Bone conduction hearing aid setup method and setup system

Abstract

A method for setting up a bone conduction hearing aid and a setting system are disclosed. The method comprises the steps of: acquiring hearing loss data of a wearer; determining a reference output parameter of the bone conduction hearing aid at each sound level in each frequency band based on the hearing loss data; acquiring an adjustment value of the reference output parameter at least associated with the frequency band at each sound level in each frequency band; and setting up the bone conduction hearing aid based on the reference output parameter and the adjustment value at each sound level in each frequency band.

Description

Technology Field

[0001] The present disclosure relates to the field of bone conduction hearing aids, and specifically, to a method for setting up a bone conduction hearing aid and a setting system. Background Technology

[0002] A bone conduction hearing aid is a hearing aid designed and manufactured using bone conduction technology. The bone conduction hearing aid may be a bone conduction hearing device or a bone conduction hearing headphone. The bone conduction hearing aid primarily amplifies external sound information, converts said external sound information into mechanical vibrations, and transmits said mechanical vibrations containing external sound information in the form of mechanical vibrations to the auditory center of the cerebral cortex through the human skull, bony labyrinth, inner ear lymph fluid, Corti, and auditory nerve. Compared to traditional electro-conduction hearing aids, the sound wave signals of the bone conduction hearing aid can be transmitted directly to the auditory nerve through the bones without penetrating the external auditory canal and eardrum; thus, it avoids the pressure and ear-blocking effects caused by traditional electro-conduction hearing aids blocking the ear canal. Furthermore, the bone conduction hearing aid allows the wearer to have a comfortable wearing experience. Additionally, the bone conduction hearing aid does not require implantation inside the ear and can effectively avoid ear canal inflammation. Therefore, the aforementioned bone conduction hearing aid is being used increasingly by patients with hearing impairments.

[0003] Since the bone conduction hearing aid transmits sound through vibrations to allow the wearer to hear, severe vibrations may occur during use, which may affect the wearer's experience. Additionally, small vibrations may affect the wearer's hearing. Therefore, it is desirable to provide a method for configuring a bone conduction hearing aid that improves the experience of wearing the bone conduction hearing aid caused by severe vibrations without affecting the wearer's hearing.

[0004] One of the embodiments of the present disclosure provides a method for setting up a bone conduction hearing aid. The method may include the steps of: acquiring hearing loss data of a wearer; determining a reference output parameter of the bone conduction hearing aid at each sound level in each frequency band based on the hearing loss data; acquiring an adjustment value of the reference output parameter at least in each frequency band at each sound level associated with the frequency band; and setting up the bone conduction hearing aid based on the reference output parameter and the adjustment value in each frequency band at each sound level.

[0005] In some embodiments, the step of setting the bone conduction hearing aid based on the reference output parameter and the adjustment value at each sound level in each frequency band may include the step of reducing the reference output parameter based on the adjustment value in a frequency band within the range of 0Hz to 625Hz.

[0006] In some embodiments, the control values ​​may be the same at different sound levels in the same frequency band.

[0007] In some embodiments, in a frequency band within the range of 0 Hz to 625 Hz, the adjustment value may be within the range of 1 dB to 12 dB.

[0008] In some embodiments, in a frequency band within the range of 0 Hz to 125 Hz, the adjustment value may be within the range of 5 dB to 12 dB; in a frequency band within the range of 125 Hz to 375 Hz, the adjustment value may be within the range of 3 dB to 9 dB; or in a frequency band within the range of 375 Hz to 625 Hz, the adjustment value may be within the range of 1 dB to 6 dB.

[0009] In some embodiments, in a frequency band within the range of 0 Hz to 125 Hz, the adjustment value is within the range of 5 dB to 7 dB; in a frequency band within the range of 125 Hz to 375 Hz, the adjustment value may be within the range of 3 dB to 5 dB; or in a frequency band within the range of 375 Hz to 625 Hz, the adjustment value may be within the range of 1 dB to 3 dB.

[0010] In some embodiments, in a frequency band within the range of 0 Hz to 125 Hz, the adjustment value may be within the range of 10 dB to 12 dB; in a frequency band within the range of 125 Hz to 375 Hz, the adjustment value may be within the range of 7 dB to 9 dB; or in a frequency band within the range of 375 Hz to 625 Hz, the adjustment value may be within the range of 4 dB to 6 dB.

[0011] In some embodiments, the control values ​​may differ at different sound levels within the same frequency band.

[0012] In some embodiments, the step of obtaining a control value of the reference output parameter at each sound level in each frequency band may include: a step of determining a first threshold corresponding to each sound level in each frequency band and also related to the degree of vibration detected by the wearer at each sound level in each frequency band; a step of determining a second threshold corresponding to each sound level in each frequency band and also related to the voice identification rate of the wearer at each sound level in each frequency band; and a step of determining the control value based on the reference output parameter, the first threshold, and the second threshold.

[0013] In some embodiments, the step of determining the adjustment value based on the reference output parameter, the first threshold, and the second threshold may include: a step of obtaining a comparison value by subtracting the first threshold from the reference output parameter with respect to the reference output parameter at a mother sound level among each sound level in the mother frequency band of each frequency band; a step of obtaining a first comparison result by comparing the comparison value with the second threshold; and a step of determining the adjustment value corresponding to the reference output parameter based on the first comparison result.

[0014] In some embodiments, the step of determining the control value corresponding to the reference output parameter based on the first comparison result may include: a step of designating the control value as 0dB when the comparison value is 0 or less; a step of designating the control value as the comparison value when the comparison value is greater than 0 and less than or equal to the second threshold; and a step of designating the control value as the second threshold value when the comparison value is greater than the second threshold.

[0015] In some embodiments, in a frequency band within the range of 0 Hz to 125 Hz, the first threshold may be within the range of 48 dB to 52 dB.

[0016] In some embodiments, in a frequency band within the range of 125 Hz to 375 Hz, the first threshold may be within the range of 49 dB to 54 dB.

[0017] In some embodiments, in a frequency band within the range of 375Hz to 625Hz, the first threshold may be within the range of 50dB to 55dB.

[0018] In some embodiments, in a frequency band within the range of 0 Hz to 125 Hz, the second threshold may be within the range of 5 dB to 10 dB.

[0019] In some embodiments, in a frequency band within the range of 125Hz to 375Hz, the second threshold may be within the range of 3dB to 7dB.

[0020] In some embodiments, in a frequency band within the range of 375Hz to 625Hz, the second threshold may be within the range of 1dB to 4dB.

[0021] In some embodiments, the step of setting the bone conduction hearing aid based on the reference output parameter and the adjustment value at each sound level in each frequency band may include the step of setting the bone conduction hearing aid using a multi-channel large dynamic range compression system based on the reference output parameter and the adjustment value at each sound level in each frequency band.

[0022] In some embodiments, the step of obtaining an adjustment value of the reference output parameter at each sound level in each frequency band may include: a step of determining a second comparison result by comparing the reference output parameter with a first threshold related to the degree of vibration detected by the wearer at each sound level in each frequency band; and a step of determining the adjustment value corresponding to the reference output parameter based on the second comparison result.

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

[0024] In some embodiments, the adjustment value may include a reduction value of the output limit of the multi-channel large dynamic range compression system when at least one of the sound levels is greater than the sound level threshold; and the step of determining the adjustment value corresponding to the reference output parameter based on the second comparison result may include: a step of setting the reduction value of the output limit to 0 dB when the reference output parameter is less than or equal to the first threshold; and a step of setting the reduction value of the output limit to a value greater than 0 dB when the reference output parameter is greater than the first threshold.

[0025] One of the embodiments of the present disclosure provides an apparatus for setting a bone conduction hearing aid. The apparatus may include: an acquisition module configured to acquire hearing loss data of a wearer; a reference output parameter determination module configured to determine a reference output parameter of the bone conduction hearing aid at each sound level in each frequency band based on each of the hearing loss data; a control value determination module configured to acquire a control value of the reference output parameter at each sound level in each frequency band; and a setting module configured to set the bone conduction hearing aid based on the reference output parameter and the control value at each sound level in each frequency band.

[0026] One of the embodiments of the present disclosure provides a system for setting up a bone conduction hearing aid. The system comprises a processing unit; and a storage unit communicating with the processing unit, said storage unit configured to store instructions, said storage unit

[0027] A non-transient computer-readable storage medium is provided for storing computer instructions of any of the embodiments of the present disclosure, and when reading computer instructions of the non-transient computer-readable storage medium, the computer may perform a method for setting up any one of the bone conduction hearing aids of the above technical methods. Brief explanation of the drawing

[0028] The present disclosure is further explained through exemplary embodiments. These exemplary embodiments are described in detail with reference to the drawings. These embodiments are not limiting exemplary embodiments, and similar reference numerals indicate similar structures. FIG. 1 is a schematic diagram illustrating an exemplary system for setting up a bone conduction hearing aid according to some embodiments of the present disclosure. FIG. 2 is a schematic diagram showing a bone conduction hearing aid according to some embodiments of the present disclosure. FIG. 3 is a block diagram showing a system for setting up a bone conduction hearing aid according to some embodiments of the present disclosure. FIG. 4 is a flowchart illustrating an exemplary process for setting up a bone conduction hearing aid according to some embodiments of the present disclosure. FIG. 5 is a flowchart illustrating an exemplary process for determining a control value according to other embodiments of the present disclosure. FIG. 6 is a flowchart illustrating an exemplary process for determining a control value according to other embodiments of the present disclosure. FIG. 7 is a flowchart illustrating the operations performed by a bone conduction hearing aid according to other embodiments of the present disclosure when in use. Figure 8 is a diagram showing vibration thresholds at different frequencies measured through experiments when a wearer wears a bone conduction hearing aid. Figure 9 is a diagram showing the experimental results of a voice identification rate test performed on Wearer 1. Figure 10 is a diagram showing the experimental results of a voice identification rate test performed on Wearer 2. Figure 11 is a diagram showing the experimental results of a voice identification rate test performed on wearer 3. Specific details for implementing the invention

[0029] To more clearly explain the technical methods related to the embodiments of the present disclosure, the drawings referenced in the description of the embodiments are briefly introduced below. Of course, the drawings described below are merely examples or embodiments of the present disclosure. Those skilled in the art can apply the present disclosure to other similar situations based on these drawings without any further creative effort. Unless clearly obtainable or described in the preceding and following text, the same reference numerals in the drawings indicate the same structure or operation.

[0030] It should be understood that the terms "system," "device," "unit," and / or "module" used herein are a method of distinguishing different components, elements, parts, sections, or assemblies at different levels. However, these words may be replaced by other expressions that achieve the same purpose.

[0031] As used in the disclosure and appended claims, terms such as “one,” “one,” or “the above” include plural forms unless explicitly indicated in the content. Generally, the terms “include” and “contain” merely emphasize that the specified procedures and elements are included, and such procedures and elements do not form an exclusive listing, and the method or apparatus may include other procedures or elements.

[0032] The flowcharts used in this disclosure are used to describe operations that a system implements based on some embodiments of this disclosure. It should be understood that subsequent operations do not need to be executed in a strict order. Conversely, each procedure may proceed in reverse order or simultaneously. At the same time, other operations may be added to these processes, and one or more operations may be removed from these processes.

[0033] FIG. 1 is a schematic diagram illustrating an exemplary system for setting up a bone conduction hearing aid according to some embodiments of the present disclosure. As shown in FIG. 1, the system (100) for setting up a bone conduction hearing aid may include a bone conduction hearing aid (110), a processing unit (120), a storage (130), one or more terminals (140), and a network (150). In some embodiments, the bone conduction hearing aid (110), the processing unit (120), the storage (130), and / or the terminals (140) may be connected to 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 of the system (100) for setting up the bone conduction hearing aid may vary. As merely an example, as shown in FIG. 1, the bone conduction hearing aid (110) may be connected to the processing unit (120) via the network (150). As another example, the bone conduction hearing aid (110) may be connected directly to the processing unit (120). As another example, as shown in FIG. 1, the storage (130) may be connected to the processing unit (120) via the network (150) or directly to the processing unit (120). As another example, as shown in FIG. 1, the terminals (140) may be connected to the processing unit (120) via the network (150) or directly to the processing unit (120).

[0034] The bone conduction hearing aid (110) may be configured to acquire sound information (e.g., ambient sounds, the wearer's voice, audio files obtained from other devices, etc.), process the acquired sound information and convert it into a vibration signal, and transmit the vibration signal to the wearer's auditory center through the wearer's bones, so that the wearer can hear the sound information transmitted as the vibration signal. Specifically, the bone conduction hearing aid may be a bone conduction hearing aid or a bone conduction hearing aid headphone. In this disclosure, the bone conduction hearing aid may be described primarily as an example.

[0035] In some embodiments, the bone conduction hearing aid (110) (e.g., the bone conduction hearing aid) may include a sound pickup member, a speaker member, etc. The sound pickup member may be configured to pick up sound information (also referred to as a "first vibration signal"; e.g., ambient sound, the wearer's voice), process the picked-up first vibration signal, and convert it into a vibration signal having the sound information. The speaker member may convert the vibration signal having the sound information obtained by the sound pickup member into a second vibration signal having the sound information, and transmit the second vibration signal having the sound information to the wearer's auditory center. Detailed descriptions of the bone conduction hearing aid (110) can be found in other descriptions in this disclosure (e.g., FIG. 2 and its detailed descriptions).

