Configuration Method and System for Bone Conduction Hearing Aids

Abstract

The present application discloses a method and system for configuring a bone conduction hearing assistance device, which includes the following steps: obtaining hearing loss data of a wearer; determining reference output parameters of the bone conduction hearing assistance device at each sound level and each frequency band 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; 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 particularly to a method and system for configuring a bone conduction hearing aid device. Background Art

[0002] A bone conduction hearing aid device is a hearing aid device designed and manufactured using bone conduction technology. The bone conduction hearing aid device can be a bone conduction hearing aid or a bone conduction assistive listening headset. The bone conduction hearing aid device mainly amplifies external sound information and converts it into mechanical vibrations, and in the form of mechanical vibrations, transmits external sounds through a person's skull, bony labyrinth, endolymph of the inner ear, spiral organ, and auditory nerve to the auditory center of the cerebral cortex in sequence. Compared with traditional air conduction hearing aids, the sound wave signals of the bone conduction hearing aid device can be directly transmitted to the auditory nerve through the bone without passing through the external auditory canal and eardrum, avoiding the pressure sensation and occlusion effect formed by the traditional air conduction hearing aid blocking the ear canal, and the bone conduction hearing aid device can enable the wearer to have a more comfortable wearing experience. In addition, the bone conduction hearing aid device does not need to be implanted into the ear and can effectively avoid ear canal inflammation. Therefore, bone conduction hearing aid devices are increasingly widely used by hearing-impaired patients.

[0003] Since the bone conduction hearing aid device enables the wearer to hear sounds through vibration transmission, there may be a situation where the vibration is relatively intense during use, which will affect the wearer's wearing experience; while lower vibration will in turn affect the wearer's sound listening effect. Therefore, a method for configuring a bone conduction hearing aid device is needed to improve the situation where the vibration of the bone conduction hearing aid device is intense in some cases without affecting the wearer's sound listening effect. Summary of the Invention

[0004] One embodiment of this application provides a method for configuring a bone conduction hearing aid device, which includes the following steps: obtaining the hearing loss data of the wearer; determining the reference output parameters of the bone conduction hearing aid device at each sound level and each frequency band based on the hearing loss data; obtaining an adjustment value of the reference output parameters, where the adjustment value is at least related to the frequency band; and configuring the bone conduction hearing aid device based on the reference output parameters and the adjustment value.

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

[0006] In some embodiments, the adjustment values at different hearing levels and the same frequency band are the same.

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

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

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

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

[0011] In some embodiments, the adjustment values at different hearing levels and in the same frequency band are different.

[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 degree of vibration feeling of the wearer for each frequency band and each sound level; determining a second threshold corresponding to each frequency band and each sound level, the second threshold being related to the speech recognition rate of the wearer at each frequency band and each sound level; 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 a certain sound level and a certain frequency band among each sound level and each frequency band of the reference output parameter; obtaining a comparison value by subtracting the first threshold from the reference output parameter; comparing the comparison value with the second threshold; and determining the adjustment value corresponding to the reference output parameter based on the comparison result between 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 0 dB; when the comparison value is greater than 0 and 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, in the frequency band greater than 0 Hz and less than or equal to 125 Hz, the first threshold is in the range of 48 dB - 52 dB.

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

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

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

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

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

[0021] In some embodiments, configuring the bone conduction hearing assistance device based on the reference output parameter and the adjustment value includes: configuring the bone conduction hearing assistance device using a multi-channel wide dynamic range compression system based on the reference output parameter 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, where the first threshold is related to the wearer's degree of vibration perception of each sound level in each frequency band; 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 the gain reduction value of the multi-channel wide dynamic range compression system when at least one of the respective sound levels is greater than the sound level threshold; based on the comparison result between the reference output parameter and the first threshold, determining the adjustment value corresponding to the reference output parameter includes: 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, the gain reduction value is the difference between the first threshold and the reference output parameter.

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

[0025] One embodiment of the present application provides a configuration system for a bone conduction hearing assistance device, which includes: 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 assistance device at each sound level and each frequency band based on the hearing loss data; an adjustment value determination module for acquiring an adjustment value of the reference output parameter; and a configuration module for configuring the bone conduction hearing assistance device based on the reference output parameter and the adjustment value.

[0026] One embodiment of the present application provides a configuration device for a bone conduction hearing assistance device, which includes: a processing device; a storage device communicatively connected to the processing device for storing instructions, and when the processing device executes the stored instructions, the processing device executes the configuration method of the bone conduction hearing assistance device according to any one of the above technical solutions.

[0027] One embodiment of the present application provides a computer-readable storage medium, where the storage medium stores computer instructions, and when a computer reads the computer instructions in the storage medium, the computer executes the configuration method of the bone conduction hearing assistance device according to any one of the above technical solutions. Description of the Drawings

[0028] The present application will be further described by way of exemplary embodiments, which will be described in detail through the drawings. These embodiments are not restrictive, and in these embodiments, the same numbers represent the same structures, where:

[0029] Figure 1Schematic diagram of a configuration device of a bone conduction hearing assistance device according to some embodiments of the present application;

[0030] Figure 2 Schematic structural diagram of a bone conduction hearing assistance device according to some embodiments of the present application;

[0031] Figure 3 Module diagram of a configuration system of a bone conduction hearing assistance device according to some embodiments of the present application;

[0032] Figure 4 Flowchart of a configuration method of a bone conduction hearing assistance device according to some embodiments of the present application;

[0033] Figure 5 Flowchart of determining an adjustment value according to some other embodiments of the present application;

[0034] Figure 6 Flowchart of determining an adjustment value according to some other embodiments of the present application;

[0035] Figure 7 Flowchart of operations performed by a bone conduction hearing assistance device during use according to some embodiments of the present application;

[0036] Figure 8 Graph of vibration perception thresholds at different frequencies when a wearer wears a bone conduction hearing assistance device measured experimentally;

[0037] Figure 9 Graph of experimental results of speech recognition rate test for wearer 1;

[0038] Figure 10 Graph of experimental results of speech recognition rate test for wearer 2;

[0039] Figure 11 Graph of experimental results of speech recognition rate test for wearer 3. Detailed implementation manners

[0040] To more clearly illustrate the technical solutions of the embodiments of this specification, the accompanying drawings required for the description of the embodiments will be briefly introduced below. Obviously, the accompanying drawings in the following description are only some examples or embodiments of this specification. For those of ordinary skill in the art, without creative efforts, this specification can also be applied to other similar scenarios based on these drawings. Unless obvious from the language context or otherwise stated, the same reference numerals in the figures represent the same structure or operation.

[0041] It should be understood that the "system", "device", "unit" and / or "module" used herein is a way to distinguish different components, elements, parts, portions or assemblies at different levels. However, if other words can achieve the same purpose, the said words can be replaced by other expressions.

[0042] As shown in this specification and the claims, unless the context clearly indicates otherwise, words such as "a", "an", "one" and / or "the" are not specifically singular and may also include the plural. Generally speaking, the terms "comprising" and "including" only indicate the inclusion of the steps and elements that have been clearly identified, and these steps and elements do not constitute an exclusive list. The method or device may also include other steps or elements.

[0043] Flowcharts are used in this specification to illustrate the operations performed by the systems according to the embodiments of this specification. It should be understood that the previous or subsequent operations do not necessarily need to be executed precisely in sequence. On the contrary, the steps can be processed in reverse order or simultaneously. At the same time, other operations can also be added to these processes, or one or more steps can be removed from these processes.

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

[0045] The bone conduction hearing assistance device 110 can be used to obtain sound information (such as ambient sound, wearer's voice, audio files obtained from other devices, etc.) and convert the obtained sound information into vibration signals after processing, and transmit them to the wearer's auditory center through the wearer's bones, etc., so that the wearer can hear the sound information carried by the vibration signals. The bone conduction hearing assistance device can specifically be a bone conduction hearing aid or a bone conduction assisted listening headset. In this specification, the bone conduction hearing assistance device is mainly described by taking the bone conduction hearing aid as an example.

[0046] In some embodiments, the bone conduction hearing assistance device 110 (such as a bone conduction hearing aid) may include a sound pickup component, a speaker component, etc. The sound pickup component is used to pick up sound information (which can also be called the first vibration signal, such as ambient sound, wearer's voice) and process and convert the picked-up first vibration signal into an electrical signal carrying sound information. The speaker component can convert the electrical signal carrying sound information obtained by the sound pickup element into a second vibration signal carrying sound information and transmit it to the wearer's auditory center. For a detailed description of the bone conduction hearing assistance device 110, reference can be made to other descriptions in this application (such as Figure 2 and its detailed description).

[0047] In some embodiments, for different wearers of the bone conduction hearing assistance device, due to different hearing levels (i.e., levels of hearing loss) of the wearers, the configurations of the bone conduction hearing assistance device can be different. As described herein, the configuration of the bone conduction hearing assistance device refers to the parameter value (which can also be called a parameter) related to the intensity of the sound signal output by the bone conduction hearing assistance device and / or its determination process, so that the bone conduction hearing assistance device can output a sound signal based on the parameter value. The parameter value related to the output signal intensity of the bone conduction hearing assistance device can include a gain value (unit: dB), an analog output value (unit: dB), etc. In some embodiments, the gain value can be the value by which the hearing aid amplifies the intensity of the sound signal, and the analog output value can be the intensity value of the output signal simulated by the hearing aid according to the input sound signal parameters (such as the intensity value of the sound signal). For example, the analog output value can be equal to the input value of the sound signal (i.e., the intensity value, unit: dB) plus the gain value (unit: dB). The bone conduction hearing assistance device configuration system 100 can determine the configuration of the bone conduction hearing assistance device corresponding to the wearer's hearing level according to the different hearing levels of the wearer. The bone conduction hearing assistance device 110 can process and output the obtained sound information (such as ambient sound, wearer's voice, audio files obtained from other devices, etc.) based on this configuration, so that the wearer can hear the sound.

[0048] The processing device 120 may process data and / or information obtained from the bone conduction hearing assistance device 110, the memory 130, and / or the terminal 140. For example, the processing device 120 may obtain hearing loss data of the wearer of the bone conduction hearing assistance device 110. As another example, the processing device 120 may determine reference output parameters of the bone conduction hearing assistance device 110 at each sound level and each frequency band based on the hearing loss data. Still another example, the processing device 120 may obtain an adjustment value of the reference output parameter. Yet another example, the processing device 120 may configure the bone conduction hearing assistance device 110 based on the reference output parameter and the adjustment value.

[0049] In some embodiments, the processing device 120 may be a single server or a server group. The server group may be centralized or distributed. In some embodiments, the processing device 120 may be local or remote. For example, the processing device 120 may access information and / or data stored in the bone conduction hearing assistance device 110, the terminal 140, and / or the memory 130 via the network 150. As another example, the processing device 120 may be directly connected to the bone conduction hearing assistance device 110, the terminal 140, and / or the memory 130 to access the stored information and / or data. In some embodiments, the processing device 120 may be implemented on a cloud platform. Merely by way of example, 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-layer cloud, etc. or any combination thereof. In some embodiments, the processing device 120 may be implemented on a computing device. In some embodiments, the processing device 120 or a part of the processing device 120 may be integrated into the bone conduction hearing assistance device 110. In some embodiments, the processing device 120 or a part of the processing device 120 may be integrated into the terminal 140.

