TW202243494A - Configuration method and system of bone conduction hearing aid device - Google Patents

Abstract

The present disclosure may disclose a configuration method and system of bone conduction hearing aid device, the method including the following operations: obtaining hearing loss information the the wearer; determining reference output parameters of the bone conduction hearing aids in each sound level and each frequency band based on the hearing loss information; obtaining the adjustment value of the reference output parameters; the adjustment value may at least be related to the frequency band; and configuring the bone conduction hearing aid device based on the reference output parameters and the hearing loss information.

Description

Configuration method and system for bone conduction hearing aid equipment

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

This application claims the priority of the international patent application with application number PCT/CN2021/090136 filed on April 27, 2021, and the Chinese patent application with application number 202110458138.6 filed on April 27, 2021, Its entire content is incorporated herein by reference.

Bone conduction hearing aids are hearing aids designed and manufactured using bone conduction technology. The bone conduction hearing aid device may be a bone conduction hearing aid or a bone conduction hearing aid earphone. Bone conduction hearing aids mainly amplify external sound information and convert it into mechanical vibration, and through the form of mechanical vibration, the external sound is sent to the cerebral cortex through the human skull, bone labyrinth, inner ear lymph fluid, spiral organ, and auditory nerve. center. Compared with traditional air conduction hearing aids, the sound wave signal of bone conduction hearing aids can be transmitted directly to the auditory nerve through bones without passing through the external auditory canal and eardrum, avoiding the pressure and ear blocking effect caused by traditional air conduction hearing aids blocking the ear canal. And the bone conduction hearing aid device can make the wearer have a more comfortable wearing experience. In addition, bone conduction hearing aids do not need to be implanted in the ear, and can effectively avoid ear canal inflammation. Therefore, bone conduction hearing aids are increasingly used by hearing-impaired patients.

Since bone conduction hearing aids are transmitted through vibration to enable the wearer to hear the sound, there may be severe vibration during use, which will affect the wearer's wearing experience; while lower vibration will affect the wearer's hearing. Therefore, it is necessary to provide a bone conduction hearing aid configuration method to improve the severe vibration of the bone conduction hearing aid under certain circumstances without affecting the listening effect of the wearer.

An embodiment of the present invention provides a method for configuring bone conduction hearing aids, which includes the following steps: acquiring hearing loss data of the wearer; based on the hearing loss data, determining the bone conduction hearing aids at each sound level and each frequency band The following reference output parameters; obtain the adjustment value of the reference output parameter, the adjustment value is at least related to the frequency band; based on the reference output parameter and the adjustment value, configure the bone conduction hearing aid.

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

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

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

In some embodiments, obtaining the adjustment value of the reference output parameter includes: determining a first threshold value corresponding to each frequency band and each sound level, and the first threshold value is related to the wearer's perception of each sound level. The vibration experience degree of each sound level in the frequency band is related; determine the second threshold value corresponding to the each frequency band and the each sound level, and the second threshold value is related to the wearer's sound level in the each frequency band. Speech recognition rate correlation; and determining the adjustment value based on the reference output parameter, the first threshold and the second threshold.

In some embodiments, determining the adjustment value based on the reference output parameter, the first threshold and the second threshold includes: for each sound level and a certain sound level and a certain sound level in each frequency band The reference output parameter under a frequency band: subtract the reference output parameter from the first threshold to obtain a comparison value; compare the comparison value with the second threshold; based on the comparison value and the As a result of the comparison of the second threshold, the adjustment value corresponding to the reference output parameter is determined.

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

In some embodiments, in the frequency band where the frequency is greater than 0 Hz and less than or equal to 125 Hz, the first threshold is in the range of 48 dB-52 dB.

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

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

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

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

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

In some embodiments, configuring the bone conduction hearing aid device based on the reference output parameter and the adjustment value includes: using a multi-channel wide dynamic range compression system based on the reference output parameter and the adjustment value, The bone conduction hearing aid device is configured.

In some embodiments, obtaining the adjustment value of the reference output parameter includes: comparing the reference output parameter with a first threshold, and the first threshold is the same as the wearer's response to each sound of each frequency band. The level of vibration experience is related to; based on the comparison result of the reference output parameter and the first threshold, the adjustment value corresponding to the reference output parameter is determined.

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

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

The embodiment of the present invention also provides a configuration system for bone conduction hearing aids, which includes: an acquisition module for acquiring hearing loss data of the wearer; a reference output parameter determination module for, based on the hearing loss data, Determine the reference output parameters of the bone conduction hearing aid device at each sound level and each frequency band; the adjustment value determination module is used to obtain the adjustment value of the reference output parameter; the configuration module is used to obtain the reference output parameter based on the reference output parameter and the adjustment value to configure the bone conduction hearing aid device.

In order to more clearly illustrate the technical solutions of the embodiments of the present invention, the following briefly introduces the drawings that need to be used in the description of the embodiments. Apparently, the accompanying drawings in the following description are only some examples or embodiments of the present invention, and for those skilled in the art, the present invention can also be translated according to these drawings without making progressive efforts. The invention applies to other similar scenarios. Unless otherwise apparent from context or otherwise indicated, like reference symbols in the drawings represent like structures or operations.

It should be understood that "system", "device", "unit" and/or "module" as used herein is a method for distinguishing different elements, components, parts, parts or assemblies of different levels. However, the words may be replaced by other expressions if other words can achieve the same purpose.

As shown in the present invention and scope of claims, words such as "a", "an", "an" and/or "the" do not refer to the singular, and may also include the plural, unless the context clearly indicates an exception. Generally speaking, the terms "comprising" and "comprising" only suggest the inclusion of clearly identified steps and elements, and these steps and elements do not constitute an exclusive list, and the method or device may also contain other steps or elements.

The flow chart is used in the present invention to illustrate the operations performed by the system according to the embodiment of the present invention. It should be understood that the preceding or following operations are not necessarily performed in the exact order. Instead, various steps may be processed in reverse order or simultaneously. At the same time, other operations can also be added to these processes, or operations of a certain step or several steps can be removed from these processes.

Fig. 1 is a schematic diagram of an apparatus for configuring bone conduction hearing aids according to some embodiments of the present invention. As shown in FIG. 1 , the bone conduction hearing aid configuration system 100 may include a bone conduction hearing aid 110 , a processing device 120 , a memory 130 , one or more terminals 140 and a network 150 . In some embodiments, the bone conduction hearing aid device 110 , the processing device 120 , the memory 130 and/or the terminal 140 may be connected and/or communicate with each other via a wireless connection (eg, the network 150 ), a wired connection or a combination thereof. The connections between the elements in the bone conduction hearing aid configuration system 100 may vary. As an example only, the bone conduction hearing aid device 110 may be connected to the processing device 120 via a network 150, as shown in FIG. 1 . For another example, the bone conduction hearing aid device 110 may be directly connected to the processing device 120 . For another example, the memory 130 may be connected to the processing device 120 through the network 150 , as shown in FIG. 1 , or directly connected to the processing device 120 . As yet another example, the terminal 140 may be connected to the processing device 120 through the network 150 , as shown in FIG. 1 , or directly connected to the processing device 120 .

The bone conduction hearing aid device 110 can be used to obtain sound information (for example, ambient sound, wearer's voice, audio files obtained from other devices, etc.) etc. to the wearer's auditory center, so that the wearer can hear the sound information carried by the vibration signal. Specifically, the bone conduction hearing aid device may be a bone conduction hearing aid, or may be a bone conduction hearing aid earphone. In this manual, a bone conduction hearing aid is mainly used as an example for illustration.

In some embodiments, the bone conduction hearing aid device 110 (eg, bone conduction hearing aid) may include sound pickup elements, speaker elements, and the like. The sound pickup element is used to pick up sound information (also referred to as a first vibration signal, for example, ambient sound, wearer's voice) and process the picked up first vibration signal into an electrical signal carrying sound information. The speaker element can convert the electric signal carrying sound information acquired by the sound pickup element into a second vibration signal carrying sound information and transmit it to the auditory center of the wearer. For a detailed description of the bone conduction hearing aid device 110 , refer to other descriptions in the present application (for example, FIG. 2 and its detailed description).

In some embodiments, for different wearers of the bone conduction hearing aids, the configurations of the bone conduction hearing aids may be different because the wearers have different hearing levels (ie hearing loss levels). As described in this article, the configuration of bone conduction hearing aids refers to the parameter values (also referred to as parameters) related to the strength of the sound signal output by the bone conduction hearing aids and/or its determination process, so that the bone conduction hearing aids The device may output a sound signal based on the parameter value. The parameter values related to the output signal strength of the bone conduction hearing aid device may include a gain value (in dB), an analog output value (in dB), and the like. In some embodiments, the gain value may be a value for the hearing aid to amplify the strength of the sound signal, and the analog output value may be the analog output signal strength value of the hearing aid according to the input sound signal parameter (eg, the strength value of the sound signal). For example, the analog output value may be equal to the input value of the sound signal (ie, the intensity value, in dB) plus the gain value (in dB). The bone conduction hearing aid configuration system 100 can determine the configuration of the bone conduction hearing aid corresponding to the wearer's hearing level according to the wearer's hearing level. Based on this configuration, the bone conduction hearing aid device 110 can process and output acquired sound information (eg, ambient sound, wearer's voice, audio files acquired in other devices, etc.), so that the wearer can hear the sound.

The processing device 120 can process data and/or information obtained from the bone conduction hearing aid device 110 , the memory 130 and/or the terminal 140 . For example, the processing device 120 may acquire hearing loss data of the wearer of the bone conduction hearing aid device 110 . For another example, the processing device 120 may determine reference output parameters of the bone conduction hearing aid device 110 at each sound level and each frequency band based on the hearing loss data. Also for example, the processing device 120 may acquire the adjustment value of the reference output parameter. For another example, the processing device 120 may configure the bone conduction hearing aid device 110 based on the reference output parameter and the adjustment value.

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

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

The terminal 140 may include a mobile device 141 , a tablet 142 , a laptop 143 , a smart watch 144 , etc., or any combination thereof. In some embodiments, the mobile device 141 may include smart home devices (for example, control devices for smart appliances, smart monitoring devices, smart TVs, smart cameras), wearable devices (for example, glasses, helmets, accessories, clothes, etc.), Mobile devices (such as mobile phones, laptops, etc.), virtual reality devices (such as virtual reality helmets, virtual reality glasses, virtual reality goggles), etc., or any combination thereof. In some embodiments, the bone conduction hearing aid device 110 can be integrated into the terminal 140, for example, integrated into glasses, accessories and the like.

