Hearing aid adaptive adjustment method based on blood pressure monitoring

Abstract

This application relates to a hearing aid adaptive adjustment method based on blood pressure monitoring. It obtains baseline parameters for the hearing aid and applies them to the hearing aid, ensuring that the parameters have initial baseline values ​​before adaptive adjustment begins. First, a predicted blood pressure value is acquired and its range is checked to determine if it falls within the normal range, indicating a possible rise in blood pressure. If blood pressure rises, it is checked if the predicted blood pressure value falls within the pre-hypertension range. If it does, the user's sound tolerance is low, so the gain is reduced to decrease the output sound of the hearing aid, and the compression ratio is increased to prevent loud external sounds from being amplified to a higher magnification. Second, a predicted blood pressure value is acquired. If blood pressure continues to rise, it is checked if it falls within the hypertensive range. If it does, the discomfort threshold is reduced. When blood pressure returns to normal and tolerance recovers, the reduced sound compensation provided by the parameters is insufficient to meet the user's normal hearing loss compensation needs; therefore, the parameters are reset to their original state.

Description

Technical Field

[0001] This application relates to the field of hearing aid technology, and in particular to a hearing aid adaptive adjustment method based on blood pressure monitoring. Background Technology

[0002] Hypertension is characterized by persistently elevated arterial blood pressure, which is especially common in the elderly. Blood pressure measurement is frequently required for control. Current blood pressure measurements are based on cuff compression tests, which are highly accurate but inconvenient to carry and cannot provide real-time alerts. Users usually only take a measurement after experiencing symptoms of elevated blood pressure.

[0003] Like high blood pressure, hearing loss is a problem that many elderly people must face. Hearing aids are small and portable, and can effectively solve hearing problems. Adding a blood pressure measurement function to hearing aids can monitor blood pressure changes in real time, provide health management plans, remind you to take medication on time, seek medical treatment, and so on. It can also provide real-time alarms in critical moments, which can effectively solve the problem of blood pressure monitoring.

[0004] On the one hand, there are very few devices on the market that combine hearing aids and blood pressure measurement functions, almost none, due to the high research and development costs. On the other hand, devices that combine hearing aids and blood pressure measurement generally operate on the same principle as traditional portable monitoring products with blood pressure measurement capabilities, such as watches and wristbands. These products only provide blood pressure monitoring but do not link this function with the hearing aid's parameters for self-adjustment. When blood pressure rises, the user's tolerance to sound decreases, and noisy environments can worsen symptoms of hypertension. Adjusting parameters appropriately based on blood pressure levels would provide a more comfortable experience for the user. Therefore, traditional solutions lack a method to adaptively adjust hearing aid parameters based on real-time blood pressure monitoring.

[0005] However, existing portable devices with blood pressure measurement functions are generally traditional wearable devices, such as wristbands and watches. They typically utilize PPG signal acquisition to measure blood pressure. However, the accuracy of PPG blood pressure measurements is affected by various factors, with motion artifacts being a common interference factor. When wearing health monitoring products like watches and wristbands, the relative position and pressure between the sensor and the skin change with movement, leading to unstable light scattering and absorption, generating noise signals that interfere with the normal acquisition and analysis of PPG signals. Furthermore, traditional wearable devices often use green light for testing. While green light introduces less noise, its poor penetration makes it difficult to reach deep blood vessels, resulting in incomplete data.

[0006] Most importantly, traditional portable devices with blood pressure measurement functions cannot automatically adjust parameters based on blood pressure. Summary of the Invention

[0007] Therefore, it is necessary to address the problem that traditional solutions lack a method for adaptively adjusting hearing aid parameters based on real-time blood pressure monitoring, and to provide a hearing aid adaptive adjustment method based on blood pressure monitoring.

[0008] This application provides a method for adaptive adjustment of a hearing aid based on blood pressure monitoring, the method comprising:

[0009] Obtain the baseline parameters of the hearing aid and apply them to the hearing aid;

[0010] The first time, the predicted blood pressure value at the current time point is obtained from the blood pressure prediction module in the hearing aid, and it is determined whether the predicted blood pressure value at the current time point is within the normal range.

[0011] If the predicted blood pressure value at the current time point is not within the normal range, then determine whether the predicted blood pressure value at the current time point is within the prehypertension range.

[0012] If the predicted blood pressure value at the current time point is within the prehypertension range, the hearing aid gain will be reduced by a first preset percentage of the current value, and the hearing aid compression ratio will be increased.

[0013] The second step is to obtain the predicted blood pressure value at the current time point from the blood pressure prediction module in the hearing aid, and determine whether the predicted blood pressure value at the current time point is within the normal range.

[0014] If the predicted blood pressure value at the current time point is not within the normal range, then determine whether the predicted blood pressure value at the current time point is within the high blood pressure range. If the predicted blood pressure value at the current time point is within the high blood pressure range, then adjust the hearing aid discomfort threshold to be reduced.

[0015] The third time, the predicted blood pressure value at the current time point is obtained from the blood pressure prediction module in the hearing aid, and it is determined whether the predicted blood pressure value at the current time point is within the normal range.

[0016] If the predicted blood pressure value at the current time point is within the normal range, then the hearing aid parameters are reset; the reset of hearing aid parameters includes resetting the hearing aid gain, hearing aid compression ratio, and hearing aid discomfort threshold to the values ​​in the baseline parameters.