[0050] The memory 130 may store data, instructions, and / or any other information. In some embodiments, the memory 130 may store data obtained from the terminal 140 and / or the processing device 120. In some embodiments, the memory 130 may store data and / or instructions that the processing device 120 may execute or use to execute the exemplary methods described in this application. In some embodiments, the memory 130 may include a mass storage device, a removable storage device, a volatile read-write memory, a read-only memory (ROM), etc., or any combination thereof. In some embodiments, the 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-layer cloud, etc., or any combination thereof. In some embodiments, the memory 130 may be connected to the network 150 to communicate with one or more other components (e.g., the processing device 120, the 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 the memory 130 via the network 150. In some embodiments, the memory 130 may be directly connected to or communicate with one or more other components (e.g., the processing device 120, the 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] The terminal 140 may include a mobile device 141, a tablet computer 142, a laptop computer 143, a smart watch 144, etc., or any combination thereof. In some embodiments, the 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, clothes, etc.), mobile devices (e.g., mobile phones, laptop computers, etc.), virtual reality devices (e.g., virtual reality helmets, virtual reality glasses, virtual reality eye masks), etc., or any combination thereof. In some embodiments, the bone conduction hearing aid 110 may be integrated into the terminal 140, e.g., integrated into glasses, accessories, etc.

[0052] In some embodiments, a user (e.g., the wearer of the bone conduction hearing aid 110, a system operator, a doctor, etc.) may interact with the bone conduction hearing aid configuration system 100 through the terminal 140. For example, the user may send a configuration request through the user interface on the terminal 140; after receiving the configuration request, the processing device 120 obtains the hearing loss data of the wearer. For example, the processing device 120 may send a hearing loss data acquisition request to the terminal 140 through the user interface, and the user may upload the hearing loss data of the wearer through the user interface after receiving the acquisition request. The processing device 120 may 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 of the bone conduction hearing assistance device configuration system 100. In some embodiments, one or more components of the bone conduction hearing assistance device configuration system 100 (e.g., the bone conduction hearing assistance device 110, the terminal 140, the processing device 120, the memory 130, etc.) may exchange information and / or data with one or more other components of the bone conduction hearing assistance device configuration system 100 via the network 150. For example, the processing device 120 may obtain the wearer's hearing loss data (e.g., hearing level) from the bone conduction hearing assistance device 110 via the network 150. As another example, the processing device 120 may obtain user instructions from the terminal 140 via the network 150. Network 150 may be and / or include a public network (e.g., the Internet), a private network (e.g., a local area network (LAN), a wide area network (WAN), etc.), a wired network (e.g., an Ethernet network), a wireless network (e.g., an 802.11 network, a Wi-Fi network, etc.), a cellular network (e.g., a Long Term Evolution (LTE) network), a frame relay network, a virtual private network ("VPN"), a satellite network, a telephone network, 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 exchange points through which one or more components of the bone conduction hearing assistance device configuration system 100 may be connected to network 150 to exchange data and / or information.

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

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

[0056] The speaker component 210 can convert a signal containing sound information into a vibration signal. In some embodiments, the sound information may include videos, audio files with specific data formats, or data or files that can be converted into sound through specific means. The signal containing sound information may include one or a combination 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. The multiple signal sources may or may not be related. In some embodiments, the bone conduction hearing assistance device 200 can obtain the signal containing sound information in a variety of different ways. The acquisition of the signal can be wired or wireless, and can be real-time or delayed. For example, the bone conduction hearing assistance device 200 can receive an electrical signal containing sound information in a wired or wireless manner. Another example is that the bone conduction hearing aid 10 may include a component with a sound collection function (e.g., the sound pickup component 220). By picking up the sound in the environment, the mechanical vibration of the sound is converted into an electrical signal, and after being processed by an amplifier, an electrical signal that meets specific requirements is obtained.

[0057] The conversion of the signal containing sound information into a vibration signal by the speaker component 210 is an energy conversion process. The conversion process may involve the coexistence and conversion of various different types of energy. The speaker component 210 may include one or more transducer devices. For example, an electrical signal can be directly converted into mechanical vibration through a transducer device to generate sound. Another example is that the sound information may be contained in an optical signal, and the transducer device can achieve the process of converting the optical signal into a vibration signal. Other types of energy that can coexist and be converted during the operation of the transducer device include thermal energy, magnetic field energy, etc. In some embodiments, the speaker component 210 can achieve the conversion from the signal of sound information to a vibration signal through the cooperation of the magnetic circuit component 211 and the vibration component 213 (the magnetic circuit component 211 and the vibration component 213 can be referred to as transducer devices). Among them, the magnetic circuit component 211 is used to provide a magnetic field, and the vibration component 213 is used to mechanically vibrate under the action of the Ampere force in the magnetic field. For example, the magnetic circuit component 211 may include a magnet. The vibration component 213 may include a magnetic oscillator and a vibration plate. The magnetic oscillator (e.g., the voice coil) moves back and forth under the action of the Ampere force in the magnetic field, and drives the vibration plate to vibrate during the movement. In the above process, the sound information may correspond to the vibration of the magnetic oscillator, and the vibration frequency and amplitude of the magnetic oscillator can be determined according to the frequency and intensity of the sound information. In some embodiments, one of the magnetic circuit component and the magnetic oscillator can be an electromagnet, and 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. Also, the vibration frequency of the magnetic oscillator can be controlled by controlling the change frequency of the current direction in the coil of the electromagnet. In this process, the sound information can also be amplified. For example, the amplification of the loudness of the sound information can be achieved by increasing the vibration amplitude of the magnetic oscillator.

[0058] The specific energy conversion methods of the vibration component may specifically include dynamic coil type, electrostatic type, piezoelectric type, moving iron type, pneumatic type, electromagnetic type, etc. The frequency response range and sound quality of the bone conduction hearing assistance device 200 will be affected by the vibration component. For example, in a dynamic coil transducer, the vibration component may include a wound columnar voice coil and a vibrating body (such as a vibrating piece or a vibrating membrane). The columnar voice coil driven by the signal current drives the vibrating body to vibrate and generate sound in the magnetic field. The stretching and contraction of the vibrating body material, the deformation of the folds, the size, shape, and fixing method, and the magnetic density of the magnetic field will all have a great impact on the sound quality of the bone conduction hearing assistance device. The vibrating body in the vibration component can be a mirror-symmetric structure, a centrosymmetric structure, or an asymmetric structure. Discontinuous hole-like structures can be provided on the vibrating body to enable the vibrating body to generate a larger displacement, so that the bone conduction hearing assistance device 200 can achieve higher sensitivity and improve the output power of vibration and sound; the vibrating body can be an annular body structure, and a plurality of struts converging towards the center can be provided inside the annular body, and the number of struts can be two or more.

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

[0060] The support component 230 can support other components in the bone conduction hearing assistance device 200 (such as the magnetic circuit component, the vibration component and / or the storage component, the power supply component, the communication component (not shown in the figure), the sound pickup component 220). The support component 230 may include one or more shells and one or more connectors. One or more shells can form an accommodation cavity 232 for accommodating the storage component, the controller, the sound pickup component 220, the communication component, the battery component, etc. One or more connectors can connect the shell to other components in the bone conduction hearing assistance device 200 (such as the magnetic circuit component, the vibration component and / or the storage component, the power supply component, the communication component (not shown in the figure), the sound pickup component 220).

[0061] The wired connections involved in the bone conduction hearing assistance device 200 may include metal cables, optical cables, or hybrid cables of metal and optical, 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, twin cables, parallel twin conductors, twisted pairs, etc., or combinations of two or more of these. The examples described above are for convenience of illustration only, and the medium of the wired connection may also be other types, such as other transmission carriers for electrical signals or optical signals, etc.

[0062] The wireless connections involved in the bone conduction hearing assistance device 200 may include radio communication, free space optical communication, acoustic communication, and electromagnetic induction, etc. Among them, radio communication may include IEEE802.11 series standards, IEEE802.15 series standards (such as Bluetooth technology and ZigBee technology, etc.), first-generation mobile communication technology, second-generation mobile communication technology (such as FDMA, TDMA, SDMA, CDMA, and SSMA, etc.), general packet radio service technology, third-generation mobile communication technology (such as CDMA2000, WCDMA, TD-SCDMA, and WiMAX, etc.), fourth-generation mobile communication technology (such as TD-LTE and FDD-LTE, etc.), satellite communication (such as GPS technology, etc.), near field communication (NFC), and other technologies operating in the ISM band (such as 2.4GHz, etc.); free space optical communication may include visible light, infrared signals, etc.; acoustic communication may include sound waves, ultrasonic signals, etc.; electromagnetic induction may include near field communication technology, etc. The examples described above are for convenience of illustration only, and the medium of the wireless connection may also be other types, such as Z-wave technology, other licensed civilian radio frequency bands, and military radio frequency bands, etc. For example, as some application scenarios of the present technology, the bone conduction hearing assistance device 200 may obtain signals containing sound information from other devices through Bluetooth technology.

[0063] The above description of the structure of the bone conduction hearing assistance device 200 is merely a specific example and should not be regarded as the only feasible implementation. Obviously, for professionals in this field, after understanding the basic principle of the bone conduction hearing assistance device 200, various modifications and changes in form and details may be made to the specific ways and steps of implementing the bone conduction hearing assistance device 200 without departing from this principle, but these modifications and changes are still within the scope described above. For example, the bone conduction hearing assistance device 200 may include one or more processors, and the processors may execute one or more sound signal processing algorithms. The sound signal processing algorithms may modify or enhance the sound signals. For example, noise reduction, acoustic feedback suppression, wide dynamic range compression, automatic gain control, active environment 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 may be performed on the sound signals, and these modifications and changes are still within the scope of protection of the claims of the present invention. For another example, the bone conduction hearing assistance device may include one or more sensors, such as a temperature sensor, a humidity sensor, a speed sensor, a displacement sensor, etc. The sensors may collect user information or environmental information. For yet another example, the storage component may not be necessary and may be removed from the bone conduction hearing assistance device.

[0064] In some embodiments, the configuration system of the bone conduction hearing assistance device is mainly configured based on the hearing loss data of the wearer according to a preset formula or a preset algorithm of the hearing aid configuration system. For example, in the hearing aid configuration system, after inputting the hearing loss data of the wearer into the hearing aid configuration system, the hearing aid configuration system may automatically output the relevant parameter values of the hearing aid based on the preset algorithm. Configuring the bone conduction hearing assistance device directly only through the preset algorithm may cause the configured bone conduction hearing assistance device 200 to vibrate violently in some scenarios (such as when the wearer speaks by himself or the environmental sound is too loud), resulting in discomfort for the wearer.

[0065] This application provides a configuration system for a bone conduction hearing assistance device. Figure 3 is a module diagram of the configuration system of the bone conduction hearing assistance device shown in some embodiments of this application. As Figure 3 shown, the configuration system 300 of the bone conduction hearing assistance device includes an acquisition module 310, a reference output parameter determination module 320, an adjustment value determination module 330, and a configuration module 340. The connection forms between the modules may be wired, wireless, or a combination of both. Any one of the modules may be local, remote, or a combination of both. The corresponding relationships between the modules may be one-to-one or one-to-many.

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

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

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

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

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

[0071] In some embodiments, the configuration module 340 can be used to configure the bone conduction hearing assist device based on the reference output parameter and the 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 the 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 assist device using a multi-channel wide dynamic range compression system based on the reference output parameter and the adjustment value.

[0072] It should be noted that the above description of the processing module is only a specific example and should not be regarded as the only feasible implementation. Each of the above modules or units is not necessary. Each module or unit can be implemented by one or more components, and the functions of each module or unit are not limited thereto. The above-mentioned various modules or units can be added or deleted according to specific implementation scenarios or needs. Obviously, for professionals in this field, after understanding the basic principles of the transport capacity scheduling process, various modifications and changes in form and details may be made to the specific implementation methods and steps of the processing module without departing from this principle. Some simple deductions or replacements can also be made, and without creative labor, certain adjustments, combinations or splits can be made to the order of each module or unit, but these modifications and changes are still within the scope of the above description.