In some embodiments, users (eg, wearers of the bone conduction hearing aid 110 , system operators, doctors, etc.) can interact with the bone conduction hearing aid configuration system 100 through the terminal 140 . For example, the user may send a configuration request through the user interaction interface on the terminal 140; the processing device 120 obtains the wearer's hearing loss data after receiving the configuration request. For example, the processing device 120 may send a hearing loss data acquisition request 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 acquisition request. The processing device 120 may configure the bone conduction hearing aid device 110 based on the hearing loss profile.

The network 150 may include any suitable network that can facilitate the exchange of information and/or data for the bone conduction assistive hearing device configuration system 100 . In some embodiments, one or more components of the bone conduction hearing aid configuration system 100 (for example, bone conduction hearing aid 110, terminal 140, processing device 120, memory 130, etc.) can communicate with one or more The multiple bone conduction hearing aids configure other components of the system 100 to exchange information and/or data. For example, the processing device 120 may obtain the wearer's hearing loss data (eg, hearing level) from the bone conduction hearing aid device 110 via the network 150 . For another example, the processing device 120 may obtain user instructions from the terminal 140 via the network 150 . The network 150 can be and/or include a public network (e.g., the Internet), a private network (e.g., a local area network (LAN), a wide area network (WAN), etc.), a wired network (e.g., an Ethernet network), wireless network (e.g., 802.11 network, Wi-Fi network, etc.), cellular network (e.g., Long Term Evolution (LTE) network), frame forwarding network, virtual private network ("VPN "), satellite network, telephone network, routers, hubs, switches, server computers and/or any combination thereof. In some embodiments, network 150 may include one or more network access points. For example, network 150 may include wired and/or wireless network access points, such as base stations and/or Internet switching points, through which bone conduction hearing aids configure one or more of the system's 100 devices. Components may be connected to network 150 to exchange data and/or information.

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

Fig. 2 is a schematic structural diagram of a bone conduction hearing aid device according to some embodiments of the present invention. As shown in FIG. 2 , the bone conduction hearing aid 200 may include a speaker element 210 , a sound pickup element 220 and a support element 230 .

The speaker element 210 can convert a signal containing sound information into a vibration signal. In some embodiments, the audio information may include video or audio files in a specific data format, or data or files that can be converted into audio through a specific method. Signals containing audio information may include one or a combination of electrical signals, optical signals, magnetic signals, mechanical signals, and the like. Signals containing audio information can come from one source or multiple sources. Multiple signal sources can be correlated or uncorrelated. In some embodiments, the bone conduction hearing aid 200 can acquire signals containing sound information in a variety of different ways, and the acquisition of signals can be wired or wireless, and can be immediate or delayed. For example, the bone conduction hearing aid 200 can receive electrical signals containing sound information in a wired or wireless manner. For another example, the bone conduction hearing aid 10 may include components with a sound collection function (for example, the sound pickup component 220). By picking up the sound in the environment, the mechanical vibration of the sound is converted into an electrical signal, which can be processed by an amplifier to meet specific requirements. electrical signal.

It is an energy conversion process for the speaker element 210 to convert a signal containing sound information into a vibration signal. The process of conversion may include the coexistence and conversion of many different types of energy. The speaker element 210 may include one or more transducing devices, for example, electrical signals may be directly converted into mechanical vibrations through the transducing devices to generate sound. For another example, sound information can be included in the light signal, and the transducing device can realize the process of converting the light signal into a vibration signal. Other types of energy that can coexist and be converted during the working process of the transducer device include thermal energy, magnetic field energy, and the like. In some embodiments, the speaker element 210 can realize the transformation from the sound information signal to the vibration signal through the cooperation of the magnetic circuit element 211 and the vibrating element 213 (the magnetic circuit element 211 and the vibrating element 213 may be referred to as a transducing device). Wherein, the magnetic circuit element 211 is used to provide a magnetic field, and the vibrating element 213 is used to mechanically vibrate under the ampere force in the magnetic field. For example, magnetic circuit element 211 may include a magnet. The vibrating element 213 may include a magnetic vibrator and a vibrating piece. The magnetic vibrator (for example, voice coil) moves back and forth in the magnetic field under the action of Ampere's force, and drives the vibrating plate to vibrate during the movement. In the above process, the sound information can correspond to the vibration of the magnetic vibrator, and the vibration frequency and amplitude of the magnetic vibrator can be determined according to the frequency and intensity of the sound information. In some embodiments, one of the magnetic circuit element and the magnetic vibrator can be an electromagnet, and the strength of the magnetic field can be controlled by controlling the number of coils and/or the current intensity in the electromagnet, thereby controlling the vibration amplitude of the magnetic vibrator. The vibration frequency of the magnetic vibrator can be controlled by controlling the change frequency of the current direction of the coil in the electromagnet. In this process, the sound information can also be amplified. For example, the loudness of the sound information can be increased by increasing the vibration amplitude of the magnetic vibrator.

The specific energy conversion methods of the vibrating element may specifically include moving coil, electrostatic, piezoelectric, moving iron, pneumatic, electromagnetic, etc. The frequency response range and sound quality of the bone conduction hearing aid 200 will be affected by the vibrating components. For example, in a moving coil transducer, the vibrating element may include a wound cylindrical voice coil and a vibrating body (such as a vibrating plate or diaphragm), and the cylindrical voice coil driven by a signal current drives the vibrating body to vibrate in a magnetic field Sound production, stretching and contraction of vibrating body material, deformation, size, shape and fixing method of folds, magnetic density of magnetic field, etc., will all have a great impact on the sound quality of bone conduction hearing aids. The vibrating body in the vibrating element can be a mirror-symmetrical structure, a centrally-symmetrical structure, or an asymmetrical structure. The vibrating body can be provided with discontinuous hole-like structures, so that the vibrating body can generate a larger displacement, so that the bone conduction hearing aid device 200 Achieve higher sensitivity and increase the output power of vibration and sound; the vibrating body can be a torus structure, and multiple struts converging towards the center are set in the torus, and the number of struts can be two or more .

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

The support element 230 can provide support for other elements in the bone conduction hearing aid device 200 (for example, magnetic circuit elements, vibration elements and/or storage elements, power supply elements, communication elements (not shown in the figure), sound pickup assembly 220) effect. The support element 230 may include one or more housings, one or more connectors. One or more housings may form a housing cavity 232 for housing storage components, controllers, pickup components 220, communication components, battery packs, and the like. One or more connectors can connect the shell with other components in the bone conduction hearing aid device 200 (for example, magnetic circuit components, vibration components and/or storage components, power supply components, communication components (not shown in the figure), pick-up components, etc. sound component 220).

The wired connections involved in the bone conduction hearing aid 200 may include metal cables, optical cables or metal and optical hybrid cables, for example, coaxial cables, communication cables, flexible cables, spiral cables, non-metallic sheathed cables, metal sheathed cables, Multi-core cables, twisted-pair cables, ribbon cables, shielded cables, telecommunication cables, twin-pair cables, parallel twin-core conductors, twisted-pair wires, etc. or a combination of multiple types. The examples described above are only used for convenience of description, and the media of the wired connection may also be other types, for example, other transmission carriers of electrical signals or optical signals.

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

The above description of the structure of the bone conduction hearing aid device 200 is only a specific example, and should not be regarded as the only feasible implementation. Obviously, for professionals in the field, after understanding the basic principle of the bone conduction hearing aid 200, it is possible to formulate the specific method and steps for implementing the bone conduction hearing aid 200 without departing from this principle. Various modifications and changes in details and details, but these modifications and changes are still within the scope of the above description. For example, the bone conduction hearing aid 200 may include one or more processors that may execute one or more sound signal processing algorithms. Sound signal processing algorithms can modify or enhance the sound signal. For example, noise reduction, acoustic feedback suppression, wide dynamic range compression, automatic gain control, active environment recognition, active anti-noise, directional processing, tinnitus processing, multi-channel wide dynamic range compression, active howling suppression, volume control, etc. Or other similar, or any combination of the above, these amendments and changes are still within the protection scope of the patent application scope of the present invention. As another example, the bone conduction hearing aid may include one or more sensors, such as temperature sensors, humidity sensors, speed sensors, displacement sensors, and the like. The sensor can collect user information or environmental information. As another example, the storage element may not be necessary and may be removed from the bone conduction hearing aid.

In some embodiments, the bone conduction hearing aid configuration system is mainly based on the hearing loss data of the wearer, and configures according to a preset formula or a preset algorithm of the hearing aid configuration system. For example, in the hearing aid configuration system, after the wearer's hearing loss information is registered in the hearing aid configuration system, the hearing aid configuration system can automatically output the relevant parameter values of the hearing aid based on a preset algorithm. Directly configuring the bone conduction hearing aids only through preset algorithms may cause the configured bone conduction hearing aids 200 to generate relatively severe vibrations in certain scenarios (such as when the wearer speaks by himself or the ambient sound is too loud), causing the wearer discomfort.

The present invention provides a configuration system for bone conduction hearing aids. FIG. 3 is a module diagram of the configuration system for bone conduction hearing aids according to some embodiments of the invention. As shown in FIG. 3 , the bone conduction hearing aid configuration system 300 includes an acquisition module 310 , a reference output parameter determination module 320 , an adjustment value determination module 330 and a configuration module 340 . The connection form between modules can be wired, wireless, or a combination of both. Either module can be local, remote, or a combination of both. The correspondence between modules can be one-to-one or one-to-many.

In some embodiments, the obtaining module 310 can be used to obtain hearing loss data of the wearer.

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

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

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

In some embodiments, when using a multi-channel wide dynamic range compression system to configure bone conduction hearing aids, the adjustment value determination module 330 can be used to: compare the reference output parameters with the first threshold; the first threshold and the wearing It is related to the degree of vibration perception of each sound level in each frequency band; based on the comparison result of the reference output parameter and the first threshold value, the adjustment value corresponding to the reference output parameter is determined. In some embodiments, the adjustment value includes 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 be used to: respond to the reference output parameter being less than or equal to the first threshold, Then set the gain reduction value to 0dB; in response to the reference output parameter being greater than the first threshold, set the gain reduction value to the difference between the first threshold and the reference output parameter. In some embodiments, the adjustment value includes a reduction value of the maximum output of the multi-channel wide dynamic range compression system; the adjustment value determination module 330 may be used to: respond to the reference output parameter being less than or equal to the first threshold value, the reduction of the maximum output The value is set to 0dB; in response to the reference output parameter being greater than the first threshold, the reduced value of the maximum output is set to be greater than 0dB.

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

It should be noted that the above description of the processing module is only a specific example, and should not be regarded as the only feasible implementation. Each of the above-mentioned modules or units is not necessary, and each module or unit can be realized by one or more components, and the function of each module or unit is not limited thereto. Each of the above-mentioned modules or units can be added or deleted according to specific implementation scenarios or needs. Obviously, for professionals in the field, after understanding the basic principle of the capacity scheduling process, it is possible to make various amendments in form and details to the specific implementation methods and steps of the processing module without departing from this principle and changes, you can also make some simple deduction or replacement, and make some adjustments, combinations or splits to the order of each module or unit without any creative work, but these corrections and changes are still in the above-described within range.

