters exist in the pressure data associated with the compression behavior model. For example, when the user presses at a position with a deviation angle of 10°, the detected pressure parameter is typically 10-15 Pa. At this point, it is necessary to determine whether the pressure value detected at the same deviation angle falls within this range. Therefore, if the pressure detection value is within the pressure fluctuation range corresponding to this pressure data, it indicates that the current pressure data is normal, triggering the cardiopulmonary detection process, or recording the current timestamp so that the data collected at the current timestamp can be used as cardiopulmonary sound detection data.

[0069] Based on the first embodiment of this application, in the fourth embodiment of this application, the same or similar content as the first embodiment can be referred to the above description, and will not be repeated hereafter. In addition to accurately determining the deviation position during the detection process, the probability of the ring exhibiting a pressing deviation under the current parameters can also be determined before pressing. Therefore, before step S10, when the start command of the cardiopulmonary sound detection device is detected, the current inertial parameters detected by the inertial measurement unit at the current moment can be obtained. Then, based on the current inertial parameters and historical inertial parameters, the confidence level of the cardiopulmonary sound detection device experiencing wearing deviation is calculated. For example, in the current inertial parameters, the acceleration is X and the angular velocity is Y. In the historical inertial data, there are a total of 10 sets of data with acceleration values ​​of [X-1, X+1] and angular velocities of [Y-1, Y+1]. The force transmission coefficient needs to be updated 4 times. At this time, it can be determined that the confidence level of wearing deviation is about 40%. Finally, if the confidence level is greater than the preset confidence level, the pressing position prompt information is directly output so that the user can adjust the wearing position of the ring or adjust the pressing position.

[0070] This application provides a cardiopulmonary sound detection ring, which includes: at least one processor; and a memory communicatively connected to the at least one processor; wherein the memory stores instructions executable by the at least one processor, which are executed by the at least one processor to enable the at least one processor to perform the control method of the cardiopulmonary sound detection device described in the first embodiment above.

[0071] The cardiopulmonary sound detection ring provided in this application, employing the control method of the cardiopulmonary sound detection device in the above embodiments, can solve the technical problem of low accuracy in cardiopulmonary sound detection due to the difficulty in judging pressure detection values ​​when using a wearable device ring for detection. Compared with the prior art, the beneficial effects of the cardiopulmonary sound detection ring provided in this application are the same as those of the control method of the cardiopulmonary sound detection device provided in the above embodiments, and other technical features of the cardiopulmonary sound detection ring are the same as those disclosed in the previous embodiment method, and will not be repeated here.

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

[0073] The above description is merely a specific embodiment of this application, but the scope of protection of this application is not limited thereto. Any variations or substitutions that can be easily conceived by those skilled in the art within the scope of the technology disclosed in this application should be included within the scope of protection of this application. Therefore, the scope of protection of this application should be determined by the scope of the claims.

[0074] This application provides a computer-readable storage medium having computer-readable program instructions (i.e., a computer program) stored thereon, the computer-readable program instructions being used to execute the control method of the cardiopulmonary sound detection device in the above embodiments.

[0075] The computer-readable storage medium provided in this application may be, for example, a USB flash drive, but is not limited to, electrical, magnetic, optical, electromagnetic, infrared, or semiconductor systems, devices, or any combination thereof. More specific examples of computer-readable storage media may include, but are not limited to: electrical connections having one or more wires, portable computer disks, hard disks, random access memory, read-only memory, erasable programmable read-only memory (EPROM, or flash memory), optical fibers, portable compact disk read-only memory (CD-ROM), optical storage devices, magnetic storage devices, or any suitable combination thereof. In this embodiment, the computer-readable storage medium may be any tangible medium containing or storing 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 may be transmitted using any suitable medium, including but not limited to: wires, optical cables, radio frequency (RF), etc., or any suitable combination thereof.

[0076] The aforementioned computer-readable storage medium may be included in the cardiopulmonary sound detection ring; or it may exist independently and not assembled into the cardiopulmonary sound detection ring.