[0073] Figure 4 is a flowchart of a configuration method of a bone conduction hearing assistance device according to some embodiments of the present application. As Figure 4 shown, the process 400 of the configuration method of the bone conduction hearing assistance device includes the following steps:

[0074] Step 410, obtaining the hearing loss data of the wearer. Specifically, step 410 can be executed by the obtaining module 310.

[0075] In some embodiments, the hearing loss data of the wearer can be understood as data related to the hearing loss situation of the wearer. The hearing loss data may include the hearing levels (also called hearing thresholds or hearing loss levels) of the wearer in each frequency band and at each sound level. In this specification, the unit used for the hearing level is dBHL. The higher the value of the hearing level, the more serious the hearing loss situation of the wearer. In some embodiments, the hearing loss data may include data related to the hearing aids worn by the wearer in the past. For example, the data related to the hearing aids worn by the wearer in the past may include the configuration data of the bone conduction hearing assistance device used by the wearer in the past.

[0076] In some embodiments, the hearing level may be in the range of 0dBHL - 80dBHL. For example, a hearing level within 0dBHL - 25dBHL may indicate normal hearing; a hearing level within 26dBHL - 40dBHL indicates mild hearing loss; a hearing level of 41dBHL - 60dBHL indicates moderate hearing loss, manifested as difficulty in hearing normal sounds; 61dBHL - 80dBHL indicates severe hearing loss, manifested as difficulty in hearing loud sounds; a hearing level greater than 80dBHL indicates profound hearing loss, manifested as difficulty in hearing sounds.

[0077] In some embodiments, the hearing levels of the wearer of the bone conduction hearing assistance device at different frequency bands can be the same at the same sound level (for the specific description of the sound level, please refer to the relevant content of step 420). For example, at a sound level of 20 dBC, the hearing levels of the wearer at different frequency bands can all be equal to a certain value within the range of 41 dBHL - 60 dBHL; at a sound level of 40 dBC, the hearing levels of the wearer at different frequency bands can all be equal to a certain value within the range of 26 dBHL - 40 dBHL; at a sound level of 60 dBC, the hearing levels of the wearer at different frequency bands can all be equal to a certain value within the range of 0 dBHL - 25 dBHL.

[0078] In some embodiments, the hearing levels of the wearer of the bone conduction hearing assistance device at different frequency bands can be different at the same sound level. For example, at a sound level of 20 dBC, the hearing levels of the wearer in the high frequency band (e.g., at 8000 Hz - 12000 Hz) can all be equal to a certain value within the range of 41 dBHL - 60 dBHL; the hearing levels in the low frequency band can all be equal to a certain value within the range of 26 dBHL - 40 dBHL.

[0079] In some embodiments, the hearing levels corresponding to different sound levels of the wearer of the bone conduction hearing assistance device at the same frequency band can be the same. For example, in the frequency band of 250 Hz - 500 Hz, the hearing levels of the wearer at different sound levels can all be equal to a certain value within 0 dBHL - 25 dBHL; in the frequency band of 500 Hz - 1000 Hz, the hearing levels of the wearer at different frequency bands can all be equal to a certain value within the range of 26 dBHL - 40 dBHL; in the frequency band of 1000 Hz - 2000 Hz, the hearing levels of the wearer at different frequency bands can all be equal to a certain value within the range of 41 dBHL - 60 dBHL.

[0080] In some embodiments, the hearing levels corresponding to different sound levels of the wearer of the bone conduction hearing assistance device at the same frequency band can be different. For example, in the frequency band of 250 Hz - 500 Hz, the hearing level of the wearer at a sound level of 20 dBC can be equal to a certain value within the range of 41 dBHL - 60 dBHL; the hearing level at a sound level of 40 dBC can all be equal to a certain value within the range of 26 dBHL - 40 dBHL; the hearing level at a sound level of 60 dBC can be equal to a certain value within the range of 0 dBHL - 25 dBHL.

[0081] In some embodiments, the hearing loss data of the wearer can be obtained by performing a real-time hearing test on the wearer. For example, a hearing aid fitter can use a hearing test device to conduct a hearing test on the wearer (such as playing sound signals at various frequency bands and various sound levels), so as to obtain the hearing loss data of the wearer. The hearing loss data collected by the hearing test device can be directly uploaded to a processing device (such as processing device 120) through a network (such as network 150) or uploaded to a storage device, and the processing device can obtain the hearing loss data from the storage device. In other embodiments, the wearer can upload his own hearing loss data through a terminal (such as terminal 140), and the bone conduction hearing assistance device configuration system (such as bone conduction hearing assistance device configuration system 100) or device (such as processing device 120) can receive the hearing loss data uploaded by the wearer himself in a wired or wireless manner. In some embodiments, the bone conduction hearing assistance device configuration system or device can retrieve the hearing loss data of the wearer from a relevant memory (such as memory 130).

[0082] Step 420: Based on the hearing loss data, determine the reference output parameters of the bone conduction hearing assistance device at each sound level and each frequency band. Specifically, step 420 can be executed by the reference output parameter determination module 320.

[0083] 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 each frequency band (i.e., the intensity value of the signal analog output by the bone conduction hearing aid, unit: 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 each frequency band (i.e., the intensity value by which the bone conduction hearing aid amplifies the sound signal, unit: dB). It should be noted that when the sound signal input to the bone conduction hearing aid under the reference output parameter (e.g., the reference gain value) satisfies 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 signal intensity corresponding to the sound level can be amplified based on the gain value to determine the analog output value. In some embodiments, for different wearers, due to their different hearing loss data (e.g., the degree of hearing loss at each sound level), the reference output parameter will be different. In some embodiments, the sound level and frequency of the sound signal will affect the reference output parameter of the bone conduction hearing aid, and different sound levels and / or different frequency bands may correspond to different reference output parameters. That is to say, at the same hearing loss level and the same sound level, different frequency bands may correspond to different reference output parameters; at the same hearing loss level and the same frequency band, different sound levels may correspond to different reference output parameters; at the same sound level and the same frequency band, different hearing loss levels may correspond to different reference output parameters.

[0084] The sound level referred to in this specification represents the intensity of the sound signal, with the unit of decibel. In this specification, the measurement of the sound level mainly uses the C frequency weighting measurement, that is, the unit of the sound level in this specification is dBC. The frequency band in this specification refers to the frequency range of the sound signal. In some embodiments, the frequency of the sound signal can be divided into multiple continuous ranges to form different frequency bands.

[0085] In some embodiments, determining the reference output parameters of a bone conduction hearing aid device at each sound level and each frequency band may refer to determining the parameter output parameters of the bone conduction hearing aid device corresponding to the hearing loss level of the wearer of the bone conduction hearing aid device at a preset sound level and / or a preset frequency, as well as at the preset sound level and the preset frequency. In some embodiments, determining the reference output parameters of a bone conduction hearing aid device at each sound level and each frequency band may refer to determining the parameter output parameters of the bone conduction hearing aid device corresponding to the hearing loss level of the wearer of the bone conduction hearing aid device at a preset sound level range and / or a preset frequency band, as well as at the preset sound level range and the preset frequency band. Based on the determined reference output parameters, the bone conduction hearing aid device can amplify the sound signal (i.e., the sound input signal) input into the bone conduction hearing aid device and convert it into a vibration signal, which is transmitted to the wearer of the bone conduction hearing aid device so that the wearer can hear the sound. In some embodiments, the preset sound level, the preset frequency, the preset sound level range, and / or the preset frequency band may be the default settings of the system (e.g., the bone conduction hearing aid device 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, etc. or a combination 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, etc. or a combination 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), etc. or a combination thereof. In some embodiments, the preset frequency band may include 20 Hz - 250 Hz (excluding 250 Hz), 250 Hz - 500 Hz (excluding 500 Hz), 500 Hz - 1000 Hz (excluding 1000 Hz), 1000 Hz - 2000 Hz (excluding 2000 Hz), 2000 Hz - 3000 Hz (excluding 3000 Hz), 3000 Hz - 4000 Hz (excluding 4000 Hz), 4000 Hz - 6000 Hz (excluding 6000 Hz), 6000 Hz - 10000 Hz (excluding 10000 Hz), etc. or a combination thereof.In some embodiments, the preset frequency band may include 0 Hz - 125 Hz (125 Hz may not be included), 125 Hz - 375 Hz (375 Hz may not be included), 375 Hz - 625 Hz (625 Hz may not be included), 625 Hz - 875 Hz (875 Hz may not be included), 875 Hz - 1375 Hz (1375 Hz may not be included), 1375 Hz - 1875 Hz (1875 Hz may not be included), 1875 Hz - 2625 Hz (2625 Hz may not be included), 2625 Hz - 4875 Hz (4875 Hz may not be included), etc. or 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., the bone conduction hearing assistance device configuration system 100) or the user. For example, it can be adjusted according to the hearing level of the wearer of the bone conduction hearing assistance device. For example, if the hearing level of the wearer is 10 dBHL when the sound level is 80 dBC (indicating that the wearer has normal hearing at this sound level), then the maximum value of the preset sound level may not exceed 80 dBC.

[0086] In some embodiments, the reference output parameter may be the reference gain value of the bone conduction hearing assistance device. The processing device 120 may determine the reference gain value of the bone conduction hearing assistance device at each sound level and each frequency band based on the hearing levels at each sound level and each frequency band in the hearing loss data and the values at each sound level and each frequency band. For example, the reference gain value of the bone conduction hearing assistance device at a sound level of 20 dBC and in the 375 Hz - 625 Hz frequency band may be determined based on the sound level of 20 dBC, the 375 Hz - 625 Hz frequency band, and the hearing level of the wearer of the bone conduction hearing assistance device in the 375 Hz - 625 Hz frequency band at a sound level of 20 dBC. 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 assistance device. The processing device 120 may determine the reference analog output signal strength value (i.e., the reference analog output value) of the bone conduction hearing assistance device at each sound level and each frequency band based on the hearing levels at each sound level and each frequency band in the hearing loss data and the values at each sound level and each frequency band. For example, the reference analog output signal strength value (i.e., the reference analog output value) of the bone conduction hearing assistance device at a sound level of 30 dBC and in the 125 Hz - 375 Hz frequency band may be determined based on the sound level of 30 dBC, the 125 Hz - 375 Hz frequency band, and the hearing level of the wearer of the bone conduction hearing assistance device in the 125 Hz - 375 Hz frequency band at a sound level of 30 dBC.

[0087] In some embodiments, the processing device 120 (reference output parameter determination module 320) may, based on the hearing loss data, first determine the reference gain values of the bone conduction hearing aid device at each sound level and each frequency band, and then determine the reference analog output signal intensity value (i.e., the reference analog output value) of the bone conduction hearing aid device at the corresponding sound level and the corresponding frequency band based on the gain values at each sound level and each frequency band.

[0088] In some embodiments, the processing device 120 (reference output parameter determination module 320) may determine the reference output parameters through a preset formula. For example, according to the hearing loss data of the wearer, the reference gain values at each sound level and each frequency band may be determined through a preset formula. In some embodiments, the preset formula may be the "1 / 2 gain principle" proposed by Lybarger, that is, for sensorineural deafness to achieve comfortable hearing, the required gain value should be half of the degree of hearing threshold improvement. That is to say, the reference gain value of the bone conduction hearing aid device may be about half of the wearer's hearing loss.

