WO2022226761A1 - 骨导听力辅助设备的配置方法及系统 - Google Patents

骨导听力辅助设备的配置方法及系统 Download PDF

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Publication number
WO2022226761A1
WO2022226761A1 PCT/CN2021/090136 CN2021090136W WO2022226761A1 WO 2022226761 A1 WO2022226761 A1 WO 2022226761A1 CN 2021090136 W CN2021090136 W CN 2021090136W WO 2022226761 A1 WO2022226761 A1 WO 2022226761A1
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WIPO (PCT)
Prior art keywords
threshold
frequency band
adjustment value
value
bone conduction
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PCT/CN2021/090136
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English (en)
French (fr)
Inventor
闫冰岩
李伯诚
唐惠芳
廖风云
齐心
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深圳市韶音科技有限公司
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Application filed by 深圳市韶音科技有限公司 filed Critical 深圳市韶音科技有限公司
Priority to CN202180078572.XA priority Critical patent/CN116491132A/zh
Priority to KR1020237023916A priority patent/KR20230118971A/ko
Priority to JP2023543182A priority patent/JP2024502884A/ja
Priority to PCT/CN2021/090136 priority patent/WO2022226761A1/zh
Priority to EP21938249.6A priority patent/EP4236370A4/en
Priority to TW111115552A priority patent/TW202243494A/zh
Publication of WO2022226761A1 publication Critical patent/WO2022226761A1/zh
Priority to US18/323,665 priority patent/US20230300544A1/en

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    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R25/00—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception
    • H04R25/35—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception using translation techniques
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R25/00—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception
    • H04R25/50—Customised settings for obtaining desired overall acoustical characteristics
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R25/00—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception
    • H04R25/35—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception using translation techniques
    • H04R25/356—Amplitude, e.g. amplitude shift or compression
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R25/00—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception
    • H04R25/35—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception using translation techniques
    • H04R25/353—Frequency, e.g. frequency shift or compression
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R25/00—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception
    • H04R25/55—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception using an external connection, either wireless or wired
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R25/00—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception
    • H04R25/60—Mounting or interconnection of hearing aid parts, e.g. inside tips, housings or to ossicles
    • H04R25/604—Mounting or interconnection of hearing aid parts, e.g. inside tips, housings or to ossicles of acoustic or vibrational transducers
    • H04R25/606—Mounting or interconnection of hearing aid parts, e.g. inside tips, housings or to ossicles of acoustic or vibrational transducers acting directly on the eardrum, the ossicles or the skull, e.g. mastoid, tooth, maxillary or mandibular bone, or mechanically stimulating the cochlea, e.g. at the oval window
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R25/00—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception
    • H04R25/70—Adaptation of deaf aid to hearing loss, e.g. initial electronic fitting
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R3/00—Circuits for transducers, loudspeakers or microphones
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R2225/00—Details of deaf aids covered by H04R25/00, not provided for in any of its subgroups
    • H04R2225/43—Signal processing in hearing aids to enhance the speech intelligibility
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R2225/00—Details of deaf aids covered by H04R25/00, not provided for in any of its subgroups
    • H04R2225/55—Communication between hearing aids and external devices via a network for data exchange
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R2430/00—Signal processing covered by H04R, not provided for in its groups
    • H04R2430/01—Aspects of volume control, not necessarily automatic, in sound systems
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R2430/00—Signal processing covered by H04R, not provided for in its groups
    • H04R2430/03—Synergistic effects of band splitting and sub-band processing
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R2460/00—Details of hearing devices, i.e. of ear- or headphones covered by H04R1/10 or H04R5/033 but not provided for in any of their subgroups, or of hearing aids covered by H04R25/00 but not provided for in any of its subgroups
    • H04R2460/13—Hearing devices using bone conduction transducers
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R25/00—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception
    • H04R25/55—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception using an external connection, either wireless or wired
    • H04R25/554—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception using an external connection, either wireless or wired using a wireless connection, e.g. between microphone and amplifier or using Tcoils

Definitions

  • the present application relates to the field of bone conduction hearing aids, and in particular, to a method and system for configuring bone conduction hearing aids.
  • Bone conduction hearing aids are hearing aids designed and manufactured using bone conduction technology.
  • the bone conduction hearing aid device can be a bone conduction hearing aid or a bone conduction hearing earphone.
  • Bone conduction hearing aids mainly amplify and convert external sound information into mechanical vibrations, and in the form of mechanical vibrations, send external sounds through the human skull, bone labyrinth, inner ear lymph, auger, and auditory nerve in turn, and send them to the cerebral cortex for hearing. center.
  • the sound wave signal of bone conduction hearing aids can be directly transmitted to the auditory nerve through the bones without passing through the external auditory canal and eardrum, avoiding the pressure and blocking effect caused by the traditional air conduction hearing aids blocking the ear canal.
  • the bone conduction hearing aid device can make the wearer have a more comfortable wearing experience.
  • 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 more and more widely used by hearing-impaired patients.
  • the vibration may be relatively severe during use, which will affect the wearer's wearing experience; while the lower vibration will affect the wearer's wearing experience. Therefore, it is necessary to provide a method for configuring a bone conduction hearing aid device, so as to improve the severe vibration of the bone conduction hearing aid device in some cases without affecting the wearer's listening effect.
  • One of the embodiments of the present application provides a method for configuring a bone conduction hearing aid device, which includes the following steps: acquiring hearing loss data of a wearer; The reference output parameter under the reference output parameter is obtained; the adjustment value of the reference output parameter is obtained, and the adjustment value is at least related to the frequency band; based on the reference output parameter and the adjustment value, the bone conduction hearing aid device is configured.
  • configuring the bone conduction hearing aid device includes reducing the reference based on the adjustment value in a frequency band with a frequency greater than 0 Hz and less than or equal to 625 Hz Output parameters.
  • the adjustment values are the same at different hearing levels and in the same frequency band.
  • the adjustment value is 1 dB-12 dB.
  • the adjustment value in a frequency band with a frequency greater than 0 Hz and less than or equal to 125 Hz, the adjustment value is set to 5dB-12dB; in a frequency band with a frequency greater than 125 Hz and less than or equal to 375 Hz, the adjustment value is set as 3dB-9dB; and/or, in a frequency band with a frequency greater than 375Hz and less than or equal to 625Hz, the adjustment value is set to be 1dB-6dB.
  • the adjustment value in a frequency band with a frequency greater than 0 Hz but less than or equal to 125 Hz, the adjustment value is 5dB-7dB; in a frequency band with a frequency greater than 125Hz and less than or equal to 375Hz, the adjustment value is 3dB-5dB; And/or, in a frequency band whose frequency is greater than 375 Hz and less than or equal to 625 Hz, the adjustment value is 1dB-3dB.
  • the adjustment value in a frequency band with a frequency greater than 0 Hz and less than or equal to 125 Hz, the adjustment value is 10dB-12dB; in a frequency band with a frequency greater than 125Hz and less than or equal to 375Hz, the adjustment value is 7dB-9dB; And/or, in a frequency band whose frequency is greater than 375 Hz and less than or equal to 625 Hz, the adjustment value is 4dB-6dB.
  • the adjustment values are different at different hearing levels and in the same frequency band.
  • the acquiring the adjustment value of the reference output parameter includes: determining the respective frequency bands and first thresholds corresponding to the respective sound levels, and the first thresholds are related to the wearer's determination of the respective sound levels.
  • the degree of vibration perception of each sound level in the frequency band is related to the degree of vibration; the second threshold value corresponding to each frequency band and each sound level is determined, and the second threshold value is related to the wearer's speech recognition of each sound level in the various frequency bands. and determining the adjustment value based on the reference output parameter, the first threshold and the second threshold.
  • the determining the adjustment value based on the reference output parameter, the first threshold and the second threshold includes: for the respective sound levels and a certain sound level in the respective frequency bands and a reference output parameter in a certain frequency band; subtract the first threshold from the reference output parameter to obtain a comparison value; compare the comparison value with the second threshold; based on the comparison value and the first threshold The comparison result of the two thresholds determines the adjustment value corresponding to the reference output parameter.
  • the determining the adjustment value corresponding to the reference output parameter based on the comparison result between the comparison value and the second threshold includes: when the comparison value is less than or equal to 0, the adjustment value is 0dB; when the comparison value is greater than 0 but less than or equal to the second threshold, the adjustment value is the comparison value; when the comparison value is greater than the second threshold, the adjustment value is the second threshold.
  • the first threshold is within a range of 48dB-52dB.
  • the first threshold is within a range of 49 dB-54 dB.
  • the first threshold in a frequency band with a frequency greater than 375 Hz and less than or equal to 625 Hz, is in the range of 50dB-55dB.
  • the second threshold is within a range of 5dB-10dB.
  • the second threshold in a frequency band with a frequency greater than 125 Hz and less than or equal to 375 Hz, is in the range of 3dB-7dB.
  • the second threshold is within a range of 1 dB-4 dB.
  • configuring the bone conduction hearing aid device based on the reference output parameter and the adjustment value comprises: using a multi-channel wide dynamic range compression system based on the reference output parameter and the adjustment value, configuring The bone conduction hearing aid device.
  • the acquiring the adjustment value of the reference output parameter includes: comparing the reference output parameter with a first threshold, the first threshold and the wearer's description of each frequency band The vibration perception degree of each sound level is related; 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.
  • the adjustment value includes a gain reduction value of the multi-channel wide dynamic range compression system when at least one of the respective sound levels is greater than a sound level threshold; based on the reference output parameter and the Determining the adjustment value corresponding to the reference output parameter according to the comparison result of the first threshold includes: if the reference output parameter is less than or equal to the first threshold, the gain reduction value is 0 dB; if the reference output parameter is less than or equal to the first threshold, the gain reduction value is 0 dB; If the 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 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 respective sound levels is greater than a sound level threshold; based on the reference output parameter and the As a result of the comparison 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.
  • One of the embodiments of the present application provides a configuration system for a bone conduction hearing aid device, which includes: an acquisition module for acquiring hearing loss data of a wearer; a reference output parameter determination module for determining bone conduction based on the hearing loss data The reference output parameters of the 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 configure the bone conduction hearing aid device based on the reference output parameter and the adjustment value.
  • One of the embodiments of the present application provides a configuration device for a bone conduction hearing aid device, which includes: a processing device; a storage device in communication with the processing device, for storing instructions, when the processing device executes the stored instruction, The processing device executes the configuration method of the bone conduction hearing aid device described in any of the above technical solutions.
  • One of the embodiments of the present application provides a computer-readable storage medium, where the storage medium stores computer instructions, and when the computer reads the computer-executed instructions in the storage medium, the computer executes any of the above technical solutions.
  • a configuration method of a bone conduction hearing aid device is provided.
  • FIG. 1 is a schematic diagram of a configuration device of a bone conduction hearing aid device according to some embodiments of the present application
  • FIG. 2 is a schematic structural diagram of a bone conduction hearing aid device according to some embodiments of the present application.
  • FIG. 3 is a block diagram of a configuration system of a bone conduction hearing aid device according to some embodiments of the present application.
  • FIG. 4 is a flowchart of a configuration method of a bone conduction hearing aid device according to some embodiments of the present application.
  • FIG. 5 is a flowchart of determining an adjustment value according to other embodiments of the present application.
  • FIG. 6 is a flowchart of determining an adjustment value according to other embodiments of the present application.
  • FIG. 7 is a flowchart of operations performed by the bone conduction hearing aid device during use according to some embodiments of the present application.
  • 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 a graph showing the experimental results of the speech recognition rate test performed on the wearer 3 .
  • system means for distinguishing different components, elements, parts, parts or assemblies at different levels.