[0036] In some embodiments, the settings of the bone conduction hearing aid may differ for different wearers of the bone conduction hearing aid because the wearers have different hearing levels (e.g., levels of hearing loss). As described in this disclosure, the settings of the bone conduction hearing aid may refer to parameter values ​​(also referred to as "parameters") or their determination processes related to the intensity of the sound signal output by the bone conduction hearing aid, and thus the bone conduction hearing aid may output the sound signal based on said parameter values. The parameter values ​​related to the intensity of the signal output by the bone conduction hearing aid may include gain values ​​(dB), analog output values ​​(dB), etc. In some embodiments, the gain value may be a value to which the hearing aid amplifies the intensity of the sound signal, and the analog output value may be an output signal intensity value simulated by the hearing aid based on input sound signal parameters (e.g., sound signal intensity values). For example, the analog output value may be equal to the result of adding the gain value (unit: dB) to the sound signal input value (e.g., intensity value, unit: dB). The system (100) for setting the bone conduction hearing aid may determine the setting of the bone conduction hearing aid corresponding to the wearer's hearing level based on the wearer's hearing level. By the setting, the bone conduction hearing aid (110) can process and output the acquired sound information (e.g., ambient sound, the wearer's voice, audio files acquired from other devices, etc.), and allow the wearer to hear the sound.

[0037] The processing device (120) may process data and / or information obtained from the bone conduction hearing aid (110), the storage (130), or the terminals (140). For example, the processing device (120) may obtain hearing loss data of the wearer of the bone conduction hearing aid (110). As another example, the processing device (120) may determine the reference output parameter of the bone conduction hearing aid (110) at each sound level in each frequency band based on the hearing loss data. As another example, the processing device (120) may obtain an adjustment value of the reference output parameter. As another example, the processing device (120) may set the bone conduction hearing aid (110) based on the adjustment value of the reference output parameter at each sound level in each frequency band.

[0038] In some embodiments, the processing unit (120) may be a single server or a group of servers. The group of servers may be centralized or distributed. In some embodiments, the processing unit (120) may be local or remote. For example, the processing unit (120) may access information or data stored in the bone conduction hearing aid (110), the terminals (140), or the storage (130) via the network (150). As another example, the processing unit (120) may be directly connected to the bone conduction hearing aid (110), the terminals (140), or the storage (130) to access the stored information or data. In some embodiments, the processing unit (120) may be implemented on a cloud platform. By example only, the cloud platform may include a private cloud, a public cloud, a mixed cloud, a community cloud, a distributed cloud, an internal cloud, a multilayer cloud, etc., or any combination thereof. In some embodiments, the processing unit (120) may be performed in a computing unit. In some embodiments, the processing unit (120) or a part of the processing unit (120) may be integrated into the bone conduction hearing aid (110). In some embodiments, the processing unit (120) or a part of the processing unit (120) may be integrated into the terminals (140).

[0039] The storage (130) may store data, instructions, or any other information. In some embodiments, the storage (130) may store data obtained from the terminals (140) or the processing unit (120). In some embodiments, the storage (130) may store data or instructions used to perform the processing unit (120) or to perform the exemplary methods described herein. In some embodiments, the storage (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 storage (130) may be implemented on a cloud platform. By way of example, the cloud platform may include a private cloud, a public cloud, a mixed cloud, a community cloud, a distributed cloud, an internal cloud, a multilayer cloud, etc., or any combination thereof. In some embodiments, the storage (130) may be connected to the network (150) which communicates with one or more other components of the system (100) for setting up the bone conduction hearing aid (e.g., the processing unit (120), the terminal (140), etc.). The system (100) for placing one or more components of the bone conduction hearing aid may access the data or commands stored in the storage (130) through the network (150). In some embodiments, the storage (130) may be directly connected to or communicate with one or more other components of the bone conduction hearing aid setting system (100) (e.g., the processing unit (120), the terminal (140), etc.). In some embodiments, the storage (130) may be part of the processing unit (120).

[0040] The terminals (140) may include a mobile device (141), a tablet (142), a laptop computer (143), a smart watch (144), etc., or any combination thereof. In some embodiments, the mobile device (141) may include a smart home device (e.g., a smart appliance control device, a smart surveillance device, a smart TV, and a smart camera), a wearable device (e.g., glasses, a helmet, accessories, clothes, etc.), a mobile device (e.g., a mobile phone, a laptop computer, etc.), a virtual reality (VR) device (e.g., a VR headset, VR glasses, VR goggles), etc., or any combination thereof. In some embodiments, the bone conduction hearing aid (110) may be integrated into the terminals (140), for example, glasses, accessories, etc.

[0041] In some embodiments, a user (e.g., a wearer of the bone conduction hearing aid (110), a system operator, a doctor, etc.) may interact with the system (100) to configure the bone conduction hearing aid through the terminals (140). For example, the user may transmit a configuration request through a user interaction interface on the terminal (140); and the processing unit (120) may obtain the wearer's hearing loss data after receiving the configuration request. For example, the processing unit (120) may transmit a request to obtain hearing loss data to the terminal (140) through the user interaction interface, and the user may upload the wearer's hearing loss data through the user interaction interface after receiving the request. The processing unit (120) may configure the bone conduction hearing aid (110) based on the hearing loss data.

[0042] The network (150) may include any suitable network, and the network may facilitate the exchange of information or data of the system (100) for setting the bone conduction hearing aid. In some embodiments, one or more components of the system (100) for setting the bone conduction hearing aid (e.g., the bone conduction hearing aid (110), the terminals (140), the processing unit (120), the storage (130), etc.) may exchange information or data with one or more other components of the system (100) for setting the bone conduction hearing aid. For example, the processing unit (120) may obtain the wearer's hearing loss data (e.g., hearing level) from the bone conduction hearing aid (110) through the network (150). As another example, the processing unit (120) may obtain user commands from the terminals (140) through the network (150). The network (150) may be 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 wireless communication network (e.g., a Long Term Evolution (LTE) network), a frame delay network, a virtual private network ("VPN"), a satellite network, a telephone network, a router, a hub, a switch, a server computer, or any combination thereof and / or may include. In some embodiments, the network (150) may include one or more network access points.For example, the network (150) may include wired or wireless network access points, for example, base stations or internet exchange points, and the system (100) for setting one or more components of the bone conduction hearing aid through these may be connected to the network (150) to exchange the data or the information.

[0043] This disclosure is for illustrative purposes only and does not limit the scope of the disclosure. Many alternatives, modifications, and variations are readily available to those skilled in the art. The features, structures, methods, and characteristics of the exemplary embodiments described herein may be combined in various ways to obtain additional or alternative exemplary embodiments. For example, the storage (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 mixed cloud. However, such various variations and modifications do not depart from the scope of the disclosure.

[0044] FIG. 2 is a schematic diagram illustrating a bone conduction hearing aid according to some embodiments of the present disclosure. As shown in FIG. 2, the bone conduction hearing aid (200) may include a speaker member (210), a sound pickup member (220), and a support member (230).

[0045] The speaker member (210) can convert a signal containing sound information into a vibration signal. In some embodiments, the sound information may include video and audio files, or data or files of a specific data format that can be converted into sound through a specific method. 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 a single signal source or multiple signal sources. The multiple signal sources may be related or unrelated. In some embodiments, the bone conduction hearing aid (200) may obtain the signal containing sound information in a different way, and the signal may be obtained in real-time or delayed by a wired or wireless method. For example, the bone conduction hearing aid (200) may receive an electrical signal containing sound information via a wired or wireless method. As another example, the bone conduction hearing aid (10) may include a member having a sound collection function (e.g., the sound pickup member (220)), said member picks up ambient sound, converts the mechanical vibration of said sound into an electrical signal, and after said electrical signal is processed by an amplifier, obtains an electrical signal that meets specific requirements.

[0046] This may be an energy conversion process in which the speaker member (210) converts a signal containing sound information into a vibration signal. The conversion process may include the coexistence and conversion of different types of energy. The speaker member (210) may include one or more conversion devices. For example, sound may be generated by directly converting the electrical signal into the mechanical vibration through the conversion device. As another example, the sound information may be contained in an optical signal, and the conversion device may perform a process of converting the optical signal into the vibration signal. Other types of energy that may coexist and be converted during the operation of the conversion device may include thermal energy, magnetic field energy, etc. In some embodiments, the loudspeaker assembly (210) may perform the conversion from the sound information signal to the vibration signal through the cooperation of a magnetic circuit member (211) and a vibration member (213) (the magnetic circuit member (211) and the vibration member (213) may also be referred to as conversion devices). The magnetic circuit member (211) may be configured to provide a magnetic field, and the vibrating member (213) may vibrate mechanically by an ampere force in the magnetic field. For example, the magnetic circuit member (211) may include a magnet. The vibrating member (213) may include a magnetic vibrator and a diaphragm. The magnetic vibrator (e.g., a voice coil) may move back and forth under the action of the magnetic field ampere force and, when operated, drive the diaphragm to vibrate. In the above process, the sound information may correspond to the vibration of the magnetic vibrator, and the vibration frequency and amplitude of the magnetic vibrator may be determined according to the frequency and intensity of the sound information. In some embodiments, one of the magnetic circuit member and the magnetic vibrator may be an electromagnet, and by controlling the number of coils or the current intensity in the electromagnet, the strength of the magnetic field may be controlled, and thus the vibration amplitude of the magnetic vibrator is controlled.The vibration frequency of the magnetic vibrator can be controlled by controlling the frequency of change of the current direction of the coil in the electromagnet. In this process, the sound information can be amplified. For example, the intensity of the sound information can be amplified by increasing the vibration amplitude of the magnetic vibrator.

[0047] The energy conversion method of the above-mentioned vibrating member may specifically include a moving coil type, an electrostatic type, a piezoelectric type, a moving iron type, a moving type, an electromagnetic type, etc. The frequency response range and sound quality of the above-mentioned bone conduction hearing aid (200) may be influenced by the above-mentioned vibrating member. For example, in a moving coil converter, the above-mentioned vibrating member may include a wound cylindrical voice coil and a vibrator (e.g., a diaphragm or a vibrating membrane). The cylindrical voice coil, driven by a signal current, may drive the vibrator to vibrate and generate sound in the magnetic field. The stretching of the vibrator material, deformation of the wrinkles, size, shape, and fixing method, and the magnetic density of the above-mentioned magnetic field, etc., may all have a significant influence on the sound quality of the above-mentioned bone conduction hearing aid. The vibrator of the above-mentioned vibrating member may have a mirror-symmetric structure, a centrosymmetric structure, or an asymmetric structure. Intermittent hole structures may be arranged in the above vibrator, thereby causing the vibrator to generate a relatively large displacement, enabling the bone conduction hearing aid (200) to achieve high sensitivity and increase the output of vibration and sound. The vibrator may be a torus structure, and two or more supports concentrated toward the center may be installed on the torus.

[0048] The sound pickup member (220) can primarily pick up the user's voice, ambient sounds in the user's environment, etc. For a hearing impaired person, the sound pickup effect of the sound pickup member (220) can affect the clarity, stability, etc. of the sound received by the hearing impaired person through the bone conduction hearing aid. In some embodiments, the sound pickup member (220) may include a microphone. In some embodiments, the sound pickup member (220) may convert an external sound signal into an electrical signal. In some embodiments, the sound pickup member (220) may include a vibrating membrane, a coil, and a magnet. The vibrating membrane may be connected to the coil, and the coil may be installed in a magnetic field generated by a magnetic field magnet. External sound waves (e.g., sound signals or vibration signals) may cause the vibrating membrane to vibrate. The vibrating membrane may drive the coil and move together. The operation of the coil in the magnetic field generated by the magnet can generate an electric current, and thus the sound signal can be converted into an electrical signal, thereby completing the pickup of the external sound.

[0049] The support member (230) may support other members of the bone conduction hearing aid (200) (e.g., the magnetic circuit member, the vibration member or storage member, the power supply member, the communication member (not shown), and the sound pickup member (220)). The support member (230) may include one or more housings and one or more connectors. The one or more housings may form one or more receiving cavities (232) for accommodating the storage member, controller, the sound pickup member (220), the communication member, the battery member, etc. The one or more connectors may connect the one or more housings to other members of the bone conduction hearing aid (200) (e.g., the magnetic circuit member, the vibration member or the storage member, the power supply member, the communication member (not shown), and the sound pickup member (220)).

[0050] The wired connection associated with the bone conduction hearing aid (200) may include, for example, a coaxial cable, a communication cable, a flexible cable, a spiral cable, a non-metallic sheathed cable, a metal sheathed cable, a multi-core cable, a twisted pair cable, a ribbon cable, a shielded cable, a telecommunication cable, a twin-core cable, a parallel twin-core conductor, a twisted pair wire, etc., or a combination thereof, a metal wire, an optical cable, or a mixed cable of a metal cable and an optical cable. The examples described above are merely for convenience of explanation, and the medium of the wired connection may be of other types, for example, an electrical signal or an optical signal, or other transmission carrier.

[0051] The wireless connection associated with the bone conduction hearing aid (200) may include wireless communication, free-space optical communication, acoustic communication, electromagnetic induction, etc. The wireless communication may include IEEE 802.11 series standards, IEEE 802.15 series standards (e.g., Bluetooth technology and Zigbee technology, etc.), first generation mobile communication technology (1G), second generation mobile communication technology (2G) (e.g., FDMA, TDMA, SDMA, CDMA, SSMA, etc.), general packet radio service technology, third generation mobile communication technology (3G) (e.g., CDMA2000, WCDMA, TD-SCDMA, WIMAX, etc.), fourth generation mobile communication technology (4G) (e.g., TD-LTE, FDD-LTE, etc.), satellite communication (e.g., GPS technology, etc.), near-field communication (NFC), and other technologies used in the ISM frequency band (e.g., 2.4 GHz, etc.). The above free-space optical communication may include visible light, infrared signals, etc. The above acoustic communication may include sound waves, ultrasonic signals, etc. The above electromagnetic induction may include short-range communication technology, etc. The examples described above are merely for convenience of explanation, and the medium of the wireless connection may be of other types, for example, Z-wave technology, other paid civilian radio frequency bands and military radio frequency bands, etc. For example, as in some applications of current technology, the bone conduction hearing aid (200) may obtain a signal containing the sound information from other devices via Bluetooth technology.