[0089] In some embodiments, the reference output parameters in step 320 may be determined through the empirical data in the following table (Table 1). For example, the reference gain values at each frequency band and each hearing loss level (determined based on the hearing loss data) may be determined through the empirical data shown in the following table, and then the reference analog output values at the corresponding frequency band and the corresponding hearing loss level may be further determined through the reference gain values. The following table takes the sound level of 60 dB SPL as an example to illustrate the reference gain values at each hearing level and each frequency band. As shown in Table 1, when the sound level is 60 dB SPL and the hearing level is 20 dB HL, the reference gain values at each frequency band are 0; when the hearing level is 40 dB HL, the reference gain value in the 125 - 375 Hz frequency band is 5. In some embodiments, when the sound level and the hearing level are fixed, as the frequency band increases, the reference gain value may first increase and then decrease. In some embodiments, when the frequency band is fixed, the reference gain value increases with the increase of the hearing level.

[0090] Table 1 takes the sound level of 60 dB SPL as an example to illustrate the reference gain values at each hearing level and each frequency band.

[0091]

[0092] In some embodiments, the processing device 120 may determine the reference output parameters according to a configuration model. The configuration model may represent the relationship between the reference output parameters and the frequency band, the sound level, and the hearing level.

[0093] Step 430, obtain the adjustment value of the reference output parameter. Among them, the adjustment value is at least related to the frequency band. Specifically, step 430 may be executed by the reference output adjustment value determination module 330.

[0094] An adjustment value refers to a value used to adjust a reference output parameter. In some embodiments, the reference output parameter can be adjusted by the adjustment value, and the adjusted reference output parameter can be used as the actual simulated output parameter of the bone conduction hearing assistance device. Taking the reference output parameter as the reference simulated output value and the reference gain value as examples respectively for illustration. For example, the reference simulated output value (the intensity value of the simulated output signal) can be adjusted by the adjustment value, and the adjusted reference simulated output value can be used as the actual simulated output value (the actual intensity value of the simulated output signal) of the bone conduction hearing assistance device. Another example is that the reference gain value (the intensity value for amplifying the sound signal) of the bone conduction hearing assistance device can be adjusted by the adjustment value, and the adjusted reference gain value can be used as the actual gain value of the bone conduction hearing assistance device.

[0095] In some embodiments, the adjustment value is used to reduce the reference output parameter. For example, the adjustment value can be a value used to attenuate the reference simulated output value, that is, the adjustment value can be subtracted from the reference output parameter. Another example is that the adjustment value can also be a value used to attenuate the reference gain value, that is, the adjustment value can be subtracted from the reference gain value. Still another example is that the adjustment value can be a proportional value less than 1, that is, the reference output parameter can be multiplied by the adjustment value.

[0096] The situation where the vibration of the bone conduction hearing assistance device is relatively strong occurs when the frequency of the sound signal input to the bone conduction hearing assistance device is relatively low. For example, bone conduction headphones are prone to vibration in the frequency band of 125 Hz to 625 Hz. Therefore, an adjustment value can be set in the frequency band of 0 Hz to 625 Hz (or in the frequency band of 125 Hz to 625 Hz) (for example, the adjustment value is used to reduce the reference output parameter in this frequency band) to improve the situation where the vibration of the bone conduction hearing assistance device is strong in this frequency band.

[0097] Figure 8 is a vibration perception threshold graph at each frequency when the wearer wears the bone conduction hearing assistance device measured experimentally. In Figure 8 the vibration perception threshold (unit: dBV) can refer to the value obtained by numerically converting the driving voltage value (unit: V) of the bone conduction hearing assistance device when the wearer can perceive the vibration. If the driving voltage value of the bone conduction hearing assistance device is X (unit: V); then the converted vibration perception threshold is 20 * log10(X / 1) (unit: dBV). Only as an example, when the driving voltage value of the bone conduction hearing assistance device is 1 V, the corresponding vibration perception threshold is 0 dBV; when the driving voltage value of the bone conduction hearing assistance device is 0.5 V, the corresponding vibration perception threshold is -6 dBV. From Figure 8It can be seen that the vibration perception threshold of the bone conduction hearing assistance device is relatively small in the frequency band below 1000 Hz, indicating that the bone conduction hearing assistance device is prone to vibration in the frequency band below 1000 Hz, especially in the frequency band of 125 Hz to 600 Hz. Among them, the bone conduction hearing assistance device is most prone to vibration at 125 Hz, 250 Hz, 400 Hz, and 500 Hz. Therefore, based on the data measured in the above experiments, the adjustment value can be set within the frequency band of 0 Hz to 625 Hz (or within the frequency band of 125 Hz to 625 Hz).

[0098] In some embodiments, the same frequency band and / or the same sound level at different hearing levels may correspond to the same adjustment value. For example, the adjustment value at a hearing level of 26 dBHL - 40 dBHL, a frequency within the frequency band of 0 Hz - 625 Hz, and a sound level of 20 dBC is the same as the adjustment value at a hearing level of 41 dBHL - 60 dBHL, a frequency within the frequency band of 0 Hz - 625 Hz, and a sound level of 20 dBC. For another example, the adjustment value at a hearing level of 26 dBHL - 40 dBHL, a frequency within the frequency band of 0 Hz - 125 Hz, and a sound level of 20 dBC is the same as the adjustment value at a hearing level of 41 dBHL - 60 dBHL, a frequency within the frequency band of 0 Hz - 125 Hz, and a sound level of 20 dBC. For another example, the adjustment value at a hearing level of 26 dBHL - 40 dBHL, a frequency within the frequency band of 125 Hz - 375 Hz, and a sound level of 20 dBC is the same as the adjustment value at a hearing level of 41 dBHL - 60 dBHL, a frequency within the frequency band of 125 Hz - 375 Hz, and a sound level of 20 dBC.

[0099] In some embodiments, the same frequency band and / or the same sound level at different hearing levels may correspond to different adjustment values. For example, the adjustment value at a hearing level of 26 dBHL - 40 dBHL, a frequency within the frequency band of 0 Hz - 625 Hz, and a sound level of 20 dBC is different from the adjustment value at a hearing level of 41 dBHL - 60 dBHL, a frequency within the frequency band of 0 Hz - 625 Hz, and a sound level of 20 dBC. For another example, the adjustment value at a hearing level of 26 dBHL - 40 dBHL, a frequency within the frequency band of 20 Hz - 125 Hz, and a sound level of 20 dBC is different from the adjustment value at a hearing level of 41 dBHL - 60 dBHL, a frequency within the frequency band of 20 Hz - 125 Hz, and a sound level of 20 dBC. For another example, the adjustment value at a hearing level of 26 dBHL - 40 dBHL, a frequency within the frequency band of 125 Hz - 375 Hz, and a sound level of 20 dBC is different from the adjustment value at a hearing level of 41 dBHL - 60 dBHL, a frequency within the frequency band of 125 Hz - 375 Hz, and a sound level of 20 dBC.

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

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

[0102] In some embodiments, the same sound level and / or the same hearing level may correspond to the same adjustment value in different frequency bands. For example, the adjustment value for a frequency band in the range of 0 Hz - 125 Hz (not including 125 Hz), a sound level in the range of 20 dBC - 40 dBC, and a hearing level of 41 dBHL - 60 dBHL may be the same as the adjustment value for a frequency band in the range of 125 Hz - 375 Hz, a sound level in the range of 20 dBC - 40 dBC, and a hearing level of 41 dBHL - 60 dBHL. As another example, the adjustment value for a frequency band in the range of 125 Hz - 375 Hz (not including 375 Hz), a sound level in the range of 40 dBC - 60 dBC, and a hearing level of 26 dBHL - 40 dBHL may be the same as the adjustment value for a frequency band in the range of 375 Hz - 625 Hz, a sound level in the range of 40 dBC - 60 dBC, and a hearing level of 26 dBHL - 40 dBHL.

[0103] In some embodiments, the same sound level and / or the same hearing level may correspond to different adjustment values at different frequency bands. For example, the adjustment values for frequencies in the range of 0 Hz - 125 Hz (excluding 125 Hz), sound levels of 20 dBC - 40 dBC, and hearing levels of 41 dBHL - 60 dBHL may be different from those for frequencies in the range of 125 Hz - 375 Hz, sound levels of 20 dBC - 40 dBC, and hearing levels of 41 dBHL - 60 dBHL. For another example, the adjustment values for frequencies in the range of 125 Hz - 375 Hz (excluding 375 Hz), sound levels of 40 dBC - 60 dBC, and hearing levels of 26 dBHL - 40 dBHL may be different from those for frequencies in the range of 375 Hz - 625 Hz, sound levels of 40 dBC - 60 dBC, and hearing levels of 26 dBHL - 40 dBHL.

[0104] In some embodiments, the adjustment value is at least related to the frequency band, and the adjustment value may be different 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, within the frequency band where the frequency is greater than 0 Hz and less than or equal to 625 Hz, the adjustment value is in the range of 1 dB - 12 dB. By setting the adjustment value to the above value within the above frequency range and then configuring the bone conduction hearing assistance device, the problem that the vibration is relatively strong in some scenarios when the wearer wears the bone conduction hearing assistance device can be improved, and the influence on speech intelligibility can also be ensured to be small. In some embodiments, as the frequency increases, the adjustment value decreases. 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; the adjustment value corresponding to a frequency of 500 Hz may be 1 dB. For 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; the adjustment value corresponding to a frequency of 500 Hz may be 4 dB. In some embodiments, within the frequency band where the frequency is greater than 625 Hz and less than or equal to 8000 Hz, the adjustment value may be 0 dB - 4 dB. In some embodiments, within the frequency band where the frequency is greater than 625 Hz and less than or equal to 8000 Hz, the adjustment value may be 0.

[0105] In some embodiments, in 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. In some embodiments, in the frequency band greater than 125 Hz and less than or equal to 375 Hz, the adjustment value is set to 3 dB - 9 dB. In some embodiments, in the frequency band greater than 375 Hz and less than or equal to 625 Hz, the adjustment value is set to 1 dB - 6 dB. By further dividing the frequency band and setting the above adjustment values in several of the above frequency bands respectively, the bone conduction hearing assistance device can have a better effect of reducing vibration.

[0106] In some embodiments, in the frequency band greater than 0 Hz and less than or equal to 125 Hz, the adjustment value is 5 dB - 7 dB. In the frequency band greater than 125 Hz and less than or equal to 375 Hz, the adjustment value is 3 dB - 5 dB. In some embodiments, in the frequency band greater than 375 Hz and less than or equal to 625 Hz, the adjustment value is 1 dB - 3 dB. By setting the adjustment value to the above values within the above frequency range and then configuring the bone conduction hearing assistance device, the vibration problem of the wearer with a hearing level of 30 dBL when wearing the bone conduction hearing assistance device in the corresponding frequency band can be solved, and it can also have almost no impact on speech intelligibility, ensuring the hearing aid effect of the wearer.

[0107] In some embodiments, in the frequency band greater than 0 Hz and less than or equal to 125 Hz, the adjustment value is 10 dB - 12 dB. In some embodiments, in the frequency band greater than 125 Hz and less than or equal to 375 Hz, the adjustment value is 7 dB - 9 dB. In some embodiments, in the frequency band greater than 375 Hz and less than or equal to 625 Hz, the adjustment value is 4 dB - 6 dB. By setting the adjustment value to the above values within the above frequency range and then configuring the bone conduction hearing assistance device, the vibration problem of the wearer with a hearing level of 40 dBL when wearing the bone conduction hearing assistance device in the corresponding frequency band can be solved, and it can also have a relatively small impact on speech intelligibility, ensuring the hearing aid effect of the wearer.