  • device means for converting components, elements, parts, parts or assemblies to different levels.
  • FIG. 1 is a schematic diagram of an apparatus for configuring a bone conduction hearing aid device according to some embodiments of the present application.
  • 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 .
  • bone conduction hearing assistive device 110, processing device 120, memory 130, and/or terminal 140 may connect and/or communicate with each other via a wireless connection (eg, network 150), a wired connection, or a combination thereof.
  • the connections between the components in the bone conduction hearing assist device configuration system 100 may vary.
  • the bone conduction hearing aid device 110 may be connected to the processing device 120 through the network 150, as shown in FIG. 1 .
  • the bone conduction hearing aid device 110 may be directly connected to the processing device 120 .
  • 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.
  • 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 acquire sound information (eg, ambient sounds, wearer sounds, audio files acquired in other devices, etc.) and process the acquired sound information into vibration signals that pass through the wearer's bones. And so on to the wearer's hearing center, so that the wearer can hear the sound information carried by the vibration signal.
  • the bone conduction hearing aid device may specifically be a bone conduction hearing aid or a bone conduction hearing earphone. In this manual, the bone conduction hearing aid is mainly used as an example for description.
  • the bone conduction hearing aid 110 may include a pickup assembly, a speaker assembly, and the like.
  • the sound pickup assembly is used to pick up sound information (also referred to as a first vibration signal, eg, ambient sound, wearer sound), process the picked up first vibration signal, and convert it into an electrical signal carrying sound information.
  • the speaker assembly can convert the electrical signal carrying the sound information acquired by the sound pickup element into a second vibration signal carrying the sound information and transmit it to the wearer's hearing center.
  • a detailed description of the bone conduction hearing aid 110 can be found elsewhere in this application (eg, FIG. 2 and its detailed description).
  • the configuration of the bone conduction hearing aid may be different for different wearers of the bone conduction hearing aid due to the wearer's hearing level (ie the level of hearing loss).
  • the configuration of a bone conduction hearing aid device refers to a parameter value (also referred to as a parameter) related to the sound signal strength output by the bone conduction hearing aid device and/or its determination process, enabling the bone conduction hearing aid
  • the device may output a sound signal based on the parameter value.
  • the parameter value related to the output signal strength of the bone conduction hearing aid device may include a gain value (unit of dB), an analog output value (unit of dB), and the like.
  • the gain value may be a value at which the hearing aid amplifies the strength of the sound signal
  • the analog output value may be an output signal strength value simulated by the hearing aid according to an input sound signal parameter (eg, the strength value of the sound signal).
  • 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 device configuration system 100 can determine the configuration of the bone conduction hearing aid device corresponding to the wearer's hearing level according to the difference in the wearer's hearing level. Based on the configuration, the bone conduction hearing aid device 110 can process and output the acquired sound information (eg, ambient sound, wearer sound, audio files acquired in other devices, etc.), so that the wearer can hear the sound.
  • the acquired sound information eg, ambient sound, wearer sound, audio files acquired in other devices, etc.
  • the processing device 120 may process data and/or information obtained from the bone conduction hearing aid device 110 , the memory 130 and/or the terminal 140 .
  • processing device 120 may obtain hearing loss data for the wearer of bone conduction hearing aid 110 .
  • the processing device 120 may determine the 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.
  • the processing device 120 may obtain the adjusted value of the reference output parameter.
  • the processing device 120 may configure the bone conduction hearing aid 110 based on the reference output parameter and the adjustment value.
  • processing device 120 may be a single server or a group of servers. Server groups can be centralized or distributed. In some embodiments, processing device 120 may be local or remote. For example, processing device 120 may access information and/or data stored in bone conduction hearing aid device 110 , terminal 140 and/or memory 130 via network 150 . As another example, the processing device 120 may be directly connected to the bone conduction hearing aid 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. For example only, the cloud platform may include a private cloud, a public cloud, a hybrid cloud, a community cloud, a distribution cloud, an internal cloud, a multi-layer cloud, etc., or any combination thereof.
  • processing device 120 may be implemented on a computing device. In some embodiments, the processing device 120 or a portion 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.
  • memory 130 may store data obtained from terminal 140 and/or processing device 120 .
  • memory 130 may store data and/or instructions that may be executed by processing device 120 or used to perform the example methods described in this application.
  • memory 130 may include mass storage devices, removable storage devices, volatile read-write memory, read-only memory (ROM), etc., or any combination thereof.
  • memory 130 may be implemented on a cloud platform.
  • the cloud platform may include a private cloud, a public cloud, a hybrid cloud, a community cloud, a distribution cloud, an internal cloud, a multi-layer cloud, etc., or any combination thereof.
  • memory 130 may be connected to network 150 to communicate with one or more other components in bone conduction hearing assistive device configuration system 100 (e.g., processing device 120, terminal 140, etc.). One or more components of bone conduction hearing aid configuration system 100 may access data or instructions stored in memory 130 via network 150 . In some embodiments, memory 130 may be directly connected to or in communication with one or more other components in bone conduction hearing aid configuration system 100 (eg, processing device 120, terminal 140, etc.). In some embodiments, memory 130 may be part of processing device 120 .
  • Terminal 140 may include mobile device 141, tablet computer 142, laptop computer 143, smart watch 144, etc., or any combination thereof.
  • the mobile device 141 may include smart home devices (eg, control devices for smart appliances, smart monitoring devices, smart TVs, smart cameras), wearable devices (eg, glasses, helmets, accessories, clothing, etc.), Mobile devices (eg, cell phones, laptops, etc.), virtual reality devices (eg, virtual reality headsets, virtual reality glasses, virtual reality goggles), etc., or any combination thereof.
  • the bone conduction hearing aid 110 may be integrated in the terminal 140, eg, in glasses, accessories, and the like.
  • a user may interact with the bone conduction hearing aid configuration system 100 through the terminal 140 .
  • the user may send a configuration request through a user interface on the terminal 140; the processing device 120 obtains the wearer's hearing loss data after receiving the configuration request.
  • the processing device 120 may send a hearing loss data acquisition request to the terminal 140 through the user interface, and the user may upload the wearer's hearing loss data through the user interface after receiving the acquisition request.
  • the processing device 120 may configure the bone conduction hearing aid 110 based on the hearing loss data.
  • Network 150 may include any suitable network that may facilitate the exchange of information and/or data for bone conduction hearing assistive device configuration system 100 .
  • one or more components of the bone conduction hearing aid configuration system 100 eg, bone conduction hearing aid 110 , terminal 140 , processing device 120 , memory 130 , etc.
  • the processing device 120 may obtain the wearer's hearing loss data (eg, hearing level) from the bone conduction hearing aid 110 via the network 150 .
  • the processing device 120 may obtain the user instruction from the terminal 140 via the network 150 .
  • the network 150 may be and/or include a public network (eg, the Internet), a private network (eg, a local area network (LAN), a wide area network (WAN), etc.), a wired network (eg, an Ethernet network), a wireless network (eg, 802.11 networks, Wi-Fi networks, etc.), cellular networks (eg, Long Term Evolution (LTE) networks), Frame Relay networks, Virtual Private Networks ("VPN"), satellite networks, telephone networks, routers, hubs, switches, server computers and/or any combination thereof.
  • network 150 may include one or more network access points.
  • network 150 may include wired and/or wireless network access points, such as base stations and/or Internet exchange points, through which one or more components of bone conduction hearing assistive device configuration system 100 may connect to network 150 to exchange data and/or information.
  • the storage 130 may be a data storage device including a cloud computing platform, eg, a public cloud, a private cloud, a community cloud, and a hybrid cloud.
  • a cloud computing platform eg, a public cloud, a private cloud, a community cloud, and a hybrid cloud.
  • FIG. 2 is a schematic structural diagram of a bone conduction hearing aid device according to some embodiments of the present application.
  • the bone conduction hearing aid device 200 may include a speaker assembly 210 , a sound pickup assembly 220 and a support assembly 230 .
  • the speaker assembly 210 can convert a signal containing sound information into a vibration signal.
  • the sound information may include video, audio files with a specific data format, or data or files that can be converted into sound through a specific approach.
  • Signals containing sound 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 from multiple sources. Multiple signal sources may or may not be correlated.
  • the bone conduction hearing aid device 200 may acquire signals containing sound information in various ways, and the acquisition of the signals may be wired or wireless, and may be real-time or delayed. For example, the bone conduction hearing aid 200 may receive electrical signals containing sound information in a wired or wireless manner.
  • the bone conduction hearing aid 10 may include a component with a sound acquisition function (for example, the sound pickup component 220 ), by picking up the sound in the environment, converting the mechanical vibration of the sound into an electrical signal, and processing it through an amplifier to obtain a signal that meets specific requirements electrical signal.
  • a component with a sound acquisition function for example, the sound pickup component 220
  • the speaker assembly 210 converts a signal containing sound information into a vibration signal, which is an energy conversion process.
  • the conversion process may involve the coexistence and conversion of many different types of energy.
  • the speaker assembly 210 may include one or more transducer devices, for example, through which electrical signals can be directly converted into mechanical vibrations to generate sound.
  • the sound information can be contained in the optical signal, and the transducer device can realize the process of converting the optical signal into a vibration signal.
  • Other types of energy that can coexist and transform during the operation of the transducer device include thermal energy, magnetic field energy, and the like.
  • the speaker assembly 210 can realize the conversion from the sound information signal to the vibration signal through the cooperation of the magnetic circuit assembly 211 and the vibration assembly 213 (the magnetic circuit assembly 211 and the vibration assembly 213 may be referred to as transducer devices).
  • the magnetic circuit component 211 is used to provide a magnetic field
  • the vibration component 213 is used to mechanically vibrate under the ampere force in the magnetic field.
  • the magnetic circuit assembly 211 may include a magnet.
  • the vibrating component 213 may include a magnetic vibrator and a vibrating piece.
  • the magnetic vibrator (for example, a voice coil) moves back and forth in the magnetic field under the action of Ampere force, and drives the vibrating piece to vibrate during the movement.
  • the sound information may correspond to the vibration of the magnetic vibrator, and the vibration frequency and amplitude of the magnetic vibrator may be determined according to the frequency and intensity of the sound information.
  • one of the magnetic circuit component and the magnetic vibrator can be an electromagnet, and the magnetic field intensity 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, and also The vibration frequency of the magnetic vibrator can be controlled by controlling the frequency of the current direction change of the coil in the electromagnet.
  • the sound information can also be gained, for example, the gain of the loudness of the sound information can be realized by increasing the vibration amplitude of the magnetic vibrator.
  • the specific energy conversion method of the vibration component may specifically include a moving coil type, an electrostatic type, a piezoelectric type, a moving iron type, a pneumatic type, an electromagnetic type, and the like.
  • the frequency response range and sound quality of the bone conduction hearing aid 200 may be affected by the vibration components.
  • the vibration component may include a wound cylindrical voice coil and a vibrating body (for example, a vibrating sheet or a diaphragm), and the cylindrical voice coil driven by a signal current drives the vibrating body to vibrate and produce sound in a magnetic field,
  • a vibrating body for example, a vibrating sheet or a diaphragm
  • the expansion and contraction of the material of the vibrating body, the deformation, size, shape and fixing method of the folds, the magnetic density of the magnetic field, etc., will have a great impact on the sound quality of the bone conduction hearing aids.
  • the vibrating body in the vibrating assembly may be a mirror-symmetrical structure, a centrally symmetric structure or an asymmetrical structure.
  • the vibrating body may be provided with an intermittent hole-like structure, so that the vibrating body can generate a greater displacement, thereby allowing the bone conduction hearing aid 200 Realize higher sensitivity and improve the output power of vibration and sound;
  • the vibrating body can be a torus structure, and a plurality of struts converging to the center are arranged in the torus body, and the number of struts can be two or more .
