Method and system for configuring a bone conduction hearing assistance device

Abstract

The application discloses a method and system for configuring a bone conduction hearing assistance device, comprising the following steps: obtaining hearing loss data of a wearer; determining reference output parameters of the bone conduction hearing assistance device at each frequency band under each sound level based on the hearing loss data; obtaining an adjustment value of the reference output parameters; the adjustment value is at least related to the frequency band; and configuring the bone conduction hearing assistance device based on the reference output parameters and the adjustment value.

Description

Technical Field

[0001] This application relates to the field of bone conduction hearing aids, and in particular to a method and system for configuring bone conduction hearing aids. Background Technology

[0002] Bone conduction hearing aids are hearing assistive devices designed and manufactured using bone conduction technology. These devices can be bone conduction hearing aids or bone conduction headphones. Bone conduction hearing aids primarily amplify external sound information and convert it into mechanical vibrations. These vibrations then transmit the sound sequentially through the skull, bony labyrinth, inner ear synovial fluid, cochlea, and auditory nerve to the auditory cortex of the brain. Compared to traditional air conduction hearing aids, the sound signals from bone conduction hearing aids are transmitted directly to the auditory nerve through the bone, bypassing the external auditory canal and eardrum. This avoids the pressure and occlusion effect caused by air conduction hearing aids blocking the ear canal, and provides a more comfortable wearing experience. Furthermore, since bone conduction hearing aids are not implanted in the ear, they effectively prevent ear canal inflammation. Therefore, bone conduction hearing aids are increasingly widely used by hearing-impaired patients.

[0003] Since bone conduction hearing aids transmit sound through vibration, there may be instances of intense vibration during use, which can affect the wearer's experience. Conversely, less intense vibration can affect the wearer's hearing performance. Therefore, there is a need to provide a configuration method for bone conduction hearing aids to improve the situation where intense vibration occurs without affecting the wearer's hearing performance. Summary of the Invention

[0004] One embodiment of this application provides a configuration method for a bone conduction hearing aid device, which includes the following steps: acquiring hearing loss data of a wearer; determining reference output parameters of the bone conduction hearing aid device at various sound levels and frequency bands based on the hearing loss data; acquiring adjustment values ​​of the reference output parameters, wherein the adjustment values ​​are at least related to the frequency bands; and configuring the bone conduction hearing aid device based on the reference output parameters and the adjustment values.

[0005] In some embodiments, configuring the bone conduction hearing aid based on the reference output parameter and the adjustment value includes: reducing the reference output parameter based on the adjustment value in a frequency band with a frequency greater than 0 Hz and less than or equal to 625 Hz.

[0006] In some embodiments, the adjustment value is the same at different hearing levels and in the same frequency band.

[0007] In some embodiments, the adjustment value is 1dB-12dB in a frequency band with a frequency greater than 0Hz and less than or equal to 625Hz.

[0008] In some embodiments, the adjustment value is set to 5dB-12dB in a frequency band with a frequency greater than 0Hz and less than or equal to 125Hz; the adjustment value is set to 3dB-9dB in a frequency band with a frequency greater than 125Hz and less than or equal to 375Hz; and / or, the adjustment value is set to 1dB-6dB in a frequency band with a frequency greater than 375Hz and less than or equal to 625Hz.

[0009] In some embodiments, the adjustment value is 5dB-7dB in a frequency band with a frequency greater than 0Hz and less than or equal to 125Hz; the adjustment value is 3dB-5dB in a frequency band with a frequency greater than 125Hz and less than or equal to 375Hz; and / or, the adjustment value is 1dB-3dB in a frequency band with a frequency greater than 375Hz and less than or equal to 625Hz.

[0010] In some embodiments, the adjustment value is 10dB-12dB in a frequency band with a frequency greater than 0Hz and less than or equal to 125Hz; the adjustment value is 7dB-9dB in a frequency band with a frequency greater than 125Hz and less than or equal to 375Hz; and / or, the adjustment value is 4dB-6dB in a frequency band with a frequency greater than 375Hz and less than or equal to 625Hz.

[0011] In some embodiments, the adjustment values ​​differ for different hearing levels and within the same frequency band.

[0012] In some embodiments, obtaining the adjustment value of the reference output parameter includes: determining a first threshold corresponding to each frequency band and each sound level, the first threshold being related to the wearer's vibration perception of each sound level in each frequency band; determining a second threshold corresponding to each frequency band and each sound level, the second threshold being related to the wearer's speech recognition rate at each sound level in each frequency band; and determining the adjustment value based on the reference output parameter, the first threshold, and the second threshold.

[0013] In some embodiments, determining the adjustment value based on the reference output parameter, the first threshold, and the second threshold includes: for each sound level and a certain sound level and a certain frequency band, a reference output parameter in a certain frequency band; subtracting the first threshold from the reference output parameter to obtain a comparison value; comparing the comparison value with the second threshold; and determining the adjustment value corresponding to the reference output parameter based on the comparison result of the comparison value and the second threshold.

[0014] In some embodiments, determining the adjustment value corresponding to the reference output parameter based on the comparison result between the comparison value and the second threshold includes: when the comparison value is less than or equal to 0, the adjustment value is 0dB; when the comparison value is greater than 0 but less than or equal to the second threshold, the adjustment value is the comparison value; when the comparison value is greater than the second threshold, the adjustment value is the second threshold.

[0015] In some embodiments, within a frequency band with a frequency greater than 0 Hz and less than or equal to 125 Hz, the first threshold is in the range of 48 dB to 52 dB.

[0016] In some embodiments, within a frequency band greater than 125Hz and less than or equal to 375Hz, the first threshold is in the range of 49dB-54dB.

[0017] In some embodiments, within a frequency band with a frequency greater than 375Hz and less than or equal to 625Hz, the first threshold is in the range of 50dB-55dB.

[0018] In some embodiments, within a frequency band with a frequency greater than 0 Hz and less than or equal to 125 Hz, the second threshold is in the range of 5 dB to 10 dB.

[0019] In some embodiments, within a frequency band greater than 125Hz and less than or equal to 375Hz, the second threshold is in the range of 3dB-7dB.

[0020] In some embodiments, within a frequency band greater than 375Hz and less than or equal to 625Hz, the second threshold is in the range of 1dB-4dB.

[0021] In some embodiments, configuring the bone conduction hearing aid based on the reference output parameters and the adjustment value includes: configuring the bone conduction hearing aid using a multi-channel wide dynamic range compression system based on the reference output parameters and the adjustment value.

[0022] In some embodiments, obtaining the adjustment value of the reference output parameter includes: comparing the reference output parameter with a first threshold, the first threshold being related to the wearer's vibration perception of each sound level in each frequency band; and determining the adjustment value corresponding to the reference output parameter based on the comparison result between the reference output parameter and the first threshold.

[0023] In some embodiments, the adjustment value includes a gain reduction value of the multi-channel wide dynamic range compression system when at least one of the various sound levels is greater than a sound level threshold; determining the adjustment value corresponding to the reference output parameter based on the comparison result of the reference output parameter and the first threshold includes: if the reference output parameter is less than or equal to the first threshold, the gain reduction value is 0dB; if the reference output parameter is greater than the first threshold, the gain reduction value is the difference between the first threshold and the reference output parameter.

[0024] In some embodiments, the adjustment value includes a reduction in the maximum output of the multi-channel wide dynamic range compression system when at least one of the sound levels is greater than a sound level threshold; determining the adjustment value corresponding to the reference output parameter based on the comparison result between the reference output parameter and the first threshold includes: if the reference output parameter is less than or equal to the first threshold, the reduction in the maximum output is 0 dB; if the reference output parameter is greater than the first threshold, the reduction in the maximum output is greater than 0 dB.

[0025] One embodiment of this application provides a configuration system for a bone conduction hearing aid, comprising: an acquisition module for acquiring hearing loss data of a wearer; a reference output parameter determination module for determining reference output parameters of the bone conduction hearing aid at various sound levels and frequency bands based on the hearing loss data; an adjustment value determination module for acquiring adjustment values ​​of the reference output parameters; and a configuration module for configuring the bone conduction hearing aid based on the reference output parameters and the adjustment values.

[0026] One embodiment of this application provides a configuration device for a bone conduction hearing aid, comprising: a processing device; and a storage device communicating with the processing device for storing instructions. When the processing device executes the stored instructions, the processing device executes the configuration method for the bone conduction hearing aid described in any of the above technical solutions.

[0027] One embodiment of this application provides a computer-readable storage medium that stores computer instructions. When a computer reads the computer execution instructions in the storage medium, the computer executes the configuration method of the bone conduction hearing aid device described in any of the above technical solutions. Attached Figure Description

[0028] This application will be further described by way of exemplary embodiments, which will be described in detail with reference to the accompanying drawings. These embodiments are not limiting; in these embodiments, the same reference numerals denote the same structures, wherein:

[0029] Figure 1This is a schematic diagram of the configuration of a bone conduction hearing aid device according to some embodiments of this application;

[0030] Figure 2 This is a schematic diagram of the structure of a bone conduction hearing aid device according to some embodiments of this application;

[0031] Figure 3 This is a block diagram of a configuration system for a bone conduction hearing aid device according to some embodiments of this application;

[0032] Figure 4 This is a flowchart illustrating a method for configuring a bone conduction hearing aid according to some embodiments of this application;

[0033] Figure 5 This is a flowchart illustrating the determination of adjustment values ​​according to other embodiments of this application;

[0034] Figure 6 This is a flowchart illustrating the determination of adjustment values ​​according to other embodiments of this application;

[0035] Figure 7 This is a flowchart illustrating the operations performed during use of the bone conduction hearing aid device according to some embodiments of this application;

[0036] Figure 8 This is a graph showing the vibration perception thresholds at different frequencies when wearers are using bone conduction hearing aids, as determined by experiments.

[0037] Figure 9 This is a graph showing the experimental results of speech recognition rate testing on wearer 1;

[0038] Figure 10 This is a graph showing the experimental results of speech recognition rate testing on wearer 2;

[0039] Figure 11 This is a graph showing the experimental results of speech recognition rate testing on wearer 3. Detailed Implementation

[0040] To more clearly illustrate the technical solutions of the embodiments in this specification, the accompanying drawings used in the description of the embodiments will be briefly introduced below. Obviously, the drawings described below are merely some examples or embodiments of this specification. For those skilled in the art, these drawings can be applied to other similar scenarios without creative effort. Unless obvious from the context or otherwise specified, the same reference numerals in the drawings represent the same structures or operations.

[0041] It should be understood that the terms “system,” “device,” “unit,” and / or “module” used herein are one way to distinguish different components, elements, parts, sections, or assemblies at different levels. However, if other terms can achieve the same purpose, they may be replaced by other expressions.

[0042] As indicated in this specification and claims, unless the context clearly indicates otherwise, the words "a," "an," "an," and / or "the" do not specifically refer to the singular and may also include the plural. Generally speaking, the terms "comprising" and "including" only indicate the inclusion of expressly identified steps and elements, which do not constitute an exclusive list, and the method or apparatus may also include other steps or elements.

[0043] Flowcharts are used in this specification to illustrate the operations performed by the system according to embodiments of this specification. It should be understood that the preceding or following operations are not necessarily performed in exact order. Instead, the steps can be processed in reverse order or simultaneously. Furthermore, other operations can be added to these processes, or one or more steps can be removed from them.

[0044] Figure 1 This is a schematic diagram of a bone conduction hearing aid configuration device according to some embodiments of this application. Figure 1 As shown, the bone conduction hearing aid configuration system 100 may include a bone conduction hearing aid 110, a processing device 120, a memory 130, one or more terminals 140, and a network 150. In some embodiments, the bone conduction hearing aid 110, processing device 120, memory 130, and / or terminal 140 may be interconnected and / or communicate with each other via a wireless connection (e.g., network 150), a wired connection, or a combination thereof. The connections between the components in the bone conduction hearing aid configuration system 100 can vary. By way of example only, the bone conduction hearing aid 110 may be connected to the processing device 120 via network 150, such as... Figure 1 As shown. For example, the bone conduction hearing aid 110 can be directly connected to the processing device 120. As another example, the memory 130 can be connected to the processing device 120 via a network 150, such as... Figure 1 As shown, it can be directly connected to processing device 120. As yet another example, terminal 140 can be connected to processing device 120 via network 150, such as... Figure 1 As shown, or directly connected to processing device 120.

[0045] The bone conduction hearing aid 110 can acquire sound information (e.g., ambient sound, wearer's voice, audio files acquired from other devices, etc.), process the acquired sound information, and convert it into vibration signals. These signals are then transmitted to the wearer's auditory center via the bones, allowing the wearer to hear the sound information carried by the vibration signals. Specifically, the bone conduction hearing aid can be a bone conduction hearing aid or a bone conduction headphone. This manual primarily uses a bone conduction hearing aid as an example for explanation.

[0046] In some embodiments, the bone conduction hearing aid 110 (such as a bone conduction hearing aid) may include a pickup component, a speaker component, etc. The pickup component is used to pick up sound information (also referred to as a first vibration signal, such as ambient sound or the wearer's voice) and process the picked-up first vibration signal, converting it into an electrical signal carrying sound information. The speaker component can convert the electrical signal carrying sound information acquired by the pickup element into a second vibration signal carrying sound information and transmit it to the wearer's auditory center. A detailed description of the bone conduction hearing aid 110 can be found elsewhere in this application (e.g., Figure 2 (and its detailed description).