[0108] Figures 9 - 11 It is a graph showing the experimental results of speech recognition rate tests on three wearers (wearer 1, wearer 2, and wearer 3) respectively. Figures 9 - 11 Taking the reference output parameter as the reference simulated output value as an example, it shows the speech recognition rate, vibration feeling, and volume of the wearer before reducing the reference simulated output value, as well as the speech recognition rate, vibration feeling, and volume of the wearer when the reference simulated output value corresponds to different adjustment values in each frequency band. Figures 9 - 11Six groups of tests were conducted for each tester. In the table, negative numbers indicate that the adjustment value reduces the reference output parameter (such as the reference simulated output value). For example, -5 means the adjustment value is 5 dB, reducing the reference simulated output value by 5 dB; another example, -15 means the adjustment value is 15 dB, reducing the reference simulated output value by 15 dB.

[0109] As Figures 9 - 11 shown, when reducing the reference simulated output value based on the adjustment value, the speech recognition rate may decrease, the vibration sensation may decrease, and the volume may also decrease. It can be seen from the table that at a frequency of 125 Hz, if the adjustment value is 5 dB (or less than this value), that is, the reference simulated output value is reduced by 5 dB, the speech recognition rate does not change significantly; at a frequency of 250 Hz, if the adjustment value is 3 dB (or less than this value), that is, the reference simulated output value is reduced by 3 dB, the speech recognition rate does not change significantly; at a frequency of 500 Hz, if the adjustment value is 1 dB (or less than this value), that is, the reference simulated output value is reduced by 1 dB, the speech recognition rate does not change significantly. At the same time, setting the adjustment value according to the above values, the tester can feel vibration when speaking himself, but the volume is okay (that is, the volume is within the range where the wearer can basically hear clearly).

[0110] At a frequency of 125 Hz, if the adjustment value is 10 dB (or greater than 5 dB and less than 10 dB), that is, the reference simulated output value is reduced by 10 dB, the reduction in the speech recognition rate is less than or equal to 5%; at a frequency of 250 Hz, if the adjustment value is 7 dB (or greater than 3 dB and less than 7 dB), that is, the reference simulated output value is reduced by 7 dB, the reduction in the speech recognition rate is less than or equal to 5%; at a frequency of 500 Hz, if the adjustment value is 4 dB (or greater than 1 dB and less than 4 dB), the reference simulated output value is reduced by 4 dB, and the reduction in the speech recognition rate is less than or equal to 5%. At the same time, setting the adjustment value according to the above values, the tester may feel more comfortable, but feel that the sound is relatively low (that is, the wearer may feel that the volume is too low).

[0111] At a frequency of 125 Hz, if the adjustment value is 17 dB (or within the range greater than 10 dB and less than 17 dB), that is, the reference analog output value is reduced by 17 dB, the reduction in speech recognition rate may be greater than 5% (such as 10%); at a frequency of 250 Hz, if the adjustment value is 15 dB (or within the range greater than 7 dB and less than 15 dB), that is, the reference analog output value is reduced by 15 dB, the reduction in speech recognition rate may be greater than 5% (such as 10%); at a frequency of 500 Hz, if the adjustment value is 10 dB (or within the range greater than 4 dB and less than 10 dB), that is, the reference analog output value is reduced by 10 dB, the reduction in speech recognition rate may be greater than 5% (such as 10%). At the same time, when setting the adjustment value according to the above numerical values, the tester may feel that the volume is small (that is, the wearer is very likely unable to hear clearly due to too low volume).

[0112] Within a certain range (such as within the range where the adjustment value is less than 17 dB), the larger the number of adjustment values, the better the effect of reducing the vibration of the bone conduction hearing aid device, but by Figures 9 - 11 It can be known that the larger the number of adjustment values may lead to a lower output signal intensity of the bone conduction hearing aid device, which will have a greater impact on the speech recognition rate (such as may cause a reduction in the speech recognition rate), and when the adjustment value is within the above range in the above embodiments, it can not only solve the vibration problem of the wearer with a hearing level of 30 dBL - 40 dBL when wearing the bone conduction hearing aid device in the corresponding frequency band, but also ensure a relatively small impact on speech intelligibility.

[0113] In some embodiments, the adjustment value of the reference output parameter can be only related to the frequency band. The adjustment values corresponding to the reference output parameter in different hearing levels and the same frequency band can be the same (such as the adjustment values in the above embodiments), and the adjustment values corresponding to the same hearing level and different frequency bands can be different; the adjustment values corresponding to the reference output parameter in the same frequency band under different sound levels can be the same, and the adjustment values in different frequency bands under the same sound level can be different; the adjustment values corresponding to the reference output parameter in the same frequency band under different sound levels and different hearing levels can be the same, and the adjustment values in different frequency bands under the same sound level and the same hearing level are different.

[0114] 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 values corresponding to the reference output parameter in different hearing levels and the same frequency band are different; the adjustment values corresponding to the reference output parameter in the same hearing level, the same frequency band, and different sound levels can be the same. For a detailed description of this embodiment, please refer to Figure 5 And its related description.

[0115] In some embodiments, the adjustment value of the reference output parameter can be related to the frequency band and sound level. The adjustment values corresponding to the same frequency band at different sound levels are different; however, the adjustment values corresponding to the same frequency band at different hearing levels, the same sound level can be the same. For a detailed description of this embodiment, please refer to Figure 6 and its related descriptions.

[0116] Step 440: Configure the bone conduction hearing assistance device based on the reference output parameter and the adjustment value. Specifically, step 440 can be executed by the configuration module 340.

[0117] In some embodiments, the processing device 120 (configuration module 340) can adjust the reference output parameter based on the adjustment value to obtain the actual output parameter, and configure the bone conduction hearing assistance device through the actual output parameter.

[0118] 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 assistance 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 directly subtracting the adjustment value from the reference output parameter, or adjusting the relevant setting parameters of other bone conduction hearing assistance devices through the adjustment value to achieve the purpose of reducing the reference output parameter.

[0119] In some embodiments, the processing device 120 (configuration module 340) can configure the magnetic circuit component based on the adjustment value and the reference output value to implement the configuration of the bone conduction hearing assistance device. In some embodiments, configuring the bone conduction hearing assistance device includes setting various parameters of the bone conduction hearing assistance device so that the parameters related to the signal output intensity of the bone conduction hearing assistance device (for example, the gain value, the analog output value) are preset values, for example, the reference parameter adjusted based on the adjustment value. For example, the reference gain value of the bone conduction hearing assistance device for the sound signal can be adjusted by adjusting the current magnitude of the electromagnet in the magnetic circuit component, adjusting the resistance magnitude of the amplification circuit of the sound pickup component, etc., and the reference analog output value of the bone conduction hearing assistance device can be adjusted to implement the configuration of the bone conduction hearing assistance device.

[0120] In some embodiments, based on the reference output parameter and the adjustment value, an equalization adjustment system (EQ system) or an automatic gain control system (AGC system) etc. can be used to configure the bone conduction hearing assistance device.

[0121] In some other embodiments, based on the reference output parameters and adjustment values, a multi-channel wide dynamic range compression system (WDRC system) can be used to configure a bone conduction hearing aid device. The multi-channel wide dynamic range compression system can first divide the sound signal into multiple channels according to frequency bands using a filter bank, and perform compression processing on the signals of each channel separately. In this way, an appropriate compression ratio and compression threshold can be designed according to the hearing loss situation corresponding to the frequency band, and then the processed signals of each channel are synthesized into one signal. The multi-channel wide dynamic range compression system can perform hearing compensation more flexibly. In the multi-channel wide dynamic range compression system, by adjusting each reference output parameter and adjustment value, the compression ratio and compression threshold of the signals of each channel can be adjusted, thereby adjusting the reference output parameters of each channel.

[0122] Figure 5 is an exemplary flowchart of the method for obtaining the adjustment 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. As Figure 5 shown, process 500 includes the following steps.

[0123] Step 510, determining a first threshold corresponding to each frequency band and each sound level, where the first threshold is related to the wearer's degree of vibration perception of each frequency band and each sound level.

[0124] The degree of vibration perception can be used to represent the degree to which the user perceives vibration when wearing the bone conduction hearing aid device. In some embodiments, the degree of vibration perception can include multiple levels for representing the degree of perceived vibration. The higher the level, the greater the degree of vibration that the user can perceive. 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 degrees of vibration perception can include "no vibration", "extremely slight vibration", "slight vibration", "obvious vibration, but acceptable", and "severe 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.

[0125] In some embodiments, the first threshold may be the output signal intensity of the bone conduction hearing aid device corresponding to a certain level of vibration perception of the wearer. That is to say, when the intensity of the output signal of the bone conduction hearing aid device reaches this first threshold, the wearer can feel the vibration of this level. For example, the first threshold may be the output signal intensity of the bone conduction hearing aid device corresponding to the wearer when the vibration perception level is at the third level (i.e., the reference output parameter). That is to say, when the intensity of the output signal of the bone conduction hearing aid device reaches this first threshold, the wearer can feel the slight vibration corresponding to the third level. For another example, the first threshold may be the output signal intensity of the bone conduction hearing aid device corresponding to the wearer when the vibration perception level is at the fourth level. That is to say, when the intensity of the output signal of the bone conduction hearing aid device reaches this first threshold, the wearer can feel the obvious vibration corresponding to the fourth level, but the vibration intensity that can be received. In some embodiments, when the intensity of the output signal of the bone conduction hearing aid device is greater than this first threshold, the wearer may feel a stronger vibration of the vibration corresponding to the level of the first threshold (for example, the slight vibration corresponding to the third level), and the wearing experience is poor. Then, it is necessary to adjust (reduce) the reference output parameter so that the intensity of the output signal of the bone conduction hearing aid device is less than the first threshold.

[0126] In some embodiments, the preliminary reference output parameters corresponding to the bone conduction hearing aid device wearer at each sound level and each frequency band can be obtained. For a detailed description of obtaining the reference output parameter, reference can be made to Figure 4 operation 420 in. In some embodiments, for different wearers, the first threshold may be different. For example, the wearer of the bone conduction hearing aid device can be tested to determine the output signal intensity and the corresponding vibration perception level of the bone conduction hearing aid device wearer at each sound level and each frequency band under this preliminary reference output parameter, and the reference output parameter can be obtained by adjusting the preliminary reference output parameter to adjust the output signal intensity and the vibration perception level so that the vibration perception level of the wearer reaches a certain level (for example, the third level, slight vibration), and then the first threshold corresponding to each frequency band and each sound level is determined. In some embodiments, the adjusted preliminary reference output parameter (i.e., the reference output parameter, such as the reference analog output value) may be equal to the adjusted signal output intensity. The first threshold may be equal to the adjusted output signal intensity or the reference analog output value corresponding to the wearer's vibration perception level reaching a certain level (for example, the third level, slight vibration).

[0127] In some embodiments, for different wearers, the first threshold may be the same. For example, the first threshold may be determined specifically according to the following method: Test multiple testers to determine the signal output intensity when each tester subjectively feels a slight vibration of the second level at each sound level and each frequency band, and use the above signal output intensity as test data; Integrate and select the test data to obtain the first threshold. This first threshold can be applied to different wearers. In some embodiments, integrating and selecting the test data may be: For a certain frequency band, only consider the lowest value of the output parameters when each tester subjectively feels a slight vibration at each sound level in this frequency band, and further select the lowest value from the lowest values of the output parameters when each tester subjectively feels a slight vibration at each sound level as the first threshold.

[0128] In some embodiments, the phenomenon of severe vibration of the bone conduction hearing assistance device in the low frequency band (such as the frequency band of 0 Hz - 625 Hz) is more obvious. An adjustment value of the reference output parameter can be set in the low frequency band to reduce the reference output parameter and reduce the vibration intensity that the user can perceive; Correspondingly, a first threshold can be set in the low frequency band (such as the frequency band of 0 Hz - 625 Hz) so as to determine the adjustment value of the reference output parameter based on the first threshold. In some embodiments, the first threshold can be set within the frequency band of 0 Hz - 625 Hz, and the adjustment value can be determined in this frequency band. In some embodiments, the first thresholds corresponding to different frequency bands are different. For example, within the frequency band greater than 0 Hz and less than or equal to 125 Hz, the first threshold is within the range of 48 dB - 52 dB. In some embodiments, within the frequency band greater than 125 Hz and less than or equal to 375 Hz, the first threshold is within the range of 49 dB - 54 dB. In some embodiments, within the frequency band greater than 375 Hz and less than or equal to 625 Hz, the first threshold is within the range of 50 dB - 55 dB. In some embodiments, at the same sound level, the higher the frequency band, the greater the first threshold.