[0017] This application relates to an adaptive adjustment method for hearing aids based on blood pressure monitoring. By acquiring and applying the hearing aid's baseline parameters, an initial baseline value is established before adaptive adjustment begins. This baseline value ensures that the adjustment result does not deviate during subsequent adjustments, improving adjustment efficiency. The method first acquires the predicted blood pressure value at the current time point from the hearing aid's blood pressure prediction module. It then determines whether the predicted blood pressure value is within the normal range, thus identifying any potential rise in blood pressure. If blood pressure rises, it further determines whether the predicted blood pressure value is within the pre-hypertension range. When within the pre-hypertension range, because the body's tolerance to sound decreases after blood pressure rises, automatically reducing the hearing aid gain by a first preset percentage lowers the output sound. Simultaneously, increasing the hearing aid compression ratio prevents loud external sounds from being amplified to a higher magnification. Then, a second predicted blood pressure value is obtained. If the blood pressure continues to rise, it is determined whether the predicted blood pressure value at the current time point is within the hypertension range. If the blood pressure is within the hypertension range, the hearing aid discomfort threshold is adjusted to be reduced. Once the blood pressure returns to normal, the user's tolerance to sound recovers. The reduced sound compensation provided by the various parameters is insufficient to meet the user's normal hearing loss compensation needs. Therefore, by resetting the hearing aid parameters, the hearing aid parameters can be restored to the hearing aid's original state. Attached Figure Description

[0018] Figure 1 This is a flowchart of a hearing aid adaptive adjustment method based on blood pressure monitoring, provided as an embodiment of this application. Detailed Implementation

[0019] To make the objectives, technical solutions, and advantages of this application clearer, the following detailed description is provided in conjunction with the accompanying drawings and embodiments. It should be understood that the specific embodiments described herein are merely illustrative and not intended to limit the scope of this application.

[0020] This application provides a hearing aid adaptive adjustment method based on blood pressure monitoring. It should be noted that the hearing aid adaptive adjustment method based on blood pressure monitoring provided in this application is applied to hearing aids.

[0021] Furthermore, the hearing aid adaptive adjustment method based on blood pressure monitoring provided in this application does not limit the executing entity. Optionally, the executing entity of the hearing aid adaptive adjustment method based on blood pressure monitoring provided in this application can be a hearing aid. Specifically, the executing entity of the hearing aid adaptive adjustment method based on blood pressure monitoring provided in this application can be one or more processors built into the hearing aid.

[0022] like Figure 1 As shown, in one embodiment of this application, the hearing aid adaptive adjustment method based on blood pressure monitoring includes:

[0023] S100: Obtain the reference parameters of the hearing aid and apply the reference parameters of the hearing aid to the hearing aid.

[0024] S200: For the first time, the predicted blood pressure value at the current time point is obtained from the blood pressure prediction module in the hearing aid, and it is determined whether the predicted blood pressure value at the current time point is within the normal range.

[0025] S210, if the predicted blood pressure value at the current time point is not within the normal range, then determine whether the predicted blood pressure value at the current time point is within the prehypertension range.

[0026] S211, if the predicted blood pressure value at the current time point is within the prehypertension range, then the hearing aid gain is reduced by a first preset percentage of the current value, and the hearing aid compression ratio is increased.

[0027] S300: The second time, the predicted blood pressure value at the current time point is obtained from the blood pressure prediction module in the hearing aid, and it is determined whether the predicted blood pressure value at the current time point is within the normal range.

[0028] S310, if the predicted blood pressure value at the current time point is not within the normal range, then determine whether the predicted blood pressure value at the current time point is within the high blood pressure range. If the predicted blood pressure value at the current time point is within the high blood pressure range, then adjust the hearing aid discomfort threshold by reducing it.

[0029] S400: The system acquires the predicted blood pressure value at the current time point from the blood pressure prediction module in the hearing aid for the third time, and determines whether the predicted blood pressure value at the current time point is within the normal range.

[0030] S500, if the predicted blood pressure value at the current time point is within the normal range, then reset the hearing aid parameters. Resetting the hearing aid parameters includes resetting the hearing aid gain, hearing aid compression ratio, and hearing aid discomfort threshold to the values ​​in the baseline parameters.

[0031] Specifically, the hearing aid includes a PPG signal acquisition module and a blood pressure prediction module. The PPG signal acquisition module collects PPG signals and sends them to the blood pressure prediction module. The blood pressure prediction module analyzes the PPG signals and generates a predicted blood pressure value based on the analysis results. While there is a certain difference between the predicted blood pressure value and the actual blood pressure value measured by a cuff blood pressure monitor, the predicted blood pressure value can generally determine whether the blood pressure falls within the various blood pressure ranges. In other words, the predicted blood pressure value has an assessment capability; although it cannot measure blood pressure with perfect accuracy, it can determine whether the blood pressure is within the normal range and whether it falls within the range of each blood pressure classification.

[0032] When blood pressure rises, hearing-impaired users have lower tolerance for sound, and noisy environments can worsen their hearing loss. Adjusting hearing aid parameters in such situations can provide a more comfortable experience. This embodiment utilizes a hearing aid adaptive adjustment method based on blood pressure monitoring to adjust hearing aid parameters in real time to adapt to fluctuations in the user's blood pressure.

[0033] The adaptive parameter adjustment method in this embodiment is based on the principle that when blood pressure rises, the body's tolerance to sound decreases, and excessive noise will make the user uncomfortable, so the sound should be reduced. This embodiment pays more attention to people with hypertension.

[0034] Gain is the amplification capability of a hearing aid to input sounds, used to compensate for a user's hearing loss. Gain amplifies external sounds indiscriminately, bringing previously inaudible speech or environmental sounds into the user's hearing range. Gain can provide personalized amplification for different frequencies of hearing loss (low, mid, and high frequencies), helping users hear sounds more clearly. The unit of gain is decibels, or dB. The gain value represents the intensity difference between the input and output sounds. For example, a gain of 30dB means the hearing aid amplifies the sound by 30dB. This embodiment uses a percentage for adjustment. In this embodiment, reducing the gain will make all output sounds quieter.