[0047] In some embodiments, the configuration of bone conduction hearing aids can differ for different users due to variations in their hearing levels (i.e., levels of hearing loss). As described herein, the configuration of a bone conduction hearing aid refers to parameter values ​​(also referred to as parameters) related to the intensity of the sound signal output by the bone conduction hearing aid and / or the process of determining these parameters, enabling the bone conduction hearing aid to output a sound signal based on these parameter values. Parameter values ​​related to the intensity of the output signal of the bone conduction hearing aid may include a gain value (in dB), an analog output value (in dB), etc. In some embodiments, the gain value may be the value by which the hearing aid amplifies the intensity of the sound signal, and the analog output value may be the simulated output signal intensity value based on the input sound signal parameters (e.g., the intensity value of the sound signal). For example, the analog output value may be equal to the input sound signal value (i.e., the intensity value, in dB) plus the gain value (in dB). The bone conduction hearing aid configuration system 100 can determine the configuration of the bone conduction hearing aid corresponding to the user's hearing level based on the user's hearing level. The bone conduction hearing aid 110 can process and output acquired sound information (e.g., ambient sound, wearer's voice, audio files acquired from other devices) based on this configuration, enabling the wearer to hear sound.

[0048] Processing device 120 can process data and / or information obtained from bone conduction hearing aid 110, memory 130, and / or terminal 140. For example, processing device 120 can acquire hearing loss data of the wearer of bone conduction hearing aid 110. As another example, processing device 120 can determine reference output parameters of bone conduction hearing aid 110 at various sound levels and frequency bands based on the hearing loss data. As yet another example, processing device 120 can acquire adjustment values ​​for the reference output parameters. Furthermore, processing device 120 can configure bone conduction hearing aid 110 based on the reference output parameters and adjustment values.

[0049] In some embodiments, processing device 120 may be a single server or a group of servers. The server group may be centralized or distributed. In some embodiments, processing device 120 may be local or remote. For example, processing device 120 may access information and / or data stored in bone conduction hearing aid 110, terminal 140, and / or memory 130 via network 150. Alternatively, processing device 120 may be directly connected to bone conduction hearing aid 110, terminal 140, and / or memory 130 to access stored information and / or data. In some embodiments, processing device 120 may be implemented on a cloud platform. By way of example only, the cloud platform may include private cloud, public cloud, hybrid cloud, community cloud, distributed cloud, internal cloud, multi-tiered cloud, etc., or any combination thereof. In some embodiments, processing device 120 may be implemented on a computing device. In some embodiments, processing device 120 or a portion thereof may be integrated into bone conduction hearing aid 110. In some embodiments, processing device 120 or a portion thereof may be integrated into terminal 140.

[0050] Memory 130 may store data, instructions, and / or any other information. In some embodiments, memory 130 may store data obtained from terminal 140 and / or processing device 120. In some embodiments, memory 130 may store data and / or instructions that processing device 120 may execute or be used to execute the exemplary methods described in this application. In some embodiments, memory 130 may include a mass storage device, a removable storage device, a volatile read-write memory, a read-only memory (ROM), or any combination thereof. In some embodiments, memory 130 may be implemented on a cloud platform. By way of example only, the cloud platform may include a private cloud, a public cloud, a hybrid cloud, a community cloud, a distributed cloud, an internal cloud, a multi-tiered cloud, or any combination thereof. In some embodiments, memory 130 may be connected to network 150 to communicate with one or more other components (e.g., processing device 120, terminal 140, etc.) in the bone conduction hearing aid configuration system 100. One or more components of the bone conduction hearing aid configuration system 100 may access the data or instructions stored in memory 130 via network 150. In some embodiments, the memory 130 may be directly connected to or communicate with one or more other components (e.g., processing device 120, terminal 140, etc.) in the bone conduction hearing aid configuration system 100. In some embodiments, the memory 130 may be part of the processing device 120.

[0051] Terminal 140 may include mobile device 141, tablet computer 142, laptop computer 143, smartwatch 144, etc., or any combination thereof. In some embodiments, mobile device 141 may include smart home devices (e.g., control devices for smart appliances, smart monitoring devices, smart TVs, smart cameras), wearable devices (e.g., glasses, helmets, accessories, clothing, etc.), mobile devices (e.g., mobile phones, laptops, etc.), virtual reality devices (e.g., virtual reality helmets, virtual reality glasses, virtual reality goggles, etc.), etc., or any combination thereof. In some embodiments, bone conduction hearing aid 110 may be integrated into terminal 140, for example, integrated into glasses, accessories, etc.

[0052] In some embodiments, users (e.g., wearers of the bone conduction hearing aid 110, system operators, doctors, etc.) can interact with the bone conduction hearing aid configuration system 100 through terminal 140. For example, users can send configuration requests through the user interface on terminal 140; after receiving the configuration request, processing device 120 obtains the wearer's hearing loss data. For example, processing device 120 can send a hearing loss data acquisition request to terminal 140 through the user interface, and users can upload the wearer's hearing loss data through the user interface after receiving the acquisition request. Processing device 120 can configure the bone conduction hearing aid 110 based on the hearing loss data.

[0053] Network 150 may include any suitable network that can facilitate the exchange of information and / or data between the bone conduction hearing aid configuration system 100. In some embodiments, components of one or more bone conduction hearing aid configuration systems 100 (e.g., bone conduction hearing aid 110, terminal 140, processing device 120, memory 130, etc.) may exchange information and / or data with other components of one or more bone conduction hearing aid configuration systems 100 via network 150. For example, processing device 120 may obtain hearing loss data (e.g., hearing level) of the wearer from bone conduction hearing aid 110 via network 150. As another example, processing device 120 may obtain user instructions from terminal 140 via network 150. Network 150 may be and / or include public networks (e.g., the Internet), private networks (e.g., local area networks (LANs), wide area networks (WANs), etc.), wired networks (e.g., Ethernet networks), wireless networks (e.g., 802.11 networks, Wi-Fi networks, etc.), cellular networks (e.g., LTE networks), Frame Relay networks, virtual private networks ("VPNs"), satellite networks, telephone networks, routers, hubs, switches, server computers, and / or any combination thereof. In some embodiments, network 150 may include one or more network access points. For example, network 150 may include wired and / or wireless network access points such as base stations and / or Internet switching points, through which one or more components of the bone conduction hearing aid configuration system 100 can connect to network 150 to exchange data and / or information.

[0054] This description is intended to be illustrative and not to limit the scope of this application. Many alternatives, modifications, and variations will be apparent to those skilled in the art. The features, structures, methods, and other features of the exemplary embodiments described herein can be combined in various ways to obtain other and / or alternative exemplary embodiments. For example, memory 130 may be a data storage device including cloud computing platforms, such as public clouds, private clouds, community clouds, and hybrid clouds. However, these variations and modifications do not depart from the scope of this application.

[0055] Figure 2 This is a structural schematic diagram of a bone conduction hearing aid device according to some embodiments of this application. For example... Figure 2 As shown, the bone conduction hearing aid 200 may include a speaker assembly 210, a pickup assembly 220, and a support assembly 230.

[0056] The speaker assembly 210 can convert a signal containing sound information into a vibration signal. In some embodiments, the sound information may include video or audio files with a specific data format, or data or files that can be converted into sound through a specific means. The signal containing sound information may include one or more combinations of electrical signals, optical signals, magnetic signals, mechanical signals, etc. The signal containing sound information may come from one signal source or multiple signal sources. Multiple signal sources may be correlated or uncorrelated. In some embodiments, the bone conduction hearing aid 200 can acquire signals containing sound information in a variety of different ways, and the acquisition of the signal may be wired or wireless, and may be real-time or delayed. For example, the bone conduction hearing aid 200 can receive electrical signals containing sound information through wired or wireless means. As another example, the bone conduction hearing aid 10 may include a component with sound acquisition function (e.g., a pickup assembly 220) that picks up sound in the environment, converts the mechanical vibration of the sound into an electrical signal, and obtains an electrical signal that meets specific requirements after being processed by an amplifier.

[0057] The loudspeaker assembly 210 converts a signal containing sound information into a vibration signal, which is an energy conversion process. This conversion may involve the coexistence and conversion of multiple different types of energy. The loudspeaker assembly 210 may include one or more transducers. For example, an electrical signal can be directly converted into mechanical vibration through a transducer to generate sound. As another example, sound information may be contained in an optical signal, and the transducer can convert the optical signal into a vibration signal. Other types of energy that can coexist and be converted during the operation of the transducer include thermal energy and magnetic field energy. In some embodiments, the loudspeaker assembly 210 can achieve the conversion from sound information signal to vibration signal through the cooperation of a magnetic circuit assembly 211 and a vibration assembly 213 (both the magnetic circuit assembly 211 and the vibration assembly 213 can be referred to as transducers). The magnetic circuit assembly 211 provides a magnetic field, and the vibration assembly 213 is subjected to Ampere force mechanical vibration within the magnetic field. For example, the magnetic circuit assembly 211 may include a magnet. The vibration assembly 213 may include a magnetic oscillator and a vibrating plate. A magnetic oscillator (e.g., a voice coil) moves back and forth within a magnetic field under the influence of the Ampere force, driving a resonator to vibrate during this motion. In this process, sound information can correspond to the vibration of the magnetic oscillator, and the vibration frequency and amplitude of the magnetic oscillator can be determined based on the frequency and intensity of the sound information. In some embodiments, one of the magnetic circuit components and the magnetic oscillator can be an electromagnet. The magnetic field strength can be controlled by controlling the number of coils and / or the current intensity in the electromagnet, thereby controlling the vibration amplitude of the magnetic oscillator. Alternatively, the vibration frequency of the magnetic oscillator can be controlled by controlling the frequency of the change in the direction of the current in the coils of the electromagnet. During this process, the sound information can also be amplified; for example, the loudness of the sound information can be increased by increasing the vibration amplitude of the magnetic oscillator.

[0058] The specific energy conversion methods of the vibration component can include moving coil, electrostatic, piezoelectric, moving iron, pneumatic, and electromagnetic types. The frequency response range and sound quality of the bone conduction hearing aid 200 are affected by the vibration component. For example, in a moving coil transducer, the vibration component can include a wound cylindrical voice coil and a vibrating body (e.g., a vibrating plate or diaphragm). The cylindrical voice coil, driven by a signal current, drives the vibrating body to vibrate and produce sound in a magnetic field. The stretching and contraction of the vibrating body material, the deformation of its folds, its size, shape, and fixing method, as well as the magnetic density of the magnetic field, all have a significant impact on the sound quality of the bone conduction hearing aid. The vibrating body in the vibration assembly can be a mirror-symmetric structure, a centrally symmetric structure, or an asymmetrical structure. The vibrating body can be provided with discontinuous perforated structures to allow the vibrating body to produce greater displacement, thereby enabling the bone conduction hearing aid 200 to achieve higher sensitivity and improve the transmission power of vibration and sound. The vibrating body can be a ring structure with multiple support rods radiating towards the center inside the ring. The number of support rods can be two or more.

[0059] The pickup component 220 is primarily used to pick up the user's voice and ambient sounds from the user's environment. For hearing-impaired individuals, the pickup effect of the pickup component 220 will affect the clarity and stability of the sound received by the hearing-impaired through bone conduction hearing aids. In some embodiments, the pickup component 220 may include a microphone. In some embodiments, the pickup component 220 can convert external sound signals into electrical signals. In some embodiments, the pickup component 220 may include a diaphragm, a coil, and a magnet. The diaphragm may be connected to the coil, and the coil may be placed in the magnetic field generated by the magnet. External sound waves (i.e., sound signals or vibration signals) can cause the diaphragm to vibrate, which can drive the coil to move together. The movement of the coil in the magnetic field generated by the magnet will generate a current, so that the sound signal is converted into an electrical signal, thereby completing the pickup of external sound.

[0060] The support assembly 230 can support other components in the bone conduction hearing aid 200 (e.g., magnetic circuit assembly, vibration assembly and / or storage assembly, power supply assembly, communication assembly (not shown), and pickup assembly 220). The support assembly 230 may include one or more housings and one or more connectors. One or more housings may form a receiving cavity 232 for accommodating the storage assembly, controller, pickup assembly 220, communication assembly, battery assembly, etc. One or more connectors can connect the housings to other components in the bone conduction hearing aid 200 (e.g., magnetic circuit assembly, vibration assembly and / or storage assembly, power supply assembly, communication assembly (not shown), and pickup assembly 220).

[0061] The wired connection involved in the bone conduction hearing aid 200 may include metallic cables, optical cables, or hybrid cables of metallic and optical types, such as coaxial cables, communication cables, flexible cables, spiral cables, non-metallic sheathed cables, metallic sheathed cables, multi-core cables, twisted-pair cables, ribbon cables, shielded cables, telecommunication cables, two-strand cables, parallel two-core conductors, twisted-pair wires, and combinations thereof. The examples described above are for illustrative purposes only; the medium for the wired connection can also be other types, such as other carriers for transmitting electrical or optical signals.

[0062] The wireless connectivity involved in the bone conduction hearing aid 200 can include radio communication, free-space optical communication, acoustic communication, and electromagnetic induction. Radio communication can include IEEE 802.11 series standards, IEEE 802.15 series standards (such as Bluetooth and Pocket Bee technologies), first-generation mobile communication technologies, second-generation mobile communication technologies (such as FDMA, TDMA, SDMA, CDMA, and SSMA), General Packet Radio Service technologies, third-generation mobile communication technologies (such as CDMA2000, WCDMA, TD-SCDMA, and WiMAX), fourth-generation mobile communication technologies (such as TD-LTE and FDD-LTE), satellite communication (such as GPS technology), near-field communication (NFC), and other technologies operating in the ISM band (such as 2.4GHz). Free-space optical communication can include visible light and infrared signals. Acoustic communication can include sound waves and ultrasonic signals. Electromagnetic induction can include near-field communication technologies. The examples described above are for illustrative purposes only. The wireless connection medium can also be other types, such as Z-wave technology, other paid civilian radio frequency bands, and military radio frequency bands. For example, as one application scenario of this technology, the bone conduction hearing aid 200 can acquire signals containing sound information from other devices via Bluetooth technology.