[0129] In some embodiments, the first thresholds corresponding to the same frequency band at different sound levels may be the same. For example, a minimum value (such as 48 dB) can be selected within the range of the first thresholds corresponding to each of the above frequency bands as the first threshold for this frequency band, so that the bone conduction hearing assistance device will not generate relatively severe vibration when the received sound signal is at the same frequency band of different sound levels. For example, within the frequency band greater than 0 Hz and less than or equal to 125 Hz, the first threshold is 48 dB. Within the frequency band greater than 125 Hz and less than or equal to 375 Hz, the first threshold is 49 dB. Within the frequency band greater than 375 Hz and less than or equal to 625 Hz, the first threshold is 50 dB.

[0130] In some embodiments, the first thresholds corresponding to the same frequency band at different sound levels 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 a frequency band 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 a frequency band 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 a frequency band 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.

[0131] In some embodiments, the first thresholds corresponding to the same frequency band at different hearing levels and different sound levels may be the same. For example, a minimum value (e.g., 48 dB) may be selected within the range of the first thresholds corresponding to the above-mentioned frequency bands as the first threshold of the frequency band, so that when the bone conduction hearing aid receives a sound signal in the same frequency band, no violent vibration will be generated regardless of the sound level of the sound signal and the hearing level of the wearer.

[0132] In some embodiments, the first thresholds corresponding to different hearing levels, different sound levels and the same frequency band are different. For example, the first threshold value may be 49dB for a hearing level of 40dBHL, a frequency greater than 125Hz and less than or equal to 375Hz, and a sound level of 60dBC. The first threshold value may be 50dB for a hearing level of 10dBHL, a frequency greater than 125Hz and less than or equal to 375Hz, and a sound level of 75dBC. For another example, the first threshold value may be 55dB for a hearing level of 30dBHL, a frequency greater than 375Hz and less than or equal to 625Hz, and a sound level of 70dBC. For example, the first threshold value may be 56dB for a hearing level of 20dBHL, a frequency greater than 375Hz and less than or equal to 625Hz, and a sound level of 75dBC. In some embodiments, the first thresholds corresponding to different frequency bands, different sound levels, and different hearing levels may be the same. For example, a minimum value (e.g., 48 dB) may be selected from the range of the first thresholds corresponding to the above-mentioned various frequency bands as the first thresholds corresponding to different sound levels in all frequency bands, so that the bone conduction hearing aid device will not produce more violent vibrations when the received sound signals are at different sound levels and different frequency bands. For example, in the frequency band greater than 0 Hz-625 Hz, the first threshold is 48 dB.

[0133] Step 520: Determine a 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.

[0134] The speech recognition rate (i.e., speech intelligibility) can be the ratio of the words understood or clearly heard to the words heard. The speech recognition rate can be used to characterize the auditory sensitivity and clarity of the language heard by the wearer after wearing a hearing aid, and thus to a certain extent reflect the hearing aid effect of the wearer. The higher the speech recognition rate, the higher the auditory sensitivity and the higher the auditory clarity of the wearer after wearing the hearing aid, and the better the hearing aid effect. In some embodiments, if the speech recognition rate is greater than or equal to 70%, the hearing aid effect can be considered good; while if the speech recognition rate is less than or equal to 50%, the hearing aid effect can be considered unsatisfactory and the bone conduction hearing assistance device needs to be re-adjusted or configured.

[0135] In some embodiments, the adjustment of the reference output parameter (such as reduction) can affect the intensity of the output signal of the bone conduction hearing assistance device, and thus may affect the speech recognition rate of the bone conduction hearing assistance device. For example, based on Figures 9 - 11 the experimental results, it can be known that within a certain range (such as within the range where the adjustment value is less than 17 dB), the larger the adjustment value, the lower the speech recognition rate may be. The second threshold can be used to ensure that the speech recognition rate after the adjustment of the reference output parameter is within a certain range (such as higher than a certain threshold). That is to say, the second threshold can be used to control the reduction amount of the speech recognition rate after the adjustment of the reference output parameter within a certain range. For example, when the adjustment value does not exceed the second threshold, the reduction amount of the speech recognition rate of the wearer wearing the hearing aid relative to when the reference output parameter is not adjusted can be small. For example, the reduction amount of the speech recognition rate can be less than or equal to 5%. The reduction amount of the speech recognition rate can be the speech recognition rate when the reference output parameter is not adjusted minus the speech recognition rate after the adjustment of the reference output parameter.

[0136] 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 assistance device at the preset speech recognition rate when the wearer wears the bone conduction hearing assistance device. That is to say, when the adjustment value corresponding to the reference output parameter of the bone conduction hearing assistance device reaches this second threshold, the speech recognition rate of the wearer wearing the bone conduction hearing assistance device is the preset threshold. When the adjustment value is greater than this second threshold, the speech recognition rate of the wearer wearing the bone conduction hearing assistance device will be less than the preset speech recognition rate.

[0137] For example, as Figure 10 shown, the second threshold can be the adjustment value corresponding to the reference output parameter when the speech recognition rate is 80% at 125 Hz when the wearer wears the bone conduction hearing assistance device, that is, the second threshold is 5 dB. That is to say, when the adjustment value corresponding to the reference output parameter of the bone conduction hearing assistance device at 125 Hz is the second threshold, the speech recognition rate of the wearer wearing the bone conduction hearing assistance device can be 80%. Another example, as Figure 11As shown, the second threshold may be an adjusted value corresponding to the reference output parameter when the speech recognition rate of the wearer wearing the bone conduction hearing aid device at 250 Hz is 60%, that is, the second threshold is 12 dB. That is to say, when the adjusted value of the reference output parameter of the bone conduction hearing aid device at 250 Hz is the second threshold, the speech recognition rate of the wearer wearing the bone conduction hearing aid device can be 60%.

[0138] In some embodiments, the second threshold may be determined according to the threshold of the preset speech recognition rate. For example, it may be based on Figures 9 - 11 the experimental results of the speech recognition rate test of the wearer in Figure 10 . Only as an example, referring to

[0139] , when the speech recognition rate of the wearer is 80% when the bone conduction hearing aid device is configured based on the unadjusted reference output parameter, if it is set that the speech recognition rate should be not less than 75% after reducing the reference output parameter (that is, the reduction amount of the speech recognition rate is less than or equal to 5%), the second threshold may be 10 dB; if it is set that the speech recognition rate should be not less than 80% (that is, the speech recognition rate hardly decreases), the second threshold may be 5 dB.

[0139] In some embodiments, the phenomenon of severe vibration of the bone conduction hearing aid device in the low frequency band (such as the frequency band of 0 Hz - 625 Hz) is more obvious. The adjusted value of the reference output parameter may be set in the low frequency band to reduce the reference output parameter and reduce the vibration intensity that the user can perceive; correspondingly, the second threshold may be set in the low frequency band (such as the frequency band of 0 Hz - 625 Hz) so as to determine the adjusted value of the reference output parameter based on the first threshold. In some embodiments, the second thresholds corresponding to different frequency bands are different. For example, in the frequency band greater than 0 Hz and less than or equal to 125 Hz, the second threshold is in the range of 5 dB - 10 dB. In some embodiments, in the frequency band greater than 125 Hz and less than or equal to 375 Hz, the second threshold is in the range of 3 dB - 7 dB. In some embodiments, in the frequency band greater than 375 Hz and less than or equal to 625 Hz, the second threshold is in the range of 1 dB - 4 dB. In some embodiments, the higher the frequency band at the same sound level, the smaller the second threshold.

[0140] In some embodiments, the second thresholds corresponding to the same frequency band at different hearing levels may be the same. For example, regardless of whether the wearer's hearing level is 30 dBHL or 40 dBHL, the second threshold may be set within the above range. In some embodiments, the second thresholds corresponding to the same frequency band at different hearing levels may be different. For example, within the frequency band greater than 0 Hz and less than or equal to 125 Hz, the hearing level is 30 dBHL, and the second threshold is 5 dB; within the frequency band greater than 0 Hz and less than or equal to 125 Hz, the hearing level is 40 dBHL, and the second threshold is 15 dB. In some embodiments, the second thresholds corresponding to the same frequency band at different sound levels may be the same. In some embodiments, a minimum value within the above range may be selected as the second threshold, so that the bone conduction hearing assistance device will not overly affect the speech recognition rate when receiving sound signals at different sound levels. For example, within the frequency band greater than 125 Hz and less than or equal to 375 Hz, the second threshold may be 3 dB. In some embodiments, within the frequency band greater than 0 Hz and less than or equal to 125 Hz, the second threshold may be 5 dB. In some embodiments, within the frequency band greater than 375 Hz and less than or equal to 625 Hz, the second threshold may be 1 dB.

[0141] In some embodiments, the second thresholds corresponding to the same frequency band at different sound levels may be different. For example, within the frequency band 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; within the frequency band greater than 0 Hz and less than or equal to 125 Hz, the sound level is 75 dBC, and the second threshold is 10 dB.

[0142] Step 530, determine an adjustment value based on the reference output parameter, the first threshold, and the second threshold.

[0143] In some embodiments, when the reference output parameter is greater than the first threshold, an initial adjustment value may be set first. The initial adjustment value may be determined based on experience or a preset formula. Then, the initial adjustment value may be compared with the second threshold. If the initial adjustment value is greater than the second threshold, the initial adjustment value is decreased so that the initial adjustment value is less than or equal to the second threshold. If the initial adjustment value is less than or equal to the second threshold, the initial adjustment value is determined as the adjustment value.

[0144] In some embodiments, a comparison value may be obtained by subtracting the first threshold corresponding to a specific frequency band and a specific sound level from the reference output parameter corresponding to the specific frequency band and the specific sound level; then, the comparison value is compared with the second threshold corresponding to the specific frequency band and the specific sound level; based on the comparison result between the comparison value and the second threshold, the adjustment value corresponding to the reference output parameter at the specific frequency band and the specific sound level is determined.

[0145] For the method of determining the first threshold and the second threshold, please refer to the relevant description above. The comparison value can be a positive number, a negative number, or zero. Comparing the comparison value with the second threshold can be a comparison of numerical magnitudes to determine the magnitude relationship between the comparison value and the second threshold. The comparison result between the comparison value and the second threshold can include that the comparison value is less than the second threshold, the comparison value is equal to the second threshold, or the comparison value is greater than the second threshold. Based on the comparison result between the comparison value and the second threshold, determining the adjustment value corresponding to the reference output parameter can be based on the magnitude relationship between the comparison value and the second threshold to determine the adjustment value.

[0146] In some embodiments, based on the comparison result between the comparison value and the second threshold, determining the adjustment value corresponding to the reference output parameter can include that when the comparison value is less than or equal to 0, the adjustment value is 0; when the comparison value is greater than 0 and 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.