[0077] The aforementioned computer-readable storage medium carries one or more programs that, when executed by the cardiopulmonary sound detection ring, cause the cardiopulmonary sound detection ring to: acquire 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 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.

[0078] Computer program code for performing the operations of this application can be written in one or more programming languages ​​or a combination thereof, including object-oriented programming languages ​​such as Java, Smalltalk, and C++, as well as conventional procedural programming languages ​​such as the "C" language or similar programming languages. The program code can be executed entirely on the user's computer, partially on the user's computer, as a standalone software package, partially on the user's computer and partially on a remote computer, or entirely on a remote computer or server. In cases involving remote computers, the remote computer can be connected to the user's computer via any type of network—including a local area network (LAN) or a wide area network (WAN)—or can be connected to an external computer (e.g., via the Internet using an Internet service provider).

[0079] The flowcharts and block diagrams in the accompanying drawings illustrate the architecture, functionality, and operation of possible implementations of systems, methods, and computer program products according to various embodiments of this application. In this regard, each block in a flowchart or block diagram may represent a module, segment, or portion of code containing one or more executable instructions for implementing a specified logical function. It should also be noted that in some alternative implementations, the functions indicated in the blocks may occur in a different order than those indicated in the drawings. For example, two consecutively indicated blocks may actually be executed substantially in parallel, and they may sometimes be executed in reverse order, depending on the functions involved. It should also be noted that each block in the block diagrams and / or flowcharts, and combinations of blocks in the block diagrams and / or flowcharts, may be implemented using a dedicated hardware-based system that performs the specified function or operation, or using a combination of dedicated hardware and computer instructions.

[0080] The modules described in the embodiments of this application can be implemented in software or hardware. The names of the modules do not necessarily limit the functionality of the unit itself.

[0081] The readable storage medium provided in this application is a computer-readable storage medium that stores computer-readable program instructions (i.e., a computer program) for executing the control method of the aforementioned cardiopulmonary sound detection device. This solves the technical problem of low accuracy in cardiopulmonary sound detection due to difficulty in determining pressure detection values ​​when using a wearable ring for detection. Compared to the prior art, the beneficial effects of the computer-readable storage medium provided in this application are the same as those of the control method of the cardiopulmonary sound detection device provided in the above embodiments, and will not be elaborated upon here.

[0082] The above description is only a part of the embodiments of this application and does not limit the patent scope of this application. All equivalent structural transformations made under the technical concept of this application and using the contents of the specification and drawings of this application, or direct / indirect applications in other related technical fields, are included in the patent protection scope of this 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, including the detection angle. The preset force transmission coefficient is updated based on the inertial parameters to obtain the target force transmission coefficient. This includes determining the angle deviation between the detection angle and the preset angle, and calculating the angle component of the angle 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; the deviation distance between the pressing area and the initial area is determined, 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 a preset linear relationship between the deviation distance and the deformation coefficient; 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; wherein the preset force transmission coefficient is the force attenuation or amplification ratio of the pressure transmitted to the PCB motherboard when the cardiopulmonary sound detection device is worn without deviation, and the target force transmission coefficient is the force transmission coefficient corresponding to the offset position of the cardiopulmonary sound detection device; The pressure detection value of the cardiopulmonary sound detection device is calculated based on the target force transmission coefficient and the deformation, wherein the magnitude of the pressure detection value is equal to the force transmission coefficient multiplied by the signal value corresponding to the deformation.

2. 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 detection value will be output. If the pressure detection value meets the preset pressure value, the heart and lung sound detection process is triggered.

3. 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.

4. 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.

5. A heart and lung sound detection device, characterized in that, The device is used to implement the control method of the cardiopulmonary sound detection device as described in any one of claims 1-4, wherein the cardiopulmonary sound detection device comprises: 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 detection value based on the deformation and the inertial parameters.

6. The cardiopulmonary sound detection device as described in claim 5, 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 detection value of the cardiopulmonary sound detection device during cardiopulmonary sound detection; The detection module is used to detect heart and lung sound data.

7. 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 5-6, 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 4.

8. 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 4.

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