  • the sound pickup component 220 may be mainly used to pick up the user's voice, the ambient sound of the environment where the user is located, and the like. For the hearing impaired, the sound pickup effect of the sound pickup assembly 220 will affect the clarity and stability of the sound received by the hearing impaired person through the bone conduction hearing aid device.
  • the pickup assembly 220 may include a microphone.
  • the pickup assembly 220 can convert external sound signals into electrical signals.
  • the pickup assembly 220 may include a diaphragm, a coil, and a magnet. The diaphragm can be connected to a coil, and the coil can be placed in the magnetic field produced by the magnet.
  • External sound waves that is, sound signals or vibration signals
  • 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. pick up.
  • the support assembly 230 may play a role in other elements in the bone conduction hearing aid device 200 (eg, magnetic circuit assembly, vibration assembly and/or storage assembly, power supply assembly, communication assembly (not shown), pickup assembly 220 ) support.
  • the support assembly 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 components, and the like.
  • One or more connectors may connect the housing to other components in the bone conduction hearing aid 200 (eg, magnetic circuit components, vibration components and/or storage components, power components, communication components (not shown), pickups, etc.). sound component 220).
  • the wired connections involved in the bone conduction hearing aid 200 may include metallic cables, optical cables, or hybrid metallic and optical cables, eg, coaxial cables, communication cables, flexible cables, helical cables, non-metallic sheathed cables, metallic sheathed cables Cable, multi-core cable, twisted pair cable, ribbon cable, shielded cable, telecommunication cable, twin-stranded cable, parallel twin-conductor, twisted pair, etc.
  • metallic cables eg, coaxial cables, communication cables, flexible cables, helical cables, non-metallic sheathed cables, metallic sheathed cables Cable, multi-core cable, twisted pair cable, ribbon cable, shielded cable, telecommunication cable, twin-stranded cable, parallel twin-conductor, twisted pair, etc.
  • the examples described above are only used for convenience of illustration, and the medium of the wired connection may also be other types, for example, other transmission carriers of electrical signals or optical signals.
  • the wireless connections involved in the bone conduction hearing aid 200 may include radio communications, free space optical communications, acoustic communications, and electromagnetic induction, among others.
  • the radio communication can include IEEE802.11 series standards, IEEE802.15 series standards (such as Bluetooth technology and Zigbee technology, etc.), the first generation mobile communication technology, the second generation mobile communication technology (such as FDMA, TDMA, SDMA, CDMA, and SSMA, etc.), general packet radio service technology, third-generation mobile communication technologies (such as CDMA2000, WCDMA, TD-SCDMA, and WIMAX, etc.), fourth-generation mobile communication technologies (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 may include visible light, infrared signals, etc.; acoustic communication may include sound waves, ultrasonic signals etc.; electromagnetic induction may include near field communication
  • the medium of wireless connection may also be other types, for example, Z-wave technology, other chargeable civil radio frequency bands and military radio frequency bands, and the like.
  • the bone conduction hearing aid device 200 may acquire signals containing sound information from other devices through the Bluetooth technology.
  • 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.
  • a bone conduction hearing aid device may include one or more sensors, such as a temperature sensor, a humidity sensor, a velocity sensor, a displacement sensor, and the like. Sensors can collect user information or environmental information.
  • the storage assembly may not be necessary and may be removed from the bone conduction hearing aid.
  • the configuration system of the bone conduction hearing aid device is mainly based on the wearer's hearing loss data, and is configured according to a preset formula or a preset algorithm of the hearing aid configuration system.
  • the hearing aid configuration system can automatically output relevant parameter values of the hearing aid based on a preset algorithm. Directly configuring the bone conduction hearing aid device only through the preset algorithm may cause the configured bone conduction hearing aid device 200 to vibrate violently in some scenarios (such as the wearer speaking by himself or the ambient sound is too loud), causing the wearer to vibrate violently. of discomfort.
  • FIG. 3 is a block diagram of a configuration system for a bone conduction hearing aid device according to some embodiments of the present application.
  • the configuration system 300 of the bone conduction hearing aid device includes an acquisition module 310 , a reference output parameter determination module 320 , an adjustment value determination module 330 and a configuration module 340 .
  • the connection form between the modules can be wired, wireless, or a combination of the two. Any module can be local, remote, or a combination of the two.
  • the correspondence between modules can be one-to-one or one-to-many.
  • the acquisition module 310 may be used to acquire the wearer's hearing loss data.
  • the reference output parameter determination module 320 may be configured 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.
  • the adjustment value determination module 330 may be used to obtain the adjustment value of the reference output parameter.
  • the adjustment values are the same at different hearing levels and in the same frequency band.
  • the adjustment value is 1dB-12dB in the frequency band whose frequency is greater than 0Hz and less than or equal to 625Hz.
  • the adjustment value in a frequency band with a frequency greater than 0 Hz but less than or equal to 125 Hz, the adjustment value is set to 5dB-12dB; in a frequency band greater than 125Hz and less than or equal to 375Hz, the adjustment value is set to 3dB-9dB; And/or, in a frequency band with a frequency greater than 375Hz and less than or equal to 625Hz, the adjustment value is set to 1dB-6dB.
  • the adjustment value in a frequency band with a frequency greater than 0 Hz but less than or equal to 125 Hz, the adjustment value is 5dB-7dB; in a frequency band with a frequency greater than 125Hz and less than or equal to 375Hz, the adjustment value is 3dB-5dB; and/or, In the frequency band whose frequency is greater than 375Hz and less than or equal to 625Hz, the adjustment value is 1dB-3dB.
  • the adjustment value in a frequency band with a frequency greater than 0 Hz and less than or equal to 125 Hz, the adjustment value is 10dB-12dB; in a frequency band with a frequency greater than 125Hz and less than or equal to 375Hz, the adjustment value is 7dB-9dB; and/or, In the frequency band whose 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.
  • the adjustment value determination module 330 may be used to: determine each frequency band and a first threshold corresponding to each sound level, where the first threshold is related to the wearer's degree of vibration perception of each frequency band and each sound level; determine each frequency band and a 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 the adjustment value is determined based on the reference output parameter, the first threshold and the second threshold.
  • the adjustment value determination module 330 may be used to: for each sound level and a certain sound level in each frequency band and a reference output parameter in a certain frequency band; subtract the first threshold from the reference output parameter to obtain a comparison value ; compare the comparison value with the second threshold value; and determine the adjustment value corresponding to the reference output parameter based on the comparison result between the comparison value and the second threshold value.
  • the adjustment value determination module 330 may be configured to: in response to the comparison value being less than or equal to 0, set the adjustment value to 0 dB; in response to the comparison value being greater than 0 but less than or equal to the second threshold, setting the adjustment value to the comparison value; In response to the comparison value being greater than the second threshold, the adjustment value is set to the second threshold.
  • the first threshold in a frequency band with a frequency greater than 0 Hz and less than or equal to 125 Hz, is in the range of 48dB-52dB. In some embodiments, in a frequency band with a frequency 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, the first threshold is in the range of 50dB to 55dB in a frequency band with a frequency greater than 375Hz and less than or equal to 625Hz. In some embodiments, the second threshold is in the range of 5dB-10dB in a frequency band with a frequency greater than 0Hz and less than or equal to 125Hz.
  • the second threshold is in the range of 3dB-7dB in a frequency band with a frequency greater than 125Hz and less than or equal to 375Hz. In some embodiments, in a frequency band with a frequency greater than 375 Hz and less than or equal to 625 Hz, the second threshold is within a range of 1 dB-4 dB.
  • the adjustment value determination module 330 may be used to: compare the reference output parameter with a first threshold; the first threshold with the wearer The degree of vibration perception of each sound level in each frequency band is related; based on the comparison result between the reference output parameter and the first threshold, the adjustment value corresponding to the reference output parameter is determined.
  • the adjustment value includes a gain reduction value when at least one of the respective sound levels is greater than a sound level threshold; the adjustment value determination module 330 may be configured to: in response to the reference output parameter being less than or equal to the first threshold, then The gain reduction value is set to 0dB; in response to the reference output parameter being greater than the first threshold, the gain reduction value is set as the difference between the first threshold and the reference output parameter.
  • 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 configured to: in response to the reference output parameter being less than or equal to the first threshold, the reduction value of the maximum output Set to 0dB; in response to the reference output parameter being greater than the first threshold, the reduction value of the maximum output is set to be greater than 0dB.
  • the configuration module 340 may 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 may also be configured to reduce the reference output parameter based on the adjustment value in a frequency band with a frequency greater than 0 Hz and less than or equal to 625 Hz. In some embodiments, the configuration module 340 may 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.
  • each module or unit may be implemented by one or more components, and the function of each module or unit is not limited thereto.
  • the above modules or units may be added or deleted according to specific implementation scenarios or needs.
  • modifications in form and details may be made to the specific implementation and steps of the processing module without departing from this principle. and changes, some simple deductions or substitutions can also be made, and certain adjustments, combinations or splits can be made to the order of each module or unit without creative work, but these amendments and changes are still within the scope of the above description. within.
  • FIG. 4 is a flowchart of a configuration method of a bone conduction hearing aid device according to some embodiments of the present application. As shown in FIG. 4 , the flow 400 of the configuration method of the bone conduction hearing aid device includes the following steps:
  • Step 410 acquiring the wearer's hearing loss data. Specifically, step 410 may be performed by the obtaining module 310 .
  • the wearer's hearing loss data may be understood as data related to the wearer's hearing loss condition.
  • Hearing loss data may include the wearer's hearing level (also called hearing threshold or hearing loss level) in each frequency band and at each sound level, and in this specification, the unit used for hearing level is dBHL. The higher the value of the hearing level, the more severe the hearing loss of the wearer.
  • the hearing loss data may include data related to the wearer's historically worn hearing aids.
  • the wearer's historically worn hearing aid-related data may include configuration data for the wearer's historically used bone conduction hearing aids.
  • the hearing level may be in the range of 0 dBHL-80 dBHL.
  • the hearing level can indicate normal hearing within 0dBHL-25dBHL; the hearing level can be 26dBHL-40dBHL, mild hearing loss; the hearing level 41dBHL-60dBHL has moderate hearing loss, which shows difficulty in hearing normal sounds; 61dBHL-80dBHL severe hearing loss Hearing loss, manifested as difficulty hearing loud voices; hearing level greater than 80dBHL, indicating severe hearing loss, manifested as difficulty hearing loud sounds.
  • the wearer of the bone conduction hearing aid device may have the same hearing level in different frequency bands under the same sound level (for details of the sound level, please refer to the related content of step 420 ).
  • the wearer's hearing level in different frequency bands can be equal to a certain value in the range of 41dBHL-60dBHL; at 40dBC sound level, the wearer's hearing level in different frequency bands can be equal to 26dBHL-40dBHL A certain value in the range; at a sound level of 60dBC, the wearer's hearing level in different frequency bands can be equal to a certain value in the range of 0dBHL-25dBHL.
  • the hearing level of the wearer of the bone conduction hearing aid device may be different in different frequency bands at the same sound level.
  • the wearer's hearing level in the high frequency band eg, 8000Hz-12000Hz
  • the hearing level in the low frequency band may all be equal to the range of 26dBHL-40dBHL a value within.
  • 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.
  • the wearer's hearing level at different sound levels can be equal to a certain value in 0dBHL-25dBHL; in the 500Hz-1000Hz frequency band, the wearer's hearing level in different frequency bands can all be equal to 26dBHL A certain value in the range of -40dBHL; in the 1000Hz-2000Hz frequency band, the wearer's hearing level in different frequency bands can be equal to a certain value in the range of 41dBHL-60dBHL.