[0063] The above description of the structure of the bone conduction hearing aid 200 is merely a specific example and should not be considered the only feasible implementation. Obviously, those skilled in the art, after understanding the basic principles of the bone conduction hearing aid 200, may make various modifications and changes in form and detail to the specific methods and steps of implementing the bone conduction hearing aid 200 without departing from these principles; however, these modifications and changes are still within the scope of the above description. For example, the bone conduction hearing aid 200 may include one or more processors, which can execute one or more sound signal processing algorithms. The sound signal processing algorithms can modify or enhance the sound signal. For example, noise reduction, acoustic feedback suppression, wide dynamic range compression, automatic gain control, active environmental recognition, active noise cancellation, directional processing, tinnitus processing, multi-channel wide dynamic range compression, active howling suppression, volume control, or other similar or any combination of the above processing can be performed on the sound signal; these modifications and changes are still within the scope of protection of the claims of this invention. As another example, the bone conduction hearing aid may include one or more sensors, such as temperature sensors, humidity sensors, speed sensors, displacement sensors, etc. The sensors can collect user information or environmental information. For example, the storage component may not be necessary and can be removed from bone conduction hearing aids.

[0064] In some embodiments, the configuration system for bone conduction hearing aids is primarily based on the wearer's hearing loss data, configured according to a preset formula or a preset algorithm of the hearing aid configuration system. For example, in the hearing aid configuration system, after the wearer's hearing loss data is input, the system can automatically output relevant parameter values ​​of the hearing aid based on a preset algorithm. Configuring the bone conduction hearing aid directly using only a preset algorithm may cause the configured bone conduction hearing aid 200 to vibrate excessively in certain scenarios (such as when the wearer speaks or when the ambient noise is too loud), causing discomfort to the wearer.

[0065] This application provides a configuration system for a bone conduction hearing aid. Figure 3 This is a block diagram of a configuration system for a bone conduction hearing aid device according to some embodiments of this application. For example... Figure 3 As shown, the configuration system 300 of the bone conduction hearing aid includes an acquisition module 310, a reference output parameter determination module 320, an adjustment value determination module 330, and a configuration module 340. The connections between the modules can be wired, wireless, or a combination of both. Any module can be local, remote, or a combination of both. The correspondence between modules can be one-to-one or one-to-many.

[0066] In some embodiments, the acquisition module 310 can be used to acquire hearing loss data of the wearer.

[0067] In some embodiments, the reference output parameter determination module 320 can be used to determine the reference output parameters of the bone conduction hearing aid at each sound level and frequency band based on hearing loss data.

[0068] In some embodiments, the adjustment value determination module 330 can be used to obtain the adjustment value of the reference output parameter. In some embodiments, the adjustment value is the same for different hearing levels and in the same frequency band. In some embodiments, the adjustment value is 1dB-12dB in the frequency band with a frequency greater than 0Hz and less than or equal to 625Hz. In some embodiments, the adjustment value is set to 5dB-12dB in the frequency band with a frequency greater than 0Hz and less than or equal to 125Hz; the adjustment value is set to 3dB-9dB in the frequency band with a frequency greater than 125Hz and less than or equal to 375Hz; and / or, the adjustment value is set to 1dB-6dB in the frequency band with a frequency greater than 375Hz and less than or equal to 625Hz. In some embodiments, the adjustment value is 5dB-7dB in the frequency band greater than 0Hz and less than or equal to 125Hz; 3dB-5dB in the frequency band greater than 125Hz and less than or equal to 375Hz; and / or, 1dB-3dB in the frequency band greater than 375Hz and less than or equal to 625Hz. In some embodiments, the adjustment value is 10dB-12dB in the frequency band greater than 0Hz and less than or equal to 125Hz; 7dB-9dB in the frequency band greater than 125Hz and less than or equal to 375Hz; and / or, 4dB-6dB in the frequency band greater than 375Hz and less than or equal to 625Hz. In some embodiments, the adjustment value varies for different hearing levels and within the same frequency band. In some embodiments, the adjustment value determination module 330 may be used to: determine a first threshold corresponding to each frequency band and each sound level, the first threshold being related to the wearer's vibration perception level at each sound level in each frequency band; determine a second threshold corresponding to each frequency band and each sound level, the second threshold being related to the wearer's speech recognition rate at each sound level in each frequency band; and determine an adjustment value based on a reference output parameter, the first threshold, and the second threshold. In some embodiments, the adjustment value determination module 330 may be used to: for each sound level and a certain sound level in each frequency band and a reference output parameter in a certain frequency band; subtract the first threshold from the reference output parameter to obtain a comparison value; compare the comparison value with the second threshold; and determine the adjustment value corresponding to the reference output parameter based on the comparison result of the comparison value and the second threshold. In some embodiments, the adjustment value determination module 330 may be used to: set the adjustment value to 0dB in response to a comparison value less than or equal to 0; set the adjustment value to the comparison value in response to a comparison value greater than 0 but less than or equal to the second threshold; and set the adjustment value to the second threshold in response to a comparison value greater than the second threshold.

[0069] In some embodiments, within a frequency band greater than 0 Hz and less than or equal to 125 Hz, the first threshold is in the range of 48 dB to 52 dB. In some embodiments, within a frequency band greater than 125 Hz and less than or equal to 375 Hz, the first threshold is in the range of 49 dB to 54 dB. In some embodiments, within a frequency band greater than 375 Hz and less than or equal to 625 Hz, the first threshold is in the range of 50 dB to 55 dB. In some embodiments, within a frequency band greater than 0 Hz and less than or equal to 125 Hz, the second threshold is in the range of 5 dB to 10 dB. In some embodiments, within a frequency band greater than 125 Hz and less than or equal to 375 Hz, the second threshold is in the range of 3 dB to 7 dB. In some embodiments, within a frequency band greater than 375 Hz and less than or equal to 625 Hz, the second threshold is in the range of 1 dB to 4 dB.

[0070] In some embodiments, when a bone conduction hearing aid is configured using a multi-channel wide dynamic range compression system, the adjustment value determination module 330 can be used to: compare a reference output parameter with a first threshold; the first threshold is related to the wearer's perception of vibration at each sound level in each frequency band; and determine an adjustment value corresponding to the reference output parameter based on the comparison result between the reference output parameter and the first threshold. In some embodiments, the adjustment value includes a gain reduction value when at least one sound level in each sound level is greater than a sound level threshold; the adjustment value determination module 330 can be used to: set the gain reduction value to 0dB in response to the reference output parameter being less than or equal to the first threshold; and set the gain reduction value to the difference between the first threshold and the reference output parameter in response to the reference output parameter being greater than the first threshold. In some embodiments, the adjustment value includes a reduction value of the maximum output of the multi-channel wide dynamic range compression system; the adjustment value determination module 330 can be used to: set the maximum output reduction value to 0dB in response to the reference output parameter being less than or equal to the first threshold; and set the maximum output reduction value to be greater than 0dB in response to the reference output parameter being greater than the first threshold.

[0071] In some embodiments, the configuration module 340 can be used to configure the bone conduction hearing aid device based on a reference output parameter and an adjustment value. In some embodiments, the configuration module 340 can also be used to reduce the reference output parameter based on the adjustment value in a frequency band greater than 0 Hz and less than or equal to 625 Hz. In some embodiments, the configuration module 340 can be used to configure the bone conduction hearing aid device using a multi-channel wide dynamic range compression system based on the reference output parameter and the adjustment value.

[0072] It is important to note that the above descriptions of the processing modules are merely specific examples and should not be considered the only feasible implementation. Each of the above modules or units is not mandatory; each module or unit can be implemented using one or more components, and the function of each module or unit is not limited to this. The above modules or units can be added or removed depending on the specific implementation scenario or needs. Obviously, for those skilled in the art, after understanding the basic principles of the capacity scheduling process, it is possible to make various formal and detailed modifications and changes to the specific implementation methods and steps of the processing modules without departing from these principles. Several simple deductions or substitutions can also be made, and the order of the modules or units can be adjusted, combined, or split without creative effort; however, these modifications and changes are still within the scope of the above description.

[0073] Figure 4 This is a flowchart illustrating a method for configuring a bone conduction hearing aid device according to some embodiments of this application.

[0074] like Figure 4 As shown, the process 400 for configuring a bone conduction hearing aid includes the following steps:

[0075] Step 410: Acquire the wearer's hearing loss data. Specifically, step 410 can be performed by the acquisition module 310.

[0076] In some embodiments, the wearer's hearing loss data can be understood as data related to the wearer's hearing loss condition. Hearing loss data may include the wearer's hearing level (also called hearing threshold or hearing loss level) across various frequency bands and sound levels. In this specification, the unit used for hearing level is dBHL. The higher the hearing level value, the more severe the wearer's hearing loss. In some embodiments, hearing loss data may include data related to the wearer's historical hearing aids. For example, data related to the wearer's historical hearing aids may include configuration data of bone conduction hearing aids used by the wearer in the past.

[0077] In some embodiments, the hearing level can range from 0 dBHL to 80 dBHL. For example, a hearing level of 0 dBHL to 25 dBHL indicates normal hearing; a hearing level of 26 dBHL to 40 dBHL indicates mild hearing loss; a hearing level of 41 dBHL to 60 dBHL indicates moderate hearing loss, manifested as difficulty hearing normal sounds; a hearing level of 61 dBHL to 80 dBHL indicates severe hearing loss, manifested as difficulty hearing loud sounds; and a hearing level greater than 80 dBHL indicates profound hearing loss, manifested as difficulty hearing loud sounds.

[0078] In some embodiments, the hearing level of a wearer of a bone conduction hearing aid can be the same across different frequency bands at the same sound level (see the relevant content in step 420 for a detailed explanation of sound levels). For example, at a sound level of 20 dBC, the wearer's hearing level across different frequency bands can all be equal to a value within the range of 41 dBHL to 60 dBHL; at a sound level of 40 dBC, the wearer's hearing level across different frequency bands can all be equal to a value within the range of 26 dBHL to 40 dBHL; and at a sound level of 60 dBC, the wearer's hearing level across different frequency bands can all be equal to a value within the range of 0 dBHL to 25 dBHL.

[0079] In some embodiments, the hearing level of a wearer of a bone conduction hearing aid may differ across different frequency bands at the same sound level. For example, at a sound level of 20 dBC, the wearer's hearing level in the high-frequency range (e.g., 8000 Hz-12000 Hz) may all be equal to a value within the range of 41 dBHL-60 dBHL; and the hearing level in the low-frequency range may all be equal to a value within the range of 26 dBHL-40 dBHL.

[0080] In some embodiments, the hearing level of a wearer of a bone conduction hearing aid can be the same at different sound levels within the same frequency band. For example, in the 250Hz-500Hz frequency band, the wearer's hearing level at different sound levels can be equal to a value between 0dBHL and 25dBHL; in the 500Hz-1000Hz frequency band, the wearer's hearing level at different frequency bands can be equal to a value between 26dBHL and 40dBHL; and in the 1000Hz-2000Hz frequency band, the wearer's hearing level at different frequency bands can be equal to a value between 41dBHL and 60dBHL.

[0081] In some embodiments, the hearing level of a wearer of a bone conduction hearing aid can vary depending on the sound level within the same frequency band. For example, in the 250Hz-500Hz frequency band, the wearer's hearing level at 20dBC can be equal to a value within the range of 41dBHL-60dBHL; at 40dBC, the hearing level can be equal to a value within the range of 26dBHL-40dBHL; and at 60dBC, the hearing level can be equal to a value within the range of 0dBHL-25dBHL.

[0082] In some embodiments, hearing loss data of the wearer can be obtained by performing real-time hearing tests on the wearer. For example, a hearing aid dispenser can use a hearing testing device to perform hearing tests on the wearer (e.g., playing sound signals at various frequency bands and sound levels) to obtain the wearer's hearing loss data. The hearing loss data collected by the hearing testing device can be directly uploaded to a processing device (e.g., processing device 120) via a network (e.g., network 150) or uploaded to a storage device, from which the processing device can retrieve the hearing loss data. In other embodiments, the wearer can upload their own hearing loss data via a terminal (e.g., terminal 140), and the bone conduction hearing aid configuration system (e.g., bone conduction hearing aid configuration system 100) or device (e.g., processing device 120) can receive the hearing loss data uploaded by the wearer via wired or wireless means. In some embodiments, the bone conduction hearing aid configuration system or device can retrieve the wearer's hearing loss data from a relevant memory (e.g., memory 130).

[0083] Step 420: Based on the hearing loss data, determine the reference output parameters of the bone conduction hearing aid at each sound level and frequency band. Specifically, step 420 can be executed by the reference output parameter determination module 320.

[0084] In some embodiments, the reference output parameter may be the reference analog output value of the bone conduction hearing aid at each sound level and frequency band (i.e., the intensity value of the simulated signal output by the bone conduction hearing aid, in dB). In some embodiments, the reference output parameter may be the reference gain value of the bone conduction hearing aid at each sound level and frequency band (i.e., the intensity value of the sound signal amplified by the bone conduction hearing aid, in dB). It should be noted that when the sound signal input to the bone conduction hearing aid at the reference output parameter (e.g., the reference gain value) meets a specific sound level and frequency band, the intensity value of the sound signal output by the bone conduction hearing aid may be equal to the reference analog output value at that specific sound level and frequency band. In some embodiments, the reference output parameter is related to the hearing loss level, sound level, frequency, etc. In some embodiments, the reference analog output value of the bone conduction hearing aid is further related to the reference gain value of the bone conduction hearing aid. For example, the analog output value can be determined by amplifying the signal intensity corresponding to the sound level based on the gain value. In some embodiments, the reference output parameter may differ for different wearers due to differences in their hearing loss data (e.g., the degree of hearing loss at each sound level). In some embodiments, the sound level and frequency of the sound signal affect the reference output parameters of the bone conduction hearing aid. Different sound levels and / or different frequency bands may correspond to different reference output parameters. That is, for the same level of hearing loss and the same sound level, different frequency bands may correspond to different reference output parameters; for the same level of hearing loss and the same frequency band, different sound levels may correspond to different reference output parameters; for the same sound level and the same frequency band, different levels of hearing loss may correspond to different reference output parameters.