[0035] Compression ratio is designed for louder external sounds, not quieter ones. Its effect is less noticeable in quieter environments. Similar to acceleration, compression ratio can be understood as increasing the amplification factor of sound. Increasing the compression ratio reduces the amplification factor, thus lowering the volume of loud sounds. Loud external sounds entering the hearing aid are amplified by the compression ratio. Increasing the compression ratio still amplifies the sound, but the amplification factor is reduced. If a particularly loud sound enters the hearing aid, such as one that reaches the discomfort threshold, it will not be amplified and may even be compressed and reduced. This can be further understood through the explanation of the discomfort threshold later.

[0036] The discomfort threshold is the upper limit of the output sound, similar to the concept of a ceiling. When hearing-impaired users reduce gain and increase compression ratio, the sound they hear becomes quieter, but this doesn't mean they can tolerate louder sounds. In fact, the opposite is true; compared to people with normal hearing, hearing-impaired users have a lower tolerance for extremely loud sounds, and their tolerance is even lower when their blood pressure is high. This can be understood as people with high blood pressure experiencing greater discomfort in the same noisy environment.

[0037] Hearing aids automatically compress sounds that exceed the discomfort threshold until they are below it. Therefore, lowering the discomfort threshold reduces the maximum output power (MPO) of the hearing aid, making the maximum sound that the user can hear quieter. This is also to create a relatively comfortable hearing environment for the user.

[0038] This embodiment adjusts only the gain and compression ratio in the pre-hypertension stage, while in the hypertensive stage, it also adds adjustment to the hearing aid discomfort threshold, achieving graded adjustment. This allows for progressively increasing the number of hearing aid parameters to address different blood pressure levels. The higher the blood pressure, the more hearing aid parameters need to be adjusted, and the greater the limitation on hearing.

[0039] Following S200, it also includes:

[0040] S220, if the predicted blood pressure value at the current time point is within the normal range, then execute S500, that is, execute the reset of hearing aid parameters.

[0041] Following the S300, it also includes:

[0042] S320, if the predicted blood pressure value at the current time point is within the normal range, then execute S500, that is, execute the reset of hearing aid parameters.

[0043] Following S210, it also includes:

[0044] S212, If the predicted blood pressure value at the current time point is not within the prehypertension range, then further determine whether the predicted blood pressure value at the current time point is within the hypertension range.

[0045] S213, if the predicted blood pressure value at the current time point is within the range of high blood pressure, then first adjust the hearing aid gain by a first preset percentage of the current value, increase the hearing aid compression ratio, and then adjust the hearing aid discomfort threshold by a reduction.

[0046] Specifically, S212 and S213 are cases where blood pressure is found to be within the high blood pressure range. In these cases, the hearing aid gain, hearing aid compression ratio, and hearing aid discomfort threshold are all adjusted.

[0047] S310 also includes:

[0048] S311, If ​​the predicted blood pressure value at the current time point is not within the normal range and not within the high blood pressure range, then no adjustment will be made, and S400 will be executed directly.

[0049] Specifically, this is the case where, after performing the adjustment in S211, the predicted blood pressure value remains unchanged within the prehypertension range. Since S211 is already the optimal adjustment for the prehypertension range, no action is needed. Instead, proceed directly to S400 to further observe the blood pressure changes.

[0050] Following the S400, it also includes:

[0051] S600: If the predicted blood pressure value at the current time point is not within the normal range, no adjustment is made, and the process of obtaining the predicted blood pressure value at the current time point output by the blood pressure prediction module in the hearing aid is repeated to determine whether the predicted blood pressure value at the current time point is within the normal range until the predicted blood pressure value at the current time point is within the normal range.

[0052] Specifically, since adjustments have already been made in S211 and S310, no further adjustments are needed. Continue monitoring blood pressure changes until the blood pressure drops to within the normal range.

[0053] It is understandable that S500 is executed whenever the predicted blood pressure value at the current time point is within the normal range, i.e., the hearing aid parameters are reset. This is because when blood pressure returns to the normal range, the user's tolerance to sound recovers, and they need to hear sounds more clearly. Therefore, the compensation after lowering the hearing aid parameters is insufficient to meet the hearing loss compensation needs, and the hearing aid parameters need to be restored to their original state. Conversely, when blood pressure is high, tolerance is low, and the user needs less noise and less focus on hearing loss compensation. The user needs rest, so the gain is lowered to reduce the discomfort threshold and create a quiet and comfortable environment.

[0054] In this embodiment, by acquiring the hearing aid's baseline parameters and applying them to the hearing aid, the hearing aid parameters have an initial baseline value before adaptive adjustment begins. This baseline value ensures that the adjustment result will not deviate during subsequent adjustments, improving adjustment efficiency. The system first acquires the predicted blood pressure value at the current time point from the hearing aid's blood pressure prediction module. It then determines whether the predicted blood pressure value at the current time point is within the normal range, indicating whether a rise in blood pressure has occurred. When blood pressure rises, it further determines whether the predicted blood pressure value at the current time point is within the pre-hypertension range. When it is within the pre-hypertension range, because the body's tolerance to sound decreases after blood pressure rises, automatically reducing the hearing aid gain by a first preset percentage can lower the output sound of the hearing aid. Simultaneously, increasing the hearing aid compression ratio ensures that loud external sounds, even after amplification, will not be amplified to a high magnification. Then, the system acquires the predicted blood pressure value a second time. If the blood pressure continues to rise, it determines whether the predicted blood pressure value at the current time point is within the hypertension range. If the blood pressure is within the hypertension range, the hearing aid's discomfort threshold is adjusted to be reduced. Once the blood pressure returns to normal, the user's tolerance to sound recovers. The reduced sound compensation provided by the various parameters is insufficient to meet the user's normal hearing loss compensation needs. Therefore, by resetting the hearing aid parameters, the hearing aid parameters can be restored to the original state of the hearing aid.