  • the wearer of the bone conduction hearing aid device may have different hearing levels corresponding to different sound levels in the same frequency band.
  • the wearer's hearing level can be equal to a value in the range of 41dBHL-60dBHL at a sound level of 20dBC; at a sound level of 40dBC, the hearing level can be equal to a value in the range of 26dBHL-40dBHL; at 60dBC
  • the hearing level at the sound level can be equal to a value in the range of 0dBHL-25dBHL.
  • obtaining the wearer's hearing loss data may be obtained by performing a real-time hearing test on the wearer.
  • a hearing aid dispenser can use a hearing test device to perform a hearing test on the wearer (eg, play sound signals in various frequency bands and sound levels), so as to obtain the wearer's hearing loss data.
  • Hearing loss data collected by the hearing testing device may be uploaded directly through a network (eg, network 150) to a processing device (eg, processing device 120) or to a storage device, from which the processing device may obtain hearing loss data.
  • the wearer can upload his/her own hearing loss data through a terminal (eg, terminal 140 ), a bone conduction hearing aid configuration system (eg, bone conduction hearing aid configuration system 100 ) or a device (eg, The processing device 120) may receive the hearing loss data uploaded by the wearer in a wired or wireless manner.
  • the bone conduction hearing assistive device configuration system or device may retrieve the wearer's hearing loss data from an associated memory (eg, memory 130).
  • Step 420 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. Specifically, step 420 may be performed by the reference output parameter determination module 320 .
  • 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 signal strength value of the analog output signal of the bone conduction hearing aid device, in dB).
  • 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 strength 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 under the reference output parameter (for example, the reference gain value) satisfies a specific sound level and frequency band, the strength value of the sound signal output by the bone conduction hearing aid device may be equal to this value.
  • the reference output parameter is related to hearing loss level, sound level, frequency, or the like.
  • 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.
  • the signal strength corresponding to the sound level may be amplified based on the gain value to determine the analog output value.
  • the reference output parameters may be different for different wearers due to their different hearing loss data (eg, the degree of hearing loss at each sound level).
  • 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.
  • 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 strength of the sound signal, and the unit is decibel.
  • the measurement of sound level mainly adopts C frequency weighted measurement, that is, the unit of sound level in this manual is dBC.
  • Frequency band in this manual refers to the frequency range of the sound signal. In some embodiments, the frequency of the sound signal may be divided into multiple consecutive ranges to form different frequency bands.
  • determining the reference output parameters of the bone conduction hearing aid device at each sound level and each frequency band may refer to determining that the bone conduction hearing aid device is at a preset sound level and/or a preset frequency and the preset sound level and the parameter output parameter corresponding to the hearing loss level of the wearer of the corresponding bone conduction hearing aid device at the preset frequency.
  • determining the reference output parameters of the bone conduction hearing aid device under each sound level and each frequency band may refer to determining that the bone conduction hearing aid device is under a preset sound level range and/or a preset frequency band and the preset The sound level range and the parameter output parameter corresponding to the hearing loss level of the wearer of the bone conduction hearing aid device corresponding to the preset frequency band.
  • the bone conduction hearing aid device can amplify and convert the sound signal (that is, the sound input signal) input to the bone conduction hearing aid device into a vibration signal, and transmit it to the wearer of the bone conduction hearing aid device, so that The wearer can hear the sound.
  • the preset sound level, preset frequency, preset sound level range, and/or preset frequency band may be default settings of the system (eg, bone conduction hearing aid configuration system 100 ) or set by a user.
  • the preset sound level may include 20dBC, 30dBC, 40dBC, 50dBC, 60dBC, 70dBC, 80dBC, etc., or a combination thereof.
  • the preset frequency may include 250 Hz, 500 Hz, 1000 Hz, 2000 Hz, 3000 Hz, 4000 Hz, 8000 Hz, 10000 Hz, etc., or a combination thereof.
  • 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 40dBC) 50dBC), 50dBC-60dBC (may exclude 60dBC), 60dBC-70dBC (may exclude 70dBC), 70dBC-80dBC (may exclude 80dBC), etc. or a combination thereof.
  • the preset frequency band may include 20Hz-250Hz (may exclude 250Hz), 250Hz-500Hz (may exclude 500Hz), 500Hz-1000Hz (may exclude 1000Hz), 1000Hz-2000Hz (may exclude 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 a combination thereof.
  • the preset frequency band may include 0Hz-125Hz (may exclude 125Hz), 125Hz-375Hz (may exclude 375Hz), 375Hz-625Hz (may exclude 625Hz), 625Hz-875Hz (may exclude 875Hz) , 875Hz-1375Hz (may exclude 1375Hz), 1375Hz-1875Hz (may exclude 1875Hz), 1875Hz-2625Hz (may exclude 2625Hz), 2625Hz-4875Hz (may exclude 4875Hz), etc. or a combination thereof.
  • the preset sound level, the preset frequency, the preset sound level range, and/or the preset frequency band may be adjusted by the system (eg, the bone conduction hearing aid configuration system 100 ) or the user.
  • adjustments may be made according to the hearing level of the wearer of the bone conduction hearing aid. For example, if the wearer's hearing level is 10dBHL when the sound level is 80dBC (indicating that the wearer has normal hearing at the sound level), the maximum value of the sound level can be preset not to exceed 80dBC.
  • the reference output parameter may be a reference gain value of the bone conduction hearing aid device
  • the processing device 120 may be based on the hearing loss data of each sound level and the hearing level in each frequency band and the value of each sound level and each frequency band, Determine the reference gain value of the bone conduction hearing aid device at each sound level and each frequency band. For example, it can be determined 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 based on the sound level of 20dBC and the frequency band of 375Hz-625Hz. the reference gain value below.
  • 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. the reference analog output value). For example, 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 and based on the sound level of 30dBC and the frequency band of 125Hz-375Hz can be determined as the sound level 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 that is, the reference analog output value).
  • the processing device 120 may first determine the reference gain value of the bone conduction hearing aid device at each sound level and each frequency band based on the hearing loss data, and then determine the reference gain value at each sound level based on the above The gain value in each frequency band determines the reference analog output signal strength value (ie, the reference analog output value) of the bone conduction hearing aid device at the corresponding sound level and the corresponding frequency band.
  • the processing device 120 may determine the reference output parameter through a preset formula.
  • the reference gain values for each sound level and each frequency band can be determined by a preset formula according to the wearer's hearing loss data.
  • 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 the degree of improvement of the hearing threshold. 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.
  • the reference output parameters in step 320 may be determined from empirical data in the following table (Table 1).
  • Table 1 the reference gain value at each hearing loss level (determined based on the hearing loss data) in each frequency band can be determined through the empirical data shown in the following table, and then the reference analog output value at the corresponding hearing loss level in the corresponding frequency band can be further determined through the reference gain value.
  • Table 1 takes the sound level of 60dBSPL as an example to illustrate the reference gain values for each hearing level and each frequency band. As shown in Table 1, when the sound level is 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.
  • the reference gain value may first increase and then decrease.
  • 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 for each hearing level and each frequency band.
  • the processing device 120 may determine the reference output parameters according to the configuration model.
  • the configuration model can represent the relationship between reference output parameters and frequency bands, sound levels, and hearing levels.
  • Step 430 Obtain the adjustment value of the reference output parameter.
  • the adjustment value is at least related to the frequency band.
  • step 430 may be performed by the reference output adjustment value determination module 330 .
  • the adjustment value is the value used to adjust the reference output parameter.
  • the reference output parameter can be adjusted by adjusting the value, and the adjusted reference output parameter can be used as the actual simulated output parameter of the bone conduction hearing aid device.
  • the reference output parameter Take the reference output parameter as the reference analog output value and the reference gain value as an example to describe respectively.
  • the reference analog output value (the signal strength value of the analog output) can be adjusted by the adjustment value, so that the adjusted reference analog output value is used as the actual analog output value of the bone conduction hearing aid device (the actual analog output signal strength value) ).
  • the reference gain value (intensity value for amplifying the sound signal) of the bone conduction hearing aid device can be adjusted by the adjustment value, so that the adjusted reference gain value is used as the actual gain value of the bone conduction hearing aid device.
  • the adjustment value is used to reduce the reference output parameter.
  • the adjustment value may be a value for attenuating the reference analog output value, that is, the adjustment value may be subtracted from the reference output parameter.
  • 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.
  • the adjustment value may be a proportional value less than 1, that is, the adjustment value may be multiplied on the basis of the reference output parameter.
  • the strong vibration of the bone conduction hearing aid occurs when the frequency of the sound signal input to the bone conduction hearing aid is low.
  • the bone conduction earphone is likely to vibrate in the frequency range of 125 Hz to 625 Hz. Therefore, the adjustment value can be set in the frequency range of 0Hz ⁇ 625Hz (or in the frequency range of 125Hz ⁇ 625Hz) (for example, the adjustment value is used to reduce the reference output parameter in this frequency band) to improve the vibration of the bone conduction hearing aid device in this frequency band strong situation.
  • FIG. 8 is a graph of experimentally determined vibration perception thresholds at various frequencies when a wearer wears a bone conduction hearing aid device.
  • the vibration perception threshold (unit dBV) may refer to the value obtained by converting 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 device is X (unit V); then the vibration perception threshold is 20*log10(X/1) (unit dBV). Just as an example, when the driving voltage value of the bone conduction hearing aid device is 1V, the corresponding vibration perception threshold is 0dBV; when the driving voltage value of the bone conduction hearing aid device is 0.5V, the corresponding vibration perception threshold value is -6dBV.
  • the vibration perception threshold of bone conduction hearing aids in the frequency band below 1000Hz is small, which means that bone conduction hearing aids are prone to vibration in the frequency band below 1000Hz, especially the frequency band 125Hz ⁇ 600Hz is the most likely to produce vibration 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 experiments, the adjustment value can be set in the frequency band of 0 Hz to 625 Hz (or in the frequency band of 125 Hz to 625 Hz).
  • the same frequency band and/or the same sound level may correspond to the same adjustment value under different hearing levels.
  • the adjustment value of hearing level in 26dBHL-40dBHL, frequency in the frequency band 0Hz-625Hz and 20dBC sound level is the same as the adjustment value of hearing level in 41dBHL-60dBHL, frequency in the frequency band 0Hz-625Hz and 20dBC sound level .
  • the hearing level can be adjusted within a frequency range of 26dBHL-40dBHL, a frequency of 0Hz-125Hz, and a sound level of 20dBC
  • the hearing level can be adjusted within a frequency range of 41dBHL-60dBHL, a frequency of 0Hz-125Hz, and a sound level of 20dBC.
  • the adjustment value of the hearing level in the frequency band of 26dBHL-40dBHL, the frequency in the frequency band of 125Hz-375Hz and the sound level of 20dBC is the same as the adjustment value of the hearing level in the frequency band of 41dBHL-60dBHL in the frequency band of 125Hz-375Hz and the sound level of 20dBC. .
  • the same frequency band and/or the same sound level may correspond to different adjustment values under different hearing levels.
  • the hearing level can be adjusted between 26dBHL-40dBHL, frequency in the frequency band 0Hz-625Hz and 20dBC sound level and hearing level in the frequency band of 41dBHL-60dBHL, frequency in the frequency band of 0Hz-625Hz and the adjustment value at 20dBC sound level Are not the same.
  • the hearing level can be adjusted in the frequency range of 26dBHL-40dBHL, in the frequency band of 20Hz-125Hz, and under the sound level of 20dBC, and the hearing level can be adjusted in the frequency range of 41dBHL-60dBHL, in the frequency band of 20Hz-125Hz, and under the sound level of 20dBC.