[0052] The description of the structure of the bone conduction hearing aid (200) above is merely a specific example and should not be considered the only implementation method. Of course, for those skilled in the art, after understanding the basic principles of the bone conduction hearing aid (200), various modifications and changes in form and detail may be made to specific implementation methods and procedures for implementing the bone conduction hearing aid (200) without deviating from these basic principles, but such modifications and changes are still within the scope of the description above. For example, the bone conduction hearing aid (200) may include one or more processors capable of performing one or more sound signal processing algorithms. The one or more sound signal processing algorithms may modify or augment the sound signal. With respect to the above sound signal, for example, noise reduction, acoustic feedback suppression, significant dynamic range compression, automatic gain control, active environment awareness, active noise prevention, direction processing, tinnitus processing, multi-channel significant dynamic range compression, active howling suppression, volume control, etc., or any combination thereof may be performed. Such modifications and variations are still within the scope of the claims of this disclosure. As another example, the bone conduction hearing aid may include one or more sensors, for example, a temperature sensor, a humidity sensor, a velocity sensor, a displacement sensor, etc. The one or more sensors may collect user information or environmental information. As another example, the storage member may not be essential and may be removed from the bone conduction hearing aid.

[0053] In some embodiments, the system for setting the bone conduction hearing aid may set the bone conduction hearing aid according to a preset formula or preset algorithm based on the wearer's hearing loss data. For example, in the system for setting the bone conduction hearing aid, after the wearer's hearing loss data is input into the system for setting the bone conduction hearing aid, the system for setting the bone conduction hearing aid may automatically output relevant parameter values ​​of the bone conduction hearing aid according to the preset algorithm. If the bone conduction hearing aid is placed directly using only the preset algorithm, the placed bone conduction hearing aid (200) may generate severe vibrations in some cases (e.g., when the wearer speaks or when the surrounding noise is loud), causing discomfort to the wearer.

[0054] The present disclosure provides a system for setting up a bone conduction hearing aid. FIG. 3 is a block diagram illustrating a system for setting up a bone conduction hearing aid according to some embodiments of the present disclosure. As shown in FIG. 3, the system (300) for setting up the bone conduction hearing aid may include an acquisition module (310), a reference output parameter determination module (320), an adjustment value determination module (330), and a setting module (340). The modules may be connected via a wired method, a wireless method, or a combination thereof. Any module may be local, remote, or a combination thereof. The modules may be one-to-one correspondence or one-to-many correspondence.

[0055] In some embodiments, the acquisition module (310) may be configured to acquire hearing loss data of the wearer.

[0056] In some embodiments, the reference output parameter determination module (320) may be configured to determine the reference output parameter of the bone conduction hearing aid at each sound level in each frequency band based on each of the hearing loss data.

[0057] In some embodiments, the adjustment value determination module (330) may be configured to obtain an adjustment value of the reference output parameter at each sound level in each frequency band. In some embodiments, the adjustment values ​​may be the same at different sound levels in the same frequency band. In some embodiments, in a frequency band within the range of 0 Hz to 625 Hz, the adjustment value may be within the range of 1 dB to 12 dB. In some embodiments, in a frequency band within the range of 0 Hz to 125 Hz, the adjustment value may be within the range of 5 dB to 12 dB; in a frequency band within the range of 125 Hz to 375 Hz, the adjustment value may be within the range of 3 dB to 9 dB; or in a frequency band within the range of 375 Hz to 625 Hz, the adjustment value may be within the range of 1 dB to 6 dB. In some embodiments, in a frequency band within the range of 0 Hz to 125 Hz, the adjustment value may be within the range of 5 dB to 7 dB; In a frequency band within the range of 125Hz to 375Hz, the adjustment value may be within the range of 3dB to 5dB; or in a frequency band within the range of 375Hz to 625Hz, the adjustment value may be within the range of 1dB to 3dB. In some embodiments, in a frequency band within the range of 0Hz to 125Hz, the adjustment value may be within the range of 10dB to 12dB; in a frequency band within the range of 125Hz to 375Hz, the adjustment value may be within the range of 7dB to 9dB; or in a frequency band within the range of 375Hz to 625Hz, the adjustment value may be within the range of 4dB to 6dB. In some embodiments, the adjustment values ​​may differ at different sound levels within the same frequency band.In some embodiments, the adjustment value determination module (330) determines a first threshold corresponding to each sound level in each frequency band and also related to the degree of vibration detected by the wearer at each sound level in each frequency band; determines a second threshold corresponding to each sound level in each frequency band and also related to the voice identification rate of the wearer at each sound level in each frequency band; and determines 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) obtains a comparison value by subtracting the first threshold from the reference output parameter with respect to the reference output parameter at a mother sound level among each sound level in the mother frequency band of each frequency band; obtains a first comparison result by comparing the comparison value with the second threshold; and determines the adjustment value corresponding to the reference output parameter based on the first comparison result. In some embodiments, the adjustment value determination module (330) may set the adjustment value to 0dB when the comparison value is 0 or less; set the adjustment value to the comparison value when the comparison value is greater than 0 and is less than or equal to the second threshold; and set the adjustment value to the second threshold value when the comparison value is greater than the second threshold.

[0058] In some embodiments, in a frequency band within the range of 0 Hz to 125 Hz, the first threshold may be within the range of 48 dB to 52 dB. In some embodiments, in a frequency band within the range of 125 Hz to 375 Hz, the first threshold may be within the range of 49 dB to 54 dB. In some embodiments, in a frequency band within the range of 375 Hz to 625 Hz, the first threshold may be within the range of 50 dB to 55 dB. In some embodiments, in a frequency band within the range of 0 Hz to 125 Hz, the second threshold may be within the range of 5 dB to 10 dB. In some embodiments, in a frequency band within the range of 125 Hz to 375 Hz, the second threshold may be within the range of 3 dB to 7 dB. In some embodiments, in a frequency band within the range of 375 Hz to 625 Hz, the second threshold may be within the range of 1 dB to 4 dB.

[0059] In some embodiments, when the bone conduction hearing aid utilizes a multi-channel large dynamic range compression system, the adjustment value determination module (330) may determine a second comparison result by comparing the reference output parameter with the first threshold. The first threshold may be related to the degree of vibration perceived by the wearer at each sound level in each frequency band. The adjustment value determination module (330) may determine the adjustment value corresponding to the reference output parameter based on the second comparison result. In some embodiments, the adjustment value may include a gain reduction value when at least one of the sound levels is greater than the sound level threshold. The adjustment value determination module (330) may set the gain reduction value to 0 dB when the reference output parameter is less than or equal to the first threshold, and set the gain reduction value to the difference between the first threshold and the reference output parameter when the reference output parameter is greater than the first threshold. In some embodiments, the control value may include a reduction value of the output limit of a multi-channel large dynamic range compression system. The control value determination module (330) may set the reduction value of the output limit to 0 dB when the parameter is below the first threshold; and when the reference output parameter is greater than the first threshold, the reduction value of the output limit may be set to a value greater than 0 dB.

[0060] In some embodiments, the setting module (340) may set the bone conduction hearing aid based on the reference output parameter and the adjustment value at each sound level in each frequency band. In some embodiments, the setting module (340) may further reduce the reference output parameter based on the adjustment value in a frequency band within the range of 0 Hz to 625 Hz. In some embodiments, the setting module (340) may set the bone conduction hearing aid based on the reference output parameter and the adjustment value at each sound level in each frequency band using a multi-channel high dynamic range compression system.

[0061] It should be noted that the above description regarding the processing module is merely a specific example and should not be considered the only embodiment. Each module or unit is not essential, and each module or unit may be executed by one or more components, and the function of each module or unit is not limited thereto. Each module or unit may be selected, added, or removed according to specific implementation scenarios or as needed. Of course, those skilled in the art, having understood the basic principles of capacity adjustment flow, may make various modifications in form and detail to the specific embodiments and procedures for implementing the processing module without departing from these basic principles, may make some simple inferences or substitutions, and may make certain adjustments, combinations, or disassemblies to the order of each module or unit without any creative effort, and such modifications and changes are still within the scope of this disclosure.

[0062] FIG. 4 is a flowchart illustrating an exemplary process for setting up a bone conduction hearing aid according to some embodiments of the present disclosure. As shown in FIG. 4, the process 400 for setting up the bone conduction hearing aid may include the following operations.

[0063] In 410, the wearer's hearing loss data can be obtained. Specifically, 410 can be performed by the acquisition module (310).

[0064] In some embodiments, the hearing loss data of the wearer is understood as data related to the wearer's hearing loss. The hearing loss data may include the hearing level (also referred to as "hearing threshold" or "hearing loss level") at each sound level in each frequency band of the wearer. In this disclosure, the unit of the hearing level may be dBHL. The higher the value of the hearing level, the more severe the wearer's hearing loss. In some embodiments, the hearing loss data may include data related to the wearer's history of hearing aids. For example, the data related to the wearer's history of hearing aids may include configuration data of bone conduction hearing aids previously used by the wearer.

[0065] In some embodiments, the hearing level may be within the range of 0 dBHL to 80 dBHL. For example, a hearing level within the range of 0 dBHL to 25 dBHL may indicate normal hearing; a hearing level within the range of 26 dBHL to 40 dBHL may indicate mild hearing loss; a hearing level within the range of 41 dBHL to 60 dBHL may indicate moderate hearing loss, expressed as difficulty hearing normal sounds; a hearing level within the range of 61 dBHL to 80 dBHL may indicate severe hearing loss, expressed as difficulty hearing loud sounds; and a hearing level within the range greater than 80 dBHL may indicate very severe hearing loss, expressed as difficulty hearing noise.

[0066] In some embodiments, the hearing levels of the wearer of the bone conduction hearing aid may be equal to sound levels in different frequency bands (detailed descriptions regarding the sound levels can be found in 420). For example, at a sound level of 20 dBC, the wearer's hearing level in different frequency bands may be equal to any value within the range of 41 dBHL to 60 dBHL; at a sound level of 40 dBC, the wearer's hearing level in different frequency bands may be equal to any value within the range of 26 dBHL to 40 dBHL; and at a sound level of 60 dBC, the wearer's hearing level in different frequency bands may be equal to any value within the range of 0 dBHL to 25 dBHL.

[0067] In some embodiments, the hearing level of the wearer of the bone conduction hearing aid may differ at the same sound level in different frequency bands. For example, at a sound level of 20 dBC, the wearer's hearing level in the high frequency band (e.g., 8000 Hz to 12000 Hz) may be equal to any value within the range of 41 dBHL to 60 dBHL; and in the low frequency band, the wearer's hearing level may be equal to any value within the range of 26 dBHL to 40 dBHL.

[0068] In some embodiments, the hearing level of the wearer of the bone conduction hearing aid may be the same at different sound levels within the same frequency band. For example, in a frequency band within the range of 250 Hz to 500 Hz, the wearer's hearing level at different sound levels may be equal to any value within the range of 0 dBHL to 25 dBHL; in a frequency band within the range of 500 Hz to 1000 Hz, the wearer's hearing level at different frequency bands may be equal to any value within the range of 26 dBHL to 40 dBHL; and in a frequency band within the range of 1000 Hz to 2000 Hz, the wearer's hearing level at different frequency bands may be equal to any value within the range of 41 dBHL to 60 dBHL.

[0069] In some embodiments, the hearing level of the wearer of the bone conduction hearing aid may differ at different sound levels within the same frequency band. For example, in a frequency band within the range of 250 Hz to 500 Hz, at a sound level of 20 dBC, the wearer's hearing level may be equal to any value within the range of 41 dBHL to 60 dBHL; at a sound level of 40 dBC, the hearing level may be equal to any value within the range of 26 dBHL to 40 dBHL; and at a sound level of 60 dBC, the hearing level may be equal to any value within the range of 0 dBHL to 25 dBHL.

[0070] In some embodiments, hearing loss data of the wearer can be obtained by performing a real-time hearing test on the wearer. For example, a hearing aid technician can obtain hearing loss data of the wearer by performing a hearing test on the wearer using hearing test equipment (e.g., playing sound signals at each sound level in each frequency band). The hearing loss data collected by the hearing test equipment can be uploaded directly to a processing device (e.g., the processing device (120)) or the storage device via a network (e.g., the network (150)), and the processing device can obtain the hearing loss data from the storage device. In other embodiments, the wearer may upload the wearer's hearing loss data through a terminal (e.g., the terminal (140)), and the system for setting the bone conduction hearing aid (e.g., the system for setting the bone conduction hearing aid (100)), or the device (e.g., the processing device (120)) may receive the hearing loss data uploaded by the wearer via a wired or wireless method. In some embodiments, the system for setting the bone conduction hearing aid or the device may retrieve the wearer's hearing loss data from a related storage (e.g., the storage (130)).

[0071] In 420, the reference output parameters of the bone conduction hearing aid at each sound level in each frequency band can be determined based on the hearing loss data. Specifically, 420 can be performed through the reference output parameter determination module (320).