[0085] The sound level mentioned in this specification refers to the intensity of a sound signal, measured in decibels (dB). In this specification, sound level is primarily measured using C-frequency weighting, meaning the unit for sound level is dBC. Frequency bands, in this specification, refer to the frequency range of a sound signal. In some embodiments, the frequency of a sound signal can be divided into multiple continuous ranges to form different frequency bands.

[0086] In some embodiments, determining the reference output parameters of the bone conduction hearing aid at various sound levels and frequency bands may refer to determining the parameter output parameters corresponding to the hearing loss level of the bone conduction hearing aid at a preset sound level and / or preset frequency, and the corresponding hearing loss level of the wearer at that preset sound level and preset frequency. In some embodiments, determining the reference output parameters of the bone conduction hearing aid at various sound levels and frequency bands may refer to determining the parameter output parameters corresponding to the hearing loss level of the bone conduction hearing aid at a preset sound level range and / or preset frequency band, and the corresponding hearing loss level of the wearer at that preset sound level range and preset frequency band. Based on these determined reference output parameters, the bone conduction hearing aid can amplify and convert the input sound signal (i.e., the sound input signal) into a vibration signal and transmit it to the wearer so that the wearer can hear the sound. In some embodiments, the preset sound level, preset frequency, preset sound level range, and / or preset frequency band may be the default settings of the system (e.g., the bone conduction hearing aid configuration system 100) or set by the user. In some embodiments, the preset sound level may include 20 dBc, 30 dBc, 40 dBc, 50 dBc, 60 dBc, 70 dBc, 80 dBc, or combinations thereof. In some embodiments, the preset frequency may include 250 Hz, 500 Hz, 1000 Hz, 2000 Hz, 3000 Hz, 4000 Hz, 8000 Hz, 10000 Hz, or combinations thereof. In some embodiments, the preset sound level range may include 10 dBc-20 dBc (excluding 20 dBc), 20 dBc-30 dBc (excluding 30 dBc), 30 dBc-40 dBc (excluding 40 dBc), 40 dBc-50 dBc (excluding 50 dBc), 50 dBc-60 dBc (excluding 60 dBc), 60 dBc-70 dBc (excluding 70 dBc), 70 dBc-80 dBc (excluding 80 dBc), or combinations thereof. In some embodiments, the preset frequency band may include 20Hz-250Hz (excluding 250Hz), 250Hz-500Hz (excluding 500Hz), 500Hz-1000Hz (excluding 1000Hz), 1000Hz-2000Hz (excluding 2000Hz), 2000Hz-3000Hz (excluding 3000Hz), 3000Hz-4000Hz (excluding 4000Hz), 4000Hz-6000Hz (excluding 6000Hz), 6000Hz-10000Hz (excluding 10000Hz), etc., or combinations thereof.In some embodiments, the preset frequency band may include 0Hz-125Hz (excluding 125Hz), 125Hz-375Hz (excluding 375Hz), 375Hz-625Hz (excluding 625Hz), 625Hz-875Hz (excluding 875Hz), 875Hz-1375Hz (excluding 1375Hz), 1375Hz-1875Hz (excluding 1875Hz), 1875Hz-2625Hz (excluding 2625Hz), 2625Hz-4875Hz (excluding 4875Hz), and combinations thereof. In some embodiments, the preset sound level, preset frequency, preset sound level range, and / or preset frequency band may be adjusted by the system (e.g., bone conduction hearing aid configuration system 100) or the user. For example, it may be adjusted according to the hearing level of the wearer of the bone conduction hearing aid. For example, if the wearer's hearing level is 10 dBHL at a sound level of 80 dBC (indicating that the wearer's hearing is normal at that sound level), then the maximum preset sound level can not exceed 80 dBC.

[0087] In some embodiments, the reference output parameter may be the reference gain value of the bone conduction hearing aid. The processing device 120 can determine the reference gain value of the bone conduction hearing aid at each sound level and frequency band based on the hearing level and the values ​​of each sound level and frequency band in the hearing loss data. For example, the reference gain value of the bone conduction hearing aid at the sound level of 20 dBc and the frequency band of 375 Hz-625 Hz can be determined based on the hearing level of the wearer of the bone conduction hearing aid at the sound level of 20 dBc and the frequency band of 375 Hz-625 Hz. In some embodiments, the reference output parameter may be the reference analog output signal strength value (i.e., the reference analog output value) of the bone conduction hearing aid. The processing device 120 can determine the reference analog output signal strength value (i.e., the reference analog output value) of the bone conduction hearing aid at each sound level and frequency band based on the values ​​of each sound level and the values ​​of each sound level and frequency band in the hearing loss data. For example, the reference analog output signal strength value (i.e., reference analog output value) of the bone conduction hearing aid at a sound level of 30 dBC and in the 125 Hz-375 Hz frequency band can be determined by the hearing level of the wearer of the bone conduction hearing aid at a sound level of 30 dBC and in the 125 Hz-375 Hz frequency band.

[0088] In some embodiments, the processing device 120 (reference output parameter determination module 320) may first determine the reference gain value of the bone conduction hearing aid at each sound level and frequency band based on hearing loss data, and then determine the reference analog output signal strength value (i.e., reference analog output value) of the bone conduction hearing aid at the corresponding sound level and frequency band based on the aforementioned gain value at each sound level and frequency band.

[0089] In some embodiments, the processing device 120 (reference output parameter determination module 320) can determine the reference output parameters using a preset formula. For example, the reference gain value for each sound level and frequency band can be determined using a preset formula based on the wearer's hearing loss data. In some embodiments, the preset formula can be the "1 / 2 gain principle" proposed by Lybarger, which states that for sensorineural hearing loss to achieve comfortable hearing, the required gain value should be half the degree of hearing threshold improvement. In other words, the reference gain value of the bone conduction hearing aid can be approximately half of the wearer's hearing loss.

[0090] In some embodiments, the reference output parameters in step 320 can be determined using empirical data from the table below (Table 1). For example, the reference gain value for each hearing loss level (determined based on hearing loss data) in each frequency band can be determined using the empirical data shown in the table below, and then the reference analog output value for the corresponding hearing loss level in the corresponding frequency band can be further determined using the reference gain value. The table below uses a sound level of 60 dBSPL as an example to illustrate the reference gain values ​​for each hearing level and each frequency band. As shown in Table 1, when the sound level is 60 dBSPL and the hearing level is 20 dBHL, the reference gain value for each frequency band is 0; when the hearing level is 40 dBHL, the reference gain value for the 125-375 Hz frequency band is 5. In some embodiments, when the sound level and hearing level are constant, the reference gain value can first increase and then decrease as the frequency band increases. In some embodiments, when the frequency band is constant, the reference gain value increases as the hearing level increases.

[0091] Table 1 illustrates the reference gain values ​​for each hearing level and frequency band, using a sound level of 60 dB SPL as an example.

[0092]

[0093]

[0094] In some embodiments, the processing device 120 may determine reference output parameters based on a configuration model. The configuration model may represent the relationship between the reference output parameters and frequency bands, sound levels, and hearing levels.

[0095] Step 430: Obtain the adjustment value of the reference output parameter. The adjustment value is at least frequency band related. Specifically, step 430 can be executed by the reference output adjustment value determination module 330.

[0096] An adjustment value refers to a numerical value used to adjust the reference output parameter. In some embodiments, the reference output parameter can be adjusted using the adjustment value, and the adjusted reference output parameter can be used as the actual analog output parameter of the bone conduction hearing aid. The following explanation uses reference analog output value and reference gain value as examples. For instance, the reference analog output value (the intensity value of the analog output signal) can be adjusted using the adjustment value to use the adjusted reference analog output value as the actual analog output value (the actual analog output signal intensity value) of the bone conduction hearing aid. As another example, the reference gain value (the intensity value of amplifying the sound signal) of the bone conduction hearing aid can be adjusted using the adjustment value to use the adjusted reference gain value as the actual gain value of the bone conduction hearing aid.

[0097] In some embodiments, the adjustment value is used to reduce the reference output parameter. For example, the adjustment value can be a numerical value used to attenuate the reference analog output value, i.e., the adjustment value can be subtracted from the reference output parameter. Another example is that the adjustment value can be a numerical value used to attenuate the reference gain value, i.e., the adjustment value can be subtracted from the reference gain value. Yet another example is that the adjustment value can be a proportional value less than 1, i.e., the adjustment value can be multiplied by the reference output parameter.

[0098] Strong vibrations in bone conduction hearing aids occur when the frequency of the input sound signal is low, such as when bone conduction headphones are prone to vibration in the 125Hz–625Hz frequency range. Therefore, an adjustment value can be set within the 0Hz–625Hz frequency range (or within the 125Hz–625Hz frequency range) to mitigate the strong vibrations in this frequency range.

[0099] Figure 8 This is a graph showing the vibration perception thresholds at various frequencies for wearers of bone conduction hearing aids, as determined experimentally. Figure 8 In this context, the vibration perception threshold (in dBV) refers to the numerical value obtained by converting the driving voltage (in V) of the bone conduction hearing aid when the wearer can perceive vibration. If the driving voltage of the bone conduction hearing aid is X (in V), then the vibration perception threshold is 20*log10(X / 1) (in dBV). For example, when the driving voltage of the bone conduction hearing aid is 1V, the corresponding vibration perception threshold is 0dBV; when the driving voltage is 0.5V, the corresponding vibration perception threshold is -6dBV. Figure 8 It can be seen that bone conduction hearing aids have a relatively low vibration perception threshold below 1000Hz, indicating that they are prone to vibration in this frequency range, especially between 125Hz and 600Hz. Specifically, bone conduction hearing aids are most likely to vibrate at 125Hz, 250Hz, 400Hz, and 500Hz. Therefore, based on the experimental data, adjustment values ​​can be set within the 0Hz–625Hz frequency range (or within the 125Hz–625Hz frequency range).

[0100] In some embodiments, the same adjustment value can correspond to the same frequency band and / or the same sound level at different hearing levels. For example, the adjustment value for a hearing level in the 26dBHL-40dBHL frequency band, 0Hz-625Hz frequency band, and at a sound level of 20dBC is the same as the adjustment value for a hearing level in the 41dBHL-60dBHL frequency band, 0Hz-625Hz frequency band, and at a sound level of 20dBC. As another example, the adjustment value for a hearing level in the 26dBHL-40dBHL frequency band, 0Hz-125Hz frequency band, and at a sound level of 20dBC is the same as the adjustment value for a hearing level in the 41dBHL-60dBHL frequency band, 0Hz-125Hz frequency band, and at a sound level of 20dBC. For example, the adjustment values ​​for hearing level in the 26dBHL-40dBHL frequency range and the 125Hz-375Hz frequency range, as well as at a sound level of 20dBC, are the same as the adjustment values ​​for hearing level in the 41dBHL-60dBHL frequency range and the 125Hz-375Hz frequency range, as well as at a sound level of 20dBC.

[0101] In some embodiments, the same frequency band and / or the same sound level may correspond to different adjustment values ​​at different hearing levels. For example, the adjustment values ​​for a hearing level at 26dBHL-40dBHL, with a frequency range of 0Hz-625Hz and a sound level of 20dBC may differ from those for a hearing level at 41dBHL-60dBHL, with a frequency range of 0Hz-625Hz and a sound level of 20dBC. As another example, the adjustment values ​​for a hearing level at 26dBHL-40dBHL, with a frequency range of 20Hz-125Hz and a sound level of 20dBC may differ from those for a hearing level at 41dBHL-60dBHL, with a frequency range of 20Hz-125Hz and a sound level of 20dBC. For example, the adjustment values ​​for hearing level in the 26dBHL-40dBHL frequency range and at a frequency of 125Hz-375Hz and a sound level of 20dBC are different from the adjustment values ​​for hearing level in the 41dBHL-60dBHL frequency range and at a frequency of 125Hz-375Hz and a sound level of 20dBC.

[0102] In some embodiments, the same adjustment value can correspond to the same frequency band and / or the same hearing level at different sound levels. For example, the adjustment value for a sound level in the 20dBC-40dBC frequency band and the 0Hz-125Hz frequency band, and the hearing level of 41dBHL-60dBHL can be the same as the adjustment value for a sound level in the 40dBC-60dBC frequency band and the 0Hz-125Hz frequency band, and the hearing level of 41dBHL-60dBHL. As another example, the adjustment value for a sound level in the 20dBC-40dBC frequency band and the 125Hz-375Hz frequency band, and the hearing level of 26dBHL-40dBHL can be the same as the adjustment value for a sound level in the 40dBC-60dBC frequency band and the 125Hz-375Hz frequency band, and the hearing level of 26dBHL-40dBHL.

[0103] In some embodiments, different adjustment values ​​may correspond to the same frequency band and / or the same hearing level at different sound levels. For example, the adjustment values ​​for sound levels in the 26dBC-40dBC frequency band, the 0Hz-125Hz frequency band, and the 41dBHL-60dBHL hearing level may be different from the adjustment values ​​for sound levels in the 40dBC-60dBC frequency band, the 0Hz-125Hz frequency band, and the 41dBHL-60dBHL hearing level. As another example, the adjustment values ​​for sound levels in the 26dBC-40dBC frequency band, the 125Hz-375Hz frequency band, and the 26dBHL-40dBHL hearing level may be different from the adjustment values ​​for sound levels in the 40dBC-60dBC frequency band, the 125Hz-375Hz frequency band, and the 26dBHL-40dBHL hearing level.