[0147] When the reference output parameter is less than or equal to the first threshold, after configuring the bone conduction hearing aid device according to the reference output parameter, the wearer has a relatively low possibility of feeling vibration when wearing the bone conduction hearing aid device, and there is no need to adjust the reference output parameter. When the reference output parameter is greater than the first threshold, after configuring the bone conduction hearing aid device according to the reference output parameter, the wearer has a relatively high possibility of feeling strong vibration when wearing the bone conduction hearing aid device, and it is necessary to adjust the reference output parameter. Further, when determining the adjustment value, not only the vibration risk of the bone conduction hearing aid device brought by the reference output parameter should be considered, but also the impact of the adjusted reference output parameter on the speech recognition rate of bone conduction hearing aid should be considered. Since the second threshold is a threshold related to the speech recognition rate, by comparing the above comparison value with the second threshold, it is ensured that the adjustment value is less than or equal to the second threshold as much as possible, and the impact on the speech recognition rate caused by the adjustment of the reference output parameter is minimized.

[0148] Figure 6 is an exemplary flowchart of the method for obtaining the adjustment value of the reference output parameter. In some embodiments, when configuring a bone conduction hearing aid device using a multi-channel wide dynamic range compression system, the process shown in Figure 6 can be adopted to determine the adjustment value corresponding to the reference output parameter. As shown in Figure 6 , the process 600 of determining the adjustment value corresponding to the reference output parameter can include the following steps:

[0149] Step 610, comparing the reference output parameter with the first threshold. Among them, the first threshold is related to the wearer's vibration perception degree for each frequency band and each sound level.

[0150] For the relevant description of the first threshold in this step and the method for determining the first threshold, please refer to the relevant content about the first threshold in step 510. Comparing the reference output parameter with the first threshold can be a comparison of the numerical magnitudes of the reference output parameter and the first threshold.

[0151] 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.

[0152] For the relevant description of the adjustment value corresponding to the reference output parameter, please refer to the relevant content of step 430. The comparison result between the reference output parameter and the first threshold can include that the reference output parameter is greater than the first threshold, the reference output parameter is equal to the first threshold, and the comparison result of the reference output parameter being equal to the first threshold. In some embodiments, it is possible to determine whether the adjustment value is 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.

[0153] In some embodiments, when using a multi-channel wide dynamic range compression system to configure a bone conduction hearing assist device, the adjustment value can include the gain reduction value of the multi-channel wide dynamic range compression system when at least one sound level is greater than the sound level threshold among various sound levels. In some embodiments, the sound level threshold can be 70 dB. During the wearer's use of the bone conduction hearing assist device, the sound level of the voice signal during daily conversations is generally about 60 dB. The situation where the sound level of the voice signal is greater than or equal to 70 dB C may occur when the wearer is speaking himself or when the environment is relatively noisy. At this time, the bone conduction hearing assist device may generate relatively strong vibrations. Therefore, setting the adjustment value to adjust (such as reducing) the reference output parameter within this sound level range can improve the vibration situation of the bone conduction hearing assist device and, at the same time, enable the speech recognition rate of the wearer during daily conversations to be hardly affected.

[0154] The gain when at least one sound level among various sound levels is greater than the sound level threshold can be referred to as the High Level Gain. The adjustment value can include the reduction value of the High Level Gain of the multi-channel wide dynamic range compression system. The High Level Gain of the multi-channel wide dynamic range compression system can be the gain when the sound level of the sound signal is greater than the sound level threshold (such as 70 dB). The gain of the multi-channel wide dynamic range compression system when at least one sound level among various sound levels is greater than the sound level threshold can be determined based on the wearer's hearing loss data. For example, it can be determined according to an empirical formula. For example, the empirical formula can be used to determine the High Level Gain of the multi-channel wide dynamic range compression system based on the wearer's hearing level. The adjustment value can be a specific value for reducing the High Level Gain obtained from the empirical formula.

[0155] In some embodiments, it can be determined whether the gain reduction value is 0 (that is, whether to reduce the gain when at least one sound level among various sound levels is greater than the sound level threshold) 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 gain reduction value is 0; when the reference output parameter is greater than the first threshold, the gain reduction value is greater than 0.

[0156] In some embodiments, after determining the gain reduction value when at least one sound level among various sound levels is greater than the sound level threshold, the gain value when the sound level is greater than the sound level threshold can be reduced by this gain reduction value, and the reduced gain value can be used as the input parameter of the multi-channel wide dynamic range compression system. When at least one sound level among various sound levels is greater than the sound level threshold, the bone conduction hearing aid device is prone to vibration. By setting the gain reduction value determined in the above manner within a set frequency band (the frequency band greater than 0 Hz and less than or equal to 625 Hz) and when the sound level is higher than the sound level threshold, and using this gain reduction value as the adjustment value, it can be ensured that the reference output parameter when the sound level of the sound signal is less than the sound level threshold is not affected, while when the sound level of the sound signal is less than the sound level threshold, the reference output parameter is reduced. This can improve the severe vibration situation of the bone conduction hearing aid device in certain scenarios while ensuring the speech recognition rate of the bone conduction hearing aid device.

[0157] In some embodiments, when the adjustment value includes the gain reduction value of the multi-channel wide dynamic range compression system when at least one sound level among various sound levels is greater than the sound level threshold, step 620 can specifically include the following steps: If the reference output parameter is less than or equal to the 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.

[0158] In this embodiment, if the reference output parameter is less than or equal to the first threshold, the probability that the wearer feels severe vibration when wearing the bone conduction hearing assistance device is small, and there is no need to adjust (reduce) the high-level gain. Therefore, the reduction value of the high-level gain is set to 0. If the reference output parameter is greater than the first threshold, the wearer is more likely to feel severe vibration when wearing the bone conduction hearing assistance device, and it is necessary to adjust (reduce) the high-level gain to reduce the reference output parameter so that the reference output parameter can be less than the first threshold.

[0159] In some embodiments, when configuring the bone conduction hearing assistance device using a multi-channel wide dynamic range compression system, the adjustment value may include the reduction value of the maximum output (Output Limit) of the multi-channel wide dynamic range compression system when at least one sound level among each sound level is greater than the sound level threshold. In some embodiments, the sound level threshold may be 70 dB. In this embodiment, the situation where the sound level of the sound signal is greater than or equal to 70 dBC may occur when the wearer is speaking by himself or when the environment is relatively noisy. At this time, the bone conduction hearing assistance device may generate relatively strong vibration. Therefore, setting the adjustment value to adjust 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 situation of the bone conduction hearing assistance device and can also make the speech recognition rate of the wearer hardly affected during daily conversations.

[0160] The maximum output can be understood as the limiting value of the reference output parameter for each frequency band. When the reference output parameter is greater than the maximum output, the reference output parameter of the bone conduction hearing assistance device is equal to the maximum output. The maximum output (Output Limit) of the multi-channel wide dynamic range compression system can be determined according to an empirical formula based on the hearing loss data of the wearer. For example, the empirical formula can be used to determine the maximum output (Output Limit) of the multi-channel wide dynamic range compression system based on the hearing level of the wearer. The adjustment value can be the specific value for reducing the maximum output obtained from the empirical formula. The empirical formula can be set by the user or be the default setting of the bone conduction hearing assistance device configuration system.

[0161] In some embodiments, when the adjustment value may include the reduction value of the maximum output (Output Limit) of the multi-channel wide dynamic range compression system when at least one sound level among each sound level is greater than the 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 value of the maximum output is 0 dB; if the reference output parameter is greater than the first threshold, the reduction value of the maximum output is greater than 0 dB.

[0162] That is to say, if the reference output parameter is less than or equal to the first threshold, the probability that the wearer feels severe vibration when wearing the bone conduction hearing aid device is small, and there is no need to adjust (reduce) the maximum output. If the reference output parameter is greater than the first threshold, the wearer has a greater probability of feeling severe vibration when wearing the bone conduction hearing aid device, and it is necessary to adjust (reduce) the maximum output so as to reduce the reference output parameter, so that the reference output parameter can be less than the first threshold.

[0163] Furthermore, when it is determined that the reduction value of the maximum output is greater than 0, the specific value of the reduction value of the maximum output parameter can be further determined. In some embodiments, for example, the maximum output can be gradually reduced in equal steps so that the reference output parameter is finally less than the first threshold. For example, gradually reducing the maximum output in equal steps can be that the value of each reduction of the maximum output is the same (such as reducing the maximum output by 2 dB each time), so as to gradually reduce the reference output parameter and finally make the reference output parameter less than the first threshold.

[0164] Since the wearer generally feels stronger vibration when speaking by himself or when the ambient sound is louder, and the sound level is higher at this time, for example, greater than or equal to 70 dB. Through method 600 and adjusting the reference output parameter, when a sound signal with a medium sound level (such as a sound level below 70 dB) is input into the bone conduction hearing aid device, the reference output parameter of the bone conduction hearing aid device is not affected, and when a sound signal with a high sound level (such as a sound level of 70 dB and above) is input into the bone conduction hearing aid device, the reference output parameter of the bone conduction hearing aid device is lower than the first threshold, thereby improving the situation that the wearer feels stronger vibration when speaking by himself or when the ambient sound is louder.

[0165] In some embodiments, the adjustment value may only include the gain reduction value when at least one sound level among all sound levels is greater than the sound level threshold. In other embodiments, the adjustment value may only include the reduction value of the maximum output (Output Limit) when at least one sound level among all sound levels is greater than the sound level threshold. In some embodiments, the adjustment value may include both the gain reduction value when at least one sound level among all sound levels is greater than the sound level threshold and the reduction value of the maximum output (Output Limit) when at least one sound level among all sound levels is greater than the sound level threshold.

[0166] In some embodiments, the setting parameters of the multi-channel wide dynamic range compression system further include the crossover frequency, lower threshold, low level gain, upper threshold, expansion threshold, expansion ratio, compressor attack, compressor release, AGCo attack, and AGCo release. Among them, the crossover frequency can be the frequency at which the audio spectrum is divided, that is, the division point of each frequency band. The lower threshold can be the lower limit threshold of the sound level in this 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 this frequency band, that is, the threshold corresponding to the high level gain. The expansion threshold can be the sound level expansion threshold in the frequency band, and the expansion ratio can be the gain ratio of the sound at the expansion threshold. The compressor attack can be the transition time when the compressor detects a sound higher than the threshold and the compressor fully takes effect. During the transition time, the gain gradually increases to the preset gain. The compressor release can be the transition time when the sound is lower than the threshold and the compressor fully takes effect. During the transition time, the gain gradually decreases to the preset gain. The gain algorithm is the automatic gain control algorithm according to output (AGCo). The AGCo attack can be 2 ms. The AGCo release can be 64 ms.

[0167] Figure 7 is a flowchart of the operations performed during the use of the bone conduction hearing assistance device according to some embodiments of the present application. As Figure 7 shown, during the use of the bone conduction hearing assistance device, the bone conduction hearing assistance device can perform the following steps:

[0168] Step 710, obtain a sound input signal. In some embodiments, the sound input signal may include an audio signal (such as a song, speech, etc.) obtained by the bone conduction hearing aid device from devices such as a storage device (e.g., memory 130), a terminal (e.g., terminal 140), etc. In some embodiments, the sound signal input to the bone conduction hearing aid device may include a sound signal picked up by the sound pickup component of the bone conduction hearing aid device. For example, the sound pickup component may pick up a sound (the first vibration signal) and convert the first vibration signal into an electrical signal after processing. The electrical signal may be transmitted to the speaker component of the bone conduction hearing aid device, and the speaker component is configured to process the electrical signal based on the reference output parameter and convert it into a second vibration signal and transmit it to the wearer.