[0072] In some embodiments, the reference output parameter may be a reference analog output value of the bone conduction hearing aid at each sound level in each frequency band (e.g., an intensity value of the signal output by the bone conduction hearing aid, expressed in dB). In some embodiments, the reference output parameter may be a reference gain value of the bone conduction hearing aid at each sound level in each frequency band (e.g., an intensity value of the sound signal amplified by the bone conduction hearing aid, expressed in dB). It should be noted that if the sound signal input by the bone conduction hearing aid corresponds to a specific sound level in a specific frequency band under the reference output parameter (e.g., the reference gain value), the intensity value of the sound signal input by the bone conduction hearing aid may be equal to the reference analog output value of the specific sound level in the specific frequency band. In some embodiments, the reference output parameter may be related to a hearing loss level, sound level, frequency, etc. In some embodiments, the reference analog output value of the bone conduction hearing aid may also be related to the reference gain value of the bone conduction hearing aid. For example, the analog output value may be determined by amplifying the signal intensity corresponding to the sound level based on the gain value. In some embodiments, the reference output parameters may differ for different wearers due to different hearing loss data (e.g., the degree of hearing loss at each sound level). In some embodiments, the sound level and frequency of the sound signal may affect the reference output parameters of the bone conduction hearing aid, and different sound levels or different frequency bands may correspond to different reference output parameters.This means that different frequency bands can correspond to different reference output parameters under the same hearing loss level and the same sound level; different sound levels can correspond to different reference output parameters under the same hearing loss level and the same frequency band; and different hearing loss levels can correspond to different reference output parameters of the same sound level in the same frequency band.

[0073] In the present disclosure, the sound level indicates the intensity of the sound signal expressed in decibels. In the present disclosure, the sound level may be measured primarily through C-frequency weighted measurements, for example, the unit of the sound level in the present disclosure is dBC. The frequency band is the frequency range of the sound signal in the present disclosure. In some embodiments, different frequency bands may be formed by dividing the frequency of the sound signal into a plurality of consecutive ranges.

[0074] In some embodiments, determining the reference output parameter of the bone conduction hearing aid at each sound level in each frequency band refers to determining the parameter of the bone conduction hearing aid for a preset sound level or preset frequency and the hearing loss level of the bone conduction hearing aid corresponding to the preset sound level and the preset frequency. In some embodiments, determining the reference output parameter of the bone conduction hearing aid at each sound level in each frequency band refers to determining the output parameter of the bone conduction hearing aid for a preset sound level range or preset frequency band and the hearing loss level of the wearer of the bone conduction hearing aid corresponding to the preset sound level range and the preset frequency band. Based on the above-determined reference output parameters, the bone conduction hearing aid may amplify a sound signal input to the bone conduction hearing aid (e.g., the sound input signal), convert the sound signal into a vibration signal, and transmit the vibration signal to the wearer of the bone conduction hearing aid so that the wearer may hear the sound. In some embodiments, the preset sound level, the preset frequency, the preset sound level range, or the preset frequency band may be a default setting of the system (e.g., the system (100) for setting the bone conduction hearing aid) or may be set by the user. In some embodiments, the preset sound level may include 20dBC, 30dBC, 40dBC, 50dBC, 60dBC, 70dBC, 80dBC, etc., or any combination thereof. In some embodiments, the preset frequency may include 250Hz, 500Hz, 1000Hz, 2000Hz, 3000Hz, 4000Hz, 8000Hz, 10000Hz, etc., or any combination thereof.In some embodiments, the preset sound level range may include 10dBC to 20dBC (may not include 20dBC), 20dBC to 30dBC (may not include 30dBC), 30dBC to 40dBC (may not include 40dBC), 40dBC to 50dBC (may not include 50dBC), 50dBC to 60dBC (may not include 60dBC), 60dBC to 70dBC (may not include 70dBC), 70dBC to 80dBC (may not include 80dBC), etc., or any combination thereof. In some embodiments, the preset frequency band may include 20Hz to 250Hz (may not include 250Hz), 250Hz to 500Hz (may not include 500Hz), 500Hz to 1000Hz (may not include 1000Hz), 1000Hz to 2000Hz (may not include 2000Hz), 2000Hz to 3000Hz (may not include 3000Hz), 3000Hz to 4000Hz (may not include 4000Hz), 4000Hz to 6000Hz (may not include 6000Hz), 6000Hz to 10000Hz (may not include 10000Hz), etc., or any combination thereof. In some embodiments, the preset frequency band may include 0Hz to 125Hz (may not include 125Hz), 125Hz to 375Hz (may not include 375Hz), 375Hz to 625Hz (may not include 625Hz), 625Hz to 875Hz (may not include 875Hz), 875Hz to 1375Hz (may not include 1375Hz), 1375Hz to 1875Hz (may not include 1875Hz), 1875Hz to 2625Hz (may not include 2625Hz), 2625Hz to 4875Hz (may not include 4875Hz), etc., or any combination thereof.In some embodiments, the preset sound level, the preset frequency, the preset sound level range, or the preset frequency band may be adjusted by the system (e.g., the system (100) for setting the bone conduction hearing aid) or by the user. For example, the preset sound level, the preset frequency, the preset sound level range, or the preset frequency band may be adjusted based on the hearing level of the wearer of the bone conduction hearing aid. For example, if the sound level is 80 dBC and the wearer's hearing level is 10 dBHL (indicating that the wearer has normal hearing at this sound level), the maximum value of the preset sound level may not exceed 80 dBC.

[0075] In some embodiments, the reference output parameter may be a reference gain value of the bone conduction hearing aid. The processing device (120) may determine the reference gain value of the bone conduction hearing aid at each sound level in each frequency band based on the hearing level of the hearing loss data at each sound level in each frequency band and the value at each sound level in each frequency band. For example, the reference gain value of the bone conduction hearing aid at a sound level of 20 dBC in a frequency band within the range of 375 Hz to 625 Hz may be determined based on the sound level of 20 dBC, the frequency band within the range of 375 Hz to 625 Hz, and the hearing level of the wearer of the bone conduction hearing aid at a sound level of 20 dBC in the frequency band within the range of 375 Hz to 625 Hz. In some embodiments, the reference output parameter may be a reference analog output signal strength value of the bone conduction hearing aid (e.g., the reference analog output value). The processing device (120) may determine the reference analog output signal strength value of the bone conduction hearing aid at each sound level in each frequency band (e.g., the reference analog output value) based on the hearing level of the hearing loss data at each sound level in each frequency band and the value at each sound level in each frequency band. For example, the reference analog output signal strength value of the bone conduction hearing aid at a sound level of 30 dBC in a frequency band within the range of 125 Hz to 375 Hz (e.g., the reference analog output value) may be determined based on a sound level of 30 dBC, a frequency band within the range of 125 Hz to 375 Hz, and the hearing level of the wearer of the bone conduction hearing aid at a sound level of 30 dBC in a frequency band within the range of 125 Hz to 375 Hz.

[0076] In some embodiments, the processing device (120) (the reference output parameter determination module (320)) may first determine the reference gain value of the bone conduction hearing aid at each sound level in each frequency band based on the hearing loss data, and then determine the reference analog output signal strength value (e.g., the reference analog output value) of the bone conduction hearing aid at a corresponding sound level in a corresponding frequency band based on the gain value at each sound level in each frequency band.

[0077] In some embodiments, the processing unit (120) (the reference output parameter determination module (320)) may determine the reference output parameter through a preset formula. For example, the reference gain value at each sound level in each frequency band may be determined based on the wearer's hearing loss data according to the preset formula. In some embodiments, the preset formula may be the "1 / 2 gain principle" submitted by Lybarger, for example, to achieve comfortable hearing for sensorineural hearing loss, and the required gain value should be half the increase in the hearing threshold. This means that the reference gain value of the bone conduction hearing aid is generally equal to half of the wearer's hearing loss.

[0078] In some embodiments, the reference output parameter in 320 may be determined through empirical data in the table below (Table 1). For example, the reference gain value for each hearing loss level (determined based on the hearing loss data) in each frequency band may be determined using the empirical data in the table below, and then the reference analog output value for the corresponding hearing loss level in the corresponding frequency band may also be further determined using the reference gain value. The table below describes the reference gain value for each hearing level in each frequency band, using a sound level of 60 dB SPL as an example. As indicated in Table 1, when the sound level is 60 dB SPL and the hearing level is 20 dBHL, the reference gain value in each frequency band is 0; when the hearing level is 40 dBHL, the reference gain value in the frequency band within the range of 125-375 Hz is 5. In some embodiments, when the sound level and the hearing level are constant, the reference gain value may first increase and then decrease as the frequency band increases. In some embodiments, when the frequency band does not change, the reference gain value may increase as the hearing level increases.

[0079] Table 1 explains the reference gain values ​​for each hearing level in each frequency band, using a sound level of 60 dB SPL as an example.

[0080]

[0081] In some embodiments, the processing device (120) may determine the reference output parameter based on a setting model. The setting model may indicate the relationship between the reference output parameter and the frequency band, the sound level, and the hearing level.

[0082] In 430, adjustment values ​​of the reference output parameters at each sound level in each frequency band can be obtained. The adjustment values ​​may be related to at least the frequency band. Specifically, 430 can be performed through the reference output adjustment value determination module (330).

[0083] The above adjustment value is a value used to adjust the above reference output parameter. In some embodiments, the above reference output parameter may be adjusted by the above adjustment value, and the adjusted reference output parameter may be used as the actual analog output parameter of the bone conduction hearing aid. The above reference output parameter may be explained by examples of the above reference analog output value and the above reference gain value. For example, the above adjustment value may be used to adjust the above reference analog output value (the above analog output signal strength value), and the adjusted above reference analog output value may be used as the actual analog output value (the above actual analog output signal strength value) of the bone conduction hearing aid. As another example, the above adjustment value may be used to adjust the above reference gain value (the strength value that amplifies the sound signal) of the bone conduction hearing aid, and the adjusted above reference gain value may be used as the actual gain value of the bone conduction hearing aid.

[0084] In some embodiments, the control value may be used to reduce the reference output parameter. For example, the control value may be a value used to attenuate the reference analog output value, for example, the control value may be subtracted from the reference output parameter. As another example, the control value may be a value used to attenuate the reference gain value, for example, the control value may be subtracted from the reference gain value. As yet another example, the control value may be a ratio value less than 1, for example, the reference output parameter may be multiplied by the control value.

[0085] The vibration of the bone conduction hearing aid may be relatively strong when the frequency of the sound signal input to the bone conduction hearing aid is low. For example, the bone conduction hearing aid may easily vibrate in a frequency band within the range of 125Hz to 625Hz. Therefore, the adjustment value (for example, the reference output parameter may be reduced using the adjustment value in the frequency band) is set to a frequency band of 0Hz to 625Hz (or a frequency band of 125Hz to 625Hz) to improve the strong vibration of the bone conduction hearing aid in the frequency band.

[0086] FIG. 8 is a diagram showing vibration thresholds at different frequencies measured by experiment when a wearer wears a bone conduction hearing aid. In FIG. 8, the vibration threshold (dBV) is a value obtained after numerical conversion of the driving voltage value (V) of the bone conduction hearing aid when the wearer receives vibration. If the driving voltage value of the bone conduction hearing aid is X(V), X(V) is converted into a vibration threshold of 20*log10(X / 1)(dBV). Just as an example, if the driving voltage value of the bone conduction hearing aid is 1 V, the vibration threshold may be 0 dBV; and if the driving voltage value of the bone conduction hearing aid is 0.5 V, the vibration threshold may be -6 dBV. Figure 8 shows that the vibration threshold of the bone conduction hearing aid may be small in frequency bands lower than 1000 Hz, which means that the bone conduction hearing aid can vibrate in frequency bands lower than 1000 Hz, particularly in frequency bands within the range of 125 Hz to 600 Hz. The bone conduction hearing aid can vibrate most easily at 125 Hz, 250 Hz, 400 Hz, and 500 Hz. Therefore, based on the data measured by the experiment, the adjustment value can be set to a frequency band within the range of 0 Hz to 625 Hz (or a frequency band within the range of 125 Hz to 625 Hz).

[0087] In some embodiments, the same frequency band or the same sound level may correspond to the same control value under different hearing levels. For example, the control value at a sound level of 20 dBC in a frequency band within the range of 0 Hz to 625 Hz under a hearing level of 26 dBHL to 40 dBHL may be the same as the control value at a sound level of 20 dBC in a frequency band within the range of 0 Hz to 625 Hz under a hearing level of 41 dBHL to 60 dBHL. As another example, the control value at a sound level of 20 dBC in a frequency band within the range of 0 Hz to 125 Hz under a hearing level of 26 dBHL to 40 dBHL may be the same as the control value at a sound level of 20 dBC in a frequency band within the range of 0 Hz to 125 Hz under a hearing level of 41 dBHL to 60 dBHL. As another example, the adjustment value at a sound level of 20 dBC in the frequency range of 125 Hz to 375 Hz under a hearing level of 26 dBHL to 40 dBHL and the adjustment value at a sound level of 20 dBC in the frequency range of 125 Hz to 375 Hz under a hearing level of 41 dBHL to 60 dBHL may be the same.

[0088] In some embodiments, the same frequency band or the same sound level may correspond to different control values ​​under different hearing levels. For example, a control value of 20 dBC at a sound level in a frequency band within the range of 0 Hz to 625 Hz under a hearing level of 26 dBHL to 40 dBHL may be different from a control value of 20 dBC at a sound level in a frequency band within the range of 0 Hz to 625 Hz under a hearing level of 41 dBHL to 60 dBHL. As another example, a control value of 20 dBC at a sound level in a frequency band within the range of 20 Hz to 125 Hz under a hearing level of 26 dBHL to 40 dBHL may be different from a control value of 20 dBC at a sound level in a frequency band within the range of 20 Hz to 125 Hz under a hearing level of 41 dBHL to 60 dBHL. As another example, the adjustment value at a sound level of 20 dBC in the frequency range of 125 Hz to 375 Hz under a hearing level of 26 dBHL to 40 dBHL and the adjustment value at a sound level of 20 dBC in the frequency range of 125 Hz to 3755 Hz under a hearing level of 41 dBHL to 60 dBHL may be different.