[0055] In one embodiment of this application, S310 includes determining whether the predicted blood pressure value at the current time point is within the hypertension range if the predicted blood pressure value at the current time point is not within the normal range, and adjusting the hearing aid discomfort threshold to reduce it if the predicted blood pressure value at the current time point is within the hypertension range.

[0056] S311, if the predicted blood pressure value at the current time point is not within the normal range, then determine whether the predicted blood pressure value at the current time point is within the range of Grade 1 hypertension.

[0057] S312a, if the predicted blood pressure value at the current time point is within the range of Grade I hypertension, then the hearing aid discomfort threshold is reduced by a second preset percentage of the current value.

[0058] S312b, execute S400, that is, execute the third acquisition of the predicted blood pressure value of the current time node output by the hearing aid internal blood pressure prediction module, and determine whether the predicted blood pressure value of the current time node is within the normal range.

[0059] Specifically, in this embodiment, S310 includes determining whether the predicted blood pressure value is within the range of Grade I hypertension, and including the adjustment method of hearing aid parameters when the predicted blood pressure value is within the range of Grade I hypertension.

[0060] The discomfort threshold is the maximum sound intensity a user can tolerate; exceeding this value will cause a harsh or uncomfortable sensation. The discomfort threshold protects users from harm caused by excessively amplified sounds, ensuring that the sound output by the hearing aid does not exceed the user's tolerance limit.

[0061] The unit of discomfort threshold is sound pressure level (dB SPL) or hearing level (dB HL). Decibels (dB SPL) directly measure the actual intensity of sound. Decibels (dB HL) are intensity units based on standardized hearing tests. During initial fitting of hearing aids, the discomfort threshold is typically converted to dB SPL within the hearing aid for limitation. Gain and discomfort threshold together determine the dynamic range of the hearing aid. Dynamic range = UCL - Hearing Threshold. Gain needs to be adjusted within this range to compensate for hearing loss without exceeding the discomfort threshold.

[0062] If the gain is insufficient, the user will not be able to hear the sound clearly, and communication will not be improved. If the gain is too high or the discomfort threshold is not set properly, it will lead to sound distortion, discomfort, and even worsen hearing damage.

[0063] In this embodiment, the discomfort threshold is the customer's maximum tolerance for sound; exceeding this volume will cause discomfort. When blood pressure is in a higher, more dangerous range than the pre-hypertension zone, adjusting the discomfort threshold by lowering the maximum sound intensity threshold can more directly and maximally alleviate the user's discomfort.

[0064] In one embodiment of this application, after S400, the method further includes: after obtaining the predicted blood pressure value at the current time point output by the hearing aid in-ear blood pressure prediction module for the third time, and determining whether the predicted blood pressure value at the current time point is within the normal range, the method further includes:

[0065] S410, if the predicted blood pressure value at the current time point is not within the normal range, then determine whether the predicted blood pressure value at the current time point is within the range of grade II hypertension.

[0066] S411, If ​​the predicted blood pressure value at the current time point is within the range of grade II hypertension, the hearing aid discomfort threshold is reduced by a third preset percentage of the current value.

[0067] S412, for the fourth time, obtain the predicted blood pressure value at the current time point output by the hearing aid's internal blood pressure prediction module, and determine whether the predicted blood pressure value at the current time point is within the normal range.

[0068] Specifically, in this embodiment, an additional determination is made as to whether the predicted blood pressure value is within the range of grade II hypertension, and a method for adjusting the hearing aid parameters when the predicted blood pressure value is within the range of grade II hypertension.

[0069] Following S412, it also includes:

[0070] S413, if the predicted blood pressure value at the current time point is within the normal range, then execute S500, that is, execute the reset of hearing aid parameters.

[0071] Following S412, it also includes:

[0072] S414, if the predicted blood pressure value at the current time point is not within the normal range, no adjustment is made, and the process of obtaining the predicted blood pressure value at the current time point output by the blood pressure prediction module in the hearing aid is repeated to determine whether the predicted blood pressure value at the current time point is within the normal range until the predicted blood pressure value at the current time point is within the normal range.

[0073] Specifically, since adjustments have already been made to S211, S312a, and S411, no further adjustments are needed. Continue monitoring blood pressure changes until the blood pressure drops to within the normal range.

[0074] In this embodiment, the judgment of whether the predicted blood pressure value at the current time point is within the hypertension value range is further subdivided into two levels: whether the predicted blood pressure value at the current time point is within the first-level hypertension value range and whether the predicted blood pressure value at the current time point is within the second-level hypertension value range. The adjustment of the discomfort threshold is continuously reduced in the case of a sudden increase in blood pressure, making the adjustment more gradient.

[0075] In one embodiment of this application, S500 includes resetting the hearing aid gain, hearing aid compression ratio, and hearing aid discomfort threshold to values ​​in the reference parameters, including:

[0076] S510 immediately resets the hearing aid gain and hearing aid compression ratio to the corresponding values ​​in the reference parameters.

[0077] S520 continuously acquires multiple predicted blood pressure values ​​within a preset time period.

[0078] S530 determines whether multiple predicted blood pressure values ​​within a preset time period are all within the normal range.

[0079] S540: If multiple predicted blood pressure values ​​within a preset time period are all within the normal range, the hearing aid discomfort threshold will be reset to the value in the baseline parameters.

[0080] Specifically, optionally, prior to S100, the baseline parameters of the hearing aid can be retrieved from the audiologist's adjustment parameter library. The audiologist's adjustment parameter library stores user profile files and the corresponding audiologist's adjustment parameters. These are initial hearing aid parameters generated by the hearing aid audiologist after personalized adjustments to various functional parameters of the hearing aid based on the user's hearing loss and wearing experience. These are initial hearing aid parameters generated using traditional fitting methods, many of which exist (see CN114827861A and CN205987370U). Fitting methods are not the focus of this application and will not be explained in detail here. The user profile file includes the user's age, gender, and hearing loss data.