[0169] Step 720, determine the reference output parameter corresponding to the frequency component based on the sound level and frequency components of the sound input signal and the reference output parameter. In some embodiments, the bone conduction hearing aid device may obtain a preset reference output parameter stored in the storage device of the bone conduction hearing aid device. The preset reference output parameter may correspond to different frequency bands, sound levels, and hearing levels. The bone conduction hearing aid device may determine the reference output parameter corresponding to the sound level and frequency components from the preset reference output parameters according to the sound level and frequency components of the sound input signal. In some embodiments, the bone conduction hearing aid device may determine the reference output parameter corresponding to the sound level, frequency components, and hearing level of the wearer from the preset reference output parameters according to the sound level, frequency components, and hearing level of the sound input signal. In some embodiments, the preset reference output parameters corresponding to different frequency bands, sound levels, and hearing levels may be determined according to Figure 4 step 420 in

[0170] Step 730, obtain the actual output parameter corresponding to the frequency component at the sound level based on the reference output parameter corresponding to the frequency component and the adjustment value corresponding to the reference output parameter of the frequency component. In some embodiments, the bone conduction hearing aid device may obtain an adjustment value of the preset reference output parameter stored in the storage device of the bone conduction hearing aid device. The preset adjustment value may correspond to the reference output parameters at different frequency bands, sound levels, and hearing levels. The bone conduction hearing aid device may determine the adjustment value corresponding to the reference output parameter corresponding to the sound level and frequency components from the preset adjustment values according to the sound level and frequency components of the sound input signal. In some embodiments, the bone conduction hearing aid device may determine the adjustment value corresponding to the reference output parameter at the sound level, frequency components, and hearing level of the wearer from the preset adjustment values according to 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 corresponding to different frequency bands, sound levels, and hearing levels may be determined according to Figure 4 step 430 in

[0171] Step 740: Control the bone conduction hearing aid device to output a sound signal based on the actual output parameters.

[0172] The reference output parameters can be understood as the parameters set initially during the configuration of the bone conduction hearing aid device, and the actual output parameters can be understood as the output parameters of the bone conduction hearing aid device adjusted based on the adjustment value. In some embodiments, the actual output parameters may include a gain value and / or an actual analog output value. In some embodiments, the actual gain value may be the value by which the hearing aid actually amplifies the intensity of the sound signal during wearing, and the actual analog output value may be the actual output signal intensity value simulated by the hearing aid according to the input sound signal parameters (e.g., the intensity value of the sound signal). For example, the actual analog output value may be equal to the input value of the sound signal (i.e., the intensity value, unit dB) plus the actual gain value (unit dB). In some embodiments, the actual analog output value corresponding to a certain specific sound level and specific frequency band may be equal to the actual output value during the use of the bone conduction hearing aid device (i.e., the intensity value of the signal actually output by the bone conduction hearing aid device, unit dB). For example, when the bone conduction hearing aid device inputs a sound signal at this specific sound level and specific frequency band. In some embodiments, when the wearer wears the bone conduction hearing aid device, the sound pickup component 220 of the bone conduction hearing aid device may execute step 710, and the magnetic circuit component of the bone conduction hearing aid device may execute steps 720 and 730. The vibration component of the bone conduction hearing aid device may execute step 740, and the vibration component may convert the actual output parameters determined by the magnetic circuit component into corresponding vibration intensities, so that the bone conduction hearing aid device outputs a sound signal by means of mechanical vibration. In some embodiments, when the wearer wears the bone conduction hearing aid device, the sound pickup component 220 of the bone conduction hearing aid device may execute step 710, and the processing device in the bone conduction hearing aid device may execute steps 720 and 730. The processing device of the bone conduction hearing aid device may control the magnetic circuit component and the vibration component to execute step 740. For example, the processing device may 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 device outputs a sound signal by means of mechanical vibration. Another example is that the processing device may control the magnitude of the current in the voice coil based on the determined actual output parameters to control the mechanical vibration intensity generated by the voice coil, thereby controlling the output signal intensity of the bone conduction hearing aid device.

[0173] In some embodiments, the actual output parameters for each frequency band and each sound level may be stored in the bone conduction hearing aid device. When the bone conduction hearing aid device obtains a sound input signal, the bone conduction hearing aid device may directly determine the actual output parameters of the bone conduction hearing aid device at the corresponding sound level and corresponding frequency band based on the sound level and frequency band of the sound input signal, and output a sound signal based on the actual output parameters.

[0174] The basic concepts have been described above. Obviously, for those skilled in the art, the above detailed disclosure is only an example and does not constitute a limitation to this application. Although not explicitly stated here, 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, so such modifications, improvements, and corrections still fall within the spirit and scope of the exemplary embodiments of this application.

[0175] At the same time, this application uses specific terms to describe the embodiments of this application. For example, "one embodiment", "an embodiment", and / or "some embodiments" mean a certain feature, structure, or characteristic related to at least one embodiment of this application. Therefore, it should be emphasized and noted that the "one embodiment" or "an embodiment" or "an alternative embodiment" mentioned twice or more at different positions in this specification does not necessarily refer to the same embodiment. In addition, certain features, structures, or characteristics in one or more embodiments of this application can be appropriately combined.

[0176] In addition, unless explicitly stated in the claims, the order of the processing elements and sequences, the use of numbers and letters, or the use of other names in this application is not used to limit the order of the processes and methods of this application. Although some currently considered useful embodiments of the invention are discussed through various examples in the above disclosure, it should be understood that such details only serve the purpose of illustration. The appended claims are not limited to the disclosed embodiments. On the contrary, the claims are intended to cover all modifications and equivalent combinations that conform to the essence and scope of the embodiments of this application. For example, although the system components described above can be implemented by hardware devices, they can also be implemented only through software solutions, such as installing the described system on existing servers or mobile devices.

[0177] Similarly, it should be noted that, in order to simplify the expression of the disclosure of this application and thus help the understanding of one or more embodiments of the invention, in the previous description of the embodiments of this application, sometimes multiple features are grouped into one embodiment, drawing, or description thereof. However, this disclosure method does not mean that the features required by the object of this application are more than those mentioned in the claims. In fact, the features of the embodiments are fewer than all the features of the individual embodiments disclosed above.

[0178] In some embodiments, numbers are used to describe components and the quantity of attributes. It should be understood that such numbers used in the description of embodiments are, in some examples, modified by the modifiers "about", "approximately" or "substantially". Unless otherwise stated, "about", "approximately" or "substantially" indicate that the stated numbers are allowed a variation of ±20%. Accordingly, in some embodiments, the numerical parameters used in the specification and claims are approximate values, which may vary according to the characteristics required by individual embodiments. In some embodiments, the numerical parameters should consider the specified significant digits and adopt the method of retaining the general number of digits. Although the numerical ranges and parameters used in some embodiments of the present application to confirm the breadth of their scope are approximate values, in specific embodiments, such numerical settings are as precise as possible within the feasible range.

[0179] For each patent, patent application, patent application publication, and other materials cited in the present application, such as articles, books, specifications, publications, documents, etc., their entire contents are hereby incorporated into the present application by reference. This excludes the application history files that are inconsistent with or conflict with the content of the present application, as well as the files that limit the broadest scope of the claims of the present application (currently or subsequently attached to the present application). It should be noted that if there are inconsistencies or conflicts between the descriptions, definitions, and / or uses of terms in the attached materials of the present application and the content described in the present application, the descriptions, definitions, and / or uses of terms in the present application shall prevail.

[0180] Finally, it should be understood that the embodiments described in the present application are only used to illustrate the principles of the embodiments of the present application. Other variations may also fall within the scope of the present application. Therefore, by way of example and not limitation, alternative configurations of the embodiments of the present application may be considered to be consistent with the teachings of the present application. Accordingly, the embodiments of the present application are not limited to the embodiments explicitly introduced and described in the present application.

Claims

1. A configuration method for a bone conduction hearing aid device, comprising the following steps: Obtain the hearing loss data of the wearer; Based on the hearing loss data, determine the reference output parameters of the bone conduction hearing aid device at each sound level and each frequency band; Obtain the adjustment value of the reference output parameter, where the adjustment value is at least related to the frequency band; wherein, obtaining the adjustment value of the reference output parameter includes: determining the first threshold corresponding to each frequency band and each sound level, where the first threshold is related to the wearer's vibration perception degree of each frequency band and each sound level; determining the second threshold corresponding to each frequency band and each sound level, where the second threshold is related to the speech recognition rate of the wearer at each frequency band and each sound level; and determining the adjustment value based on the reference output parameter, the first threshold, and the second threshold; the second threshold is the maximum value of the adjustment value corresponding to the reference output parameter; Configure the bone conduction hearing aid device based on the reference output parameter and the adjustment value.

2. The configuration method according to claim 1, wherein, The configuring the bone conduction hearing aid device based on the reference output parameter and the adjustment value includes: In the frequency band greater than 0 Hz and less than or equal to 625 Hz, reduce the reference output parameter based on the adjustment value.

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

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

6. The configuration method according to claim 1, wherein, The adjustment values at different hearing levels and the same frequency band are different.

7. The configuration method according to claim 1, wherein, The determining the adjustment value based on the reference output parameter, the first threshold, and the second threshold includes: For the reference output parameter at a certain sound level and a certain frequency band among each sound level and each frequency band; Obtain a comparison value by subtracting the first threshold from the reference output parameter; Compare the comparison value with the second threshold; Based on the comparison result between the comparison value and the second threshold, determine the adjustment value corresponding to the reference output parameter.

8. The configuration method according to claim 7, wherein, The 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 0 dB; When the comparison value is greater than 0 and 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.

9. The configuration method according to claim 1, wherein, In the frequency band greater than 0 Hz and less than or equal to 125 Hz, the first threshold is in the range of 48 dB - 52 dB; In the frequency band greater than 125 Hz and less than or equal to 375 Hz, the first threshold is in the range of 49 dB - 54 dB; and / or, In the frequency band greater than 375 Hz and less than or equal to 625 Hz, the first threshold is in the range of 50 dB - 55 dB; In the frequency band greater than 0 Hz and less than or equal to 125 Hz, the second threshold is in the range of 5 dB - 10 dB; In the frequency band greater than 125 Hz and less than or equal to 375 Hz, the second threshold is in the range of 3 dB - 7 dB; and / or, In the frequency band greater than 375 Hz and less than or equal to 625 Hz, the second threshold is in the range of 1 dB - 4 dB.

10. The configuration method according to claim 1, wherein, Configuring the bone conduction hearing assistance device based on the reference output parameter and the adjustment value includes: Configuring the bone conduction hearing assistance device using a multi-channel wide dynamic range compression system based on the reference output parameter and the adjustment value.

11. The configuration method according to claim 10, wherein 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 degree of each sound level in each frequency band; Determining the adjustment value corresponding to the reference output parameter based on the comparison result between the reference output parameter and the first threshold.

12. The configuration method according to claim 11, wherein, The adjustment value includes the 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 the 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 gain reduction value is 0 dB; 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.

13. The configuration method according to claim 11, wherein, The adjustment value includes the reduction value of the maximum output of the multi-channel wide dynamic range compression system when at least one sound level in each sound level is greater than the 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 value of the maximum output is 0 dB; If the reference output parameter is greater than the first threshold, the reduction value of the maximum output is greater than 0 dB.

14. A configuration system for a bone conduction hearing assistance device, comprising: An acquisition module for acquiring the hearing loss data of the wearer; A reference output parameter determination module, configured to determine reference output parameters of a bone conduction hearing aid device at each sound level and each frequency band based on hearing loss data; An adjustment value determination module, configured to obtain an adjustment value of the reference output parameter; wherein, 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 degree of vibration feeling of the wearer for each frequency band and each sound level; determining a second threshold corresponding to each frequency band and each sound level, the second threshold being related to the speech recognition rate of the wearer at each frequency band and each sound level; and determining the adjustment value based on the reference output parameter, the first threshold, and the second threshold; the second threshold is the maximum value of the adjustment value corresponding to the reference output parameter; and A configuration module, configured to configure a bone conduction hearing aid device based on the reference output parameter and the adjustment value.

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