[0089] In some embodiments, the same frequency band or the same hearing level under different sound levels may correspond to the same control value. For example, the control value at a sound level of 20 dBC to 40 dBC in a frequency band within the range of 0 Hz to 125 Hz under a hearing level of 41 dBHL to 60 dBHL may be the same as the control value at a sound level of 40 dBC to 60 dBC in a frequency band within the range of 0 Hz to 125 Hz under a hearing level of 41 dBHL to 60 dBHL. As another example, the control value at a sound level of 20 dBC to 40 dBC in a frequency band within the range of 125 Hz to 375 Hz under a hearing level of 26 dBHL to 40 dBHL may be the same as the control value at a sound level of 20 dBC to 40 dBC in a frequency band within the range of 125 Hz to 375 Hz under a hearing level of 26 dBHL to 40 dBHL.

[0090] In some embodiments, the same frequency band or the same hearing level at different sound levels may correspond to different control values. For example, the control value for a sound level of 26 dBC to 40 dBC in a frequency band within the range of 0 Hz to 125 Hz under a hearing level of 41 dBHL to 60 dBHL may be different from the control value for a sound level of 40 dBC to 60 dBC in a frequency band within the range of 0 Hz to 125 Hz under a hearing level of 41 dBHL to 60 dBHL. As another example, the control value for a sound level of 26 dBC to 40 dBC in a frequency band within the range of 125 Hz to 375 Hz under a hearing level of 26 dBHL to 40 dBHL may be different from the control value for a sound level of 40 dBC to 60 dBC in a frequency band within the range of 125 Hz to 375 Hz under a hearing level of 26 dBHL to 40 dBHL.

[0091] In some embodiments, the same sound level or the same hearing level in different frequency bands may correspond to the same control value. For example, a control value at a sound level of 20 dBC to 40 dBC in a frequency band within the range of 0 Hz to 125 Hz (which may not include 125 Hz) under a hearing level of 20 dBHL to 40 dBHL may be the same as a control value at a sound level of 0 dBC to 40 dBC in a frequency band within the range of 125 Hz to 375 Hz under a hearing level of 20 dBHL to 40 dBHL. As another example, the control value at a sound level of 40 dBC to 60 dBC in a frequency band within the range of 125 Hz to 375 Hz (which may not include 125 Hz) under a hearing level of 40 dBHL to 60 dBHL and the control value at a sound level of 40 dBC to 60 dBC in a frequency band within the range of 375 Hz to 625 Hz under a hearing level of 26 dBHL to 40 dBHL may be the same.

[0092] In some embodiments, the same sound level or the same hearing level in different frequency bands may correspond to different control values. For example, a control value for a sound level of 20 dBC to 40 dBC in a frequency band within the range of 0 Hz to 125 Hz (which may not include 125 Hz) under a hearing level of 41 dBHL to 60 dBHL may be different from a control value for a sound level of 20 dBC to 40 dBC in a frequency band within the range of 125 Hz to 375 Hz under a hearing level of 41 dBHL to 60 dBHL. As another example, the control value at a sound level of 40 dBC to 60 dBC in a frequency band within the range of 125 Hz to 375 Hz (which may not include 375 Hz) under a hearing level of 40 dBHL to 60 dBHL and the control value at a sound level of 40 dBC to 60 dBC in a frequency band within the range of 375 Hz to 625 Hz under a hearing level of 26 dBHL to 40 dBHL may be different.

[0093] In some embodiments, the adjustment value may be associated with the frequency band, and the adjustment value may differ in different frequency bands. In some embodiments, different frequency bands may correspond to different adjustment values, and in the same frequency band, the frequency may correspond to the same adjustment value. In some embodiments, different frequencies may correspond to different adjustment values. In some embodiments, in a frequency band within the range of 0 Hz to 625 Hz, the adjustment value may be within the range of 1 dB to 12 dB. By setting the adjustment value to a value within the frequency range and configuring the bone conduction hearing aid, the problem of the wearer detecting strong vibrations in some cases when wearing the bone conduction hearing aid can be improved, and the impact on speech comprehension can be reduced. In some embodiments, the adjustment value may decrease as the frequency increases. For example, the adjustment value corresponding to a frequency of 125 Hz may be 5 dB; the adjustment value corresponding to a frequency of 250 Hz may be 3 dB; The adjustment value corresponding to a frequency of 500 Hz may be 1 dB. As another example, the adjustment value corresponding to a frequency of 125 Hz may be 10 dB; the adjustment value corresponding to a frequency of 250 Hz may be 7 dB; and the adjustment value corresponding to a frequency of 500 Hz may be 4 dB. In some embodiments, in a frequency band within the range of 625 Hz to 8000 Hz, the adjustment value may be within the range of 0 dB to 4 dB. In some embodiments, in a frequency band within the range of 625 Hz to 8000 Hz, the adjustment value may be 0.

[0094] In some embodiments, in a frequency band within the range of 0 Hz to 125 Hz, the adjustment value may be within the range of 5 dB to 12 dB. In some embodiments, in a frequency band within the range of 125 Hz to 375 Hz, the adjustment value may be within the range of 3 dB to 9 dB. In some embodiments, in a frequency band within the range of 375 Hz to 625 Hz, the adjustment value may be within the range of 1 dB to 6 dB. Furthermore, by dividing the frequency band and setting the adjustment values ​​in some frequency bands within the frequency band, the vibration reduction effect of the bone conduction hearing aid can be improved.

[0095] In some embodiments, in a frequency band within the range of 0 Hz to 125 Hz, the adjustment value may be within the range of 5 dB to 7 dB. In a frequency band within the range of 125 Hz to 375 Hz, the adjustment value may be within the range of 3 dB to 5 dB. In some embodiments, in a frequency band within the range of 375 Hz to 625 Hz, the adjustment value may be within the range of 1 dB to 3 dB. By setting the adjustment value to a value within the frequency range and setting the bone conduction hearing aid, vibration issues when a wearer with a hearing level of 30 dBL wears the bone conduction hearing aid in the corresponding frequency band can be resolved so as to have almost no effect on speech comprehension, thereby ensuring the wearer's hearing effect.

[0096] In some embodiments, in a frequency band within the range of 0 Hz to 125 Hz, the adjustment value may be within the range of 10 dB to 12 dB. In some embodiments, in a frequency band within the range of 125 Hz to 375 Hz, the adjustment value may be within the range of 7 dB to 9 dB. In some embodiments, in a frequency band within the range of 375 Hz to 625 Hz, the adjustment value may be within the range of 4 dB to 6 dB. By setting the adjustment value to a value within the frequency range and setting the bone conduction hearing aid, vibration issues when a wearer with a hearing level of 40 dBL wears the bone conduction hearing aid in the corresponding frequency band can be resolved so as to have a small effect on speech comprehension, thereby ensuring the wearer's hearing effect.

[0097] FIGS. 9 to 11 are drawings showing the experimental results of voice recognition rates tested on three wearers (Wearer 1, Wearer 2, and Wearer 3). FIGS. 9 to 11 as a whole illustrates the voice recognition rate, vibration sensation, and volume of the wearer before the reference analog output value is reduced, and the voice recognition rate, vibration sensation, and volume of the wearer when the reference analog output value corresponds to different control values ​​in each frequency band. In FIGS. 9 to 11, six sets of tests were performed for each tester. In the table, a negative number indicates that the control value reduces the reference output parameter (e.g., the reference analog output value). For example, -5 indicates that the control value is 5 dB and reduces the reference analog output by 5 dB. As another example, -15 indicates that the above adjustment value is 15dB and the above reference analog output value is reduced by 15dB.

[0098] As shown in FIGS. 9 to 11, when the reference analog output value is reduced based on the adjustment value, the voice identification rate may be reduced and the vibration sensation may be reduced, but the volume may be reduced. As can be seen from the table, at a frequency of 125 Hz, if the adjustment value is 5 dB (or less than 5 dB), for example, the reference analog output value is reduced by 5 dB and the voice identification rate does not change significantly; at a frequency of 250 Hz, if the adjustment value is 3 dB (or less than 3 dB), for example, the reference analog output value is reduced by 3 dB and the voice identification rate does not change significantly; at a frequency of 500 Hz, if the adjustment value is 1 dB (or less than 1 dB), for example, the reference analog output value is reduced by 1 dB and the voice identification rate does not change significantly. At the same time, when the above adjustment value is set based on the above values, the tester can feel vibration when the tester speaks, but the volume is good (for example, the volume is within a volume range that the wearer can hear clearly by default).

[0099] At a frequency of 125 Hz, if the adjustment value is 10 dB (or a range greater than 5 dB and less than 10 dB), for example, the reference analog output value is reduced by 10 dB, and the reduction in voice recognition rate may be 5% or less; at a frequency of 250 Hz, if the adjustment value is 7 dB (or a range greater than 3 dB and less than 7 dB), for example, the reference analog output value is reduced by 7 dB, and the reduction in voice recognition rate may be 5% or less; at a frequency of 500 Hz, if the adjustment value is 4 dB (or a range greater than 1 dB and less than 4 dB), for example, the reference analog output value is reduced by 4 dB, and the reduction in voice recognition rate may be 5% or less. At the same time, if the adjustment value is set based on the above values, the tester may feel more comfortable, but the sound is relatively low (for example, the wearer may feel that the volume is relatively low).

[0100] At a frequency of 125 Hz, if the adjustment value is 17 dB (or in the range greater than 10 dB and less than 17 dB), for example, the reference analog output value is reduced by 17 dB, and the reduction in the voice identification rate may be greater than 5% (e.g., 10%); at a frequency of 250 Hz, if the adjustment value is 15 dB (or greater than 7 dB and less than 15 dB), for example, the reference analog output value is reduced by 15 dB, and the reduction in the voice identification rate may be greater than 5% (e.g., 10%); at a frequency of 500 Hz, if the adjustment value is 10 dB (or greater than 4 dB and less than 10 dB), for example, the reference analog output value is reduced by 10 dB, and the reduction in the voice identification rate may be greater than 5% (e.g., 10%). At the same time, if the above adjustment value is set based on the above values, the tester may perceive that the volume is relatively low (for example, the wearer cannot hear clearly because the volume is relatively low).

[0101] Within a certain range (e.g., the adjustment value is in a range smaller than 17 dB), the larger the adjustment value, the better the vibration reduction effect of the bone conduction hearing aid. However, as can be seen in FIGS. 9 to 11, a relatively large adjustment value may result in a low output signal strength of the bone conduction hearing aid, which may have a significant impact on the voice recognition rate (e.g., the amount of reduction in the voice recognition rate). When the adjustment value is within the range of the above embodiment, the problem of vibration in the corresponding frequency band can be resolved when a wearer with a hearing level of 30 dBL-40 dBL wears the bone conduction hearing aid, and the impact on voice comprehension may be small.

[0102] In some embodiments, the adjustment value of the reference output parameter at each sound level in each frequency band may be related only to the frequency band. The corresponding adjustment values ​​of the reference output parameters at different hearing levels in the same frequency band may be the same (e.g., the adjustment values ​​in the embodiments above), and the corresponding adjustment values ​​of the same hearing level in different frequency bands may be different; the corresponding adjustment values ​​of the reference output parameters in the same frequency band at different sound levels may be the same, and the adjustment values ​​of the reference output parameters in different frequency bands at the same sound level may be different; the corresponding adjustment values ​​of the reference output parameters in the same frequency band at different sound levels and different hearing levels may be the same, and the adjustment values ​​of different frequency bands at the same sound level and the same hearing level may be different.

[0103] In some embodiments, the adjustment value of the reference output parameter at each sound level in each frequency band may be related to the frequency band and the wearer's hearing level. The corresponding adjustment values ​​of the reference output parameters in the same frequency band may differ at different hearing levels. The corresponding adjustment values ​​of the reference output parameters under the same hearing level in the same frequency band at different sound levels may be the same. Detailed descriptions of this embodiment can be found in FIG. 5 and its related description.

[0104] In some embodiments, the adjustment value of the reference output parameter at each sound level in each frequency band may be related to the frequency band and the sound level. The corresponding adjustment values ​​of the reference output parameters for different sound levels in the same frequency band may be different. However, the corresponding adjustment values ​​of the reference output parameters for different auditory levels in the same frequency band and the same sound level may be the same. Detailed descriptions of this embodiment can be found in FIG. 6 and its related description.

[0105] In 440, the bone conduction hearing aid can be positioned according to the reference output parameter and the adjustment value at each sound level in each frequency band. Specifically, 440 can be performed through the setting module (340).

[0106] In some embodiments, the processing device (120) (setting module (340)) can obtain an actual output parameter by adjusting the reference output parameter at each sound level in each frequency band based on the adjustment value, and the bone conduction hearing aid is set through the actual output parameter.

[0107] In some embodiments, the processing device (120) (setting module (340)) can obtain the actual output parameter by reducing the reference output parameter based on the adjustment value at each sound level in each frequency band, and set the bone conduction hearing aid based on the reduced reference output parameter (e.g., the actual output parameter). Reducing the reference output parameter based on the adjustment value at each sound level in each frequency band can be achieved by directly subtracting the adjustment value from the reference output parameter, or by adjusting other related settings of the parameters of the bone conduction hearing aid through the adjustment value at each sound level in each frequency band to achieve the purpose of reducing the reference output parameter.

[0108] In some embodiments, the processing device (120) (setting module (340)) can set the bone conduction hearing aid by arranging the magnetic circuit member based on the adjustment value and the reference output value at each sound level in each frequency band. In some embodiments, setting the bone conduction hearing aid may include setting various parameters of the bone conduction hearing aid, and making the parameters of the bone conduction hearing aid related to signal output strength (e.g., the gain value and the analog output value) become reference parameters adjusted based on preset values, e.g., the adjustment value. For example, by adjusting the current of the electromagnet in the magnetic circuit member, the resistance of the amplifier circuit of the sound pickup member, etc., the reference gain value and the reference analog output value of the bone conduction hearing aid for the sound signal of the bone conduction hearing aid can be adjusted, thereby achieving the setting of the bone conduction hearing aid.