[0104] In some embodiments, the same sound level and / or the same hearing level can correspond to the same adjustment value across different frequency bands. For example, the adjustment value for a sound level of 20dBC-40dBC and a hearing level of 41dBHL-60dBHL in the 0Hz-125Hz frequency band (excluding 125Hz) can be the same as the adjustment value for a sound level of 20dBC-40dBC and a hearing level of 41dBHL-60dBHL in the 125Hz-375Hz frequency band. As another example, the adjustment value for a sound level of 40dBC-60dBC and a hearing level of 26dBHL-40dBHL in the 125Hz-375Hz frequency band (excluding 375Hz) can be the same as the adjustment value for a sound level of 40dBC-60dBC and a hearing level of 26dBHL-40dBHL in the 375Hz-625Hz frequency band.

[0105] In some embodiments, the same sound level and / or the same hearing level may correspond to different adjustment values ​​in different frequency bands. For example, the adjustment values ​​for the 0Hz-125Hz frequency band (excluding 125Hz), sound level of 20dBC-40dBC, and hearing level of 41dBHL-60dBHL may be different from the adjustment values ​​for the 125Hz-375Hz frequency band. As another example, the adjustment values ​​for the 125Hz-375Hz frequency band (excluding 375Hz), sound level of 40dBC-60dBC, and hearing level of 26dBHL-40dBHL may be different from the adjustment values ​​for the 375Hz-625Hz frequency band.

[0106] In some embodiments, the adjustment value is at least frequency band related, and the adjustment value may differ in different frequency bands. In some embodiments, different frequency bands may correspond to different adjustment values, and frequencies within the same frequency band may correspond to the same adjustment value; in some embodiments, different frequencies may correspond to different adjustment values. In some embodiments, in frequency bands with frequencies greater than 0 Hz and less than or equal to 625 Hz, the adjustment value is in the range of 1 dB to 12 dB. By setting the adjustment value to the above values ​​within the above frequency range and then configuring the bone conduction hearing aid, the problem of strong vibrations in certain scenarios when wearing the bone conduction hearing aid can be improved, while also ensuring minimal impact on speech intelligibility. In some embodiments, the adjustment value decreases as the frequency increases. For example, the adjustment value corresponding to a frequency of 125 Hz may be 5 dB; the adjustment value corresponding to a frequency of 250 Hz may be 3 dB; and the adjustment value corresponding to a frequency of 500 Hz may be 1 dB. As another example, the adjustment value corresponding to a frequency of 125 Hz may be 10 dB; the adjustment value corresponding to a frequency of 250 Hz may be 7 dB; and the adjustment value corresponding to a frequency of 500 Hz may be 4 dB. In some embodiments, within a frequency band greater than 625Hz and less than or equal to 8000Hz, the adjustment value can be 0dB-4dB. In some embodiments, within a frequency band greater than 625Hz and less than or equal to 8000Hz, the adjustment value can be 0.

[0107] In some embodiments, the adjustment value is set to 5dB-12dB in the frequency band greater than 0Hz and less than or equal to 125Hz. In some embodiments, the adjustment value is set to 3dB-9dB in the frequency band greater than 125Hz and less than or equal to 375Hz. In some embodiments, the adjustment value is set to 1dB-6dB in the frequency band greater than 375Hz and less than or equal to 625Hz. Further dividing the frequency bands and setting the above adjustment values ​​in several frequency bands can improve the vibration reduction effect of the bone conduction hearing aid.

[0108] In some embodiments, the adjustment value is 5dB-7dB in the frequency band greater than 0Hz and less than or equal to 125Hz. In the frequency band greater than 125Hz and less than or equal to 375Hz, the adjustment value is 3dB-5dB. In some embodiments, the adjustment value is 1dB-3dB in the frequency band greater than 375Hz and less than or equal to 625Hz. By setting the adjustment values ​​to the above values ​​within the aforementioned frequency ranges and then configuring the bone conduction hearing aid, the vibration problem when wearing the bone conduction hearing aid in the corresponding frequency band for wearers with a hearing level of 30dBL can be solved, and it also has almost no impact on speech intelligibility, ensuring the wearer's hearing aid effect.

[0109] In some embodiments, the adjustment value is 10dB-12dB in the frequency band greater than 0Hz and less than or equal to 125Hz. In some embodiments, the adjustment value is 7dB-9dB in the frequency band greater than 125Hz and less than or equal to 375Hz. In some embodiments, the adjustment value is 4dB-6dB in the frequency band greater than 375Hz and less than or equal to 625Hz. By setting the adjustment value to the above values ​​within the above frequency range and then configuring the bone conduction hearing aid, the vibration problem when wearers with a hearing level of 40dBL wear the bone conduction hearing aid in the corresponding frequency band can be solved, and the impact on speech intelligibility can be minimized, ensuring the hearing aid effect for the wearer.

[0110] Figure 9-11 The figure shows the experimental results of speech recognition rate tests conducted on three wearers (wearer 1, wearer 2, and wearer 3). Figure 9-11 Using the reference output parameters as the reference analog output values ​​as examples, the speech recognition rate, vibration sensation, and volume of the wearer before the reference analog output value is reduced are shown, as well as the speech recognition rate, vibration sensation, and volume of the wearer when the reference analog output value is adjusted to different values ​​in each frequency band. Figure 9-11Six sets of tests were conducted for each tester. In the table, negative numbers indicate that the adjustment value reduced the reference output parameter (such as the reference simulated output value). For example, -5 means that the adjustment value is 5dB, which reduces the reference simulated output value by 5dB; and -15 means that the adjustment value is 15dB, which reduces the reference simulated output value by 15dB.

[0111] like Figure 9-11 As shown, when the reference analog output value is reduced based on the adjustment value, the speech recognition rate may decrease, the vibration sensation may decrease, but the volume may also decrease. The table shows that at 125Hz, if the adjustment value is 5dB (or less), i.e., the reference analog output value is reduced by 5dB, the speech recognition rate does not change significantly; at 250Hz, if the adjustment value is 3dB (or less), i.e., the reference analog output value is reduced by 3dB, the speech recognition rate does not change significantly; at 500Hz, if the adjustment value is 1dB (or less), i.e., the reference analog output value is reduced by 1dB, the speech recognition rate does not change significantly. Furthermore, with the adjustment values ​​set as described above, the tester could feel the vibration while speaking, but the volume remained adequate (i.e., the volume was within the range that the wearer could basically hear).

[0112] At 125Hz, if the adjustment value is 10dB (or within the range of greater than 5dB but less than 10dB), meaning the reference analog output value decreases by 10dB, the speech recognition rate decreases by less than or equal to 5%. At 250Hz, if the adjustment value is 7dB (or within the range of greater than 3dB but less than 7dB), meaning the reference analog output value decreases by 7dB, the speech recognition rate decreases by less than or equal to 5%. At 500Hz, if the adjustment value is 4dB (or within the range of greater than 1dB but less than 4dB), meaning the reference analog output value decreases by 4dB, the speech recognition rate decreases by less than or equal to 5%. Furthermore, with these adjustment values ​​set, the tester may feel comfortable, but the sound may feel rather low (i.e., the wearer may feel the volume is too low).

[0113] At 125Hz, if the adjustment value is 17dB (or within the range of greater than 10dB but less than 17dB), meaning the reference analog output value is reduced by 17dB, the speech recognition rate may decrease by more than 5% (e.g., 10%). At 250Hz, if the adjustment value is 15dB (or within the range of greater than 7dB but less than 15dB), meaning the reference analog output value is reduced by 15dB, the speech recognition rate may decrease by more than 5% (e.g., 10%). At 500Hz, if the adjustment value is 10dB (or within the range of greater than 4dB but less than 10dB), meaning the reference analog output value is reduced by 10dB, the speech recognition rate may decrease by more than 5% (e.g., 10%). Furthermore, with the adjustment values ​​set above, the tester may perceive the volume as too low (i.e., the wearer may be unable to hear clearly due to the low volume).

[0114] Within a certain range (e.g., an adjustment value less than 17 dB), a larger adjustment value results in better vibration reduction of the bone conduction hearing aid. However, due to… Figure 9-11 It can be seen that a larger adjustment value may lead to a lower output signal strength of the bone conduction hearing aid, which will have a greater impact on speech recognition rate (such as a possible decrease in speech recognition rate). When the adjustment value is within the range described in the above embodiments, it can solve the vibration problem when wearers with hearing levels of 30dBL-40dBL wear bone conduction hearing aids in the corresponding frequency band, while ensuring that the impact on speech intelligibility is minimal.

[0115] In some embodiments, the adjustment value of the reference output parameter may be only related to the frequency band. The adjustment value of the reference output parameter within the same frequency band at different hearing levels may be the same (as in the embodiments above), while the adjustment value within different frequency bands at the same hearing level may be different; the adjustment value of the reference output parameter within the same frequency band at different sound levels may be the same, while the adjustment value within different frequency bands at the same sound level may be different; the adjustment value of the reference output parameter within the same frequency band at different sound levels and different hearing levels may be the same, while the adjustment value within different frequency bands at the same sound level and the same hearing level may be different.

[0116] In some embodiments, the adjustment value of the reference output parameter can be related to the frequency band and the wearer's hearing level. The adjustment value of the reference output parameter differs within the same frequency band at different hearing levels; the adjustment value of the reference output parameter can be the same at the same hearing level, the same frequency band, but different sound levels. For a detailed description of this embodiment, please refer to [link to detailed description]. Figure 5 And related explanations.

[0117] In some embodiments, the adjustment value of the reference output parameter can be related to the frequency band and sound level. The adjustment value of the reference output parameter differs within the same frequency band at different sound levels; however, the adjustment value of the reference output parameter can be the same across different hearing levels, the same sound level, and the same frequency band. For a detailed description of this embodiment, please refer to [link / reference]. Figure 6 And related explanations.

[0118] Step 440: Configure the bone conduction hearing aid based on the reference output parameters and adjustment values. Specifically, step 440 can be performed by the configuration module 340.

[0119] In some embodiments, the processing device 120 (configuration module 340) can adjust the reference output parameters based on the adjustment value to obtain the actual output parameters, and configure the bone conduction hearing aid device using the actual output parameters.

[0120] In some embodiments, the processing device 120 (configuration module 340) can reduce the reference output parameter according to the adjustment value to obtain the actual output parameter, and configure the bone conduction hearing aid device based on the reduced reference output parameter (i.e., the actual output parameter). Reducing the reference output parameter according to the adjustment value can be done by directly subtracting the adjustment value from the reference output parameter, or by adjusting the relevant setting parameters of other bone conduction hearing aid devices through the adjustment value to achieve the purpose of reducing the reference output parameter.

[0121] In some embodiments, the processing device 120 (configuration module 340) can configure the magnetic circuit assembly based on adjustment values ​​and reference output values ​​to configure the bone conduction hearing aid. In some embodiments, configuring the bone conduction hearing aid includes setting various parameters of the bone conduction hearing aid so that parameters related to signal output intensity (e.g., gain value, analog output value) are preset values, such as reference parameters adjusted based on the adjustment values. For example, the reference gain value of the bone conduction hearing aid for sound signals can be adjusted by adjusting the current of the electromagnet in the magnetic circuit assembly, or by adjusting the resistance of the amplification circuit of the pickup assembly, thereby configuring the bone conduction hearing aid.

[0122] In some embodiments, based on reference output parameters and adjustment values, bone conduction hearing aids can be configured using equalization adjustment systems (EQ systems) or automatic gain control systems (AGC systems).

[0123] In other embodiments, a multi-channel wide dynamic range compression system (WDRC system) can be used to configure bone conduction hearing aids based on reference output parameters and adjustment values. The WDRC system first divides the sound signal into multiple channels according to frequency bands using a filter bank, compressing the signal of each channel individually. This allows for the design of appropriate compression ratios and thresholds based on the hearing loss corresponding to that frequency band. The processed signals from each channel are then combined into a single signal. The WDRC system offers greater flexibility in hearing compensation. In the WDRC system, the compression ratio and threshold of each channel's signal can be adjusted by regulating each reference output parameter and adjustment value, thereby regulating the reference output parameters of each channel.

[0124] Figure 5 This is an exemplary flowchart of the method for obtaining the adjusted value of the reference output parameter. Using... Figure 5 The adjustment value determined by the method shown is related to the wearer's hearing level. For example... Figure 5 As shown, process 500 includes the following steps.

[0125] Step 510: Determine the first threshold corresponding to each frequency band and each sound level, wherein the first threshold is related to the wearer's degree of vibration perception of each frequency band and each sound level.

[0126] Vibration perception level can be used to indicate the degree of vibration perceived by a user when wearing a bone conduction hearing aid. In some embodiments, vibration perception level can include multiple levels to represent the degree of vibration perceived. The higher the level, the greater the degree of vibration perceived by the user. In some embodiments, the levels can include a first level, a second level, a third level, a fourth level, and a fifth level, and the corresponding vibration perception levels can be "no vibration," "extremely slight vibration," "slight vibration," "obvious vibration, but acceptable," and "intense vibration, unacceptable." In some embodiments, different levels can be represented by scores. For example, the first level can be 1 point, the second level can be 2 points, the third level can be 3 points, the fourth level can be 4 points, and the fifth level can be 5 points.

[0127] In some embodiments, the first threshold can be the output signal strength of the bone conduction hearing aid corresponding to a certain level of vibration perception by the wearer. That is, when the output signal strength of the bone conduction hearing aid reaches the first threshold, the wearer can perceive that level of vibration. For example, the first threshold can be the output signal strength of the bone conduction hearing aid corresponding to a third level of vibration perception (i.e., a reference output parameter). In other words, when the output signal strength of the bone conduction hearing aid reaches the first threshold, the wearer can perceive the slight vibration corresponding to the third level. As another example, the first threshold can be the output signal strength of the bone conduction hearing aid corresponding to a fourth level of vibration perception. That is, when the output signal strength of the bone conduction hearing aid reaches the first threshold, the wearer can perceive a noticeable vibration corresponding to the fourth level, but at a manageable intensity. In some embodiments, when the output signal strength of the bone conduction hearing aid is greater than the first threshold, the wearer may feel a stronger vibration at the level corresponding to the first threshold (e.g., the slight vibration corresponding to the third level), resulting in a poor wearing experience. In such cases, it is necessary to adjust (reduce) the reference output parameters so that the output signal strength of the bone conduction hearing aid is less than the first threshold.