[0081] When retrieving the audiologist's adjustment parameters, all user profile files in the audiologist's adjustment parameter library can be traversed. The user profile file with the highest similarity to the sample user profile file can be searched as the approximate user profile file. Finally, the audiologist's adjustment parameters corresponding to the approximate user profile file are retrieved as the sample's audiologist's adjustment parameters. There are several methods for calculating similarity. Optionally, each sub-parameter of the user's age, gender, and hearing loss status data can be assigned a weight. Then, the difference between the user's age and gender can be normalized to the [0, 1] interval. If the users are the same gender, the normalization is 0; if the users are different genders, the normalization is 1. Similarly, the difference between each sub-parameter of the user's hearing loss status data can be normalized to the [0, 1] interval. Finally, the weights of each data point are multiplied by the normalized values, and the sum of these weights multiplied by the normalized values ​​is taken as the similarity value. The smaller the similarity value, the smaller the difference; the larger the similarity value, the larger the difference. We identified the user profile file with the lowest similarity value to the sample as the approximate user profile file, and obtained the audiologist's adjustment parameters corresponding to the approximate user profile file as the audiologist's adjustment parameters for the sample. Furthermore, we used a preset percentage of the audiologist's adjustment parameters for the sample as the baseline parameters for the hearing aid.

[0082] Therefore, the baseline parameters of the hearing aid best match the hearing compensation under normal conditions. After the blood pressure returns to normal, this embodiment resets all hearing aid parameters to the corresponding values ​​in the baseline parameters, which can meet the user's normal hearing needs.

[0083] The gain and compression ratio are immediately restored to the values ​​in the baseline parameters, while the discomfort threshold is restored to the values ​​in the baseline parameters after a preset time period. This is because it is difficult for the body to recover synchronously after blood pressure is restored, similar to the body being very weak after recovering from a serious illness. At this time, parameters such as gain and compression ratio, which are important for hearing loss compensation, are restored immediately to make the user hear more clearly and loudly. However, the maximum sound threshold is still controlled. After the preset time period has passed and the body has recovered, the restriction on the maximum sound threshold of the discomfort threshold is lifted, that is, the discomfort threshold is also restored to the values ​​in the baseline parameters.

[0084] In one embodiment of this application, the normal value range includes a normal diastolic blood pressure range and a normal systolic blood pressure range. The normal diastolic blood pressure range is greater than or equal to 78 mmHg and less than or equal to 82 mmHg, and the normal systolic blood pressure range is greater than or equal to 118 mmHg and less than or equal to 122 mmHg.

[0085] In one embodiment of this application, the prehypertension range includes a diastolic prehypertension range and a systolic prehypertension range. The diastolic prehypertension range is greater than 82 mmHg and less than or equal to 84 mmHg, and the systolic prehypertension range is greater than 122 mmHg and less than or equal to 129 mmHg.

[0086] In one embodiment of this application, the grade I hypertension value range includes a diastolic grade I hypertension value range and a systolic grade I hypertension value range. The diastolic grade I hypertension value range is greater than 84 mmHg and less than or equal to 89 mmHg, and the systolic grade I hypertension value range is greater than 129 mmHg and less than or equal to 139 mmHg.

[0087] In one embodiment of this application, the grade II hypertension value range includes a diastolic grade II hypertension value range and a systolic grade II hypertension value range. The diastolic grade II hypertension value range is greater than 89 mmHg and less than or equal to 99 mmHg, and the systolic grade II hypertension value range is greater than 139 mmHg and less than or equal to 159 mmHg.

[0088] In one embodiment of this application, the value of increasing the compression ratio of the hearing aid is 0.2.

[0089] In one embodiment of this application, the preset time period is not less than 30 minutes.

[0090] In one embodiment of this application, the first preset percentage is 10%, the second preset percentage is 10%, and the third preset percentage is 10%.

[0091] The following details how predicted blood pressure values ​​are obtained.

[0092] As mentioned above, the hearing aid is equipped with a PPG signal acquisition module and a blood pressure prediction module. The PPG signal acquisition module of this application uses PPG technology, namely photoplethysmography (PPG), to acquire PPG signals.

[0093] PPG technology is primarily based on the absorption and reflection characteristics of light in human tissues. While muscles and bones maintain a stable level of light absorption, hemoglobin in the blood has high absorbency, and its concentration in arteries changes periodically with heartbeats. During systole, arterial blood pressure rises, blood vessels fill, and blood volume increases, leading to increased light absorption by hemoglobin. During diastole, blood pressure decreases, blood vessels constrict, blood volume decreases, and light absorption decreases accordingly.

[0094] The PPG signal acquisition module consists of two sets of red light sources and two sets of photodetectors. The light sources emit light of a specific wavelength that shines onto the skin surface. After scattering and absorption by the skin tissue, some of the light is reflected back to the photodetectors. The photodetectors convert the received light signal into an electrical signal, and the change in its intensity over time reflects the dynamic changes in blood volume, thus forming the PPG signal.

[0095] The red light source can be a red LED, which can emit red light at a specific frequency.

[0096] A photodetector can be a photodiode, used to receive reflected light.

[0097] The next step is to analyze the PPG signal, focusing on correlating the PPG signal with blood pressure.

[0098] Changes in arterial blood pressure are the fundamental cause of the periodic changes in blood volume. When blood pressure rises, arteries dilate, propelling more blood into peripheral vessels, increasing local blood volume, which is reflected in a higher peak in the pulse wave (PPG) signal. Conversely, when blood pressure falls, blood vessels constrict, blood volume decreases, and the peak decreases. Furthermore, other characteristic parameters of the PPG signal are also correlated with blood pressure. For example, the rise time, fall time, and position and morphology of characteristic points such as the dicrotic notch of the pulse wave change with variations in blood pressure.