Fig. 4 is a flowchart of a configuration method of a bone conduction hearing aid device according to some embodiments of the present invention. As shown in FIG. 4 , the flow of the configuration method of the bone conduction hearing aid device includes the following steps. Step 410 , acquiring hearing loss data of the wearer. Specifically, step 410 may be executed by the acquiring module 310 .

In some embodiments, the wearer's hearing loss information can be understood as information related to the wearer's hearing loss. The hearing loss data may include the wearer's hearing level (also called hearing threshold or hearing loss level) in each frequency band and at each sound level. In this manual, the unit used for the hearing level is dBHL. The higher the value of the hearing class, the more severe the wearer's hearing loss. In some embodiments, the hearing loss data may include data related to the wearer's historical hearing aids. For example, the data related to the hearing aids worn by the wearer in history may include the configuration data of bone conduction hearing aids used by the wearer in history.

In some embodiments, the hearing level may be in the range of 0dBHL-80dBHL. For example, the hearing level can be within 0dBHL-25dBHL to indicate normal hearing; the hearing level can be 26dBHL-40dBHL, mild hearing loss; the hearing level is 41dBHL-60dBHL, moderate hearing loss, showing difficulty hearing normal sounds; 61dBHL-80dBHL is severe Hearing loss, manifested as difficulty in hearing loud sounds; hearing level greater than 80dBHL, indicating severe hearing loss, manifested as difficulty in hearing loud sounds.

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

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

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

In some embodiments, a wearer of the bone conduction hearing aid may have different hearing levels corresponding to different sound levels in the same frequency band. For example, in the 250Hz-500Hz frequency band, the wearer's hearing level at 20dBC can be equal to a certain value in the range of 41dBHL-60dBHL; at 40dBC, the hearing level can be equal to a certain value in the range of 26dBHL-40dBHL; at 60dBC The hearing level under the sound level can be equal to a certain value in the range of 0dBHL-25dBHL.

In some embodiments, the wearer's hearing loss data can be obtained by performing an instant hearing test on the wearer. For example, a hearing aid fitter can use a hearing test device to perform a hearing test on the wearer (such as playing sound signals in various frequency bands and at various sound levels), so as to obtain the hearing loss information of the wearer. The hearing loss data collected by the hearing test equipment can be directly uploaded to the processing device (eg, the processing device 120 ) or to the storage device through the network (for example, the network 150 ), and the processing device can obtain the hearing loss data from the storage device. In some other embodiments, the wearer can upload his own hearing loss information through the terminal (for example, terminal 140), and the bone conduction hearing aids configuration system (for example, the bone conduction hearing aids configuration system 100) or the device (for example, The processing device 120) may receive the hearing loss data uploaded by the wearer in a wired or wireless manner. In some embodiments, the bone conduction hearing aid configuration system or device can retrieve the wearer's hearing loss data from the relevant memory (eg, memory 130 ). Step 420 , based on the hearing loss data, determine the reference output parameters of the bone conduction hearing aids at each sound level and each frequency band. Specifically, step 420 may be performed by the reference output parameter determination module 320 .

In some embodiments, the reference output parameter may be a reference analog output value of the bone conduction hearing aid device at each sound level and each frequency band (ie, the strength value of the signal analogously output by the bone conduction hearing aid device, in dB). In some embodiments, the reference output parameter may be a reference gain value of each sound level and each frequency band of the bone conduction hearing aid device (ie, the intensity value of the sound signal amplified by the bone conduction hearing aid device, in dB). It should be noted that when the sound signal input by the bone conduction hearing aid device meets the specified sound level and frequency band under the reference output parameters (for example, the reference gain value), the intensity value of the sound signal output by the bone conduction hearing aid device can be equal to the Reference analog output values for specific sound levels and frequency bands. In some embodiments, the reference output parameter is related to hearing loss level, sound level, frequency, and the like. In some embodiments, the reference analog output value of the bone conduction hearing aid is further related to the reference gain value of the bone conduction hearing aid. For example, the signal strength corresponding to the sound level may be amplified based on the gain value to determine the analog output value. In some embodiments, for different wearers, due to their different hearing loss data (eg, the degree of hearing loss at various sound levels), the reference output parameters will be different. In some embodiments, the sound level and frequency of the sound signal will affect the reference output parameters of the bone conduction hearing aid device, and different sound levels and/or different frequency bands may correspond to different reference output parameters. That is to say, under the same hearing loss level and the same sound level, different frequency bands may correspond to different reference output parameters; under the same hearing loss level and the same frequency band, different sound levels may correspond to different reference output parameters; Under the same sound level and the same frequency band, different hearing loss levels may correspond to different reference output parameters.

The sound level involved in this manual indicates the intensity of the sound signal, and the unit is decibel. In this specification, the measurement of sound level mainly adopts C frequency weighting measurement, that is, the unit of sound level in this specification is dBC. A frequency band refers to a frequency range of a sound signal in this specification. In some embodiments, the frequency of the sound signal can be divided into multiple continuous ranges to form different frequency bands.

In some embodiments, determining the reference output parameters of the bone conduction hearing aid device at each sound level and each frequency band may refer to determining the bone conduction hearing aid device at a preset sound level and/or a preset frequency and the preset sound output parameters. level and the reference output parameters corresponding to the hearing loss level of the wearer of the bone conduction hearing aid device at the preset frequency. In some embodiments, determining the reference output parameters of the bone conduction hearing aid device at each sound level and each frequency band may refer to determining the bone conduction hearing aid device at a preset sound level range and/or a preset frequency band and the preset Reference output parameters corresponding to the sound level range and the hearing loss level of the wearer of the bone conduction hearing aid device corresponding to the preset frequency band. Based on the determined reference output parameters, the bone conduction hearing aid device can amplify the sound signal input to the bone conduction hearing aid device (that is, the sound input signal) and convert it into a vibration signal, which is transmitted to the wearer of the bone conduction hearing aid device, so that The wearer can hear the sound. In some embodiments, the preset sound level, preset frequency, preset sound level range and/or preset frequency band may be a default setting of the system (for example, bone conduction hearing aid configuration system 100 ) or be set by the user . In some embodiments, the preset sound level may include 20dBC, 30dBC, 40dBC, 50dBC, 60dBC, 70dBC, 80dBC, etc. or a combination thereof. In some embodiments, the preset frequency may include 250Hz, 500Hz, 1000Hz, 2000Hz, 3000Hz, 4000Hz, 8000Hz, 10000Hz, etc. or a combination thereof. In some embodiments, the preset sound level range may include 10dBC-20dBC (may not include 20dBC), 20dBC-30dBC (may not include 30dBC), 30dBC-40dBC (may not include 40dBC), 40dBC-50dBC (may not include 50dBC), 50dBC-60dBC (may not include 60dBC), 60dBC-70dBC (may not include 70dBC), 70dBC-80dBC (may not include 80dBC), etc. or a combination thereof. In some embodiments, the preset frequency band may include 20Hz-250Hz (may not include 250Hz), 250Hz-500Hz (may not include 500Hz), 500Hz-1000Hz (may not include 1000Hz), 1000Hz-2000Hz (may not include 2000Hz) , 2000Hz-3000Hz (may not include 3000Hz), 3000Hz-4000Hz (may not include 4000Hz), 4000Hz-6000Hz (may not include 6000Hz), 6000Hz-10000Hz (may not include 10000Hz), etc. or combinations thereof. In some embodiments, the preset frequency bands may include 0Hz-125Hz (may not include 125Hz), 125Hz-375Hz (may not include 375Hz), 375Hz-625Hz (may not include 625Hz), 625Hz-875Hz (may not include 875Hz) , 875Hz-1375Hz (may not include 1375Hz), 1375Hz-1875Hz (may not include 1875Hz), 1875Hz-2625Hz (may not include 2625Hz), 2625Hz-4875Hz (may not include 4875Hz), etc. or combinations thereof. In some embodiments, the preset sound level, preset frequency, preset sound level range and/or preset frequency band may be adjusted by the system (eg, bone conduction hearing aid configuration system 100 ) or the user. For example, adjustments may be made to the hearing level of the wearer of the bone conduction hearing aid. For example, if the hearing level of the wearer is 10dBHL when the sound level is 80dBC (indicating that the wearer has normal hearing at this sound level), the maximum value of the preset sound level may not exceed 80dBC.

In some embodiments, the reference output parameter may be a reference gain value of the bone conduction hearing aid device, and the processing device 120 may be based on the hearing loss level and the value of each sound level and each frequency band in the hearing loss data, Determine the reference gain value of bone conduction hearing aids at each sound level and each frequency band. For example, based on the sound level of 20dBC, the frequency band of 375Hz-625Hz and the hearing level of the wearer of the bone conduction hearing aid device under the sound level of 20dBC and the frequency band of 375Hz-625Hz, it can be determined that the sound level of the bone conduction hearing aid device is 20dBC and the frequency band of 375Hz-625Hz The reference gain value below. In some embodiments, the reference output parameter may be a reference analog output signal strength value (ie, a reference analog output value) of the bone conduction hearing aid device. The processing device 120 may determine the reference analog output signal strength value ( i.e. refer to the analog output value). For example, the sound level of 30dBC and the frequency band of 125Hz-375Hz can be determined based on the hearing level of the wearer of the bone conduction hearing aid device at the sound level of 30dBC and the frequency band of 125Hz-375Hz. The reference analog output signal strength value (ie the reference analog output value).

In some embodiments, the processing device 120 (reference output parameter determination module 320) may first determine the reference gain values of the bone conduction hearing aids at each sound level and each frequency band based on the hearing loss data, and then based on the above-mentioned The gain value under each frequency band of the level determines the reference analog output signal strength value (that is, the reference analog output value) of the bone conduction hearing aid device at the corresponding sound level and corresponding frequency band.

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

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

Table 1 takes the sound level of 60dB SPL as an example to illustrate the reference gain values at each listening level and at each frequency band Frequency (Hz) Hearing Level (dBHL) 125-375 375-625 625-1375 1375-2625 2625-5375 5375-8000 20 0 0 0 0 0 0 40 5 8 10 10 8 5 60 10 16 20 20 16 10 80 15 twenty four 30 30 twenty four 15 100 20 32 40 40 32 20

In some embodiments, the processing device 120 may determine the reference output parameters according to the configuration model. The configuration model may represent the relationship between reference output parameters and frequency bands, sound levels, and hearing levels. Step 430 , acquiring the adjustment value of the reference output parameter. Wherein, the adjustment value is at least related to the frequency band. Specifically, step 430 may be performed by the adjustment value determining module 330 .