[0128] In some embodiments, preliminary reference output parameters for bone conduction hearing aid wearers at various sound levels and frequency bands can be obtained. A detailed description of obtaining the reference output parameters can be found in [reference needed]. Figure 4 Operation 420 in the text. In some embodiments, the first threshold may be different for different wearers. For example, wearers of bone conduction hearing aids may be tested to determine the output signal strength and corresponding vibration perception level of the wearer at each sound level and frequency band under the initial reference output parameters. A reference output parameter is obtained by adjusting the initial reference output parameter to adjust the output signal strength and vibration perception level, so that the wearer's vibration perception level reaches a certain level (e.g., level three, slight vibration), thereby determining the first threshold corresponding to each frequency band and each sound level. In some embodiments, the adjusted initial reference output parameter (i.e., the reference output parameter, such as the reference analog output value) may be equal to the adjusted signal output strength. The first threshold may be equal to the adjusted output signal strength or the reference analog output value corresponding to when the wearer's vibration perception level reaches a certain level (e.g., level three, slight vibration).

[0129] In some embodiments, the first threshold may be the same for different wearers. For example, the first threshold may be determined by: testing multiple testers to determine the signal output intensity when each tester subjectively perceives a slight vibration of the second level at various sound levels and frequency bands, and using the signal output intensity as test data; integrating and selecting the test data to obtain the first threshold. This first threshold may be applicable to different wearers. In some embodiments, integrating and selecting the test data may involve: for a certain frequency band, considering only the lowest value of the output parameter when each tester subjectively perceives a slight vibration at various sound levels in that frequency band, and further selecting the lowest value from the lowest values ​​of the output parameter when each tester subjectively perceives a slight vibration at various sound levels as the first threshold.

[0130] In some embodiments, bone conduction hearing aids exhibit significant vibration in the low-frequency range (e.g., the 0Hz-625Hz band). An adjustment value for the reference output parameter can be set in the low-frequency range to reduce the reference output parameter and decrease the vibration intensity perceived by the user. Correspondingly, a first threshold can be set in the low-frequency range (e.g., the 0Hz-625Hz band) to determine the adjustment value of the reference output parameter. In some embodiments, the first threshold can be set within the 0Hz-625Hz band, and the adjustment value can be determined within this band. In some embodiments, the first threshold varies for different frequency bands. For example, in the frequency band greater than 0Hz and less than or equal to 125Hz, the first threshold is in the range of 48dB-52dB. In some embodiments, in the frequency band greater than 125Hz and less than or equal to 375Hz, the first threshold is in the range of 49dB-54dB. In some embodiments, in the frequency band greater than 375Hz and less than or equal to 625Hz, the first threshold is in the range of 50dB-55dB. In some embodiments, the higher the frequency band at the same sound level, the larger the first threshold.

[0131] In some embodiments, the first threshold corresponding to the same frequency band at different sound levels can be the same. For example, a minimum value (e.g., 48 dB) can be selected from the range of the first thresholds corresponding to the aforementioned frequency bands as the first threshold for that frequency band, so that the bone conduction hearing aid device will not produce excessive vibrations when the received sound signals are at the same frequency band at different sound levels. For example, in the frequency band with a frequency greater than 0 Hz and less than or equal to 125 Hz, the first threshold is 48 dB. In the frequency band with a frequency greater than 125 Hz and less than or equal to 375 Hz, the first threshold is 49 dB. In the frequency band with a frequency greater than 375 Hz and less than or equal to 625 Hz, the first threshold is 50 dB.

[0132] In some embodiments, the first threshold corresponding to different sound levels in the same frequency band may be different. In some embodiments, the higher the sound level in the same frequency band, the larger the first threshold may be. For example, in the frequency band with a frequency greater than 0 Hz and less than or equal to 125 Hz, the sound level is 20 dBc-40 dBc, and the first threshold is 48 dB; in the frequency band with a sound level of 0 Hz and less than or equal to 125 Hz, the sound level is 40 dBc-50 dBc, and the first threshold is 49 dB; in the frequency band with a sound level of 0 Hz and less than or equal to 125 Hz, the sound level is 50 dBc-60 dBc, and the first threshold is 50 dB.

[0133] In some embodiments, the first threshold corresponding to the same frequency band for different hearing levels and different sound levels can be the same. For example, a minimum value (e.g., 48dB) can be selected as the first threshold for the frequency band within the range of the first thresholds corresponding to the above-mentioned frequency bands, so that when the bone conduction hearing aid device receives sound signals of the same frequency band, no matter what sound level the sound signal is or what hearing level the wearer has, it will not produce severe vibrations.

[0134] In some embodiments, the first threshold values ​​corresponding to different hearing levels and different sound levels within the same frequency band are different. For example, for a hearing level of 40 dBHL within a frequency band greater than 125 Hz and less than or equal to 375 Hz and a sound level of 60 dBC, the first threshold value can be 49 dB. For a hearing level of 10 dBHL within a frequency band greater than 125 Hz and less than or equal to 375 Hz and a sound level of 75 dBC, the first threshold value can be 50 dB. As another example, for a hearing level of 30 dBHL within a frequency band greater than 375 Hz and less than or equal to 625 Hz and a sound level of 70 dBC, the first threshold value can be 55 dB. For example, for a hearing level of 20 dBHL within a frequency band greater than 375 Hz and less than or equal to 625 Hz and a sound level of 75 dBC, the first threshold value can be 56 dB. In some embodiments, the first threshold corresponding to different frequency bands, sound levels, and hearing levels can be the same. For example, a minimum value (e.g., 48 dB) can be selected from the range of the first thresholds corresponding to each of the aforementioned frequency bands as the first threshold corresponding to different sound levels in all frequency bands, so that the bone conduction hearing aid device will not produce excessive vibrations when receiving sound signals of different sound levels and frequency bands. For example, in the frequency band with frequencies greater than 0 Hz-625 Hz, the first threshold is 48 dB.

[0135] Step 520: Determine the second threshold corresponding to each frequency band and each sound level, wherein the second threshold is related to the wearer's speech recognition rate in each frequency band.

[0136] Speech recognition rate (i.e., speech intelligibility) is the ratio of the number of words that are understood or clearly heard to the number of words heard. Speech recognition rate can be used to characterize the wearer's auditory sensitivity and clarity of spoken language after wearing hearing aids, thus reflecting the effectiveness of the hearing aids to some extent. A higher speech recognition rate indicates greater auditory sensitivity and clarity after wearing hearing aids, and a better hearing aid effect. In some embodiments, a speech recognition rate greater than or equal to 70% is considered a good hearing aid effect; while a speech recognition rate less than or equal to 50% is considered an unsatisfactory hearing aid effect, requiring readjustment or configuration of the bone conduction hearing aid device.

[0137] In some embodiments, adjustments to the reference output parameters (e.g., reduction) can affect the strength of the output signal of the bone conduction hearing aid, and thus potentially affect the speech recognition rate of the bone conduction hearing aid. For example, based on Figure 9-11 Experimental results show that within a certain range (e.g., an adjustment value less than 17 dB), a larger adjustment value may result in a lower speech recognition rate. A second threshold can be used to ensure that the speech recognition rate after adjusting the reference output parameters remains within a certain range (e.g., above a certain threshold). In other words, the second threshold can be used to control the reduction in speech recognition rate after adjusting the reference output parameters within a certain range. For example, when the adjustment value does not exceed the second threshold, the reduction in the speech recognition rate of the wearer wearing the hearing aid relative to the state when the reference output parameters are not adjusted can be relatively small; for example, the reduction in speech recognition rate can be less than or equal to 5%. The reduction in speech recognition rate can be calculated by subtracting the speech recognition rate after adjusting the reference output parameters from the speech recognition rate when the reference output parameters are not adjusted.

[0138] In some embodiments, the second threshold can be the maximum value of the adjustment value corresponding to the reference output parameter of the bone conduction hearing aid at a preset speech recognition rate when the wearer wears the bone conduction hearing aid. That is, when the adjustment value corresponding to the reference output parameter of the bone conduction hearing aid reaches the second threshold, the speech recognition rate when the wearer wears the bone conduction hearing aid is the preset threshold. When the adjustment value is greater than the second threshold, the speech recognition rate when the wearer wears the bone conduction hearing aid will be less than the preset speech recognition rate.

[0139] For example, such as Figure 10 As shown, the second threshold can be the adjusted value corresponding to the reference output parameter when the wearer achieves a speech recognition rate of 80% at 125Hz while wearing the bone conduction hearing aid, i.e., the second threshold is 5dB. In other words, when the adjusted value corresponding to the reference output parameter of the bone conduction hearing aid at 125Hz is the second threshold, the wearer's speech recognition rate while wearing the bone conduction hearing aid can be 80%. For example, as... Figure 11As shown, the second threshold can be the adjustment value corresponding to the reference output parameter at 250Hz when the wearer wears the bone conduction hearing aid, which corresponds to a speech recognition rate of 60%. That is, the second threshold is 12dB. In other words, when the adjustment value corresponding to the reference output parameter of the bone conduction hearing aid at 250Hz is the second threshold, the speech recognition rate when the wearer wears the bone conduction hearing aid can be 60%.

[0140] In some embodiments, a second threshold can be determined based on a preset speech recognition rate threshold. For example, it can be based on... Figure 9-11 The second threshold was determined based on experimental results of speech recognition rate tests conducted on wearers. This is for illustrative purposes only. Figure 10 When the bone conduction hearing aid is configured based on the unadjusted reference output parameters, the wearer's speech recognition rate is 80%. If the speech recognition rate is to be no less than 75% after reducing the reference output parameters (i.e., the reduction in speech recognition rate is less than or equal to 5%), then the second threshold can be 10dB; if the speech recognition rate is to be no less than 80% (i.e., the speech recognition rate is almost not reduced), then the second threshold can be 5dB.

[0141] In some embodiments, bone conduction hearing aids exhibit significant vibration in the low-frequency range (e.g., 0Hz-625Hz). An adjustment value for the reference output parameter can be set in the low-frequency range to reduce the reference output parameter and decrease the vibration intensity perceived by the user. Correspondingly, a second threshold can be set in the low-frequency range (e.g., 0Hz-625Hz) to determine the adjustment value of the reference output parameter based on the first threshold. In some embodiments, the second threshold varies for different frequency bands. For example, in the frequency band greater than 0Hz and less than or equal to 125Hz, the second threshold is in the range of 5dB-10dB. In some embodiments, in the frequency band greater than 125Hz and less than or equal to 375Hz, the second threshold is in the range of 3dB-7dB. In some embodiments, in the frequency band greater than 375Hz and less than or equal to 625Hz, the second threshold is in the range of 1dB-4dB. In some embodiments, at the same sound level, the higher the frequency band, the smaller the second threshold.

[0142] In some embodiments, the second threshold corresponding to the same frequency band for different hearing levels can be the same. For example, regardless of whether the wearer's hearing level is 30 dBHL or 40 dBHL, the second threshold can be set according to the above range. In some embodiments, the second threshold corresponding to the same frequency band for different hearing levels can be different. For example, in the frequency band with a frequency greater than 0 Hz and less than or equal to 125 Hz, if the hearing level is 30 dBHL, the second threshold is 5 dB; in the frequency band with a frequency band with a hearing level of 0 Hz and less than or equal to 125 Hz, if the hearing level is 40 dBHL, the second threshold is 15 dB. In some embodiments, the second threshold corresponding to the same frequency band for different sound levels can be the same. In some embodiments, a minimum value within the above range can be selected as the second threshold so that the bone conduction hearing aid does not significantly affect the speech recognition rate when the received sound signal is at different sound levels. For example, in the frequency band with a frequency greater than 125 Hz and less than or equal to 375 Hz, the second threshold can be 3 dB. In some embodiments, in the frequency band with a frequency greater than 0 Hz and less than or equal to 125 Hz, the second threshold can be 5 dB. In some embodiments, the second threshold may be 1 dB in a frequency band greater than 375 Hz and less than or equal to 625 Hz.

[0143] In some embodiments, the second threshold corresponding to different sound levels in the same frequency band may be different. For example, in a frequency band with a frequency greater than 0 Hz and less than or equal to 125 Hz, the sound level is 60 dBc and the second threshold is 5 dB; in a frequency band with a frequency of 0 Hz and less than or equal to 125 Hz, the sound level is 75 dBc and the second threshold is 10 dB.

[0144] Step 530: Determine the adjustment value based on the reference output parameters, the first threshold, and the second threshold.

[0145] In some embodiments, when the reference output parameter is greater than a first threshold, an initial adjustment value can be set. This initial adjustment value can be determined based on experience or a preset formula. Then, this initial adjustment value can be compared with a second threshold. If the initial adjustment value is greater than the second threshold, the initial adjustment value is reduced so that it is less than or equal to the second threshold. If the initial adjustment value is less than or equal to the second threshold, then the initial adjustment value is determined as the adjustment value.

[0146] In some embodiments, a comparison value can be obtained by subtracting a first threshold corresponding to the specific frequency band and specific sound level from the reference output parameter corresponding to the specific frequency band and specific sound level; then, the comparison value is compared with a second threshold corresponding to the specific frequency band and specific sound level; based on the comparison result between the comparison value and the second threshold, an adjustment value corresponding to the reference output parameter under the specific frequency band and specific sound level is determined.