  • the values are not the same.
  • the hearing level can be adjusted in the frequency band of 26dBHL-40dBHL, the frequency is in the frequency band of 125Hz-375Hz, and the adjustment value under the sound level of 20dBC is the same as the adjustment value of the hearing level in the frequency band of 41dBHL-60dBHL in the frequency band of 125Hz-375Hz and the sound level of 20dBC.
  • the adjustment value under the sound level of 20dBC is the same as the adjustment value of the hearing level in the frequency band of 41dBHL-60dBHL in the frequency band of 125Hz-375Hz and the sound level of 20dBC.
  • the same frequency band and/or the same hearing level may correspond to the same adjustment value at different sound levels.
  • the adjustment value of sound level in the frequency band of 20dBC-40dBC, frequency of 0Hz-125Hz and hearing level of 41dBHL-60dBHL and the adjustment value of sound level of 40dBC-60dBC, frequency of 0Hz-125Hz and hearing level of 41dBHL-60dBHL can be the same.
  • the adjustment value of the hearing level is 26dBHL-40dBHL
  • the adjustment value of the sound level is in the frequency band of 40dBC-60dBC
  • the frequency is in the frequency band of 125Hz-375Hz
  • the hearing level is 26dBHL-40dBHL.
  • the adjustment value can be the same.
  • the same frequency band and/or the same hearing level may correspond to different adjustment values at different sound levels.
  • the adjustment value of sound level in 26dBC-40dBC, frequency in 0Hz-125Hz frequency band and hearing level 41dBHL-60dBHL may be different from the adjustment value of sound level in 40dBC-60dBC, frequency in 0Hz-125Hz frequency band and hearing level 41dBHL-60dBHL same.
  • the sound level is in the 26dBC-40dBC
  • the frequency is in the 125Hz-375Hz frequency band
  • the adjustment value of the hearing level is 26dBHL-40dBHL
  • the sound level is in the 40dBC-60dBC
  • the frequency is in the 125Hz-375Hz frequency band
  • the adjustment value of the hearing level 26dBHL-40dBHL can be different.
  • the same sound level and/or the same hearing level in different frequency bands may correspond to the same adjustment value.
  • the frequency is in the frequency range of 0Hz-125Hz (125Hz may not be included)
  • the sound level is 20dBC-40dBC and the adjustment value of the hearing level 41dBHL-60dBHL is in the frequency range of 125Hz-375Hz
  • the sound level is 20dBC-40dBC and the hearing level 41dBHL-
  • the adjustment value of 60dBHL can be the same.
  • the frequency is in the 125Hz-375Hz frequency band (375Hz may not be included)
  • the sound level is 40dBC-60dBC and the hearing level is 26dBHL-40dBHL and the frequency is in the 375Hz-625Hz frequency band.
  • the sound level is 40dBC-60dBC and the hearing level
  • the adjustment value of 26dBHL-40dBHL can be the same.
  • the same sound level and/or the same hearing level in different frequency bands may correspond to different adjustment values.
  • the frequency is in the frequency range of 0Hz-125Hz (125Hz may not be included)
  • the sound level is 20dBC-40dBC and the adjustment value of the hearing level 41dBHL-60dBHL is in the frequency range of 125Hz-375Hz
  • the sound level is 20dBC-40dBC and the hearing level 41dBHL-
  • the adjustment value of 60dBHL can be different.
  • the frequency is in the 125Hz-375Hz frequency band (375Hz may not be included)
  • the sound level is 40dBC-60dBC and the hearing level is 26dBHL-40dBHL and the frequency is in the 375Hz-625Hz frequency band.
  • the sound level is 40dBC-60dBC and the hearing level
  • the adjustment value of 26dBHL-40dBHL can be different.
  • the adjustment value is at least related to the frequency band, and in different frequency bands, the adjustment value may be different.
  • different frequency bands may correspond to different adjustment values, and frequencies within the same frequency band may correspond to the same adjustment value; in some embodiments, different frequencies may correspond to different adjustment values.
  • the adjustment value is in the range of 1dB-12dB in a frequency band with a frequency greater than 0Hz and less than or equal to 625Hz.
  • the adjustment value decreases as the frequency increases.
  • the adjustment value corresponding to the frequency of 125Hz may be 5dB; the adjustment value corresponding to the frequency of 250Hz may be 3dB; the adjustment value corresponding to the frequency of 500Hz may be 1dB.
  • the adjustment value corresponding to the frequency of 125 Hz may be 10 dB; the adjustment value corresponding to the frequency of 250 Hz may be 7 dB; and the adjustment value corresponding to the frequency of 500 Hz may be 4 dB.
  • the adjustment value in a frequency band with a frequency greater than 625 Hz and less than or equal to 8000 Hz, the adjustment value may be 0dB-4dB. In some embodiments, in a frequency band with a frequency greater than 625 Hz and less than or equal to 8000 Hz, the adjustment value may be 0.
  • the adjustment value in a frequency band whose frequency is greater than 0 Hz and less than or equal to 125 Hz, is set to 5dB-12dB. In some embodiments, the adjustment value is set to 3dB-9dB in a frequency band with a frequency greater than 125Hz and less than or equal to 375Hz. In some embodiments, the adjustment value is set to 1dB-6dB in a frequency band with a frequency greater than 375Hz and less than or equal to 625Hz. Further dividing the frequency bands and setting the above adjustment values in several frequency bands of the above frequency bands can make the bone conduction hearing aid device have a better effect of reducing vibration.
  • the adjustment value in a frequency band with a frequency greater than 0 Hz and less than or equal to 125 Hz, the adjustment value is 5dB-7dB. In the frequency band whose frequency is greater than 125Hz and less than or equal to 375Hz, the adjustment value is 3dB-5dB. In some embodiments, in a frequency band with a frequency greater than 375 Hz and less than or equal to 625 Hz, the adjustment value is 1 dB-3 dB.
  • the adjustment value in a frequency band whose frequency is greater than 0 Hz and less than or equal to 125 Hz, the adjustment value is 10 dB-12 dB. In some embodiments, in a frequency band with a frequency greater than 125 Hz and less than or equal to 375 Hz, the adjustment value is 7dB-9dB. In some embodiments, in a frequency band with a frequency greater than 375 Hz and less than or equal to 625 Hz, the adjustment value is 4dB-6dB.
  • Figures 9-11 are graphs of experimental results of speech recognition rate tests performed on three wearers (wearer 1, wearer 2, and wearer 3) respectively.
  • Figures 9-11 take the reference output parameter as the reference analog output value as an example, and show the wearer's speech recognition rate, vibration sense and volume before the reference analog output value is reduced, and the reference analog output value corresponding to different frequency bands The adjustment value of the wearer's speech recognition rate, vibration and volume.
  • Figures 9-11 have carried out 6 sets of tests for each tester.
  • a negative number indicates that the adjustment value reduces the reference output parameter (such as the reference analog output value), for example, -5 indicates that the adjustment value is 5dB, and the reference analog output value is The value is reduced by 5dB; as another example, -15 means that the adjustment value is 15dB, which reduces the reference analog output value by 15dB.
  • the speech recognition rate may decrease, the vibration sensation may decrease but the volume may decrease. It can be seen from the table that at the 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 the 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. rate did not change significantly.
  • 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).
  • the adjustment value is 10dB (or greater than 5dB but less than 10dB), that is, the reference analog output value is reduced by 10dB, and the reduction of speech recognition rate is less than or equal to 5%; at the frequency of 250Hz, if the adjustment The value is 7dB (or more than 3dB but less than 7dB), 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 the frequency of 500Hz, if the adjustment value is 4dB (or more than 1dB and less than 4dB), the reference analog output value is reduced by 4dB, and the reduction in speech recognition rate is less than or equal to 5%.
  • the adjustment value is set according to the above value, the tester may feel more comfortable, but the sound may be lower (that is, the wearer may feel that the volume is too low).
  • the reduction in speech recognition rate may be greater than 5% (for example, 10%); at 250Hz At the frequency, if the adjustment value is 15dB (or greater than 7dB but less than 15dB), that is, the reference analog output value is reduced by 15dB, the reduction in speech recognition rate may be greater than 5% (for example, 10%); at a frequency of 500Hz, If the adjustment value is 10dB (or greater than 4dB but less than 10dB), that is, the reference analog output value is reduced by 10dB, the speech recognition rate may be reduced by more than 5% (eg, 10%). At the same time, if the adjustment value is set according to the above value, 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).
  • the adjustment value is within the range of less than 17dB
  • the larger the number of adjustment values the better the effect of reducing the vibration of the bone conduction hearing aids.
  • the speech recognition rate may be greatly affected (for example, the speech recognition rate may be reduced).
  • the value is 30dBL-40dBL, it can not only solve the vibration problem of wearers with hearing level of 30dBL-40dBL when wearing bone conduction hearing aids in the corresponding frequency band, but also ensure that the impact on speech intelligibility is small.
  • the adjustment value of the reference output parameter may only be related to the frequency band.
  • the adjustment values corresponding to the reference output parameters in different hearing levels and in the same frequency band may be the same (such as the adjustment values in the above embodiments), and the corresponding adjustment values in the same hearing level and in different frequency bands may be different; the reference output parameters in different 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 with different sound levels and different hearing levels can be the same, the same The adjustment values in different frequency bands of the same hearing level are different.
  • the adjusted value of the reference output parameter may be related to the frequency band and the wearer's hearing level.
  • the corresponding adjustment values of the reference output parameters in the same frequency band of different hearing levels are different; the corresponding adjustment values of the reference output parameters under the same hearing level, the same frequency band, and different sound levels may be the same.
  • FIG. related instructions please refer to FIG. related instructions.
  • the adjustment value of the reference output parameter may be related to frequency band and sound level.
  • the reference output parameters have different adjustment values in the same frequency band under different sound levels; however, the corresponding adjustment values of the reference output parameters in different hearing levels, the same sound level, and the same frequency band can be the same.
  • the adjustment value of the reference output parameter may be related to frequency band and sound level.
  • Step 440 based on the reference output parameter and the adjustment value, configure the bone conduction hearing aid device. Specifically, step 440 may be performed by the configuration module 340 .
  • the processing device 120 may adjust the reference output parameters based on the adjustment values to obtain actual output parameters, and configure the bone conduction hearing aid device with the actual output parameters.
  • the processing device 120 may 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 using the reference output parameter minus the adjustment value, or adjusting the relevant setting parameters of other bone conduction hearing aids through the adjustment value to achieve the purpose of reducing the reference output parameter.
  • the processing device 120 may configure the magnetic circuit assembly based on the adjustment value and the reference output value to enable configuration of the bone conduction hearing aid device.
  • configuring the bone conduction hearing aid device includes setting various parameters of the bone conduction hearing aid device, so that the bone conduction hearing aid device has parameters (eg, gain value, analog output value) related to the signal output intensity. is a preset value, for example, a reference parameter adjusted based on the adjustment value.
  • the reference gain value of the bone conduction hearing aid device to the sound signal can be adjusted by adjusting the current size of the electromagnet in the magnetic circuit assembly, adjusting the resistance size of the amplifier circuit of the pickup assembly, etc., and adjusting the reference gain value of the bone conduction hearing aid device. Simulate output values to enable configuration of bone conduction hearing aids.
  • an equalization adjustment system EQ system
  • an automatic gain control system AGC system or the like may be used to configure the bone conduction hearing aid device.
  • a multi-channel wide dynamic range compression system may be used to configure the bone conduction hearing aid.
  • the multi-channel wide dynamic range compression system can first use a 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 the appropriate compression ratio can be designed according to the hearing loss corresponding to the frequency band. and compression threshold, and then combine the processed signals of each channel into one signal.