The adjustment value is the value used to adjust the reference output parameter. In some embodiments, the reference output parameter can be adjusted by adjusting the value, and the adjusted reference output parameter can be used as an actual analog output parameter of the bone conduction hearing aid device. Take the reference output parameter as the reference analog output value and reference gain value as an example to illustrate. For example, the reference analog output value (the strength value of the analog output signal) can be adjusted by adjusting the value, so that the adjusted reference analog output value can be used as the actual analog output value of the bone conduction hearing aid device (the actual analog output signal strength value ). For another example, the reference gain value (the strength value for amplifying the sound signal) of the bone conduction hearing aid device may be adjusted by adjusting the value, so that the adjusted reference gain value may be used as the actual gain value of the bone conduction hearing aid device.

In some embodiments, the adjustment value is used to lower the reference output parameter. For example, the adjustment value may be a value used to attenuate the reference analog output value, that is, the adjustment value may be subtracted from the reference output parameter. For another example, the adjustment value may also be a value used to attenuate the reference gain value, that is, the adjustment value may be subtracted from the reference gain value. For another example, the adjustment value may be a proportional value less than 1, that is, the reference output parameter may be multiplied by the adjustment value.

The vibration of bone conduction hearing aids is relatively strong when the frequency of the sound signal input to the bone conduction hearing aids is low. For example, bone conduction earphones are prone to vibration in the frequency range of 125Hz~625Hz. Therefore, the adjustment value can be set in the 0Hz~625Hz frequency band (or in the 125Hz~625Hz frequency band) (for example, use the adjustment value to reduce the reference output parameter in this frequency band) to improve the strong vibration of bone conduction hearing aids in this frequency band Case.

Fig. 8 is a graph of vibration perception thresholds at various frequencies when a wearer wears a bone conduction hearing aid device measured through experiments. In FIG. 8 , the vibration perception threshold (unit: dBV) may refer to the value obtained after numerical conversion of the driving voltage value (unit: V) of the bone conduction hearing aid device when the wearer can perceive vibration. If the driving voltage value of the bone conduction hearing aid is X (unit V); then the vibration perception threshold is converted to 20*log10(X/1) (unit dBV). As an example only, when the driving voltage of the bone conduction hearing aid is 1V, the corresponding vibration perception threshold is 0dBV; when the driving voltage of the bone conduction hearing aid is 0.5V, the corresponding vibration perception threshold is -6dBV. It can be seen from Figure 8 that the vibration perception threshold of bone conduction hearing aids in the frequency band below 1000 Hz is small, which means that bone conduction hearing aids are prone to vibration in the frequency band below 1000 Hz, especially in the frequency band of 125 Hz ~ 600 Hz. vibration. Among them, bone conduction hearing aids are most likely to vibrate at 125Hz, 250Hz, 400Hz, and 500Hz. Therefore, based on the data measured by the above experiment, the adjustment value can be set within the frequency range of 0 Hz to 625 Hz (or within the frequency range of 125 Hz to 625 Hz).

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

In some embodiments, the same frequency band and/or the same sound level may correspond to different adjustment values at different hearing levels. For example, the adjustment value of the hearing level at 26dBHL-40dBHL, the frequency range of 0Hz-625Hz and the 20dBC sound level can be the same as the adjustment value of the hearing level at 41dBHL-60dBHL, the frequency range of 0Hz-625Hz and the 20dBC sound level Are not the same. For another example, the adjustment value of the hearing level at 26dBHL-40dBHL, the frequency range of 20Hz-125Hz and the sound level of 20dBC and the adjustment of the hearing level at the frequency of 41dBHL-60dBHL, the frequency range of 20Hz-125Hz and the sound level of 20dBC The values are not the same. For another example, the adjustment value of the hearing level in the frequency band of 26dBHL-40dBHL, the frequency of 125Hz-375Hz and the sound level of 20dBC can be the same as the adjustment value of the hearing level in the frequency band of 41dBHL-60dBHL of the frequency of 125Hz-375Hz and the sound level of 20dBC Are not the same.

In some embodiments, the same frequency band and/or the same hearing level may correspond to the same adjustment value under different sound levels. For example, the adjustment value of the sound level in the frequency band of 20dBC-40dBC, the frequency of 0Hz-125Hz and the hearing level of 41dBHL-60dBHL and the adjustment value of the sound level of 40dBC-60dBC, the frequency range of 0Hz-125Hz and the hearing level of 41dBHL-60dBHL Can be the same. Another example, the adjustment value of the sound level in the frequency range of 20dBC-40dBC, the frequency of 125Hz-375Hz and the hearing level of 26dBHL-40dBHL is the same as the adjustment value of the sound level of 40dBC-60dBC, the frequency of the frequency range of 125Hz-375Hz and the hearing level of 26dBHL-40dBHL The adjustment values can be the same.

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

In some embodiments, the same sound level and/or the same hearing level in different frequency bands may correspond to the same adjustment value. For example, if the frequency is in the 0Hz-125Hz frequency band (may not include 125Hz), the adjustment value of the sound level is 20dBC-40dBC and the hearing level 41dBHL-60dBHL is the same as the adjustment value of the frequency 125Hz-375Hz frequency band, the sound level is 20dBC-40dBC and the hearing level 41dBHL- The adjustment value of 60dBHL can be the same. For another example, the frequency is in the frequency range of 125Hz-375Hz (may not include 375Hz), the sound level is in the range of 40dBC-60dBC and the adjustment value of the hearing level is 26dBHL-40dBHL, and the frequency is in the frequency range of 375Hz-625Hz, the sound level is in the range of 40dBC-60dBC and the hearing level The adjustment value of 26dBHL-40dBHL can be the same.

In some embodiments, the same sound level and/or the same hearing level in different frequency bands may correspond to different adjustment values. For example, if the frequency is in the 0Hz-125Hz frequency band (may not include 125Hz), the adjustment value of the sound level is 20dBC-40dBC and the hearing level 41dBHL-60dBHL is the same as the adjustment value of the frequency 125Hz-375Hz frequency band, the sound level is 20dBC-40dBC and the hearing level 41dBHL- The adjustment value of 60dBHL can be different. For another example, the frequency is in the frequency range of 125Hz-375Hz (may not include 375Hz), the sound level is in the range of 40dBC-60dBC and the adjustment value of the hearing level is 26dBHL-40dBHL, and the frequency is in the frequency range of 375Hz-625Hz, the sound level is in the range of 40dBC-60dBC and the hearing level The adjustment values of 26dBHL-40dBHL can be different.

In some embodiments, the adjustment value is at least related to a frequency band, and the adjustment value may be different in different frequency bands. In some embodiments, different frequency bands may correspond to different adjustment values, and frequencies in the same frequency band may correspond to the same adjustment value; in some embodiments, different frequencies may correspond to different adjustment values. In some embodiments, the adjustment value is in the range of 1dB-12dB in the frequency band where the frequency is greater than 0 Hz and less than or equal to 625 Hz. By setting the adjustment value to the above-mentioned value within the above-mentioned frequency range, and then configuring the bone conduction hearing aid device, the problem that the wearer wears the bone conduction hearing aid device in some scenes with relatively strong vibration can be improved, and it can also Guaranteed to have a small impact on speech intelligibility. In some embodiments, as the frequency increases, the adjustment value decreases. For example, the adjustment value corresponding to a frequency of 125 Hz may be 5 dB; the adjustment value corresponding to a frequency of 250 Hz may be 3 dB; and the adjustment value corresponding to a frequency of 500 Hz may be 1 dB. For another example, the adjustment value corresponding to a frequency of 125 Hz may be 10 dB; the adjustment value corresponding to a frequency of 250 Hz may be 7 dB; the adjustment value corresponding to a frequency of 500 Hz may be 4 dB. In some embodiments, in the frequency band where the frequency is greater than 625 Hz and less than or equal to 8000 Hz, the adjustment value may be 0dB-4dB. In some embodiments, the adjustment value may be 0 in the frequency band where the frequency is greater than 625 Hz and less than or equal to 8000 Hz.

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

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

In some embodiments, the adjustment value is 10dB-12dB in the frequency band where the frequency is greater than 0 Hz and less than or equal to 125 Hz. In some embodiments, the adjustment value is 7dB-9dB in the frequency band where the frequency is greater than 125Hz and less than or equal to 375Hz. In some embodiments, the adjustment value is 4dB-6dB in the frequency band where the frequency is greater than 375Hz and less than or equal to 625Hz. By setting the adjustment value to the above-mentioned value in the above-mentioned frequency range, and then configuring the bone-conduction hearing aid device, the vibration problem when the wearer with a hearing level of 40dBL wears the bone-conduction hearing aid device in the corresponding frequency band can be solved, and also It can have little impact on the speech intelligibility and ensure the hearing aid effect of the wearer.

Figures 9 to 11 are graphs showing the experimental results of the speech recognition rate tests on three wearers (wearer 1, wearer 2 and wearer 3). Figures 9 to 11 all take the reference output parameter as the reference analog output value as an example, showing the wearer's speech recognition rate, vibration feeling and volume before the reference analog output value is reduced, and the corresponding reference analog output value in each frequency band. The wearer's speech recognition rate, vibration sense and volume at different adjustment values. Figures 9 to 11 have carried out 6 sets of tests for each tester. In the table, negative numbers indicate that the adjustment value has reduced the reference output parameter (such as the reference analog output value). For example, -5 indicates that the adjustment value is 5dB, and the reference The output value is reduced by 5dB; for another example, -15 means that the adjustment value is 15dB, which reduces the reference analog output value by 15dB.

As shown in FIGS. 9 to 11 , when the reference analog output value is lowered based on the adjustment value, the speech recognition rate may be lowered, the sense of vibration may be reduced but the volume may be reduced. It can be seen from the table that at a frequency of 125Hz, if the adjustment value is 5dB (or less than this value), that is, the reference analog output value is reduced by 5dB, the speech recognition rate does not change significantly; at a frequency of 250Hz, if the adjustment value is 3dB (or less than this value), that is, the reference analog output value is reduced by 3dB, and the speech recognition rate has no significant change; at a frequency of 500Hz, if the adjustment value is 1dB (or less than this value), that is, the reference analog output value is reduced by 1dB, the speech recognition rate rate did not change significantly. At the same time, if the adjustment value is set according to the above values, the tester can feel the vibration when he speaks, but the volume is good (that is, the volume is within the volume range that the wearer can basically hear clearly).