[0147] Please refer to the relevant instructions above for the methods of determining the first and second thresholds. The comparison value can be positive, negative, or zero. Comparing the comparison value with the second threshold can be a numerical comparison to determine the relationship between the comparison value and the second threshold. The comparison result can include the comparison value being less than the second threshold, the comparison value being equal to the second threshold, or the comparison value being greater than the second threshold. Based on the comparison result, the adjustment value corresponding to the reference output parameter is determined, which can be based on the relationship between the comparison value and the second threshold.

[0148] In some embodiments, determining the adjustment value corresponding to the reference output parameter based on the comparison result between the comparison value and the second threshold may include: when the comparison value is less than or equal to 0, the adjustment value is 0; when the comparison value is greater than 0 but less than or equal to the second threshold, the adjustment value is the comparison value; when the comparison value is greater than the second threshold, the adjustment value is the second threshold.

[0149] When the reference output parameter is less than or equal to the first threshold, the wearer is less likely to experience vibration after wearing the bone conduction hearing aid when configured according to the reference output parameter, and no adjustment to the reference output parameter is required. When the reference output parameter is greater than the first threshold, the wearer is more likely to experience stronger vibration after wearing the bone conduction hearing aid when configured according to the reference output parameter, and adjustment of the reference output parameter is necessary. Furthermore, when determining the adjustment value, not only the vibration risk of the bone conduction hearing aid caused by the reference output parameter should be considered, but also the impact of the adjusted reference output parameter on the speech recognition rate of the bone conduction hearing aid. Since the second threshold is a threshold related to the speech recognition rate, by comparing the above comparison value with the second threshold, the adjustment value should be kept as close to or equal to the second threshold as possible to minimize the impact on the speech recognition rate caused by the adjustment of the reference output parameter.

[0150] Figure 6 This is an exemplary flowchart of a method for obtaining adjusted values ​​of reference output parameters. In some embodiments, when configuring a bone conduction hearing aid using a multi-channel wide dynamic range compression system, the following can be employed: Figure 6 The process shown in step 600 determines the adjustment value corresponding to the reference output parameter. For example... Figure 6 As shown, the process 600 for determining the adjustment value corresponding to the reference output parameter may include the following steps:

[0151] Step 610: Compare the reference output parameters with the first threshold. The first threshold is related to the wearer's perception of vibration at each sound level in each frequency band.

[0152] For details regarding the first threshold and the method for determining it, please refer to the section on the first threshold in step 510. Comparing the reference output parameter with the first threshold can be done by comparing their numerical values.

[0153] Step 620: Based on the comparison result between the reference output parameter and the first threshold, determine the adjustment value corresponding to the reference output parameter.

[0154] For details regarding the adjustment value corresponding to the reference output parameter, please refer to the relevant content in step 430. The comparison result between the reference output parameter and the first threshold can include a comparison result where the reference output parameter is greater than the first threshold, the reference output parameter is equal to the first threshold, and the reference output parameter is equal to the first threshold. In some embodiments, the adjustment value can be determined to be 0 based on whether the reference output parameter is greater than the first threshold. For example, when the reference output parameter is less than the first threshold, the adjustment value is 0; when the reference output parameter is greater than the first threshold, the adjustment value is greater than 0.

[0155] In some embodiments, when configuring a bone conduction hearing aid using a multi-channel wide dynamic range compression system, the adjustment value may include a gain reduction of the multi-channel wide dynamic range compression system when at least one sound level is greater than a sound level threshold. In some embodiments, this sound level threshold may be 70 dB. During the use of a bone conduction hearing aid, the sound level of the audio signal in everyday conversation is generally around 60 dB. Sound signal levels greater than or equal to 70 dB may occur when the wearer is speaking or in a noisy environment. In these cases, the bone conduction hearing aid may vibrate more strongly. Therefore, setting an adjustment value to regulate (e.g., reduce) the reference output parameter within this sound level range can improve the vibration of the bone conduction hearing aid while ensuring that the wearer's speech recognition rate is almost unaffected during everyday conversations.

[0156] The gain at which at least one sound level in each channel exceeds a sound level threshold can be termed high-level gain. The adjustment value can include a reduction in the high-level gain of the multi-channel wide dynamic range compressor system. The high-level gain of the multi-channel wide dynamic range compressor system can be the gain when the sound signal level exceeds a sound level threshold (e.g., 70 dB). The gain of the multi-channel wide dynamic range compressor system at which at least one sound level in each channel exceeds the sound level threshold can be determined based on the wearer's hearing loss data, for example, according to an empirical formula. For example, an empirical formula can be used to determine the high-level gain of the multi-channel wide dynamic range compressor system based on the wearer's hearing level. The adjustment value can be a specific numerical reduction of the high-level gain derived from the empirical formula.

[0157] In some embodiments, the gain reduction value (i.e., whether the gain is reduced when at least one sound level is greater than the sound level threshold) can be determined based on whether the reference output parameter is greater than a first threshold. For example, the gain reduction value is 0 when the reference output parameter is less than the first threshold; and the gain reduction value is greater than 0 when the reference output parameter is greater than the first threshold.

[0158] In some embodiments, after determining the gain reduction value when at least one sound level is greater than a sound level threshold, this gain reduction value can be used to reduce the gain value when the sound level is greater than the sound level threshold, and the reduced gain value is used as the input parameter of the multi-channel wide dynamic range compression system. When at least one sound level is greater than the sound level threshold, the bone conduction hearing aid is prone to vibration. By setting the gain reduction value as described above within a set frequency band (frequency greater than 0Hz and less than or equal to 625Hz) and when the sound level is greater than the sound level threshold, and using this gain reduction value as an adjustment value, it can be ensured that the reference output parameter is not affected when the sound signal level is less than the sound level threshold, while the reference output parameter is reduced when the sound signal level is less than the sound level threshold. This can improve the situation where the bone conduction hearing aid vibrates severely in certain scenarios while maintaining the speech recognition rate of the bone conduction hearing aid.

[0159] In some embodiments, when the adjustment value includes a gain reduction value of the multi-channel wide dynamic range compression system when at least one sound level in each sound level is greater than a sound level threshold, step 620 may specifically include the following steps: if the reference output parameter is less than or equal to a first threshold, the gain reduction value is 0; if the reference output parameter is greater than the first threshold, the gain reduction value is the difference between the first threshold and the reference output parameter.

[0160] In this embodiment, if the reference output parameter is less than or equal to the first threshold, the probability of the wearer experiencing severe vibration while wearing the bone conduction hearing aid is relatively low, and there is no need to adjust (reduce) the high-level gain; therefore, the high-level gain reduction value is set to 0. If the reference output parameter is greater than the first threshold, the wearer is more likely to experience severe vibration while wearing the bone conduction hearing aid, and it is necessary to adjust (reduce) the high-level gain to reduce the reference output parameter so that the reference output parameter is less than the first threshold.

[0161] In some embodiments, when configuring a bone conduction hearing aid using a multi-channel wide dynamic range compression system, the adjustment value may include a reduction in the maximum output limit of the multi-channel wide dynamic range compression system when at least one sound level is greater than a sound level threshold. In some embodiments, this sound level threshold may be 70 dB. In this embodiment, a sound signal level greater than or equal to 70 dBc may occur when the wearer is speaking or in a noisy environment. In such cases, the bone conduction hearing aid may vibrate more strongly. Therefore, setting an adjustment value to regulate the reference output parameter (the maximum output of the multi-channel wide dynamic range compression system) within this sound level range can improve the vibration of the bone conduction hearing aid while ensuring that the wearer's speech recognition rate is almost unaffected during daily conversations.

[0162] Maximum output can be understood as a limit value for the reference output parameter at each frequency band. When the reference output parameter is greater than the maximum output, the reference output parameter of the bone conduction hearing aid is equal to the maximum output. The maximum output limit of the multi-channel wide dynamic range compression system can be determined based on the wearer's hearing loss data using an empirical formula. For example, the empirical formula can be based on the wearer's hearing level to determine the maximum output limit of the multi-channel wide dynamic range compression system. The adjustment value can be a specific numerical reduction of the maximum output derived from the empirical formula. The empirical formula can be user-defined or a default setting configured in the bone conduction hearing aid system.

[0163] In some embodiments, when the adjustment value may include a reduction in the maximum output limit of the multi-channel wide dynamic range compression system when at least one of the sound levels is greater than a sound level threshold, step 620 may further include the following steps: if the reference output parameter is less than or equal to the first threshold, the reduction in the maximum output is 0 dB; if the reference output parameter is greater than the first threshold, the reduction in the maximum output is greater than 0 dB.

[0164] In other words, if the reference output parameter is less than or equal to the first threshold, the wearer is less likely to experience severe vibrations when wearing the bone conduction hearing aid, and there is no need to adjust (reduce) the maximum output; if the reference output parameter is greater than the first threshold, the wearer is more likely to experience severe vibrations when wearing the bone conduction hearing aid, and it is necessary to adjust (reduce) the maximum output, thereby reducing the reference output parameter so that the reference output parameter can be less than the first threshold.

[0165] Furthermore, when it is determined that the decrease in the maximum output is greater than 0, the specific value of the decrease in the maximum output parameter can be further determined. In some embodiments, for example, the maximum output can be gradually decreased in equal steps so that the reference output parameter eventually becomes less than the first threshold. For example, gradually decreasing the maximum output in equal steps can be done by decreasing the maximum output by the same amount each time (e.g., decreasing the maximum output by 2dB each time) to gradually reduce the reference output parameter and eventually make the reference output parameter less than the first threshold.

[0166] Since wearers typically experience stronger vibrations when they speak or in loud environments, at which point the sound level is relatively high, for example, greater than or equal to 70 dB, by using method 600 and adjusting the reference output parameters, the reference output parameters of the bone conduction hearing aid can be kept unaffected when a mid-level sound signal (such as a sound level below 70 dB) is input into the bone conduction hearing aid. However, when a high-level sound signal (such as a sound level of 70 dB or higher) is input into the bone conduction hearing aid, the reference output parameters of the bone conduction hearing aid are lower than the first threshold, thereby improving the situation where wearers experience stronger vibrations when they speak or in loud environments.

[0167] In some embodiments, the adjustment value may include only the gain reduction when at least one sound level is greater than a sound level threshold. In other embodiments, the adjustment value may include only the reduction in the maximum output limit when at least one sound level is greater than a sound level threshold. In some embodiments, the adjustment value may include both the gain reduction when at least one sound level is greater than a sound level threshold and the reduction in the maximum output limit when at least one sound level is greater than a sound level threshold.

[0168] In some embodiments, the setting parameters of the multi-channel wide dynamic range compression system further include crossover frequency, lower threshold, low level gain, upper threshold, expansion threshold, expansion ratio, compressor attack, compressor release, AGCo attack, and AGCo release. The crossover frequency can be the frequency at which the audio spectrum is divided, i.e., the dividing point of each frequency band. The lower threshold can be the lower limit threshold of the sound level in that frequency band. The low level gain can be the gain when the input sound level is less than the lower threshold. The upper threshold can be the upper limit threshold of the sound level in that frequency band, i.e., the threshold corresponding to the high level gain. The expansion threshold can be the expansion threshold of the sound level in that frequency band, and the expansion ratio can be the gain ratio of the sound at the expansion threshold. The effect generation time can be the transition time from when the effect detects a sound above a threshold to when it fully activates, during which the gain gradually increases to the preset gain. The effect release time can be the transition time from when the sound falls below the threshold to when the effect fully activates, during which the gain gradually decreases to the preset gain. The gain algorithm is an Automatic Gain Control (AGCo) algorithm based on the output. The gain algorithm generation time can be 2ms. The gain algorithm release time can be 64ms.

[0169] Figure 7 This is a flowchart illustrating the operations performed during use of a bone conduction hearing aid device according to some embodiments of this application. For example... Figure 7 As shown, the bone conduction hearing aid can perform the following steps during use:

[0170] Step 710: Acquire an audio input signal. In some embodiments, the audio input signal may include an audio signal (e.g., a song, speech, etc.) acquired by the bone conduction hearing aid from a device such as a storage device (e.g., memory 130), a terminal (e.g., terminal 140). In some embodiments, the audio signal input to the bone conduction hearing aid may include an audio signal picked up by the pickup component of the bone conduction hearing aid. For example, the pickup component may pick up sound (a first vibration signal) and process the first vibration signal to convert it into an electrical signal. The electrical signal may be transmitted to the speaker component of the bone conduction hearing aid, which processes the electrical signal based on reference output parameters to convert it into a second vibration signal and transmit it to the wearer.

[0171] Step 720: Based on the sound level and frequency components of the sound input signal and the reference output parameters, determine the reference output parameters corresponding to the frequency components. In some embodiments, the bone conduction hearing aid can acquire preset reference output parameters stored in a storage device within the bone conduction hearing aid. These preset reference output parameters can correspond to different frequency bands, sound levels, and hearing levels. The bone conduction hearing aid can determine the reference output parameters corresponding to the sound level and frequency components from the preset reference output parameters based on the sound level and frequency components of the sound input signal. In some embodiments, the bone conduction hearing aid can determine the reference output parameters corresponding to the sound level, frequency components, and hearing level from the preset reference output parameters based on the sound level, frequency components, and the wearer's hearing level. In some embodiments, the preset reference output parameters corresponding to different frequency bands, sound levels, and hearing levels can be determined based on... Figure 4 Step 420 in the process is determined.