  • the multi-channel wide dynamic range compression system can be more flexible for hearing compensation.
  • 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 flowchart of a method according to the method for obtaining an adjustment value of a reference output parameter.
  • the adjustment value determined using the method shown in Figure 5 is related to the wearer's hearing level.
  • the process 500 includes the following steps.
  • Step 510 Determine the first threshold corresponding to each frequency band and each sound level, wherein the first threshold is related to the degree of vibration perception of the wearer to each sound level of each frequency band.
  • the degree of vibration perception can be used to indicate the degree to which the user perceives vibration when wearing the bone conduction hearing aid.
  • the degree of vibration perception may include multiple levels for representing the degree to which vibration is perceived. The higher the level, the more vibration the user can perceive.
  • the levels may include a first level, a second level, a third level, a fourth level, and a fifth level, and the corresponding vibration sensation levels may include "no vibration”, “extremely slight vibration", “slight vibration”, and “slight vibration”. Vibration”, “Vibration is obvious but acceptable", “Vibration is severe and unacceptable”.
  • the different levels may be represented by scores.
  • 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
  • the fifth level may be 5 points.
  • the first threshold value may be the output signal strength of the corresponding bone conduction hearing aid device when the wearer's vibration perception level is below a certain level, that is, when the strength of the output signal of the bone conduction hearing aid device reaches At this first threshold, the wearer can feel this level of vibration.
  • the first threshold may be the output signal strength (ie, the reference output parameter) of the corresponding bone conduction hearing aid device when the wearer's vibration perception level is below 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.
  • the first threshold may be the output signal strength of the corresponding bone conduction hearing aid device when the wearer's vibration perception level is below 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 received.
  • the wearer may feel more vibration at the level corresponding to the first threshold (eg, slight vibration corresponding to the third level) If the vibration is strong and the wearing experience is poor, the reference output parameter needs to be adjusted (reduced), so that the output signal strength of the bone conduction hearing aid device is less than the first threshold.
  • preliminary reference output parameters corresponding to the wearer of the bone conduction hearing aid device at each sound level and each frequency band may be obtained.
  • reference may be made to operation 420 in FIG. 4 .
  • the first threshold may be different for different wearers.
  • a test can be performed on the wearer of the bone conduction hearing aid device to determine the output signal strength and the corresponding vibration perception level of the wearer of the bone conduction hearing aid device under the preliminary reference output parameter 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 the degree of vibration perception, so that the wearer's vibration perception degree reaches a certain level (for example, the third level, slight vibration), and then determine each frequency band and each sound level the corresponding first threshold.
  • the adjusted preliminary reference output parameter ie, the reference output parameter, eg, the reference analog output value
  • the first threshold may be equal to the corresponding adjusted output signal strength or the reference analog output value when the wearer's vibration feeling degree reaches a certain level (eg, the third level, slight vibration).
  • the first threshold may be the same for different wearers.
  • the first threshold value can be specifically determined according to the following method: testing a plurality of testers to determine the signal output intensity when each tester subjectively feels the slight vibration of the second level at each sound level and each frequency band, 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 may be applicable to different wearers.
  • the integration and selection of the test data may be as follows: for a certain frequency band, only the lowest value of the output parameter when each tester subjectively feels slight vibration at each sound level in the frequency band is considered, And further select the lowest value as the first threshold value from the lowest value of the output parameter when each tester subjectively feels slight vibration at each sound level.
  • the severe vibration phenomenon of the bone conduction hearing aid device in the low frequency band is more obvious, and the adjustment value of the reference output parameter can be set in the low frequency band, so as to reduce the reference output parameter and reduce the user can Perceived vibration intensity; correspondingly, a first threshold may be set in a low frequency band (eg, 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, the first threshold may be set in a frequency band of 0 Hz-625 Hz, and the adjustment value may be determined in this frequency band. In some embodiments, the first thresholds corresponding to different frequency bands are different.
  • the first threshold in a frequency band with a frequency greater than 0 Hz and less than or equal to 125 Hz, is in the range of 48dB-52dB. In some embodiments, in a frequency band with a frequency 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 a frequency band with a frequency greater than 375 Hz and less than or equal to 625 Hz, the first threshold is in the range of 50dB-55dB. In some embodiments, the higher the frequency band at the same sound level, the larger the first threshold.
  • the first thresholds corresponding to the same frequency band with different sound levels may be the same, for example, a minimum value (eg, 48dB) may be selected within the range of the corresponding first thresholds in the above-mentioned frequency bands as the first threshold value of the frequency band
  • the threshold value is set so that the bone conduction hearing aid device will not generate severe vibration when the received sound signals are of different sound levels and the same frequency band.
  • the first threshold in a frequency band with a frequency greater than 0 Hz but less than or equal to 125 Hz, the first threshold is 48 dB.
  • the first threshold value is 49 dB.
  • the first threshold is 50 dB.
  • the first thresholds corresponding to the same frequency band with different sound levels may be different.
  • the higher the sound level in the same frequency band the larger the first threshold may be.
  • the sound level in the frequency band greater than 0Hz but less than or equal to 125Hz, the sound level is 20dBC-40dBC, and the first threshold is 48dB; in the frequency band of 0Hz but less than or equal to 125Hz, the sound level is 40dBC-50dBC, and the first threshold is 49dB; In the frequency band of 0Hz and less than or equal to 125Hz, the sound level is 50dBC-60dBC, and the first threshold is 50dB.
  • the first thresholds corresponding to the same frequency band with different hearing levels and different sound levels may be the same.
  • a minimum value for example, 48dB
  • the first threshold of so that when the received sound signal of the bone conduction hearing aid device is in the same frequency band, no matter the sound level of the sound signal and the hearing level of the wearer, no more severe vibration will be generated.
  • the first thresholds corresponding to the same frequency band at different hearing levels and different sound levels are different.
  • the first threshold may be 49 dB.
  • the first threshold may be 50dB when the frequency of 10dBHL is greater than 125Hz but less than or equal to 375Hz and the sound level is 75dBC.
  • the first threshold may be 55dB for the hearing level at a frequency of 30dBHL in a frequency band greater than 375Hz but less than or equal to 625Hz and a sound level of 70dBC.
  • the first threshold may be 56 dB.
  • the first thresholds corresponding to different sound levels in different frequency bands and different hearing levels may be the same.
  • a minimum value for example, 48dB
  • 48dB may be selected within the range of the corresponding first thresholds in the above-mentioned frequency bands as all frequency bands
  • First thresholds corresponding to different sound levels so that the bone conduction hearing aid device will not generate severe vibration when the received sound signals are of different sound levels and different frequency bands.
  • the first threshold is 48dB.
  • Step 520 Determine 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
  • the speech recognition rate can be used to characterize the wearer's hearing sensitivity and clarity to the language heard after wearing the hearing aid, thereby reflecting the wearer's hearing aid effect to a certain extent.
  • the higher the speech recognition rate the higher the hearing sensitivity of the wearer after wearing the hearing aid, and the higher the hearing clarity, the better the hearing aid effect.
  • 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.
  • the adjustment (eg, reduction) of the reference output parameter can 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.
  • the second threshold may be used to ensure that the speech recognition rate adjusted by the reference output parameter is within a certain range (eg, higher than a certain threshold). That is to say, the second threshold may be used to control the amount of decrease of the speech recognition rate adjusted by the reference output parameter within a certain range.
  • the reduction in the speech recognition rate of the wearer wearing the hearing aid relative to the reference output parameter when not adjusted may be small, eg, the reduction in speech recognition rate may be less than or equal to 5%.
  • the amount of decrease in 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.
  • the second threshold may be the maximum value of the adjustment value corresponding to the reference output parameter of the bone conduction hearing aid device corresponding to the preset speech recognition rate when the wearer wears the bone conduction hearing aid device, that is, when the wearer wears the bone conduction hearing aid device
  • the speech recognition rate when the wearer wears the bone conduction hearing aid device is a preset threshold value.
  • the speech recognition rate will be lower than the preset speech recognition rate when the wearer wears the bone conduction hearing aid device.
  • 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 device at 125 Hz is the second threshold, the speech recognition rate when the wearer wears the bone conduction hearing aid device may be 80%.
  • the second threshold may be an adjustment value corresponding to a reference output parameter with a speech recognition rate of 60% at 250 Hz when the wearer wears the bone conduction hearing aid device, that is, the second threshold is 12 dB. That is, when the adjustment value corresponding to the reference output parameter of the bone conduction hearing aid device at 250 Hz is the second threshold, the speech recognition rate when the wearer wears the bone conduction hearing aid device may be 60%.
  • the second threshold may be determined according to a preset speech recognition rate threshold.
  • the second threshold may be determined based on the experimental results of the speech recognition rate tests performed on the wearer in FIGS. 9-11 .
  • the wearer's speech recognition rate is 80%, and if the reference output parameters are set to be reduced, the speech recognition rate is not less than 75% ( That is, the reduction of speech recognition rate is less than or equal to 5%)
  • the second threshold may be 10dB; if the speech recognition rate is set to be not less than 80% (ie, the speech recognition rate is hardly reduced), the second threshold may be 5dB.
  • the severe vibration phenomenon of the bone conduction hearing aid device in the low frequency band is more obvious, and the adjustment value of the reference output parameter can be set in the low frequency band, so as to reduce the reference output parameter and reduce the user can The perceived vibration intensity; correspondingly, a second threshold may be set in a low frequency band (eg, 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.
  • the second thresholds corresponding to different frequency bands are different. For example, in a frequency band with a frequency greater than 0 Hz and less than or equal to 125 Hz, the second threshold is in the range of 5dB-10dB.
  • the second threshold is in the range of 3dB-7dB in a frequency band with a frequency greater than 125Hz and less than or equal to 375Hz. In some embodiments, in a frequency band with a frequency greater than 375 Hz and less than or equal to 625 Hz, the second threshold is within a range of 1 dB-4 dB. In some embodiments, the higher the frequency band at the same sound level, the smaller the second threshold.
  • the second thresholds corresponding to the same frequency band at different hearing levels may be the same. For example, regardless of whether the wearer's hearing level is 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 band greater than 0Hz but less than or equal to 125Hz, the hearing level is 30dBHL, and the second threshold is 5dB; in the frequency band of 0Hz but less than or equal 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 with different sound levels may be the same.
  • 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 of different sound levels.
  • the second threshold in a frequency band with a frequency 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 in a frequency band with a frequency greater than 0 Hz and less than or equal to 125 Hz. In some embodiments, in a frequency band with a frequency greater than 375 Hz and less than or equal to 625 Hz, the second threshold may be 1 dB.
  • the second thresholds corresponding to the same frequency band with different sound levels may be different.
  • the sound level is 60dBC
  • the second threshold is 5dB
  • the sound level is 75dBC
  • the second threshold is 10dB.
  • Step 530 determining an adjustment value based on the reference output parameter, the first threshold and the second threshold.
  • an initial adjustment value 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.
  • a comparison value may be obtained by subtracting the first threshold value corresponding to the specific frequency band and the specific sound level from the reference output parameter corresponding to the specific frequency band and the specific sound level; then, the comparison value is compared with the specific frequency band and the specific sound level.
  • the second threshold value corresponding to the sound level is compared; based on the comparison result between the comparison value and the second threshold value, the adjustment value corresponding to the specific frequency band and the reference output parameter at the specific sound level is determined.
  • the comparison value can be positive, negative, or zero. Comparing the comparison value with the second threshold may be a comparison of magnitudes of numerical values to determine the magnitude relationship between the comparison value and the second threshold.
  • the comparison result of the comparison value and the second threshold value may include that the comparison value is smaller than the second threshold value, the comparison value is equal to the second threshold value, or the comparison value is larger than the second threshold value.