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

At a frequency of 125Hz, if the adjustment value is 17dB (or greater than 10dB but less than 17dB range), that is, the reference analog output value is reduced by 17dB, the reduction in speech recognition rate may be greater than 5% (such as 10%); at 250Hz At the frequency, if the adjustment value is 15dB (or greater than 7dB but less than 15dB range), that is, the reference analog output value is reduced by 15dB, and the reduction of the speech recognition rate may be greater than 5% (such as 10%); at a frequency of 500Hz, If the adjustment value is 10dB (or greater than 4dB but less than 10dB range), that is, the reference analog output value is reduced by 10dB, the reduction in speech recognition rate may be greater than 5% (such as 10%). At the same time, if the adjustment value is set according to the above values, the tester may feel that the volume is low (that is, the wearer may not be able to hear clearly because the volume is too low).

Within a certain range (such as the range where the adjustment value is less than 17dB), the greater the number of adjustment values, the better the effect of reducing the vibration of bone conduction hearing aids. However, it can be seen from Figures 9 to 11 that the adjustment value The larger the number may lead to lower output signal strength of bone conduction hearing aids, which will greatly affect the speech recognition rate (for example, it may lead to a lower speech recognition rate), and when the adjustment value is within the above range in the above embodiment When the value is , it can not only solve the vibration problem when the wearer with a hearing level of 30dBL-40dBL wears bone conduction hearing aids in the corresponding frequency band, but also ensure that the impact on speech intelligibility is small.

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

In some embodiments, the adjusted value of the reference output parameter may be related to the frequency band and the hearing level of the wearer. The corresponding adjustment values of the reference output parameters in the same frequency band at different hearing levels are different; the corresponding adjustment values of the reference output parameters at the same hearing level, the same frequency band, and different sound levels can be the same. For a detailed description of this embodiment, please refer to Figure 5 and its Related instructions.

In some embodiments, the adjusted value of the reference output parameter may be related to frequency band and sound level. The corresponding adjustment values of the reference output parameters in the same frequency band under different sound levels are different; however, the corresponding adjustment values of the reference output parameters in different listening levels, the same sound level, and the same frequency band can be the same. For the detailed description of this embodiment, please refer to the figure 6 and its related instructions. Step 440 , configure the bone conduction hearing aid device based on the reference output parameter and the adjustment value. Specifically, step 440 may be performed by the configuration module 340 .

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

In some embodiments, the processing device 120 (configuration module 340) can reduce the reference output parameter according to the adjustment value to obtain the actual output parameter, and configure the bone conduction hearing aid device based on the reduced reference output parameter (ie, the actual output parameter) . Reducing the reference output parameter according to the adjustment value can be directly subtracting the adjustment value from the reference output parameter, or adjusting related setting parameters of other bone conduction hearing aids through the adjustment value, so as to achieve the purpose of reducing the reference output parameter.

In some embodiments, the processing device 120 (configuration module 340 ) can configure the magnetic circuit element based on the adjustment value and the reference output value, so as to realize the configuration of the bone conduction hearing aid device. In some embodiments, configuring the bone conduction hearing aid includes setting various parameters of the bone conduction hearing aid, so that the bone conduction hearing aid has parameters related to signal output strength (for example, gain value, analog output value) is a preset value, for example, a reference parameter adjusted based on an adjustment value. For example, the reference gain value of the bone conduction hearing aids to the sound signal can be adjusted by adjusting the current of the electromagnet in the magnetic circuit element, the resistance of the amplifier circuit of the pickup element, etc., and the reference gain of the bone conduction hearing aids can be adjusted. Analog output value to realize the configuration of bone conduction hearing aids.

In some embodiments, based on the reference output parameters and adjustment values, an equalization adjustment system (EQ system) or an automatic gain control system (AGC system), etc. may be used to configure the bone conduction hearing aid.

In other embodiments, based on the reference output parameters and adjustment values, a multi-channel wide dynamic range compression system (WDRC system) may be used to configure the bone conduction hearing aid. The multi-channel wide dynamic range compression system can first use the filter bank to divide the sound signal into multiple channels according to the frequency band, and compress the signal of each channel separately, so that an appropriate compression ratio can be designed according to the hearing loss corresponding to the frequency band and compression threshold, and then synthesize the processed signals of each channel into one signal. The multi-channel wide dynamic range compression system allows for more flexible hearing compensation. In the multi-channel wide dynamic range compression system, by adjusting each reference output parameter and adjustment value, the compression ratio and compression threshold of the signal of each channel can be adjusted, thereby adjusting the reference output parameter of each channel.

Fig. 5 is an exemplary flow chart according to the method for obtaining an adjustment value of a reference output parameter. The adjustment values determined using the method shown in FIG. 5 are related to the hearing level of the wearer. As shown in Figure 5, the process includes the following steps. Step 510 , determining first thresholds corresponding to each frequency band and each sound level, wherein the first threshold is related to the wearer's vibration perception degree to each sound level of each frequency band.

The degree of vibration perception may be used to indicate the degree of vibration perceived by the user when wearing the bone conduction hearing aid. In some embodiments, the degree of vibration perception may include a plurality of grades used to indicate the degree of perceived vibration. The higher the level, the greater the vibration that the user can perceive. In some embodiments, the levels may include the first level, the second level, the third level, the fourth level, and the fifth level, and the corresponding vibration experience levels may include "no vibration", "extremely slight vibration", "slight vibration". Vibration", "obvious vibration, but acceptable", "severe vibration, unacceptable". In some embodiments, different levels may be represented by 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.

In some embodiments, the first threshold may be the output signal intensity of the corresponding bone conduction hearing aid device when the wearer's vibration perception level is below a certain level, that is, when the intensity of the output signal of the bone conduction hearing aid device reaches When the first threshold is reached, the wearer can feel the vibration at this level. For example, the first threshold may be the output signal strength of the corresponding bone conduction hearing aid device (that is, the reference output parameter) when the wearer's vibration perception level is at the third level, that is, when the output signal strength of the bone conduction hearing aid device is When the first threshold is reached, the wearer can feel the slight vibration corresponding to the third level. For another example, the first threshold may be the output signal strength of the corresponding bone conduction hearing aid device when the wearer's vibration experience is at the fourth level, that is, when the output signal strength of the bone conduction hearing aid device reaches the first threshold , the wearer can feel the obvious vibration corresponding to the fourth level, but the vibration intensity can be accepted. In some embodiments, when the output signal strength of the bone conduction hearing aid device is greater than the first threshold, the wearer may feel the vibration at the level corresponding to the first threshold (for example, the slight vibration corresponding to the third level) If there is strong vibration and poor wearing experience, it is necessary to adjust (reduce) the reference output parameter so that the output signal strength of the bone conduction hearing aid is less than the first threshold.

In some embodiments, preliminary reference output parameters corresponding to each sound level and each frequency band of the wearer of the bone conduction hearing aid device can be obtained. For detailed description on obtaining reference output parameters, refer to operation 420 in FIG. 4 . In some embodiments, the first threshold may be different for different wearers. For example, the wearer of the bone conduction hearing aid device can be tested to determine the output signal strength and the corresponding vibration feeling degree of the wearer of the bone conduction hearing aid device under the preliminary reference output parameters at each sound level and each frequency band, and The reference output parameters are obtained by adjusting the preliminary reference output parameters to adjust the output signal strength and vibration perception, so that the wearer's vibration perception reaches a certain level (for example, the third level, slight vibration), and then determine each frequency band and each sound level corresponding to the first threshold. In some embodiments, the adjusted preliminary reference output parameter (ie, the reference output parameter, such as a reference analog output value) may be equal to the adjusted signal output strength. The first threshold may be equal to the corresponding adjusted output signal strength or the reference analog output value when the wearer's vibration experience reaches a certain level (for example, the third level, slight vibration).

In some embodiments, the first threshold may be the same for different wearers. For example, the first threshold can be specifically determined according to the following method: multiple testers are tested to determine the signal output strength of each tester when they subjectively feel the slight vibration of the second level at each sound level and each frequency band, and the The above signal output strength is used as test data; the test data are integrated and selected to obtain the first threshold. This first threshold can be adapted to different wearers. In some embodiments, the integration and selection of the test data can be: for a certain frequency band, only considering the lowest value of the output parameter when each tester subjectively feels a slight vibration in each sound level under the frequency band, And the lowest value is further selected from the lowest values of the output parameters when the slight vibration is subjectively felt by each tester in each sound level as the first threshold value.

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

In some embodiments, the first thresholds corresponding to the same frequency band with different sound levels can be the same, for example, a minimum value (for example, 48 dB) can be selected as the first threshold of the frequency band in the range of the corresponding first thresholds in the above-mentioned frequency bands. A threshold value, so that the bone conduction hearing aids will not generate severe vibrations when the received sound signals are in the same frequency band with different sound levels. For example, in the frequency band where the frequency is greater than 0 Hz and less than or equal to 125 Hz, the first threshold is 48 dB. In the frequency band where the frequency is greater than 125 Hz and less than or equal to 375 Hz, the first threshold is 49 dB. In the frequency band where the frequency is greater than 375 Hz and less than or equal to 625 Hz, the first threshold is 50 dB.

In some embodiments, the first thresholds corresponding to the same frequency band at different sound levels may be different. In some embodiments, the higher the sound level in the same frequency band, the greater the first threshold may be. For example, in the frequency range from 0 Hz to 125 Hz, the sound level is 20dBC-40dBC, and the first threshold is 48 dB; in the frequency range from 0 Hz to 125Hz, the sound level is 40dBC-50dBC, The first threshold is 49 dB; in the frequency band between 0 Hz and less than or equal to 125 Hz, the sound level is 50dBC-60dBC, and the first threshold is 50 dB.

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 (for example, 48 dB) may be selected as the first threshold within the range of the corresponding first thresholds in each of the above frequency bands. The first threshold value of the frequency band, so that when the sound signal received by the bone conduction hearing aid device is in the same frequency band, no matter what sound level the sound signal is and no matter what hearing level the wearer is at, no relatively severe vibration will be generated.

In some embodiments, different hearing levels and different sound levels correspond to different first thresholds corresponding to the same frequency band. For example, at a hearing level of 40dBHL within a frequency band greater than 125 Hz and less than or equal to 375 Hz and a sound level of 60dBC, the first threshold may be 49 dB. While the hearing level is 10dBHL frequency in the frequency band greater than 125Hz but less than or equal to 375 Hz and the sound level of 75dBC, the first threshold can be 50 dB. For another example, when the hearing level is 30dBHL within the frequency band greater than 375 Hz and less than or equal to 625 Hz and the sound level is 70dBC, the first threshold may be 55dB. For example, at a hearing level of 20dBHL within a frequency band greater than 375 Hz and less than or equal to 625 Hz and a sound level of 75dBC, the first threshold may be 56dB. In some embodiments, the first thresholds corresponding to different sound levels and different hearing levels in different frequency bands may be the same. The first thresholds corresponding to different sound levels in the frequency bands, so that the bone conduction hearing aids will not generate severe vibrations when the received sound signals are in different sound levels and different frequency bands. For example, in the frequency band where the frequency is greater than 0 Hz-625 Hz, the first threshold is 48 dB. Step 520 , determining the second threshold corresponding to each frequency band and each sound level, wherein the second threshold is related to the speech recognition rate of the wearer in each frequency band.