[0172] Step 730: Based on the reference output parameters corresponding to the frequency components and the adjustment values ​​corresponding to the reference output parameters of the frequency components, obtain the actual output parameters corresponding to the frequency components at the sound level. In some embodiments, the bone conduction hearing aid can obtain preset adjustment values ​​of reference output parameters stored in the storage device of the bone conduction hearing aid. The preset adjustment values ​​can correspond to reference output parameters at different frequency bands, sound levels, and hearing levels. The bone conduction hearing aid can determine the adjustment value corresponding to the reference output parameters corresponding to the sound level and frequency components from the preset adjustment values ​​based on the sound level and frequency components of the sound input signal. In some embodiments, the bone conduction hearing aid can determine the adjustment value corresponding to the reference output parameters at the sound level, frequency components, and hearing level from the preset adjustment values ​​based on the sound level, frequency components, and hearing level of the sound input signal. In some embodiments, the adjustment values ​​corresponding to the preset reference output parameters for different frequency bands, sound levels, and hearing levels can be determined based on... Figure 4 Step 430 in the process is determined.

[0173] Step 740: Based on the actual output parameters, control the bone conduction hearing aid to output sound signals.

[0174] Reference output parameters can be understood as parameters initially set during the configuration of a bone conduction hearing aid, while actual output parameters can be understood as output parameters adjusted by the bone conduction hearing aid based on adjustment values. In some embodiments, actual output parameters may include gain values ​​and / or actual analog output values. In some embodiments, the actual gain value may be the actual amplification of the sound signal intensity by the hearing aid during wear, and the actual analog output value may be the actual output signal intensity value simulated by the hearing aid based on the input sound signal parameters (e.g., the sound signal intensity value). For example, the actual analog output value may be equal to the input sound signal value (i.e., intensity value, in dB) plus the actual gain value (in dB). In some embodiments, the actual analog output value corresponding to a specific sound level and frequency band may be equal to the actual output value during the use of the bone conduction hearing aid (i.e., the intensity value of the signal actually output by the bone conduction hearing aid, in dB), for example, when the bone conduction hearing aid inputs a sound signal at that specific sound level and frequency band. In some embodiments, when a wearer wears the bone conduction hearing aid, the pickup component 220 of the bone conduction hearing aid can perform step 710, and the magnetic circuit component of the bone conduction hearing aid can perform steps 720 and 730. The vibration component of the bone conduction hearing aid can perform step 740, whereby the vibration component can convert the actual output parameters determined by the magnetic circuit component into corresponding vibration intensities, so that the bone conduction hearing aid outputs sound signals through mechanical vibration. In some embodiments, when a wearer wears the bone conduction hearing aid, the pickup component 220 of the bone conduction hearing aid can perform step 710, and the processing device in the bone conduction hearing aid can perform steps 720 and 730. The processing device of the bone conduction hearing aid can control the magnetic circuit component and the vibration component to perform step 740. For example, the processing device can control the vibration component to generate a vibration intensity corresponding to the actual output parameters based on the determined actual output parameters, so that the bone conduction hearing aid outputs sound signals through mechanical vibration. For example, the processing device can control the current in the voice coil based on the determined actual output parameters, thereby controlling the intensity of the mechanical vibration generated by the voice coil and thus controlling the output signal strength of the bone conduction hearing aid.

[0175] In some embodiments, the bone conduction hearing aid may store actual output parameters for each frequency band and each sound level. When the bone conduction hearing aid receives a sound input signal, it can directly determine the actual output parameters of the bone conduction hearing aid at the corresponding sound level and frequency band based on the sound input signal, and output a sound signal based on the actual output parameters.

[0176] The basic concepts have been described above. Obviously, for those skilled in the art, the detailed disclosure above is merely illustrative and does not constitute a limitation of this application. Although not explicitly stated herein, those skilled in the art may make various modifications, improvements, and corrections to this application. Such modifications, improvements, and corrections are suggested in this application, and therefore remain within the spirit and scope of the exemplary embodiments of this application.

[0177] Furthermore, this application uses specific terms to describe embodiments of the application. For example, "an embodiment," "one embodiment," and / or "some embodiments" refer to a particular feature, structure, or characteristic associated with at least one embodiment of the application. Therefore, it should be emphasized and noted that "an embodiment," "one embodiment," or "an alternative embodiment" mentioned twice or more in different locations in this specification do not necessarily refer to the same embodiment. In addition, certain features, structures, or characteristics in one or more embodiments of the application can be appropriately combined.

[0178] Furthermore, unless expressly stated in the claims, the order of processing elements and sequences, the use of numbers and letters, or other names described in this application are not intended to limit the order of the processes and methods of this application. Although the foregoing disclosure has discussed some currently considered useful embodiments of the invention through various examples, it should be understood that such details are for illustrative purposes only, and the appended claims are not limited to the disclosed embodiments; rather, the claims are intended to cover all modifications and equivalent combinations that conform to the substance and scope of the embodiments of this application. For example, while the system components described above can be implemented using hardware devices, they can also be implemented solely through software solutions, such as installing the described system on existing servers or mobile devices.

[0179] Similarly, it should be noted that, in order to simplify the description of the present application and thus aid in the understanding of one or more embodiments of the invention, the foregoing description of the embodiments of the present application sometimes combines multiple features into a single embodiment, drawing, or description thereof. However, this disclosure method does not imply that the subject matter of the application requires more features than those mentioned in the claims. In fact, the embodiments contain fewer features than all the features of the single embodiments disclosed above.

[0180] In some embodiments, numbers describing the quantity of components and attributes are used. It should be understood that such numbers used in the description of embodiments are modified in some examples with the terms "approximately," "approximately," or "generally." Unless otherwise stated, "approximately," "approximately," or "generally" indicates that the numbers are allowed to vary by ±20%. Accordingly, in some embodiments, the numerical parameters used in the specification and claims are approximate values, which may be changed depending on the characteristics required by individual embodiments. In some embodiments, numerical parameters should take into account specified significant digits and employ a general method of digit reservation. Although the numerical ranges and parameters used to confirm their breadth of scope in some embodiments of this application are approximate values, in specific embodiments, such values ​​are set as precisely as feasible.

[0181] For each patent, patent application, patent application publication, and other material such as articles, books, specifications, publications, and documents referenced in this application, the entire contents of that patent are incorporated herein by reference. This excludes historical application documents that are inconsistent with or conflict with the content of this application, as well as documents that limit the broadest scope of the claims in this application (currently or subsequently appended to this application). It should be noted that if there are any inconsistencies or conflicts between the descriptions, definitions, and / or terminology used in the supplementary materials of this application and the content of this application, the descriptions, definitions, and / or terminology used in this application shall prevail.

[0182] Finally, it should be understood that the embodiments described in this application are merely illustrative of the principles of the embodiments of this application. Other modifications may also fall within the scope of this application. Therefore, alternative configurations of the embodiments of this application are considered as examples and not limitations, and are regarded as consistent with the teachings of this application. Accordingly, the embodiments of this application are not limited to the embodiments explicitly described and illustrated in this application.

Claims

1. A method for configuring a bone conduction hearing aid, comprising the following steps: Acquire the wearer's hearing loss data, which includes hearing levels at various sound levels and at various frequency bands; Based on the hearing level and the values ​​of each sound level and each frequency band in the hearing loss data, the reference output parameters of the bone conduction hearing aid device are determined at each sound level and each frequency band. The adjustment value of the reference output parameter is obtained, and the bone conduction hearing aid is configured based on the reference output parameter and the adjustment value, wherein the adjustment value is different at different hearing levels and in the same frequency band; The process of obtaining the adjustment value of the reference output parameter includes: A first threshold is determined for each frequency band and each sound level, and the first threshold is related to the wearer's degree of vibration perception of each sound level in each frequency band; Determine the second threshold corresponding to each frequency band and each sound level. The second threshold is the maximum value of the adjustment value corresponding to the reference output parameter under the preset speech recognition rate when the wearer wears the bone conduction hearing aid. The comparison value is obtained by subtracting the first threshold from the reference output parameter. The comparison value is compared with the second threshold; When the comparison value is less than or equal to 0, the adjustment value is 0 dB; When the comparison value is greater than 0 but less than or equal to the second threshold, the adjustment value is the comparison value; When the comparison value is greater than the second threshold, the adjustment value is the second threshold.

2. The configuration method as described in claim 1, wherein, The configuration of the bone conduction hearing aid based on the reference output parameters and the adjustment value includes: Within a frequency band greater than 0 Hz but less than or equal to 625 Hz, the reference output parameter is reduced based on the adjustment value.

3. The configuration method as described in claim 2, wherein, Within a frequency band greater than 0 Hz and less than or equal to 625 Hz, the adjustment value is 1 dB - 12 dB.

4. The configuration method as described in claim 2, wherein, Within the frequency band greater than 0 Hz and less than or equal to 125 Hz, the adjustment value is set to 5 dB - 12 dB; Within the frequency band greater than 125Hz and less than or equal to 375Hz, the adjustment value is set to 3 dB - 9 dB; and / or, Within the frequency band greater than 375Hz and less than or equal to 625Hz, the adjustment value is set to 1 dB - 6dB.

5. The configuration method as described in claim 2, wherein, Within the frequency band greater than 0 Hz and less than or equal to 125 Hz, the adjustment value is 5 dB - 7 dB; Within a frequency band greater than 125Hz and less than or equal to 375Hz, the adjustment value is 3dB - 5dB; and / or, Within the frequency band greater than 375Hz and less than or equal to 625Hz, the adjustment value is 1dB - 3dB.

6. The configuration method as described in claim 2, wherein, Within the frequency band greater than 0 Hz and less than or equal to 125 Hz, the adjustment value is 10 dB - 12 dB; Within a frequency band greater than 125Hz and less than or equal to 375Hz, the adjustment value is 7dB - 9dB; and / or, Within the frequency band greater than 375Hz and less than or equal to 625Hz, the adjustment value is 4dB - 6dB.

7. The configuration method as described in claim 1, wherein, Within a frequency band greater than 0 Hz and less than or equal to 125 Hz, the first threshold is in the range of 48 dB to 52 dB; Within a frequency band greater than 125Hz and less than or equal to 375Hz, the first threshold is in the range of 49 dB - 54 dB; and / or, Within a frequency band greater than 375Hz and less than or equal to 625Hz, the first threshold is in the range of 50 dB - 55 dB.

8. The configuration method as described in claim 1, wherein, Within the frequency band of 0 Hz and less than or equal to 125 Hz, the second threshold is in the range of 5 dB - 10 dB; Within the frequency band greater than 125Hz and less than or equal to 375Hz, the second threshold is in the range of 3 dB - 7 dB; and / or, Within the frequency band of 375Hz or higher and 625Hz or lower, the second threshold is in the range of 1 dB - 4 dB.

9. The configuration method as described in claim 1, wherein, Based on the reference output parameters and the adjustment value, configuring the bone conduction hearing aid includes: Based on the reference output parameters and the adjustment values, the bone conduction hearing aid is configured using a multi-channel wide dynamic range compression system.

10. The configuration method as described in claim 9, wherein when using the multi-channel wide dynamic range compression system, obtaining the adjustment value of the reference output parameter includes: The reference output parameter is compared with a first threshold, which is related to the wearer's perception of vibration at each sound level in each frequency band; Based on the comparison result between the reference output parameter and the first threshold, the adjustment value corresponding to the reference output parameter is determined.

11. The configuration method as described in claim 10, wherein, The adjustment value includes the gain reduction value of the multi-channel wide dynamic range compression system when at least one of the various sound levels is greater than the sound level threshold. Based on the comparison result between the reference output parameter and the first threshold, the adjustment value corresponding to the reference output parameter is determined, including: If the reference output parameter is less than or equal to the first threshold, the gain reduction value is 0 dB; If the reference output parameter is greater than the first threshold, then the gain reduction value is the difference between the first threshold and the reference output parameter.

12. The configuration method as described in claim 10, wherein, The adjustment value includes a reduction in the maximum output of the multi-channel wide dynamic range compression system when at least one of the sound levels is greater than a sound level threshold. Based on the comparison result between the reference output parameter and the first threshold, the adjustment value corresponding to the reference output parameter is determined, including: If the reference output parameter is less than or equal to the first threshold, the decrease in the maximum output is 0 dB; If the reference output parameter is greater than the first threshold, then the decrease in the maximum output is greater than 0 dB.

13. A configuration system for a bone conduction hearing aid, comprising: The acquisition module is used to acquire the wearer's hearing loss data, which includes the hearing loss data of each sound level and the hearing level in each frequency band; The reference output parameter determination module is used to determine the reference output parameters of the bone conduction hearing aid device at each sound level and each frequency band based on the hearing level and the values ​​of each sound level and each frequency band in the hearing loss data. The adjustment value determination module is used to obtain the adjustment value of the reference output parameter, wherein the adjustment value is different at different hearing levels and in the same frequency band; The process of obtaining the adjustment value of the reference output parameter includes: A first threshold is determined for each frequency band and each sound level, and the first threshold is related to the wearer's degree of vibration perception of each sound level in each frequency band; Determine the second threshold corresponding to each frequency band and each sound level. The second threshold is the maximum value of the adjustment value corresponding to the reference output parameter under the preset speech recognition rate when the wearer wears the bone conduction hearing aid. The comparison value is obtained by subtracting the first threshold from the reference output parameter. The comparison value is compared with the second threshold; When the comparison value is less than or equal to 0, the adjustment value is 0 dB; When the comparison value is greater than 0 but less than or equal to the second threshold, the adjustment value is the comparison value; When the comparison value is greater than the second threshold, the adjustment value is the second threshold; and The configuration module is used to configure bone conduction hearing aids based on reference output parameters and adjustment values.

14. A device for configuring a bone conduction hearing aid, comprising: Processing equipment; A storage device that communicates with the processing device is used to store instructions, and when the processing device executes the stored instructions, the processing device performs the configuration method of the bone conduction hearing aid device according to any one of claims 1-12.

15. A computer-readable storage medium storing computer instructions, wherein when a computer reads the computer execution instructions in the storage medium, the computer executes a configuration method for a bone conduction hearing aid as described in any one of claims 1-12.

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