[0099] By coupling the actual blood pressure value measured by the cuff blood pressure monitor, the PPG signal characteristics, and the GBDT model, the GBDT model is trained to obtain a GBDT (gradient boosting decision tree) model between systolic and diastolic blood pressure. This model can preliminarily assess blood pressure status and obtain predicted blood pressure values. Although it cannot provide extremely accurate blood pressure values ​​like the cuff blood pressure monitor, which is an objective fact, it can determine whether blood pressure deviates significantly from the normal range, providing an important data foundation for the self-adjustment of hearing aids.

[0100] In one embodiment of this application, before obtaining the reference parameters of the hearing aid and applying the reference parameters to the hearing aid, the hearing aid adaptive adjustment method based on blood pressure monitoring further includes:

[0101] S010, the PPG signal acquisition module acquires PPG data during the acquisition period and sends it to the blood pressure prediction module.

[0102] S020, during the data collection period, the actual blood pressure value is synchronously acquired and sent to the blood pressure prediction module.

[0103] Specifically, S010 and S020 can be performed synchronously. A red LED emits red light with a wavelength of 660nm, which is projected onto the skin inside the ear canal. As the red light illuminates the skin on the surface of the ear canal, part of the light is absorbed by the skin, tissue, and blood, while the rest is reflected back and received by the photodetector. The sampling frequency can be 125Hz, meaning one PPG data point is collected every 0.008 seconds. Therefore, a 5-second PPG signal will yield a total of 625 data points. Each data point can be represented by (time, voltage). For example, (0ms, 12mV), (8ms, 38mV), (16ms, 64mV), ..., (496ms, 27mV)... ms is the unit of time (millisecond), and mV is the unit of voltage (millivolt).

[0104] S030 preprocesses the PPG data and actual blood pressure values.

[0105] S030 includes:

[0106] S031, sort the PPG data according to the time node order to generate the PPG signal feature set.

[0107] S032, sort multiple real blood pressure values ​​according to the time node order to generate a real blood pressure feature set.

[0108] S033, generate PPG waveform curves based on PPG signal feature sets.

[0109] S034, perform noise reduction processing on the PPG waveform curve.

[0110] The denoising process for the PPG waveform curve includes removing high and low frequency noise, removing low frequency baseline drift, eliminating motion artifacts, removing ambient light noise, and removing circuit noise floor, among other things. This step is to remove these noises to obtain a clean PPG waveform curve.

[0111] To remove low-frequency baseline drift, a 4th-order Butterworth low-pass filter (with a cutoff frequency of 0.5Hz, which can filter out low-frequency interference such as breathing and body temperature changes) can be used, which can reduce baseline fluctuations from ±15mV to ±2mV.

[0112] High-frequency noise suppression can be achieved using a Savitzky-Golay filter (31-point window, polynomial order 3). After noise suppression, the signal-to-noise ratio is improved from 8dB to 22dB.

[0113] S040, perform feature extraction on the preprocessed PPG data to obtain the features of the PPG data, and store the features of the PPG data in the feature dataset.

[0114] Specifically, PPG data features include three main categories: time-domain features, frequency-domain features, and statistical features.

[0115] Time-domain characteristics may include one or more of the following: peak amplitude, waveform amplitude ratio, pulse wave propagation time, peak time, rise time, fall time, and waveform area.

[0116] Peak amplitude is the maximum amplitude of the PPG waveform, which is related to blood pressure. Changes in blood pressure affect the degree of vascular filling, which in turn affects the peak value of the PPG signal.

[0117] Peak time is the time from the start of the signal to its peak value, reflecting the heart's contractile function and the elasticity of blood vessels.

[0118] Ascent time and descent time reflect the rate of blood perfusion and emptying in blood vessels and are related to vascular resistance and blood pressure.

[0119] The waveform area is calculated by integration and is related to the overall change in blood volume.

[0120] The formula for calculating the waveform amplitude ratio is:

[0121] WAR=(A_sys-A_dia) / (A_sys+A_dia) Formula 1.

[0122] Where WAR is the waveform amplitude ratio. A_sys is the peak amplitude during systole, in mV. A_dia is the trough amplitude during diastole, in mV.

[0123] The formula for pulse wave conduction time can be:

[0124] PWTT = T_ECG_R wave - T_PPG rising edge formula 2.

[0125] Wherein, PWTT is the pulse wave conduction time, T_ECG_R wave is the timestamp of the R wave in the electrocardiogram. The rising edge of T_PPG is the starting point of the PPG waveform curve (the time point when the derivative exceeds 0.1mV / ms).

[0126] Frequency domain features are obtained through Fast Fourier Transform (FFT). The PPG waveform curve is transformed to the frequency domain using FFT, and the dominant frequency, harmonic frequency, dominant frequency energy ratio, harmonic distortion, and power spectral density features are extracted.

[0127] The formula for calculating the main frequency energy ratio can be expressed as Formula 3:

[0128] FER=P(f0) / ΣP(f) Formula 3.

[0129] Wherein, FER is the main frequency energy ratio, P(f0) is the fundamental frequency power, that is, the power at the frequency corresponding to the heart rate, and ΣP(f) is the total power between 0.5Hz and 20Hz.

[0130] The formula for calculating harmonic distortion can be expressed as Formula 4:

[0131] Formula 4.

[0132] Where THD stands for harmonic distortion. It is the sum of the power of the second harmonic (2f0) and the third harmonic (3f0). P(f0) is the fundamental frequency power.

[0133] The calculation principle of harmonic distortion (THD) involves determining the ratio between the total power of the second and third harmonics and the fundamental frequency power. Taking the square root of the sum of the harmonic powers converts the power value back to amplitude dimensions, ensuring consistency with the units of the fundamental frequency power P(f0) in the denominator (power is the square of amplitude). THD quantifies the intensity of harmonic components relative to the fundamental frequency. When arteriosclerosis or increased peripheral resistance occurs, harmonic components intensify, leading to an increase in THD.