[0109] In some embodiments, the bone conduction hearing aid can be configured using an equalization control system (EQ system) or an automatic gain control system (AGC system), etc., according to the reference output parameter and the adjustment value at each sound level in each frequency band.

[0110] In other embodiments, the bone conduction hearing aid can be configured using a multi-channel large dynamic range compression system (WDRC system) according to the reference output parameter and the control value at each sound level in each frequency band. The multi-channel large dynamic range compression system first uses a filter bank to decompose the sound signal into multiple channels based on the frequency band, compresses the signal of each channel independently, and thus designs an appropriate compression rate and compression threshold based on the hearing loss corresponding to the frequency band, and then synthesizes the processed signals of each channel into a single signal. The multi-channel large dynamic range compression system can perform hearing compensation more flexibly. In the multi-channel large dynamic range compression system, by adjusting the reference output parameter and the control value at each sound level in each frequency band, the compression rate and the compression threshold of the signal of each channel can be adjusted, and thus the reference output parameter of each channel can be adjusted.

[0111] FIG. 5 is a flowchart illustrating an exemplary process for obtaining an adjustment value of the reference output parameter at each sound level in each frequency band. The adjustment value determined using the process in FIG. 5 may be related to the wearer's hearing level. As shown in FIG. 5, the process 500 may include the following operations.

[0112] In 510, a first threshold corresponding to each sound level in each frequency band can be determined, and the first threshold may be related to the degree of vibration detected by the wearer at each sound level in each frequency band.

[0113] The vibration level detected by the wearer may indicate the vibration level detected by the wearer when wearing the bone conduction hearing aid. In some embodiments, the vibration level detected by the wearer may include a plurality of levels indicating the vibration level detected by the wearer. The higher the level, the greater the vibration level detected by the wearer. In some embodiments, the levels may include a first level, a second level, a third level, a fourth level, and a fifth level, and the corresponding vibration levels detected by the wearer may include "no vibration," "very mild vibration," "mild vibration," "clear vibration but acceptable," and "severe vibration but unacceptable." In some embodiments, different levels may be indicated as scores. For example, the first level may be 1 point, the second level may be 2 points, the third level may be 3 points, the fourth level may be 4 points, and the fifth level may be 5 points.

[0114] In some embodiments, the first threshold may be the output signal strength of the corresponding bone conduction hearing aid when the vibration level detected by the wearer is lower than a certain level, for example, when the output signal strength of the bone conduction hearing aid is the first threshold, the wearer may detect vibration at that level. For example, the first threshold may be the output signal strength of the bone conduction hearing aid when the vibration level detected by the wearer is at the third level (e.g., the reference output parameter), for example, when the output signal strength of the bone conduction hearing aid reaches the first threshold, the wearer may feel mild vibration corresponding to the third level. As another example, the first threshold may be the output signal strength of the bone conduction hearing aid when the vibration level detected by the wearer is the fourth level, for example, when the output signal strength of the bone conduction hearing aid reaches the first threshold, the wearer may feel a clear but acceptable vibration corresponding to the fourth level. In some embodiments, when the output signal strength of the bone conduction hearing aid is greater than the first threshold, the wearer may feel a vibration stronger than the level corresponding to the first threshold (e.g., a mild vibration corresponding to the third level) and may have a poor wearing experience. Then, the reference output parameter may be adjusted (reduced) to make the output signal strength of the bone conduction hearing aid smaller than the first threshold.

[0115] In some embodiments, a preliminary reference output parameter corresponding to each sound level in each frequency band of the wearer of the bone conduction hearing aid can be obtained. Detailed descriptions regarding obtaining the preliminary output parameter can be found in 420 in FIG. 4. In some embodiments, the first threshold may differ for different wearers. For example, by testing the wearer of the bone conduction hearing aid, the output signal strength at each sound level in each frequency band of the wearer of the bone conduction hearing aid and the vibration level detected by the wearer corresponding to the output signal strength can be determined under the preliminary reference output parameter, and by adjusting the preliminary reference output parameter to obtain the preliminary output parameter, the output signal strength and the vibration level detected by the wearer can be adjusted, so that the vibration level detected by the wearer can reach a certain level (e.g., the third level, mild vibration), and thus the first threshold corresponding to each sound level in each frequency band can be determined. In some embodiments, the adjusted rudimentary reference output parameter (e.g., the reference output parameter, e.g., the reference analog output value) may be equal to the adjusted signal output intensity. When the vibration level detected by the wearer reaches a certain level (e.g., the third level, mild vibration), the first threshold may be equal to the adjusted output signal intensity or the reference analog output value.

[0116] In some embodiments, the first threshold may be the same for different wearers. For example, the first threshold may be determined specifically through the following processes: by testing a plurality of testers, the signal output strength of each tester when the tester subjectively detects a second level of mild vibration at each sound level in each frequency band may be determined and said signal output strength may be used as test data; and said test data may be integrated and selected to obtain the first threshold. The first threshold may be applied to different wearers. In some embodiments, the integration and selection of said test data may proceed as follows: in a given frequency band, only the minimum value of said output parameter when each tester subjectively detects a mild vibration at each sound level in said frequency band may be considered, and the minimum value selected from the minimum value of said output parameter when each tester subjectively detects a mild vibration at each sound level in said frequency band is set as the first threshold value.

[0117] In some embodiments, severe vibrations of the bone conduction hearing aid may be more pronounced in a low frequency band (e.g., the frequency band within the range of 0 Hz to 625 Hz), and the adjustment value of the reference output parameter may be set to the low frequency band to reduce the reference output parameter and reduce the vibration intensity perceived by the user. Correspondingly, by setting the first threshold in the low frequency band (e.g., the frequency band within the range of 0 Hz to 625 Hz), the adjustment value of the reference output parameter may be determined based on the first threshold. In some embodiments, the first threshold may be set to a frequency band within the range of 0 Hz to 625 Hz, and the adjustment value may be determined in the frequency band. In some embodiments, the first thresholds corresponding to different frequency bands may be different. For example, in a frequency band within the range of 0 Hz to 125 Hz, the first threshold may be within the range of 48 dB to 52 dB. In some embodiments, in a frequency band within the range of 125 Hz to 375 Hz, the first threshold may be within the range of 49 dB to 54 dB. In some embodiments, in a frequency band within the range of 375 Hz to 625 Hz, the first threshold may be within the range of 50 dB to 55 dB. In some embodiments, at the same sound level, the higher the frequency band, the greater the first threshold.

[0118] In some embodiments, the first thresholds corresponding to different sound levels in the same frequency band may be the same. For example, a minimum value within the range of the first threshold in the frequency band (e.g., 48 dB) may be selected as the first threshold of the frequency band, so that the bone conduction hearing aid may not generate severe vibrations when the received sound signals are at different sound levels in the same frequency band. For example, in a frequency band within the range of 0 Hz to 125 Hz, the first threshold may be 48 dB. In a frequency band within the range of 125 Hz to 375 Hz, the first threshold may be 49 dB. In a frequency band within the range of 375 Hz to 625 Hz, the first threshold may be 50 dB.

[0119] In some embodiments, the first thresholds corresponding to different sound levels in the same frequency band may differ. In some embodiments, the higher the sound level in the same frequency band, the greater the first threshold may be. For example, in a frequency band within the range of 0 Hz to 125 Hz, if the sound level is 20 dBC to 40 dBC, the first threshold may be 48 dB; in a frequency band within the range of 0 Hz to 125 Hz, if the sound level is 40 dBC to 50 dBC, the first threshold may be 49 dB; and in a frequency band within the range of 0 Hz to 125 Hz, if the sound level is 50 dBC to 60 dBC, the first threshold may be 50 dB.

[0120] In some embodiments, the first thresholds corresponding to different hearing levels and different sound levels in the same frequency band may be the same. For example, a minimum value (e.g., 48 dB) within the range of the first threshold corresponding to each frequency band may be selected as the first threshold, so that when the sound signal received by the bone conduction hearing aid is in the same frequency band, relatively severe vibration may not occur regardless of whether the sound signal is at a certain sound level and what hearing level the wearer has.

[0121] In some embodiments, the first thresholds corresponding to different hearing levels and different sound levels in the same frequency band may differ. For example, in a frequency band within the range of 125 Hz to 375 Hz, at a hearing level of 40 dBHL and a sound level of 60 dBC, the first threshold may be 49 dB. In a frequency band within the range of 125 Hz to 375 Hz, at a hearing level of 10 dBHL and a sound level of 75 dBC, the first threshold may be 50 dB. As another example, in a frequency band within the range of 375 Hz to 625 Hz, at a hearing level of 30 dBHL and a sound level of 70 dBC, the first threshold may be 55 dB. For example, in a frequency band within the range of 375 Hz to 625 Hz, at a hearing level of 20 dBHL and a sound level of 75 dBC, the first threshold may be 56 dB. In some embodiments, the first thresholds corresponding to different sound levels and different hearing levels in different frequency bands may be the same. For example, a minimum value (e.g., 48 dB) within the range of the first thresholds corresponding to the frequency band may be selected as the first thresholds corresponding to different sound levels in the frequency band, so that the bone conduction hearing aid may not generate severe vibrations when the received sound signals are at different sound levels in different frequency bands. For example, in a frequency band within the range of 0 Hz to 625 Hz, the first threshold may be 48 dB.

[0122] In 520, a second threshold corresponding to each sound level in each frequency band can be determined, and the second threshold may be related to the voice identification rate of the wearer in each frequency band.

[0123] The above speech identification rate (e.g., speech comprehension) may be the ratio of words that are understood or clearly understood to words that are heard. The above speech identification rate may indicate auditory sensitivity and the clarity of language heard by the wearer wearing the hearing aid, and reflects the wearer's hearing effect to a certain extent. The higher the speech identification rate, the higher the wearer's auditory sensitivity, the higher the auditory clarity, and the better the hearing effect after wearing the hearing aid. In some embodiments, if the speech identification rate is 70% or higher, the hearing effect may be considered good; if the speech identification rate is 50% or lower, the hearing effect may be considered not ideal, and the bone conduction hearing aid may be readjusted or set.

[0124] In some embodiments, the adjustment (e.g., reduction) of the reference output parameter may affect the output signal strength of the bone conduction hearing aid, and consequently affect the voice identification rate of the bone conduction hearing aid. For example, from the experimental results in FIGS. 9–11, it can be seen that within a certain range (e.g., a range where the adjustment value is less than 17 dB), the higher the adjustment value, the lower the voice identification rate may be. The second threshold may be used to ensure that the voice identification rate adjusted by the reference output parameter is within a certain range (e.g., higher than a certain threshold). This means that the second threshold may be used to control the reduction of the voice identification rate adjusted by the reference output parameter within a certain range. For example, if the above adjustment value does not exceed the above second threshold, the amount of reduction in the voice identification rate of the wearer wearing the hearing aid may be small compared to the voice identification rate not adjusted by the above reference output parameter, for example, the amount of reduction in the voice identification rate may be 5% or less. The amount of reduction in the voice identification rate may be the result of subtracting the voice identification rate adjusted by the above reference output parameter from the voice identification rate not adjusted by the above reference output parameter.

[0125] In some embodiments, the second threshold may be the maximum value among the adjustment values ​​corresponding to the reference output parameter of the bone conduction hearing aid under the preset voice identification rate when the wearer wears the bone conduction hearing aid; for example, when the adjustment value corresponding to the reference output parameter of the bone conduction hearing aid corresponds to the second threshold, the voice identification rate when the wearer wears the bone conduction hearing aid may be the preset threshold. When the adjustment value is greater than the second threshold, the voice identification rate when the wearer wears the bone conduction hearing aid may be lower than the preset voice identification rate.

[0126] For example, as shown in FIG. 10, the second threshold may be the adjustment value corresponding to the reference output parameter when the wearer wears the bone conduction hearing aid, and the voice identification rate is 80%. At 125 Hz, for example, the second threshold may be 5 dB. This means that when the adjustment value corresponding to the reference output parameter of the bone conduction hearing aid at 125 Hz is the second threshold, the voice identification rate may be 80% when the wearer wears the bone conduction hearing aid. As another example, as shown in FIG. 11, the second threshold may be the adjustment value corresponding to the reference output parameter when the wearer wears the bone conduction hearing aid, and the voice identification rate may be 60% at 250 Hz, for example, the second threshold may be 12 dB. This means that when the adjustment value corresponding to the reference output parameter of the bone conduction hearing aid at 50Hz is the second threshold, the voice identification rate may be 60% when the wearer wears the bone conduction hearing aid.

[0127] In some embodiments, the second threshold may be determined according to a preset voice identification rate threshold. For example, in FIGS. 9 to 11, the second threshold may be determined based on experimental results of a voice identification rate test performed on the wearer. Referring only to FIG. 10, when the bone conduction hearing aid is configured based on a voice identification rate not adjusted by the reference output parameter, the wearer's voice identification rate may be 80%, and if the voice identification rate is set to 75% or higher (e.g., the amount of reduction in voice identification rate may be 5% or less) after the reference output parameter is reduced, the second threshold may be 10 dB; and if the voice identification rate is set to 80% or higher (e.g., the voice identification rate is hardly reduced), the second threshold may be 5 dB.

[0128] In some embodiments, severe vibrations of the bone conduction hearing aid may be more pronounced in a low-frequency band (e.g., a frequency band within the range of 0 Hz to 625 Hz), and the adjustment value of the reference output parameter is set to the low-frequency band to reduce the reference output parameter and reduce the vibration intensity perceived by the wearer. Correspondingly, the second threshold may be set in the low-frequency band (e.g., a frequency band within the range of 0 Hz to 625 Hz) to determine the adjustment value of the reference output parameter based on the first threshold. In some embodiments, the second thresholds corresponding to different frequency bands may be different. For example, in a frequency band within the range of 0 Hz to 125 Hz, the second threshold may be within the range of 5 dB to 10 dB. In some embodiments, in a frequency band within the range of 125 Hz to 375 Hz, the second threshold may be within the range of 3 dB to 7 dB. In some embodiments, in a frequency band within the range of 375Hz to 625Hz, the second threshold may be within the range of 1dB to 4dB. In some embodiments, at the same sound level, the higher the frequency band, the smaller the second threshold.