Speech recognition rate (ie, speech intelligibility) can be the ratio of understood or clearly understood words to heard words. The speech recognition rate can be used to characterize the hearing sensitivity and clarity of the language heard by the wearer wearing the hearing aid, and then reflect the hearing aid effect of the wearer to a certain extent. The higher the speech recognition rate, the higher the hearing sensitivity of the wearer after wearing the hearing aid, the higher the hearing clarity, and the better the hearing aid effect. In some embodiments, if the speech recognition rate is greater than or equal to 70%, it can be considered that the hearing aid effect is good; and if the speech recognition rate is less than or equal to 50%, it can be considered that the hearing aid effect is not ideal and needs to be re-adjusted or configured Bone conduction hearing aids.

In some embodiments, the adjustment (for example, reduction) of the reference output parameter may affect the strength of the output signal of the bone conduction hearing aid device, which in turn may affect the speech recognition rate of the bone conduction hearing aid device. For example, based on the experimental results in FIGS. 9 to 11 , it can be known that within a certain range (such as the range where the adjusted value is less than 17 dB), the larger the adjusted value, the lower the speech recognition rate may be. The second threshold may be used to ensure that the speech recognition rate adjusted by the reference output parameter is within a certain range (for example, higher than a certain threshold). That is to say, the second threshold can be used to control the reduction of the speech recognition rate adjusted by the reference output parameter within a certain range. For example, when the adjustment value does not exceed the second threshold, the decrease in the speech recognition rate of the wearer wearing the hearing aid can be small compared to the unadjusted reference output parameter, for example, the decrease in the speech recognition rate can be less than or equal to 5%. The reduction of the speech recognition rate may be the speech recognition rate when the reference output parameter is not adjusted minus the speech recognition rate after the reference output parameter is adjusted.

In some embodiments, the second threshold may be the maximum value of the adjustment value corresponding to the reference output parameter of the bone conduction hearing aid at the preset speech recognition rate when the wearer wears the bone conduction hearing aid, that is, when When the adjustment value corresponding to the reference output parameter of the bone conduction hearing aid device reaches the second threshold, the speech recognition rate when the wearer wears the bone conduction hearing aid device is the preset threshold. When the adjustment value is greater than the second threshold, the speech recognition rate will be lower than the preset speech recognition rate when the wearer wears the bone conduction hearing aid.

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 device and the speech recognition rate is 80% at 125 Hz, that is, the second threshold is 5dB. That is to say, when the adjustment value corresponding to the reference output parameter of the bone conduction hearing aid at 125 Hz is the second threshold, the speech recognition rate can be 80% when the wearer wears the bone conduction hearing aid. For another example, as shown in FIG. 11 , the second threshold may be the adjustment value corresponding to the reference output parameter with a speech recognition rate of 60% at 250 Hz when the wearer wears the bone conduction hearing aid, that is, the second threshold is 12dB. That is to say, when the adjustment value corresponding to the reference output parameter of the bone conduction hearing aid at 250 Hz is the second threshold, the speech recognition rate can be 60% when the wearer wears the bone conduction hearing aid.

In some embodiments, the second threshold may be determined according to a preset speech recognition rate threshold. For example, the second threshold may be determined based on the experimental results of the speech recognition rate test performed on the wearer in FIGS. 9 to 11 . As an example only, referring to FIG. 10 , when the bone conduction hearing aid is configured based on the unadjusted reference output parameters, the speech recognition rate of the wearer is 80%, and if the reference output parameter is set to be reduced, the speech recognition rate is not less than 75% ( That is, if the reduction of the speech recognition rate is less than or equal to 5%), the second threshold can be 10dB; if the speech recognition rate is set to be no less than 80% (that is, the speech recognition rate hardly decreases), the second threshold can be 5dB.

In some embodiments, the severe vibration phenomenon of bone conduction hearing aids is more obvious in the low frequency band (such as the frequency band of 0Hz-625Hz), and the adjustment value of the reference output parameter can be set in the low frequency band to reduce the reference output parameter and reduce the user's Vibration intensity that can be perceived; correspondingly, a second threshold can be set in a low frequency band (such as a frequency band of 0 Hz-625 Hz), so as to determine the adjustment value of the reference output parameter based on the first threshold. In some embodiments, different frequency bands correspond to different second thresholds. For example, in the frequency band where the frequency is greater than 0 Hz and less than or equal to 125 Hz, the second threshold is within the range of 5dB-10dB. In some embodiments, the second threshold is in the range of 3dB-7dB in the frequency band where the frequency is greater than 125Hz and less than or equal to 375Hz. In some embodiments, the second threshold is in the range of 1dB-4dB in the frequency band where the frequency is greater than 375Hz and less than or equal to 625Hz. In some embodiments, the higher the frequency band at the same sound level, the smaller the second threshold.

In some embodiments, the second thresholds corresponding to the same frequency band at different hearing levels may be the same. For example, no matter whether the hearing level of the wearer is 30dBHL or 40dBHL, the second threshold can be set according to the above range. In some embodiments, the second thresholds corresponding to the same frequency band at different hearing levels may be different. For example, in the frequency range from 0Hz to 125Hz, the hearing level is 30dBHL, and the second threshold is 5dB; in the frequency range from 0Hz to 125Hz, the hearing level is 40dBHL, and the second threshold is 15dB. In some embodiments, the second thresholds corresponding to the same frequency band at different sound levels may be the same. In some embodiments, a minimum value within the above range may be selected as the second threshold, so that the bone conduction hearing aid device will not affect the speech recognition rate too much when the received sound signals are at different sound levels. For example, in a frequency band whose frequency is greater than 125 Hz and less than or equal to 375 Hz, the second threshold may be 3 dB. In some embodiments, the second threshold may be 5dB within a frequency band where the frequency is greater than 0 Hz and less than or equal to 125 Hz. In some embodiments, the second threshold may be 1dB within a frequency band where the frequency is greater than 375Hz and less than or equal to 625Hz.

In some embodiments, the second thresholds corresponding to the same frequency band with different sound levels may be different. For example, in the frequency range between 0 Hz and 125 Hz, the sound level is 60 dBC, and the second threshold is 5 dB; in the frequency range between 0 Hz and 125 Hz, the sound level is 75 dBC, and the second threshold is 10 dB. Step 530 , determining an adjustment value based on the reference output parameter, the first threshold and the second threshold.

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 can be determined based on experience or a preset formula. The initial adjustment value may then be compared with a second threshold, and if the initial adjustment value is greater than the second threshold, the initial adjustment value is decreased so that the initial adjustment value is less than or equal to the second threshold. If the initial adjustment value is less than or equal to the second threshold, the initial adjustment value is determined as the adjustment value.

In some embodiments, a reference output parameter corresponding to a specific frequency band and a specific sound level can be subtracted from the first threshold corresponding to the specific frequency band and specific sound level to obtain a comparison value; then, the comparison value is compared with the specific frequency band and specific sound level The second threshold value corresponding to the sound level is compared; based on the comparison result of the comparison value and the second threshold value, the adjustment value corresponding to the reference output parameter in the specific frequency band and the specific sound level is determined.

For the determination methods of the first threshold and the second threshold, please refer to the relevant description above. The comparison value can be positive, negative, or zero. Comparing the comparison value with the second threshold may be a numerical comparison to determine a magnitude relationship between the comparison value and the second threshold. The comparison result of the comparison value and the second threshold may include that the comparison value is smaller than the second threshold, the comparison value is equal to the second threshold, or the comparison value is greater than the second threshold. The adjustment value corresponding to the reference output parameter is determined based on a comparison result between the comparison value and the second threshold, which may be based on a magnitude relationship between the comparison value and the second threshold.

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

When the reference output parameter is less than or equal to the first threshold, after the bone conduction hearing aid is configured according to the reference output parameter, the wearer is less likely to feel vibration after wearing the bone conduction hearing aid, and there is no need to adjust the reference output parameter . When the reference output parameter is greater than the first threshold, after the bone conduction hearing aid is configured according to the reference output parameter, the wearer is more likely to feel a strong vibration after wearing the bone conduction hearing aid, and the reference output parameter needs to be adjusted . Furthermore, when determining the adjustment value, not only the vibration risk of the bone conduction hearing aid brought by the reference output parameter should be considered, but also the influence of the adjusted reference output parameter on the speech recognition rate of the bone conduction hearing aid should be considered. Since the second threshold is a threshold related to the speech recognition rate, by comparing the above comparison value with the second threshold, try to ensure that the adjustment value is less than or equal to the second threshold, and minimize the impact on the speech caused by the adjustment of the reference output parameters. impact on the recognition rate.

Fig. 6 is an exemplary flow chart according to the method for obtaining an adjustment value of a reference output parameter. In some embodiments, when using a multi-channel wide dynamic range compression system to configure a bone conduction hearing aid, the process shown in FIG. 6 may be used to determine the adjustment value corresponding to the reference output parameter. As shown in FIG. 6 , the process of determining the adjustment value corresponding to the reference output parameter may include the following steps: Step 610 , comparing the reference output parameter with a first threshold. Wherein, the first threshold is related to the wearer's degree of vibration perception of each sound level in each frequency band.

For the relevant description of the first threshold in this step and the method for determining the first threshold, please refer to the relevant content about the first threshold in step 510 . Comparing the reference output parameter with the first threshold may be comparing the reference output parameter with the first threshold in magnitude.

Step 620, based on the comparison result of the reference output parameter and the first threshold, determine the adjustment value corresponding to the reference output parameter.

Refer to the related content of step 430 for the relevant description of the adjustment value corresponding to the output parameter. The comparison result of the reference output parameter and the first threshold may include comparison results of the reference output parameter being greater than the first threshold, the reference output parameter being equal to the first threshold, and the reference output parameter being equal to the first threshold. In some embodiments, it may be determined whether the adjustment value is 0 based on whether the reference output parameter is greater than the first threshold. For example, when the reference output parameter is smaller than the first threshold, the adjustment value is 0; when the reference output parameter is greater than the first threshold, the adjustment value is greater than 0.