  • the adjustment value corresponding to the reference output parameter is determined based on the comparison result between the comparison value and the second threshold, which may be determined based on the magnitude relationship between the comparison value and the second threshold.
  • determining the adjustment value corresponding to the reference output parameter may include that when the comparison value is less than or equal to 0, the adjustment value is 0; when the comparison value is greater than 0 but less than or equal to the first When there are two thresholds, 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 wearer When the reference output parameter is less than or equal to the first threshold, after the bone conduction hearing aid device is configured according to the reference output parameter, the wearer is less likely to experience vibration after wearing the bone conduction hearing aid device, and there is no need to adjust the reference output parameter .
  • the reference output parameter is greater than the first threshold, after the bone conduction hearing aid device is configured according to the reference output parameter, the wearer is more likely to experience strong vibration after wearing the bone conduction hearing aid device, and the reference output parameter needs to be adjusted. . Further, when determining the adjustment value, not only the vibration risk of the bone conduction hearing aid brought by the reference output parameter, but also the influence of the adjusted reference output parameter on the speech recognition rate of the bone conduction hearing aid should be considered.
  • the second threshold is a threshold related to the speech recognition rate, by comparing the above-mentioned 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 speech caused by the adjustment of the reference output parameters. The impact of recognition rate.
  • FIG. 6 is an exemplary flowchart of a method according to the method for obtaining an adjustment value of a reference output parameter.
  • the process 600 shown in FIG. 6 may be used to determine the adjustment value corresponding to the reference output parameter.
  • the process 600 of determining the adjustment value corresponding to the reference output parameter may include the following steps:
  • Step 610 compare the reference output parameter with the first threshold.
  • the first threshold is related to the degree of the wearer's vibration perception of each sound level in each frequency band.
  • Comparing the reference output parameter with the first threshold may be a numerical magnitude comparison of the reference output parameter with the first threshold.
  • Step 620 Determine an adjustment value corresponding to the reference output parameter based on the comparison result between the reference output parameter and the first threshold.
  • the comparison result of the reference output parameter and the first threshold may include comparison results that the reference output parameter is greater than the first threshold, the reference output parameter is equal to the first threshold, and the reference output parameter is equal to the first threshold.
  • whether the adjustment value is 0 may be determined 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 larger than the first threshold, the adjustment value is larger than 0.
  • the adjustment value may include a gain of the multi-channel wide dynamic range compression system when at least one of the respective sound levels is greater than a sound level threshold Decrease the value.
  • the sound level threshold may be 70dB.
  • 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, which may occur when the wearer speaks by himself or when the environment is relatively noisy.
  • the bone conduction hearing aids may generate relatively strong vibrations. Therefore, the adjustment value is set to be within the sound level range.
  • Internal adjustment (eg, lowering) of the reference output parameter can improve the vibration of the bone conduction hearing aid device, and can also make the wearer's speech recognition rate almost unaffected during daily conversations.
  • the gain when at least one sound level in each sound level is greater than the sound level threshold value can be called the 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. Decrease 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 (eg, 70 dB).
  • the gain of the multi-channel wide dynamic range compression system when at least one of the sound levels is greater than a sound level threshold may be determined based on the wearer's hearing loss data, eg, may be determined according to an empirical formula. For example, an empirical formula may be based on the wearer's hearing level to determine the High Level Gain of a multi-channel wide dynamic range compression system.
  • the adjustment value can be a specific value that reduces the high level gain derived from the empirical formula.
  • whether the gain reduction value is 0 (ie, whether to reduce the gain when at least one of the sound levels is greater than the sound level threshold) may be determined based on whether the reference output parameter is greater than the first threshold. For example, when the reference output parameter is less than the first threshold, the gain reduction value is 0; when the reference output parameter is greater than the first threshold, the gain reduction value is greater than 0.
  • 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 gain
  • the gain value is used as the input parameter of the multi-channel wide dynamic range compression system.
  • the sound level threshold is set, the gain reduction value is determined according to the above method, and the gain reduction value is used as the adjustment value, which can ensure that the reference output parameter is not affected when the sound level of the sound signal is less than 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 device, it can also improve the situation that the bone conduction hearing aid device vibrates violently in some scenarios.
  • step 620 may specifically include the following steps: if the reference output parameter is less than or equal to the first threshold value, the gain reduction value is 0; if the reference output parameter is greater than the first threshold value, the gain reduction value is the difference between the first threshold value and the reference output parameter.
  • the reference output parameter is less than or equal to the first threshold, the probability of the wearer feeling severe vibration when wearing the bone conduction hearing aid device is small, and there is no need to adjust (reduce) the high-level gain.
  • the gain reduction value is set to 0. If the reference output parameter is greater than the first threshold, there is a high probability that the wearer will experience severe vibration when wearing the bone conduction hearing aid, and the high level gain needs to be adjusted (reduced), thereby reducing the reference output parameter so that the reference output The parameter can be smaller than the first threshold.
  • the adjustment value may include a maximum 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 The lower value of the output (Output Limit).
  • the sound level threshold may be 70dB.
  • the sound level of the sound signal greater than or equal to 70dBC may occur when the wearer speaks by himself or when the environment is relatively noisy. At this time, the bone conduction hearing aid device may generate relatively strong vibration.
  • the adjustment value is set using 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 the bone conduction hearing aids and make the wearer's speech recognition rate almost unaffected during daily conversations. influences.
  • the maximum output can be understood as a limited value for the reference output parameter in each frequency band. When the reference output parameter is greater than the maximum output, the reference output parameter of the bone conduction hearing aid device is equal to the maximum output.
  • the maximum output (Output Limit) of the multi-channel wide dynamic range compression system can be determined according to an empirical formula based on the wearer's hearing loss data. For example, an empirical formula may be based on the wearer's hearing level to determine the maximum output (Output Limit) of a multi-channel wide dynamic range compression system.
  • the adjustment value can be a specific value that reduces the maximum output derived from the empirical formula.
  • the empirical formula may be set by the user or a default setting of the bone conduction hearing aid configuration system.
  • step 620 may further include the following Steps: if the reference output parameter is less than or equal to the first threshold, the reduction value of the maximum output is 0dB; if the reference output parameter is greater than the first threshold, the reduction value of the maximum output is greater than 0dB.
  • the reference output parameter is less than or equal to the first threshold, the probability of the wearer feeling severe vibration when wearing the bone conduction hearing aid device is small, and there is no need to adjust (reduce) the maximum output; if the reference output parameter is greater than the first threshold threshold, the wearer has a high probability of experiencing severe vibration when wearing the bone conduction hearing aid device, and the maximum output needs to be adjusted (reduced), thereby reducing the reference output parameter so that the reference output parameter can be smaller than the first threshold.
  • the specific value of the reduction value of the maximum output parameter may be further determined.
  • the maximum output may be stepped down in equal steps so that the reference output parameter is eventually smaller than the first threshold. For example, reducing the maximum output stepwise with equal steps may reduce the maximum output by the same value each time (eg, reduce 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 .
  • the sound level at this time is relatively large, for example, greater than or equal to 70dB
  • the medium sound level such as When the sound signal with a sound level below 70dB
  • the reference output parameters of the bone conduction hearing aid will not be affected, and when the sound signal with a high sound level (such as a sound level of 70dB and above) is input into the bone conduction hearing aid
  • the reference output parameter of the bone conduction hearing aid device is lower than the first threshold, so as to improve the situation that the wearer feels stronger vibration when he speaks or when the ambient sound is louder.
  • the adjustment values may only include gain reduction values when at least one of the respective sound levels is greater than a sound level threshold. In other embodiments, the adjustment value may only include a reduced value of the maximum output (Output Limit) when at least one of the respective sound levels is greater than the sound level threshold. In some embodiments, the adjustment value may include both a gain reduction value when at least one of the sound levels is greater than a sound level threshold, and the adjustment value may only include a gain reduction value when at least one of the sound levels is greater than a sound level threshold The lower value of the maximum output (Output Limit).
  • the setting parameters of the multi-channel wide dynamic range compression system further include a crossover frequency (Crossover Frequency), a lower threshold (Lower Threshold), a low level gain (Low Level Gain), an upper threshold (Upper Threshold), amplification Threshold (Expansion Threshold), Amplification Ratio (Expansion Ratio), Effector Attack Time (Compressor Attack), Effector Release Time (Compressor Release), Gain Algorithm Generation Time (AGCo Attack), Gain Algorithm Release Time (AGCo Release).
  • the crossover frequency (Crossover Frequency) may be the frequency at which the audio frequency spectrum is divided, that is, the 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 the gain when the input sound level is less than the 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 the sound level amplification threshold in the frequency band, and the amplification ratio may be the gain ratio of the sound with the amplification threshold.
  • the effector generation time can be a transition time when the effector detects a sound higher than the threshold, and the effector fully works, and the gain gradually increases to the preset gain during the transitional time.
  • the release time of the effector can be the transitional time when the effect is fully activated when the sound is below the threshold, and the gain is gradually reduced to the preset gain during the transitional time.
  • the gain algorithm is an output-based automatic gain control algorithm (Automatic Gain Control according to Output, AGCo), and the gain algorithm generation time can be 2ms.
  • the gain algorithm release time can be 64ms.
  • FIG. 7 is a flowchart of operations performed by the bone conduction hearing aid device during use according to some embodiments of the present application. 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:
  • the sound input signal may include an audio signal (eg, song, voice, etc.) obtained by the bone conduction hearing aid device from a storage device (eg, memory 130 ), a terminal (eg, terminal 140 ), and the like.
  • the sound signal input to the bone conduction hearing aid device may include a sound signal picked up by a sound pickup component of the bone conduction hearing aid device.
  • the sound pickup assembly can pick up sound (the first vibration signal), and convert the first vibration signal into an electrical signal after processing.
  • the electrical signal can be transmitted to the speaker component of the bone conduction hearing aid device, and the speaker component is used to process the electrical signal based on the reference output parameter and convert the electrical signal into a second vibration signal, which is transmitted to the wearer.
  • Step 720 Determine the reference output parameter corresponding to the frequency component based on the sound level, the frequency component and the reference output parameter of the sound input signal.
  • 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 can correspond to different frequency bands, sound levels and hearing levels.
  • the bone conduction hearing aid device may determine the reference output parameter corresponding to the sound level and the frequency component from the preset reference output parameters according to the sound level and frequency component of the sound input signal.
  • the bone conduction hearing aid device may determine a reference corresponding to the sound level, frequency component and hearing level from preset reference output parameters according to the sound level, frequency component of the sound input signal and the hearing level of the wearer Output parameters.
  • 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, obtain the actual output parameter corresponding to the frequency component at the sound level.
  • the bone conduction hearing aid device may 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 different frequency bands, sound levels, and reference output parameters under the hearing level.
  • the bone conduction hearing aid device can determine the adjustment value corresponding to the reference output parameter corresponding to the sound level and the frequency component from the preset adjustment values according to the sound level and the frequency component of the sound input signal.
  • the bone conduction hearing aid device may determine the reference output corresponding to the sound level, frequency component and hearing level from preset adjustment values according to the sound level, frequency component of the sound input signal and the hearing level of the wearer The adjustment value corresponding to the parameter.
  • 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 based on the actual output parameters, control the bone conduction hearing aid device to output sound signals.
  • the reference output parameter can be understood as the parameter initially set in the process of configuring the bone conduction hearing aid device, and the actual output parameter can be understood as the output parameter adjusted by the bone conduction hearing aid device based on the adjustment value.
  • the actual output parameters may include gain values and/or actual analog output values.