[0129] In some embodiments, the second thresholds corresponding to different hearing levels in the same frequency band may be the same. For example, the second threshold may be set according to the range, regardless of whether the wearer's hearing level is 30 dBHL or 40 dBHL. In some embodiments, the second thresholds corresponding to different hearing levels in the same frequency band may be different. For example, in a frequency band within the range of 0 Hz to 125 Hz, if the hearing level is 30 dBHL, the second threshold may be 5 dB. In a frequency band within the range of 0 Hz to 125 Hz, if the hearing level is 40 dBHL, the second threshold may be 15 dB. In some embodiments, the second thresholds corresponding to different sound levels in the same frequency band may be the same. In some embodiments, a minimum value within the range may be selected as the second threshold, so that the bone conduction hearing aid may not have too much effect on the voice identification rate when the received sound signals are at different sound levels. For example, in a frequency band within the range of 125 Hz to 375 Hz, the second threshold may be 3 dB. In some embodiments, in a frequency band within the range of 0 Hz to 125 Hz, the second threshold may be 5 dB. In some embodiments, in a frequency band within the range of 375 Hz to 625 Hz, the second threshold may be 1 dB.

[0130] In some embodiments, the second thresholds corresponding to different sound levels in the same frequency band may be different. For example, in a frequency band within the range of 0 Hz to 125 Hz, if the sound level is 60 dBC, the second threshold may be 5 dB; and in a frequency band within the range of 0 Hz to 125 Hz, if the sound level is 60 dBC, the second threshold may be 10 dB.

[0131] In 530, the above adjustment value can be determined based on the above reference output parameter, the above first threshold, and the above second threshold.

[0132] 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 may be reduced so that the initial adjustment value becomes 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 may be determined as the adjustment value.

[0133] In some embodiments, a comparison value may be obtained by subtracting the first threshold corresponding to the sound level in the specified frequency band from the reference output parameter corresponding to the sound level in the specified frequency band. Then, a first comparison result may be obtained by comparing the comparison value with the second threshold corresponding to the sound level in the specified frequency band, and the adjustment value corresponding to the reference output parameter of the sound level in the specified frequency band may be determined based on the first comparison result.

[0134] The determination process for the first threshold and the second threshold can be found in the relevant description above. The comparison value may be positive, negative, or zero. The comparison between the comparison value and the second threshold is a numerical comparison, which can determine the magnitude relationship between the comparison value and the second threshold. The first comparison result may include a comparison value smaller than the second threshold, a comparison value equal to the second threshold, or a comparison value larger than the second threshold. Determining the adjustment value corresponding to the reference output parameter based on the first comparison result may involve determining the adjustment value based on the magnitude relationship between the comparison value and the second threshold.

[0135] In some embodiments, determining the control value corresponding to the reference output parameter based on the first comparison result may include: if the comparison value is 0 or less, the control value is 0; if the comparison value is greater than 0 and is 0 or less than the second threshold, the control value is the comparison value; and if the comparison value is greater than the second threshold, the control value is the second threshold.

[0136] If the reference output parameter is below the first threshold, after setting the bone conduction hearing aid based on the reference output parameter, the wearer may be less likely to detect the vibration after wearing the bone conduction hearing aid, and the reference output parameter may not be adjusted. If the reference output parameter is greater than the first threshold, after setting the bone conduction hearing aid based on the reference output parameter, the wearer may be more likely to detect strong vibration after wearing the bone conduction hearing aid, and the reference output parameter may need to be adjusted. Furthermore, when determining the adjustment value, not only the risk of the bone conduction hearing aid caused by the reference output parameter may be considered, but the influence of the adjusted reference output parameter on the voice identification rate of the bone conduction hearing aid may also be considered. Since the second threshold is a threshold related to the voice identification rate, by comparing the comparison value with the second threshold, the adjustment value can be as low as possible as the second threshold, and the influence of the adjustment of the reference output parameter on the voice can be minimized.

[0137] FIG. 6 is a flowchart illustrating an exemplary process for obtaining an adjustment value of the reference output parameter. In some embodiments, when the bone conduction hearing aid is configured using a multi-channel large dynamic range compression system, the adjustment value corresponding to the reference output parameter may be determined using process 600 in FIG. 6. As shown in FIG. 6, the process 600 for determining the adjustment value corresponding to the reference output parameter may include the following operations.

[0138] In 610, the second comparison result can be determined by comparing the reference output parameter with the first threshold. The first threshold may be related to the degree of vibration detected by the wearer at each sound level in each frequency band.

[0139] Related descriptions regarding the first threshold and the processing for determining the first threshold can be found in the related description regarding the first threshold in 510. The comparison of the reference output parameter and the first threshold is the reference output parameter and the first threshold

[0140] In 620, the adjustment value corresponding to the reference output parameter can be determined based on the second comparison result.

[0141] A related description regarding the control value corresponding to the output parameter can be found in the related description in 430. The second comparison result may include a comparison result in which the reference output parameter is greater than the first threshold, a comparison result in which the reference output parameter and the first threshold are the same, and a comparison result in which the reference output parameter is smaller than the first threshold. In some embodiments, whether the control value is 0 may be determined based on whether the reference output parameter is greater than the first threshold. For example, if the reference output parameter is smaller than the first threshold, the control value may be set to 0; and if the reference output parameter is greater than the first threshold, the control value may be set to greater than 0.

[0142] In some embodiments, when the bone conduction hearing aid device is deployed using a multi-channel high dynamic range compression system, the control value may include a gain reduction value of the multi-channel high dynamic range compression system when at least one of the sound levels is greater than the sound level threshold. In some embodiments, the sound level threshold may be 70 dB. When the wearer uses the bone conduction hearing aid, the sound level of the sound signal during everyday conversation may generally be about 60 dB. The sound level of the sound signal being 70 dB or higher may occur when the wearer speaks or when ambient sounds are relatively loud. The bone conduction hearing aid may generate relatively strong vibrations, and the control value may be set to adjust (e.g., reduce) the reference output parameter within the range of the sound level, thereby improving the vibration of the bone conduction hearing aid and ensuring that the wearer's voice identification rate is not affected during everyday conversation.

[0143] The gain when at least one of the sound levels of each of the above sound levels is greater than the sound level threshold may also be referred to as high-level gain. The adjustment value may include a reduced value of the high-level gain of the multi-channel high-dynamic range compression system. The high-level gain of the multi-channel high-dynamic range compression system may be the gain when the sound level of the sound signal is greater than the sound level threshold (e.g., 70 dB). The gain of the multi-channel high-dynamic range compression system when at least one of the sound levels of each of the above sound levels is greater than the sound level threshold may be determined based on the wearer's hearing loss data, for example, according to an empirical formula. For example, the empirical formula may determine the high-level gain of the multi-channel high-dynamic range compression system based on the wearer's hearing level. The adjustment value may be a specific numerical value obtained by reducing the high-level gain derived from the empirical formula.

[0144] In some embodiments, whether the gain reduction value is zero (e.g., whether the gain is reduced when at least one of the sound levels is greater than the sound level threshold) may be determined based on whether the reference output parameter is greater than the first threshold. For example, if the reference output parameter is less than the first threshold, the gain reduction value may be specified as zero; and if the reference output parameter is greater than the first threshold, the gain reduction value may be specified as greater than zero.

[0145] In some embodiments, after determining the gain reduction value when at least one of the sound levels is greater than the sound level threshold, the gain value when it is greater than the sound level threshold can be reduced using the gain reduction value, and the reduced gain value can be used as an input parameter of the multi-channel high dynamic range compression system. When at least one of the sound levels is greater than the sound level threshold, the bone conduction hearing aid may be prone to vibrating. When the sound level is higher than the sound level threshold in the set frequency band, the gain reduction value can be determined based on the setting method, and by using the gain reduction value as a control value, the reference output parameter can be reduced so that it is not affected when the sound level of the sound signal is less than the sound level threshold and when the sound level is less than the sound level threshold. Therefore, while ensuring the voice identification rate of the bone conduction hearing aid, it is possible to improve severe vibrations of the bone conduction hearing aid in some cases.

[0146] In some embodiments, where the control value includes a gain reduction value of the multi-channel large dynamic range compression system when at least one of the sound levels is greater than the sound level threshold, 620 specifically includes an operation of setting the gain reduction value to 0dB when the reference output parameter is less than or equal to the first threshold, and an operation of setting the gain reduction value to the difference between the first threshold and the reference output parameter when the reference output parameter is greater than the first threshold.

[0147] In this embodiment, if the reference output parameter is below the first threshold, the wearer may be less likely to detect severe vibrations when wearing the bone conduction hearing aid, and the high-level gain may not be adjusted (reduced), and therefore the high-level gain reduction value may be set to 0. If the reference output parameter is greater than the first threshold, the wearer may be more likely to detect severe vibrations when wearing the bone conduction hearing aid, and the high-level gain may be adjusted (reduced), and therefore the reference output parameter may be reduced, and the reference output parameter is made smaller than the first threshold.

[0148] In some embodiments, when the bone conduction hearing aid is deployed using the multi-channel high dynamic range compression system, the adjustment value may include a reduction value of the output limit of the multi-channel high dynamic range compression system when at least one of the sound levels is greater than the sound level threshold. In some embodiments, the sound level threshold may be 70 dB. In this embodiment, a situation where the sound level of the sound signal is 70 dBC or higher may occur when the wearer is speaking or when ambient sounds are relatively loud. At this time, the bone conduction hearing aid may generate relatively strong vibrations, and thus, by setting the adjustment value to adjust the reference output parameter (the output limit of the multi-channel high dynamic range compression system) to within the range of the sound level, the vibration of the bone conduction hearing aid can be improved, and the wearer's voice identification rate is hardly affected during daily conversation.

[0149] The above output limit can be understood as a limiting value of the above reference output parameter in each frequency band. If the above reference output parameter is greater than the above output limit, the reference output parameter of the bone conduction hearing aid may be equal to the above output limit. The output limit of the above multi-channel wide dynamic range compression system may be determined according to an empirical formula based on the wearer's hearing loss data. For example, the above empirical formula may determine the output limit of the above multi-channel wide dynamic range compression system based on the wearer's hearing level. The above adjustment value may be a specific numerical value that reduces the above output limit derived from the above empirical formula. The above empirical formula may be set by the user or may be a default setting in the system for setting the above bone conduction hearing aid.

[0150] In some embodiments, where the control value includes a reduction value of the output limit of the multi-channel large dynamic range compression system when at least one sound level among each sound level is greater than the sound level threshold, operation 620 may further include an operation of setting the reduction value of the output limit to 0dB when the reference output parameter is less than or equal to the first threshold, and an operation of setting the reduction value of the output limit to a value greater than 0dB when the reference output parameter is greater than the first threshold.

[0151] This means that if the reference output parameter is below the first threshold, the wearer may be less likely to detect severe vibrations when wearing the bone conduction hearing aid, and the output limit may not be adjusted (reduced); and if the reference output parameter is greater than the first threshold, the wearer is more likely to detect severe vibrations when wearing the bone conduction hearing aid, and the output limit may be adjusted (reduced), and thus the reference output parameter is reduced and becomes smaller than the first threshold.

[0152] Additionally, if it is determined that the reduction value of the output limit is greater than 0, a specific numerical value of the reduction value of the output parameter limit may be further determined. In some embodiments, for example, the output limit may be gradually reduced in equal steps, and the reference output parameter may be made smaller than the first threshold. For example, by gradually reducing the output limit in equal steps, the output limit may be reduced to the same value each time (for example, by reducing the output limit by 2 dB each time), the reference output parameter may be gradually reduced, and the reference output parameter may be made smaller than the first threshold.

[0153] Since the wearer generally detects relatively strong vibrations when the wearer speaks or when the surrounding sounds are loud, the sound level may be relatively high, for example, 70 dB or higher. By adjusting the reference output parameter using the processing 600, when a sound signal having an intermediate sound level (for example, a sound signal having a sound level of 0 dB or lower) is input to the bone conduction hearing aid, the reference output parameters of the bone conduction hearing aid may not be affected; and when a sound signal having a high sound level (for example, a sound signal having a sound level of 70 dB or higher) is input to the bone conduction hearing aid, the reference output parameter of the bone conduction hearing aid may be lower than the first threshold, thereby improving the situation where the wearer detects relatively large vibrations when the wearer speaks or when the surrounding sounds are loud.

[0154] In some embodiments, when at least one of the sound levels is greater than the sound level threshold, the control value may include only the gain reduction value. In some other embodiments, when at least one of the sound levels is greater than the sound level threshold, the control value may include only the output limit reduction value. In some embodiments, the control value may include both the gain reduction value when at least one of the sound levels is greater than the sound level threshold and the output limit reduction value when at least one of the sound levels is greater than the sound level threshold.

[0155] In some embodiments, setting the parameters of the multi-channel large dynamic range compression system may further include a crossover frequency, a lower threshold, a lower level gain, an upper threshold, an extension threshold, an extension rate, a compressor attack time, a compressor release time, an automatic gain control algorithm based on output (AGCo) shock, and an automatic gain control algorithm based on output (AGCo) release. The crossover frequency may be a frequency among which the audio frequency spectrum is decomposed, for example, a split point of each frequency band. The lower threshold may be a lower threshold of the sound level in the frequency band. The lower level gain may be a gain when the input sound level is lower than the lower threshold. The upper threshold may be an upper threshold of the sound level in the frequency band, for example, a threshold corresponding to the high level gain. The above expansion threshold may be an expansion threshold of sound level in a frequency band, and the above expansion rate may be a gain ratio of sound at the above expansion threshold. The above compressor attack time is a transient time during which the compressor fully operates when the compressor detects a sound higher than the threshold, and the gain may gradually increase within the transient time until it reaches a preset gain. The above compressor release time is a transient time during which the compressor fully operates when the sound is lower than the threshold, and the gain gradually decreases within the transient time until it reaches the preset gain. AGCo is an automatic gain control algorithm based on the above output, and the AGCo attack time may be 2 ms. The AGCo release time may be 64 ms.