In some embodiments, when the bone conduction hearing aid device is configured using a multi-channel wide dynamic range compression system, the adjustment value may include the multi-channel wide dynamic range compression system when at least one of the sound levels is greater than the sound level threshold Gain reduction value. In some embodiments, the sound level threshold may be 70 dB. During the wearer's use of the bone conduction hearing aid, the sound level of the sound signal of the daily conversation is generally about 60dB. The sound level of the sound signal is greater than or equal to 70dBC may occur when the wearer speaks by himself or the environment is relatively noisy. At this time, the bone conduction hearing aids may generate relatively strong vibrations, so the adjustment value is set for this sound level range Internal adjustment (such as lowering) of the reference output parameters can improve the vibration of bone conduction hearing aids, and can make the speech recognition rate of the wearer almost unaffected in daily conversations.

The gain when at least one sound level in each sound level is greater than the sound level threshold can be called high level gain (High Level Gain), and the adjustment value can include the high level gain (High Level Gain) of the multi-channel wide dynamic range compression system Lower the value. The high level gain (High Level Gain) of the multi-channel wide dynamic range compression system may be the gain when the sound level of the sound signal is greater than a sound level threshold (for example, 70dB). The gain of the multi-channel wide dynamic range compression system when at least one of the sound levels is greater than the sound level threshold can be determined based on the wearer's hearing loss data, for example, can be determined according to an empirical formula. For example, the empirical formula may be to determine the high level gain (High Level Gain) of the multi-channel wide dynamic range compression system based on the wearer's hearing level. The adjustment value may be a specific value for reducing the high-level gain obtained by an empirical formula.

In some embodiments, based on whether the reference output parameter is greater than the first threshold, it may be determined whether the gain reduction value is 0 (that is, whether to reduce the gain when at least one of the sound levels is greater than the sound level threshold). For example, when the reference output parameter is smaller than the first threshold, the gain reduction value is 0; when the reference output parameter is greater than the first threshold, the gain reduction value is greater than 0.

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 reduction value can be used to reduce the gain value when the sound level is greater than the sound level threshold, and the reduced The gain value of is used as the input parameter of the multi-channel wide dynamic range compression system. When at least one sound level in each sound level is greater than the sound level threshold, bone conduction hearing aids are prone to vibration, through the set frequency band (frequency range greater than 0Hz and less than or equal to 625Hz) and when the sound level is higher than the sound level When the level threshold is set, the gain reduction value is determined in the above-mentioned way, and the gain reduction value is used as the adjustment value, which can ensure that the reference output parameters are not affected when the sound level of the sound signal is lower than the sound level threshold, and when the sound level of the sound signal Below the sound level threshold, the reference output parameter is reduced. In this way, while ensuring the speech recognition rate of the bone conduction hearing aid, it can also improve the severe vibration of the bone conduction hearing aid in certain scenes.

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

In this embodiment, if the reference output parameter is less than or equal to the first threshold, the wearer is less likely to experience severe vibration when wearing the bone conduction hearing aid, and there is no need to adjust (reduce) the high-level gain, so the high-level gain The gain reduction value is set to 0. If the reference output parameter is greater than the first threshold, the wearer has a high probability of feeling severe vibration when wearing the bone conduction hearing aid, and needs to adjust (reduce) the high-level gain to reduce the reference output parameter so that the reference output The parameter can be less than the first threshold.

In some embodiments, when the bone conduction hearing aid device is configured using a multi-channel wide dynamic range compression system, the adjustment value may include the multi-channel wide dynamic range compression system when at least one of the sound levels is greater than the sound level threshold Reduced value for Output Limit. In some embodiments, the sound level threshold may be 70 dB. In this embodiment, the situation that the sound level of the sound signal is greater than or equal to 70dBC may occur when the wearer speaks by himself or the environment is relatively noisy. At this time, the bone conduction hearing aid device may generate relatively strong vibrations, so setting the adjustment value with Adjusting the reference output parameters (the maximum output of the multi-channel wide dynamic range compression system) within this sound level range can improve the vibration of bone conduction hearing aids, and can make the speech recognition rate of the wearer hardly affected during daily conversations. influences.

The maximum output can be understood as the limit value of the reference output parameters in each frequency band. When the reference output parameters are greater than the maximum output, the reference output parameters of the bone conduction hearing aids are equal to the maximum output. The maximum output (Output Limit) of the multi-channel wide dynamic range compression system can be determined according to an empirical formula based on the wearer's hearing loss data. For example, the empirical formula may be to determine the maximum output (Output Limit) of the multi-channel wide dynamic range compression system based on the hearing level of the wearer. The adjustment value may be a specific numerical value that reduces the maximum output obtained by an empirical formula. The empirical formula can be set by the user or a default setting of the bone conduction hearing aid configuration system.

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

That is to say, if the reference output parameter is less than or equal to the first threshold, the wearer is less likely to experience severe vibration when wearing the bone conduction hearing aid, and there is no need to adjust (reduce) the maximum output; if the reference output parameter is greater than the first threshold threshold, the wearer has a higher probability of feeling severe vibration when wearing the bone conduction hearing aid device, and needs to adjust (reduce) the maximum output, thereby reducing the reference output parameter, so that the reference output parameter can be smaller than the first threshold.

Further, when it is determined that the reduced value of the maximum output is greater than 0, a specific numerical value of the reduced value of the maximum output parameter may be further determined. In some embodiments, for example, the maximum output may be gradually reduced in equal steps, so that the reference output parameter is finally smaller than the first threshold. For example, gradually reducing the maximum output with equal steps may be to reduce the maximum output by the same value each time (such as reducing the maximum output by 2dB each time), so as to gradually reduce the reference output parameter, and finally make the reference output parameter smaller than the first threshold. .

Since the wearer generally feels stronger vibrations when he or she speaks or the ambient sound is louder, the sound level at this time is larger, for example, greater than or equal to 70dB, and the middle sound level ( For example, when a sound signal with a sound level below 70dB is input into the bone conduction hearing aid device, the reference output parameters of the bone conduction hearing aid device will not be affected. When assisting the device, the reference output parameter of the bone conduction hearing aid is lower than the first threshold, so as to improve the situation that the wearer feels relatively strong vibration when he speaks or the ambient sound is loud.

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

In some embodiments, the setting parameters of the multi-channel wide dynamic range compression system also include crossover frequency (Crossover Frequency), lower threshold (Lower Threshold), low level gain (Low Level Gain), upper threshold (Upper Threshold), amplification Threshold (Expansion Threshold), amplification ratio (Expansion Ratio), effector generation time (Compressor Attack), effector release time (Compressor Release), gain algorithm generation time (AGCo Attack), gain algorithm release time (AGCo Release) . Wherein, the crossover frequency (Crossover Frequency) may be a frequency at which the audio frequency spectrum is divided, that is, a division point of each frequency band. The lower threshold may be the lower threshold of the sound level in the frequency band. The low-level gain may be a gain when the input sound level is less than a lower threshold. The upper threshold may be the upper threshold of the sound level in the frequency band, that is, the threshold corresponding to the high level gain. The amplification threshold may be an amplification threshold of a sound level in a frequency band, and the amplification ratio may be a gain ratio of a sound at the amplification threshold. The generation time of the effect device can be the transition time when the effect device detects a sound higher than the threshold, and the effect device fully works, and the gain gradually increases to the preset gain within the transition time. The release time of the effect device may be a transition time for the effect device to fully take effect when the sound is lower than the threshold, and the gain gradually decreases to the preset gain during the transition time. The gain algorithm is based on the output automatic gain control algorithm (Automatic Gain Control according to Output, AGCo), and the generation time of the gain algorithm can be 2 ms. Gain algorithm release time can be 64 ms.

Fig. 7 is a flowchart of operations performed by the bone conduction hearing aid device during use according to some embodiments of the present invention. As shown in Figure 7, the bone conduction hearing aid device can perform the following steps during the use of the bone conduction hearing aid device:

Step 710, acquiring a sound input signal. In some embodiments, the sound input signal may include an audio signal (eg, song, voice, etc.) acquired by the bone conduction hearing aid device from a storage device (eg, memory 130 ), a terminal (eg, terminal 140 ), and other devices. In some embodiments, the sound signal input to the bone conduction hearing aid device may include the sound signal picked up by the sound pickup element of the bone conduction hearing aid device. For example, the sound pickup element can pick up sound (the first vibration signal), and convert the first vibration signal into an electrical signal after being processed. The electrical signal can be transmitted to the speaker element of the bone conduction hearing aid device, and the speaker element is used to process the electrical signal based on the reference output parameters and convert it into a second vibration signal, which is transmitted to the wearer.

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

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

Step 740: Control the bone conduction hearing aid device to output sound signals based on the actual output parameters.

The reference output parameters can be understood as parameters that are initially set during the process of configuring the bone conduction hearing aids, and the actual output parameters can be understood as output parameters adjusted by the bone conduction hearing aids based on the adjustment value. In some embodiments, actual output parameters may include gain values and/or actual analog output values. In some embodiments, the actual gain value may be the value at which the hearing aid actually amplifies the intensity of the sound signal during the wearing process, and the actual analog output value may be the analogue value of the hearing aid according to the input sound signal parameters (for example, the intensity value of the sound signal). The actual output signal strength value of . For example, the actual analog output value may be equal to the input value of the sound signal (ie, the intensity value, in dB) plus the actual gain value (in dB). In some embodiments, the actual analog output value corresponding to a specific sound level and a specific frequency band may be equal to the actual output value during the use of the bone conduction hearing aid device (that is, the strength value of the signal actually output by the bone conduction hearing aid device, The unit is dB), for example, when the input sound signal of the bone conduction hearing aid device is at the specific sound level and specific frequency band. In some embodiments, when the wearer wears the bone conduction hearing aid, the sound pickup element 220 of the bone conduction hearing aid can perform step 710 , and the magnetic circuit element of the bone conduction hearing aid can perform steps 720 and 730 . The vibration element of the bone conduction hearing aid device can perform step 740, and the vibration element can convert the actual output parameters determined by the magnetic circuit element into corresponding vibration intensity, so that the bone conduction hearing aid device outputs sound signals through mechanical vibration. In some embodiments, when the wearer wears the bone conduction hearing aid, the sound pickup element 220 of the bone conduction hearing aid can perform step 710 , and the processing device in the bone conduction hearing aid can perform steps 720 and 730 . The processing device of the bone conduction hearing aid device can control the magnetic circuit element and the vibration element to perform step 740 . For example, the processing device may control the vibrating element to generate a vibration intensity corresponding to the actual output parameter based on the determined actual output parameter, so that the bone conduction hearing aid device outputs the sound signal through mechanical vibration. For another example, the processing device may control the magnitude of the current in the voice coil based on the determined actual output parameters, so as to control the strength of the mechanical vibration generated by the voice coil, thereby controlling the output signal strength of the bone conduction hearing aid device.