[0134] Statistical characteristics can include one or more of the following: mean, variance, standard deviation, skewness, and kurtosis. These characteristics can reflect the distribution and variation characteristics of a signal.

[0135] W050 normalizes the features of PPG data.

[0136] Specifically, the purpose of normalization is to unify the dimensions and facilitate computer calculations. There are many methods, but they are not the focus of this application and will not be described in detail. Normalization can be achieved by dividing the difference between the original feature value and the average value of the original feature value in the feature set by the standard deviation of the feature set.

[0137] W060, construct the GBDT model and train the GBDT model.

[0138] Specifically, W060 includes:

[0139] W061, Create a decision tree.

[0140] The number of decision trees can be 500, the depth of a single tree can be 5 layers, the learning rate can be 0.1, and the feature sampling rate can be 80%.

[0141] The iterative prediction formula for decision trees can be found in Formula 5.

[0142] F_t(x) = F_{t-1}(x)+η×h_t(x) Formula 5.

[0143] Here, the cumulative predicted value of the GBDT model in the t-th iteration, i.e., the cumulative predicted value of the GBDT model after adding the t-th tree, is in mmHg, the same unit as blood pressure. For example, if predicting systolic blood pressure, F_10(x)=125 means that the cumulative predicted value of the first 10 trees is 125 mmHg, and when the number of decision trees is 500, F_500(x)=126.7 mmHg is the final predicted systolic blood pressure value.

[0144] η is the learning rate, which controls the contribution of each tree. The larger the learning rate, the faster the model converges, but the greater the oscillation. The smaller the learning rate, the slower the model converges, but the more stable it is.

[0145] h_t(x) is the predicted value of the t-th tree. F_{t-1}(x) is the historical predicted value of the first t-1 iterations.

[0146] Example of building a single decision tree (taking the first tree as an example):

[0147] Root node split: \text{Optimal splitting feature} = PA_norm, \text{threshold} = 0.75

[0148] \text{MSE left child node}=12.4, \text{MSE right child node}=8.6\\

[0149] Information gain = 15.2 - (0.4 × 12.4 + 0.6 × 8.6) = 3.04

[0150] The effect of splitting is to separate samples with high pressure >135 mmHg into the right branch.

[0151] Example of calculating leaf node predicted values:

[0152] leaf node predicted value = 1 / N sum y_i - F_{prev}(x_i)

[0153] For example, if a leaf node contains 30 samples and the average residual is +3.2 mmHg, the predicted value is 3.2.

[0154] W062 performs gradient boosting iterations on the decision tree.

[0155] For example, the first tree predicts a systolic blood pressure of 123.5 mmHg, the second tree learns the true residual value of 128 - 123.5 = 4.5, and updates formula 5, i.e., F_2(x) = F_1(x) + 0.1 × \text{the second tree's predicted value}. After multiple iterations, it converges, and the number of iterations can be up to 500.

[0156] W070: Input the standardized dataset into the trained GBDT model, start the trained GBDT model, and obtain the predicted blood pressure value.

[0157] Example of a tree traversal path:

[0158] Tree 1: PA_norm>0.75→RT_norm<0.7→Prediction +3.2mmHg

[0159] Tree 2: SA_norm>0.6 → Prediction +1.8mmHg

[0160] ...\\

[0161] Tree 500: PA_norm < 0.8 → Predicted -0.3 mmHg

[0162] The final predicted value is the baseline blood pressure (120 / 80) + η × h_t(x) = 126.7 / 83.4 mmHg. η is the learning rate, which, as mentioned earlier, can be 0.1.

[0163] W080 uses actual blood pressure values ​​to dynamically calibrate predicted blood pressure values.

[0164] Specifically, for example, if the predicted blood pressure values ​​at one time point are 128 and 85, and the actual blood pressure values ​​are 130 and 84, and the predicted blood pressure values ​​at another time point are 125 and 82, and the actual blood pressure value is 83, the calibration coefficient calculation process is as follows:

[0165] a_{sys}=\frac{130+127}{128+125}=1.016

[0166] b_{sys}=\frac{(130-128)+(127-125)}{2}=2.0

[0167] Δ_{sys} = sliding window mean (-2, -2) = -2.0

[0168] a_{sys} is the individual slope correction coefficient, with an initial value of 1. b_{sys} is the individual intercept correction coefficient, with an initial value of 0. Δ_{sys} is the dynamic compensation amount based on recent measurements.

[0169] The predicted blood pressure value after dynamic calibration is:

[0170] The systolic blood pressure after dynamic calibration is 126.7 × 1.016 + 2.0 - 2.0 = 128.7 mmHg.

[0171] The diastolic blood pressure after dynamic calibration is 83.4 × 1.012 + 1.5 - 1.2 = 84.2 mmHg.

[0172] The dynamically calibrated systolic blood pressure and dynamically calibrated diastolic blood pressure are used as predicted blood pressure values ​​in the S100.

[0173] The technical features of the above embodiments can be combined arbitrarily, and the execution order of the method steps is not restricted. For the sake of brevity, not all possible combinations of the technical features in the above embodiments are described. However, as long as there is no contradiction in the combination of these technical features, they should be considered to be within the scope of this specification.

[0174] The embodiments described above are merely illustrative of several implementation methods of this application, and while the descriptions are specific and detailed, they should not be construed as limiting the scope of this patent application. It should be noted that those skilled in the art can make various modifications and improvements without departing from the concept of this application, and these all fall within the protection scope of this application. Therefore, the protection scope of this application should be determined by the appended claims.