[0156] FIG. 7 is a flowchart illustrating the operations performed by a bone conduction hearing aid according to other embodiments of the present disclosure when in use. As shown in FIG. 7, the bone conduction hearing aid can perform the following operations when in use.

[0157] In 710, a sound input signal can be obtained. In some embodiments, the sound input signal may include an audio signal (e.g., a song, voice, etc.) obtained by the bone conduction hearing aid from a storage device (e.g., the storage (130)), a terminal (e.g., the terminal (140)), or other devices. In some embodiments, the sound input signal of the bone conduction hearing aid may include a sound signal picked up by the sound pickup member of the bone conduction hearing aid. For example, the sound pickup member may pick up a sound (the first vibration signal), process the first vibration signal, and convert the first vibration signal into an electrical signal. The electrical signal may be transmitted to a speaker member of the bone conduction hearing aid. The speaker member may be configured to process the electrical signal based on the reference output parameter, convert the electrical signal into a second vibration signal, and transmit the second vibration signal to the wearer.

[0158] In 720, the reference output parameter corresponding to the frequency component may be determined based on the sound level, frequency component, and reference output parameter of the sound input signal. In some embodiments, the bone conduction hearing aid may obtain preset reference output parameters stored in the storage device of the bone conduction hearing aid. The preset reference output parameter may correspond to different sound levels and hearing levels in different frequency bands. The bone conduction hearing aid may determine the reference output parameter corresponding to the sound level and the frequency component from the preset reference output parameters based on the sound level and the frequency component of the sound input signal. In some embodiments, the bone conduction hearing aid may determine the reference corresponding to the sound level, the frequency component, and the hearing level from the preset reference output parameters based on the sound level, the frequency component, and the hearing level of the sound input signal. In some embodiments, the preset reference output parameters corresponding to different sound levels and auditory levels in different frequency bands may be determined according to 420 in FIG. 4.

[0159] In 730, an actual output parameter corresponding to the frequency component of the sound level can be obtained based on a reference output parameter corresponding to the frequency component and an adjustment value corresponding to the reference output parameter of the frequency component. In some embodiments, the bone conduction hearing aid can obtain adjustment values ​​of the preset reference output parameters stored in the storage device of the bone conduction hearing aid. The preset adjustment values ​​may correspond to reference output parameters at different sound levels and hearing levels in different frequency bands. The bone conduction hearing aid can determine an adjustment value of the reference output parameter corresponding to the sound level and the frequency component from the preset adjustment values ​​based on the sound level and the frequency component of the sound input signal. In some embodiments, the bone conduction hearing aid can determine an adjustment value of the reference output corresponding to the sound level, the frequency component, and the hearing level from the preset adjustment values ​​based on the sound level, the frequency component, and the wearer's hearing level of the sound input signal. In some embodiments, the adjustment values ​​of the preset reference output parameters corresponding to different sound levels and auditory levels in different frequency bands may be determined according to 430 in FIG. 4.

[0160] In 740, the bone conduction hearing aid can be controlled based on the actual output parameters to output a sound signal.

[0161] The reference output parameter can be understood as an initial setting parameter for the process of setting the bone conduction hearing aid, and the actual output parameters can be understood as output parameters controlled by the bone conduction hearing aid based on the adjustment value. In some embodiments, the actual output parameter may include a gain value or an actual analog output value. In some embodiments, the actual gain value may be a value at which the hearing aid actually amplifies the intensity of the sound signal during the sound signal wearing process, and the actual analog output value may be a value simulated by the hearing aid based on an input sound signal parameter (e.g., the sound signal intensity value). For example, the actual analog output value may be equal to the result of adding the actual gain value (unit: dB) to the sound signal input value (e.g., the intensity value, unit: dB). In some embodiments, for example, when the input sound signal of the bone conduction hearing aid is at the specified sound level and the specified frequency band, the actual analog output value corresponding to the specified sound level and the specified frequency band may be equal to the actual output value when using the bone conduction hearing aid (for example, the actual output signal intensity value of the bone conduction hearing aid, the unit is dB). In some embodiments, when the wearer wears the bone conduction hearing aid, the sound pickup member (220) of the bone conduction hearing aid may perform 710, and the magnetic circuit member of the bone conduction hearing aid may perform 720 and 730. The vibration member of the bone conduction hearing aid may perform 740. The above vibration member can convert the actual output parameter determined by the above magnetic circuit member into a corresponding vibration intensity, and can enable the bone conduction hearing aid to output the sound signal through mechanical vibration.In some embodiments, when the wearer wears the bone conduction hearing aid, the sound pickup member (220) of the bone conduction hearing aid may perform 710, and the processing unit of the bone conduction hearing aid may perform 720 and 730. The processing unit of the bone conduction hearing aid may perform 740 by controlling the magnetic circuit member and the vibration member. For example, the processing unit may control the vibration member based on the determined actual output parameter to generate a vibration intensity corresponding to the actual output parameter, and cause the bone conduction hearing aid to output the sound signal through mechanical vibration. As another example, the processing unit may control the intensity of the mechanical vibration generated by the voice coil by controlling the magnitude of the current in the voice coil based on the determined actual output parameter, and control the output signal intensity of the bone conduction hearing aid.

[0162] In some embodiments, actual output parameters at each sound level in each frequency band of the parameter may be stored in the bone conduction hearing aid. When the bone conduction hearing aid acquires the sound input signal, the bone conduction hearing aid device may directly determine the actual output parameters of the bone conduction hearing aid at the corresponding sound level in the frequency band based on the sound level in the frequency band of the sound input signal, and output the sound signal based on the actual output parameters.

[0163] The basic principles have been explained above. Of course, to those skilled in the art, the detailed description above is merely an example and does not constitute a limitation to the present disclosure. Although not explicitly interpreted herein, those skilled in the art may make various modifications, improvements, and variations to the present disclosure. Such modifications, improvements, and variations are taught by the present disclosure and remain within the essence and scope of the exemplary embodiments of the present disclosure.

[0164] On the one hand, the present disclosure describes embodiments of the present disclosure using specific words. For example, “one embodiment,” “one embodiment,” and / or “some embodiments” refer to specific features, structures, or characteristics related to at least one embodiment of the present disclosure. Accordingly, it is emphasized and cautioned herein that “one embodiment,” “one embodiment,” or “alternative embodiment” appearing two or more times in different parts of the present disclosure do not need to refer to the same embodiment. Furthermore, the specific features, structures, or characteristics in one or more embodiments of the present disclosure may be appropriately combined.

[0165] And, unless explicitly stated in the claims, the use of quantities and letters, or other designations, described in this disclosure is not used to limit the order of processing and methods in this disclosure. Although the foregoing disclosure has been discussed in the manner of various examples of some embodiments of the invention currently recognized as useful, it should be understood that such details are for illustrative purposes only and are not limited to the embodiments disclosed in the appended claims, but are intended to cover all modifications and equivalent combinations falling within the gist and scope of the embodiments of this disclosure. For example, the implementation of the various components described above may be implemented in a hardware device, but may also be implemented as a solution of software alone mounted on an existing server or mobile device.

[0166] Likewise, it should be noted that, for the sake of simplifying the description of the present disclosure and to aid in understanding one or more embodiments of the present invention, in the foregoing description of the embodiments of the present disclosure, multiple features may be combined in any case in one embodiment, drawing, or description thereof. The method of description does not imply that the subject matter of the present disclosure requires more features than those described in the claims. Rather, the claimed subject matter may have fewer features than all the features of the one disclosed embodiment.

[0167] In some embodiments, numerical values ​​are used to describe the quantities of components and properties. It should be understood that the quantities used in the description of these embodiments are modified with the modifiers “about,” “generally,” or “substantially” in some embodiments. Unless otherwise noted, “about,” “generally,” or “substantially” implies that a variation of ±20% is permitted in the claimed values. Correspondingly, in some embodiments, the numerical parameters used in this specification and claims are approximations that may vary based on the desired characteristics of individual embodiments. In some embodiments, numerical parameters must be considered by applying specific effective values ​​and general numerical holding methods. While the numerical ranges and parameters used to determine the breadth of the range in some embodiments of this disclosure are approximations, in the specified embodiments, the setting of these figures is as accurate as possible within the possible range.

[0168] Each patent, patent application, publication of patent application, and other materials referenced herein, such as sentences, books, specifications, publications, documents, etc., are incorporated herein by reference in their entirety, and any litigation history of the present application, documents that are inconsistent with or conflict with the content of the present documents, or content that has a limiting effect on the maximum scope of the present or subsequent relevant documents are excluded from the present specification. For example, if the use of technology, definitions, and / or terms in the attached application of the present disclosure is inconsistent with or conflicts with the content described in the present disclosure, the technology, definitions, and / or terms in the present disclosure shall be used as the basis.

[0169] In conclusion, as described above, it will be understood that the embodiments of this application disclosed herein are illustrative of the principles of the embodiments of this application. Other modifications may be applied within the scope of this application. Accordingly, for example, non-limiting alternative forms of the embodiments of this application may be utilized in accordance with the implications provided herein. Therefore, the embodiments of this application are not limited to exactly as shown and described.

Claims

Claim 1 A method for setting up a bone conduction hearing aid, comprising: a step of acquiring hearing loss data of a wearer; a step of determining a reference output parameter of the bone conduction hearing aid at each sound level in each frequency band based on the hearing loss data; a step of acquiring an adjustment value of the reference output parameter at least in relation to the frequency band at each sound level in each frequency band, wherein the adjustment values ​​differ at different sound levels in the same frequency band, and the step of acquiring the adjustment value of the reference output parameter at each sound level in each frequency band comprises: a step of determining a first threshold corresponding to each sound level in each frequency band and also related to the vibration detected by the wearer at each sound level in each frequency band; a step of determining a second threshold corresponding to each sound level in each frequency band and also related to the voice identification rate of the wearer at each sound level in each frequency band; and a step of determining the adjustment value based on the reference output parameter, the first threshold, and the second threshold. A method for setting a bone conduction hearing aid, comprising the step of setting the bone conduction hearing aid based on the reference output parameter and the adjustment value at each sound level in each frequency band, wherein the step of setting the bone conduction hearing aid includes the step of reducing the reference output parameter based on the adjustment value in a frequency band within the range of 0Hz to 625Hz. Claim 2 In claim 1, the adjustment values ​​are a method for setting the same bone conduction hearing aid at different sound levels in the same frequency band. Claim 3 A method for setting a bone conduction hearing aid in the frequency band within the range of 0Hz to 625Hz, wherein the adjustment value is within the range of 1dB to 12dB. Claim 4 A method for setting a bone conduction hearing aid according to claim 1, wherein in a frequency band within the range of 0Hz to 125Hz, the adjustment value is within the range of 5dB to 12dB, or in a frequency band within the range of 125Hz to 375Hz, the adjustment value is within the range of 3dB to 9dB, or in a frequency band within the range of 375Hz to 625Hz, the adjustment value is within the range of 1dB to 6dB. Claim 5 A method for setting a bone conduction hearing aid according to claim 1, wherein the step of determining the adjustment value based on the reference output parameter, the first threshold, and the second threshold comprises: a step of obtaining a comparison value by subtracting the first threshold from the reference output parameter with respect to the reference output parameter at a mother sound level among each sound level in a mother frequency band of each frequency band; a step of obtaining a first comparison result by comparing the comparison value with the second threshold; and a step of determining the adjustment value corresponding to the reference output parameter based on the first comparison result. Claim 6 A method for setting a bone conduction hearing aid according to claim 5, wherein the step of determining the adjustment value corresponding to the reference output parameter based on the first comparison result comprises: a step of designating the adjustment value as 0dB when the comparison value is 0 or less; a step of designating the adjustment value as the comparison value when the comparison value is greater than 0 and is 2 or less than the second threshold; and a step of designating the adjustment value as the second threshold value when the comparison value is greater than the second threshold. Claim 7 A method for setting a bone conduction hearing aid according to claim 1, wherein in a frequency band within the range of 0Hz to 125Hz, the first threshold is within the range of 48dB to 52dB, or in a frequency band within the range of 125Hz to 375Hz, the first threshold is within the range of 49dB to 54dB, or in a frequency band within the range of 375Hz to 625Hz, the first threshold is within the range of 50dB to 55dB. Claim 8 A method for setting a bone conduction hearing aid according to claim 1, wherein in a frequency band within the range of 0Hz to 125Hz, the second threshold is within the range of 5dB to 10dB, or in a frequency band within the range of 125Hz to 375Hz, the second threshold is within the range of 3dB to 7dB, or in a frequency band within the range of 375Hz to 625Hz, the second threshold is within the range of 1dB to 4dB. Claim 9 A method for setting a bone conduction hearing aid according to claim 1, wherein the step of setting the bone conduction hearing aid based on the reference output parameter and the adjustment value at each sound level in each frequency band further comprises the step of setting the bone conduction hearing aid using a multi-channel large dynamic range compression system based on the reference output parameter and the adjustment value at each sound level in each frequency band. Claim 10 delete Claim 11 delete Claim 12 delete Claim 13 delete Claim 14 delete Claim 15 delete Claim 16 delete Claim 17 delete Claim 18 delete Claim 19 delete Claim 20 delete

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