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

The basic concept has been described above, obviously, for those with ordinary knowledge in the technical field, the above detailed disclosure is only an example, and does not constitute a limitation to the present invention. Although not explicitly described herein, various modifications, improvements and amendments to the present invention can be made by those skilled in the art. Such modifications, improvements and corrections are suggested in the present invention, so such modifications, improvements and corrections still belong to the spirit and scope of the exemplary embodiments of the present invention.

Meanwhile, the present invention uses specific words to describe the embodiments of the present invention. For example, "one embodiment", "an embodiment", and/or "some embodiments" refer to a certain feature, structure or characteristic related to at least one embodiment of the present invention. Therefore, it should be emphasized and noted that two or more references to "an embodiment" or "an embodiment" or "an alternative embodiment" in different places in this specification do not necessarily refer to the same embodiment . In addition, certain features, structures or characteristics of one or more embodiments of the present invention may be properly combined.

In addition, unless clearly stated in the scope of the patent application, the order of processing elements and sequences, the use of numbers and letters, or the use of other names in the present invention are not used to limit the order of the flow and methods of the present invention. While the above disclosure discusses by way of example some embodiments of the invention that are presently believed to be useful, it should be understood that such details are for illustrative purposes only and that the appended claims are not limited to the disclosed embodiments, but rather, The scope of the patent application is intended to cover all modifications and equivalent combinations that conform to the spirit and scope of the embodiments of the present invention. For example, although the above-described system components can be implemented by hardware devices, they can also be implemented by only software solutions, such as installing the described system on an existing server or mobile device.

In the same way, it should be noted that in order to simplify the expression of the disclosure of the present invention and help the understanding of one or more embodiments of the invention, in the foregoing description of the embodiments of the present invention, sometimes multiple features are combined into one embodiment , drawings or descriptions thereof. However, this disclosure does not imply that the object of the invention requires more features than those mentioned in the claims. Indeed, embodiment features are less than all features of a single foregoing disclosed embodiment.

In some embodiments, numbers describing the quantity of components and attributes are used. It should be understood that such numbers used in the description of the embodiments use the modifiers "about", "approximately" or "substantially" in some examples. grooming. Unless otherwise stated, "about", "approximately" or "substantially" indicates that the stated figure allows for a variation of ±20%. Accordingly, in some embodiments, the numerical parameters used in the specification and claims are approximations that may vary depending upon the desired characteristics of individual embodiments. In some embodiments, numerical parameters should take into account the specified number of significant digits and adopt the general digit reservation method. Although the numerical ranges and parameters used to demonstrate the breadth of scope in some embodiments of the invention are approximations, in specific embodiments such numerical values are set as precisely as practicable.

The entire contents of each patent, patent application, published patent application, and other material, such as articles, books, specifications, publications, documents, etc., cited in this application are hereby incorporated by reference into this application. Application history documents that are inconsistent with or conflict with the content of this application, as well as documents (currently or hereafter appended to this application) that limit the broadest scope of this application's claimed patent scope, are excluded. It should be noted that if there is any inconsistency or conflict between the descriptions, definitions, and/or terms used in the attached materials of the application and the contents of the application, the descriptions, definitions and/or terms of the application shall be Use shall prevail.

Finally, it should be understood that the embodiments described in the present invention are only used to illustrate the principles of the embodiments of the present invention. Other modifications are also possible within the scope of the present invention. Accordingly, by way of illustration and not limitation, alternative configurations of the embodiments of the present invention may be considered consistent with the teachings of the present invention. Accordingly, the embodiments of the present invention are not limited to the embodiments of the present invention explicitly shown and described.

100: Bone conduction hearing aids configuration system 110: Bone Conduction Hearing Aids 120: Processing equipment 130: memory 140: terminal 141:Mobile devices 142: Tablet PC 143: Laptop 144:Smart watch 150: Network 210: Loudspeaker components 211: Magnetic circuit components 213: vibration element 220: pickup element 230: support element 232: accommodating cavity 300: Bone conduction hearing aids configuration system 310: Get the module 320: Refer to the output parameter to determine the module 330: Adjustment value determination module 340: Configuration module 410: Step 420: Step 430: step 440: step 510: step 520: step 530: step 610: Step 620: Step 710: Step 720: step 730: step 740: step

The invention will be further illustrated by way of exemplary embodiments which will be described in detail by means of the accompanying drawings. These embodiments are not limiting, and in these embodiments, the same reference numerals represent the same structure, wherein:

[Fig. 1] is a schematic diagram of a configuration device for bone conduction hearing aids according to some embodiments of the present invention;

[Fig. 2] is a schematic structural diagram of a bone conduction hearing aid device according to some embodiments of the present invention;

[Fig. 3] It is a module diagram of the configuration system of bone conduction hearing aids according to some embodiments of the present invention;

[ FIG. 4 ] is a flow chart of a configuration method of a bone conduction hearing aid device according to some embodiments of the present invention;

[Fig. 5] is a flow chart of determining adjustment values according to other embodiments of the present invention;

[Fig. 6] is a flow chart of determining adjustment values according to other embodiments of the present invention;

[Fig. 7] is a flow chart of the operations performed by the bone conduction hearing aid device during use according to some embodiments of the present invention;

[Fig. 8] Vibration perception threshold diagrams at different frequencies when the wearer wears bone conduction hearing aids, which are experimentally determined;

[Fig. 9] is the experimental result diagram of the speech recognition rate test performed on the wearer 1;

[Fig. 10] is the experimental result diagram of the speech recognition rate test performed on the wearer 2;

[ Fig. 11 ] is an experimental result diagram of a speech recognition rate test performed on the wearer 3 .

410: Step

420: Step

430: step

440: step

Claims (13)

A method for configuring a bone conduction hearing aid, comprising: Obtain information on the wearer's hearing loss; Based on the hearing loss data, determine the reference output parameters of the bone conduction hearing aid device at each sound level and each frequency band; obtaining an adjustment value of the reference output parameter, the adjustment value being at least related to the frequency band; and The bone conduction hearing aid device is configured based on the reference output parameter and the adjustment value. The configuration method according to claim 1, wherein configuring the bone conduction hearing aid device based on the reference output parameter and the adjustment value includes: In a frequency band where the frequency is greater than 0 Hz and less than or equal to 625 Hz, the reference output parameter is reduced based on the adjustment value. The configuration method according to claim 2, wherein, in the frequency band where the frequency is greater than 0 Hz and less than or equal to 625 Hz, the adjustment value is 1dB-12dB. The configuration method according to claim 1, wherein the adjustment values are different at different hearing levels and at the same frequency band. The configuration method according to claim 4, wherein obtaining the adjustment value of the reference output parameter includes: Determining the first thresholds corresponding to the respective frequency bands and the respective sound levels, the first thresholds are related to the wearer's degree of vibration perception of the respective sound levels in the respective frequency bands; determining the second thresholds corresponding to the respective frequency bands and the respective sound levels, the second thresholds being related to the speech recognition rate of the wearer in the respective sound levels in the respective frequency bands; and The adjustment value is determined based on the reference output parameter, the first threshold and the second threshold. The configuration method according to claim 5, wherein determining the adjustment value based on the reference output parameter, the first threshold and the second threshold includes: For each sound level and a certain sound level in each frequency band and the reference output parameter under a certain frequency band: subtracting the first threshold from the reference output parameter to obtain a comparison value; comparing the comparison value with the second threshold; Based on a comparison result between the comparison value and the second threshold, the adjustment value corresponding to the reference output parameter is determined. The configuration method according to claim 6, wherein, based on a comparison result between the comparison value and the second threshold, determining the adjustment value corresponding to the reference output parameter includes: When the comparison value is less than or equal to 0, the adjustment value is 0 dB; When the comparison value is greater than 0 and less than or equal to the second threshold, the adjustment value is the comparison value; When the comparison value is greater than the second threshold, the adjustment value is the second threshold. The configuration method according to claim 5, wherein, in the frequency band where the frequency is greater than 0 Hz and less than or equal to 125 Hz, the first threshold is in the range of 48 dB-52 dB; and/or, In the frequency band where the frequency is greater than 125Hz and less than or equal to 375Hz, the first threshold is in the range of 49 dB-54 dB; and/or, In the frequency band where the frequency is greater than 375Hz and less than or equal to 625Hz, the first threshold is in the range of 50 dB-55 dB; and/or, In the frequency band where the frequency is greater than 0 Hz and less than or equal to 125 Hz, the second threshold is in the range of 5 dB-10 dB; and/or, In the frequency band where the frequency is greater than 125Hz and less than or equal to 375Hz, the second threshold is in the range of 3 dB-7 dB; and/or, In the frequency band where the frequency is greater than 375 Hz and less than or equal to 625 Hz, the second threshold is within the range of 1 dB-4 dB. The configuration method according to claim 1, wherein configuring the bone conduction hearing aid device based on the reference output parameter and the adjustment value includes: Based on the reference output parameter and the adjustment value, the bone conduction hearing aid device is configured using a multi-channel wide dynamic range compression system. According to the configuration method of claim item 9, obtaining the adjustment value of the reference output parameter includes: comparing said reference output parameter with a first threshold, said first threshold being related to said wearer's degree of vibration perception of said respective sound levels in said respective frequency bands; Based on a comparison result between the reference output parameter and the first threshold, the adjustment value corresponding to the reference output parameter is determined. The configuration method according to claim 10, wherein the adjustment value includes a gain reduction value of the multi-channel wide dynamic range compression system when at least one of the sound levels is greater than a sound level threshold; based on the reference output The comparison result of the parameter and the first threshold value to determine the adjustment value corresponding to the reference output parameter includes: If the reference output parameter is less than or equal to the first threshold, the gain reduction value is 0 dB; If the reference output parameter is greater than the first threshold, the gain reduction value is the difference between the first threshold and the reference output parameter. The configuration method according to claim 10, wherein the adjustment value includes a reduction value of the maximum output of the multi-channel wide dynamic range compression system when at least one of the sound levels is greater than a sound level threshold; based on the Determining the adjustment value corresponding to the reference output parameter based on a comparison result between the reference output parameter and the first threshold includes: If the reference output parameter is less than or equal to the first threshold, the reduction value of the maximum output is 0 dB; If the reference output parameter is greater than the first threshold, the reduction of the maximum output is greater than 0 dB. A configuration system for bone conduction hearing aids, comprising: Obtain the module, which is used to obtain the hearing loss data of the wearer; The reference output parameter determination module is used to determine the reference output parameters of the bone conduction hearing aids at each sound level and each frequency band based on the hearing loss data; an adjustment value determination module, configured to acquire the adjustment value of the reference output parameter; and A configuration module configured to configure the bone conduction hearing aid based on the reference output parameter and the adjustment value.

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