Claims

1. A method for adaptive adjustment of hearing aids based on blood pressure monitoring, characterized in that, The method includes: Obtain the baseline parameters of the hearing aid and apply them to the hearing aid; The first time, the predicted blood pressure value at the current time point is obtained from the blood pressure prediction module in the hearing aid, and it is determined whether the predicted blood pressure value at the current time point is within the normal range. If the predicted blood pressure value at the current time point is not within the normal range, then determine whether the predicted blood pressure value at the current time point is within the prehypertension range. If the predicted blood pressure value at the current time point is within the prehypertension range, the hearing aid gain will be reduced by a first preset percentage of the current value, and the hearing aid compression ratio will be increased. The second step is to obtain the predicted blood pressure value at the current time point from the blood pressure prediction module in the hearing aid, and determine whether the predicted blood pressure value at the current time point is within the normal range. If the predicted blood pressure value at the current time point is not within the normal range, then determine whether the predicted blood pressure value at the current time point is within the high blood pressure range. If the predicted blood pressure value at the current time point is within the high blood pressure range, then adjust the hearing aid discomfort threshold to be reduced. The third time, the predicted blood pressure value at the current time point is obtained from the blood pressure prediction module in the hearing aid, and it is determined whether the predicted blood pressure value at the current time point is within the normal range. If the predicted blood pressure value at the current time point is within the normal range, then the hearing aid parameters are reset; the reset of hearing aid parameters includes resetting the hearing aid gain, hearing aid compression ratio, and hearing aid discomfort threshold to the values ​​in the baseline parameters.

2. The hearing aid adaptive adjustment method based on blood pressure monitoring according to claim 1, characterized in that, If the predicted blood pressure value at the current time point is not within the normal range, then it is determined whether the predicted blood pressure value at the current time point is within the hypertension range. If the predicted blood pressure value at the current time point is within the hypertension range, then the hearing aid discomfort threshold is adjusted to be reduced, including: If the predicted blood pressure value at the current time point is not within the normal range, then determine whether the predicted blood pressure value at the current time point is within the range of stage 1 hypertension. If the predicted blood pressure value at the current time point is within the range of Grade 1 hypertension, the hearing aid discomfort threshold will be reduced by the second preset percentage of the current value. The third step involves obtaining the predicted blood pressure value at the current time point from the hearing aid's internal blood pressure prediction module, and determining whether the predicted blood pressure value at the current time point is within the normal range.

3. The hearing aid adaptive adjustment method based on blood pressure monitoring according to claim 2, characterized in that, After obtaining the predicted blood pressure value at the current time point from the hearing aid's in-hearing aid blood pressure prediction module for the third time, and determining whether the predicted blood pressure value at the current time point is within the normal range, the process further includes: If the predicted blood pressure value at the current time point is not within the normal range, then determine whether the predicted blood pressure value at the current time point is within the range of grade II hypertension. If the predicted blood pressure value at the current time point is within the range of grade II hypertension, the hearing aid discomfort threshold will be reduced by a third preset percentage of the current value. The system retrieves the predicted blood pressure value at the current time point from the hearing aid's internal blood pressure prediction module for the fourth time point, and determines whether the predicted blood pressure value at the current time point is within the normal range.

4. The hearing aid adaptive adjustment method based on blood pressure monitoring according to claim 3, characterized in that, The step of resetting the hearing aid gain, hearing aid compression ratio, and hearing aid discomfort threshold to the values ​​in the baseline parameters includes: Immediately reset the hearing aid gain and hearing aid compression ratio to the corresponding values ​​in the baseline parameters; Continuously acquire multiple predicted blood pressure values ​​within a preset time period; Determine whether multiple predicted blood pressure values ​​within a preset time period are all within the normal range; If multiple predicted blood pressure values ​​within a preset time period are all within the normal range, the hearing aid discomfort threshold will be reset to the value in the baseline parameters.

5. The hearing aid adaptive adjustment method based on blood pressure monitoring according to claim 4, characterized in that, The normal range includes the normal range of diastolic blood pressure and the normal range of systolic blood pressure. The normal range of diastolic blood pressure is greater than or equal to 78 mmHg and less than or equal to 82 mmHg, and the normal range of systolic blood pressure is greater than or equal to 118 mmHg and less than or equal to 122 mmHg.

6. The hearing aid adaptive adjustment method based on blood pressure monitoring according to claim 5, characterized in that, The prehypertension range includes the prehypertension range of diastolic blood pressure and the prehypertension range of systolic blood pressure. The prehypertension range of diastolic blood pressure is greater than 82 mmHg and less than or equal to 84 mmHg, and the prehypertension range of systolic blood pressure is greater than 122 mmHg and less than or equal to 129 mmHg.

7. The hearing aid adaptive adjustment method based on blood pressure monitoring according to claim 6, characterized in that, The first-degree hypertension range includes the first-degree hypertension range of diastolic blood pressure and the first-degree hypertension range of systolic blood pressure. The first-degree hypertension range of diastolic blood pressure is greater than 84 mmHg and less than or equal to 89 mmHg, and the first-degree hypertension range of systolic blood pressure is greater than 129 mmHg and less than or equal to 139 mmHg.

8. The hearing aid adaptive adjustment method based on blood pressure monitoring according to claim 7, characterized in that, The grade II hypertension range includes the diastolic grade II hypertension range and the systolic grade II hypertension range. The diastolic grade II hypertension range is greater than 89 mmHg and less than or equal to 99 mmHg, and the systolic grade II hypertension range is greater than 139 mmHg and less than or equal to 159 mmHg.

9. The hearing aid adaptive adjustment method based on blood pressure monitoring according to claim 8, characterized in that, The compression ratio of the hearing aid is increased by 0.

2.

10. The hearing aid adaptive adjustment method based on blood pressure monitoring according to claim 9, characterized in that, The preset time period is no less than 30 minutes.

Images