  • the actual gain value may be the value that the hearing aid actually amplifies the strength of the sound signal during wearing
  • the actual analog output value may be the hearing aid simulated according to the input sound signal parameter (for example, the strength value of the sound signal) The actual output signal strength value.
  • 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).
  • 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, unit dB), for example, when the input sound signal of the bone conduction hearing aid is at the specific sound level and the specific frequency band.
  • the sound pickup assembly 220 of the bone conduction hearing aid may perform step 710, and the magnetic circuit assembly of the bone conduction hearing aid may perform steps 720 and 730.
  • the vibration component of the auxiliary bone conduction hearing device may perform step 740, and the vibration component may convert the actual output parameter determined by the magnetic circuit component into a corresponding vibration intensity, so that the auxiliary bone conduction hearing device outputs sound signals through mechanical vibration.
  • the sound pickup assembly 220 of the bone conduction hearing aid may perform step 710, and the processing device in the bone conduction hearing aid may perform steps 720 and 730.
  • the processing device of the bone conduction hearing aid device may control the magnetic circuit component and the vibration component to perform step 740 .
  • the processing device may control the vibration component 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 sound signals through mechanical vibration.
  • the processing device may control the magnitude of the current in the voice coil based on the determined actual output parameter, so as to control the strength of mechanical vibration generated by the voice coil, thereby controlling the strength of the output signal of the bone conduction hearing aid device.
  • actual output parameters of each frequency band and each sound level may be stored in the bone conduction hearing aid device.
  • 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 the corresponding frequency band based on the sound level and frequency band of the sound input signal, and based on the sound level and frequency band of the sound input signal, the bone conduction hearing aid device can directly determine the actual output parameters The actual output parameter outputs a sound signal.

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Abstract

本申请公开了一种配置骨导听力辅助设备的方法及系统，其包括以下步骤: 获取佩戴者的听力损失数据; 基于所述听力损失数据，确定骨导听力辅助设备在各个声级各个频段下的参考输出参数; 获取所述参考输出参数的调整值; 所述调整值至少与所述频段相关; 基于所述参考输出参数和所述调整值，配置所述骨导听力辅助设备。

Description

骨导听力辅助设备的配置方法及系统 技术领域
本申请涉及骨传导听力辅助领域，特别涉及一种配置骨导听力辅助设备的方法及系统。
背景技术
骨导听力辅助设备是利用骨传导技术而进行设计和制造的一种听力辅助设备。骨导听力辅助设备可以为骨导助听器或骨导辅听耳机。骨导听力辅助设备主要将外部声音信息放大并转化为机械振动，并通过机械振动的形式，将外界声音依次通过人的颅骨、骨迷路、内耳淋巴液、螺旋器、听神经，送入大脑皮层听觉中枢。相比于传统气传导助听器，骨导听力辅助设备的声波信号可直接通过骨头传至听神经，而无需经过外耳道和耳膜，避免了传统气传导助听器阻塞耳道而形成的压迫感及堵耳效应，且骨导听力辅助设备能够使得佩戴者具有更舒适的佩戴体验。另外，骨导听力辅助设备无需植入耳内，也能够有效避免耳道发炎。因此，骨导听力辅助设备越来越广泛地被听障患者使用。
由于骨导听力辅助设备是通过振动传递以使佩戴者听到声音，在使用过程可能会出现振动比较剧烈的情况，会影响佩戴者的佩戴体验；而较低的振动则又会影响佩戴者的听音效果，因此，需要提供一种骨导听力辅助设备配置方法，以改善骨导听力辅助设备在某些情况下振动剧烈的情况又不会影响佩戴者听音效果。
发明内容
本申请实施例之一提供一种骨导听力辅助设备的配置方法，其包括以下步骤：获取佩戴者的听力损失数据；基于所述听力损失数据，确定骨导听力辅助设备在各个声级各个频段下的参考输出参数；获取所述参考输出参数的调整值，所述调整值至少与所述频段相关；基于所述参考输出参数和所述调整值，配置所述骨导听力辅助设备。
在一些实施例中，基于所述参考输出参数和所述调整值，配置所述骨导听力辅助设备包括：在频率大于0Hz而小于或等于625Hz的频段内，基于所述调整值降低所述参考输出参数。
在一些实施例中，在不同听力级以及相同频段下的所述调整值相同。
在一些实施例中，在频率大于0Hz而小于或等于625Hz的频段内，所述调整值为1dB -12dB。
在一些实施例中，在频率大于0Hz而小于或等于125Hz的频段内，所述调整值设定为5dB-12dB；在频率大于125Hz而小于或等于375Hz的频段内，所述调整值设定为3dB-9dB；和/或，在频率大于375Hz而小于或等于625Hz的频段内，所述调整值设定为1dB-6dB。
在一些实施例中，在频率大于0Hz而小于或等于125Hz的频段内，所述调整值为5dB-7dB；在频率大于125Hz而小于或等于375Hz的频段内，所述调整值为3dB-5dB；和/或，在频率大于375Hz而小于或等于625Hz的频段内，所述调整值为1dB-3dB。
在一些实施例中，在频率大于0Hz而小于或等于125Hz的频段内，所述调整值为10dB-12dB；在频率大于125Hz而小于或等于375Hz的频段内，所述调整值为7dB-9dB；和/或，在频率大于375Hz而小于或等于625Hz的频段内，所述调整值为4dB-6dB。
在一些实施例中，在不同听力级以及相同频段下的所述调整值不同。
在一些实施例中，所述获取所述参考输出参数的调整值包括：确定所述各个频段以及所述各个声级对应的第一阈值，所述第一阈值与所述佩戴者对所述各个频段所述各个声级的振动感受程度相关；确定所述各个频段以及所述各个声级对应的第二阈值，所述第二阈值与所述佩戴者在所述各个频段各个声级的言语识别率相关；以及基于所述参考输出参数、所述第一阈值和所述第二阈值确定所述调整值。
在一些实施例中，所述基于所述参考输出参数、所述第一阈值和所述第二阈值确定所述调整值包括：对于所述各个声级以及所述各个频段中的某一声级以及某个频段下的参考输出参数；将所述参考输出参数减去所述第一阈值而获得比较值；将所述比较值与所述第二阈值进行比较；基于所述比较值与所述第二阈值的比较结果，确定所述参考输出参数对应的调整值。
在一些实施例中，所述基于所述比较值与所述第二阈值的比较结果，确定所述参考输出参数对应的调整值包括：当所述比较值小于或等于0时，所述调整值为0dB；当所述比较值大于0而小于等于所述第二阈值时，所述调整值为所述比较值；当所述比较值大于所述第二阈值时，所述调整值为所述第二阈值。
在一些实施例中，在频率大于0Hz而小于等于125Hz的频段内，所述第一阈值在48dB-52dB范围内。
在一些实施例中，在频率大于125Hz而小于等于375Hz的频段内，所述第一阈值在49dB-54dB范围内。
在一些实施例中，在频率大于375Hz而小于等于625Hz的频段内，所述第一阈值在 50dB-55dB范围内。
在一些实施例中，在频率大于0Hz而小于等于125Hz的频段内，所述第二阈值在5dB-10dB范围内。
在一些实施例中，在频率大于125Hz而小于等于375Hz的频段内，所述第二阈值在3dB-7dB范围内。
在一些实施例中，在频率大于375Hz而小于等于625Hz的频段内，所述第二阈值在1dB-4dB范围内。
在一些实施例中，基于所述参考输出参数和所述调整值，配置所述骨导听力辅助设备包括：基于所述参考输出参数和所述调整值，使用多通道宽动态范围压缩系统，配置所述骨导听力辅助设备。
在一些实施例中，所述获取所述参考输出参数的调整值，包括：将所述参考输出参数与第一阈值进行比较，所述第一阈值与所述佩戴者对所述各个频段所述各个声级的振动感受程度相关；基于所述参考输出参数与所述第一阈值的比较结果，确定所述参考输出参数对应的所述调整值。
在一些实施例中，所述调整值包括在所述各个声级中至少一个声级大于声级阈值时所述多通道宽动态范围压缩系统的增益降低值；基于所述参考输出参数与所述第一阈值的比较结果，确定所述参考输出参数对应的所述调整值，包括：如果所述参考输出参数小于或等于所述第一阈值，则所述增益降低值为0dB；如果所述参考输出参数大于所述第一阈值，则所述增益降低值为所述第一阈值与所述参考输出参数的差值。
在一些实施例中，所述调整值包括在所述各个声级中至少一个声级大于声级阈值时所述多通道宽动态范围压缩系统的最大输出的降低值；基于所述参考输出参数与所述第一阈值的比较结果，确定所述参考输出参数对应的调整值，包括：如果所述参考输出参数小于或等于所述第一阈值，则所述最大输出的降低值为0dB；如果所述参考输出参数大于所述第一阈值，则所述最大输出的降低值大于0dB。
本申请实施例之一提供一种骨导听力辅助设备的配置系统，其包括：获取模块，用于获取佩戴者的听力损失数据；参考输出参数确定模块，用于基于听力损失数据，确定骨导听力辅助设备在各个声级各个频段下的参考输出参数；调整值确定模块，用于获取参考输出参数的调整值；配置模块，用于基于参考输出参数和调整值，配置骨导听力辅助设备。
本申请实施例之一提供一种骨导听力辅助设备的配置装置，其包括：处理设备；与所述处理设备通信的存储设备，用于存储指令，当所述处理设备执行所述存储指令，所述处理 设备执行上述任一技术方案所述的骨导听力辅助设备的配置方法。
本申请实施例之一提供一种计算机可读存储介质，所述存储介质存储计算机指令，当计算机读取所述存储介质中的计算机执指令时，所述计算机执行上述任一技术方案所述的骨导听力辅助设备的配置方法。
附图说明
本申请将以示例性实施例的方式进一步说明，这些示例性实施例将通过附图进行详细描述。这些实施例并非限制性的，在这些实施例中，相同的编号表示相同的结构，其中：
图1是根据本申请一些实施例所示的骨导听力辅助设备的配置装置的示意图；
图2是根据本申请一些实施例所示的骨导听力辅助设备的结构示意图；
图3是根据本申请一些实施例所示的骨导听力辅助设备的配置系统的模块图；
图4是根据本申请一些实施例所示的骨导听力辅助设备的配置方法的流程图；
图5是根据本申请另一些实施例所示的确定调整值的流程图；
图6是根据本申请另一些实施例所示的确定调整值的流程图；
图7是根据本申请一些实施例所示的骨导听力辅助设备在使用过程中所执行操作的流程图；
图8是实验测定的佩戴者佩戴骨导听力辅助设备时在不同频率下的振动感知阈值图；
图9是对佩戴者1进行言语识别率测试的实验结果图；
图10是对佩戴者2进行言语识别率测试的实验结果图；
图11是对佩戴者3进行言语识别率测试的实验结果图。
具体实施方式
为了更清楚地说明本说明书实施例的技术方案，下面将对实施例描述中所需要使用的附图作简单的介绍。显而易见地，下面描述中的附图仅仅是本说明书的一些示例或实施例，对于本领域的普通技术人员来讲，在不付出创造性劳动的前提下，还可以根据这些附图将本说明书应用于其它类似情景。除非从语言环境中显而易见或另做说明，图中相同标号代表相同结构或操作。
应当理解，本文使用的“系统”、“装置”、“单元”和/或“模块”是用于区分不同级别的不同组件、元件、部件、部分或装配的一种方法。然而，如果其他词语可实现相同的目的，则可通过其他表达来替换所述词语。
如本说明书和权利要求书中所示，除非上下文明确提示例外情形，“一”、“一个”、 “一种”和/或“该”等词并非特指单数，也可包括复数。一般说来，术语“包括”与“包含”仅提示包括已明确标识的步骤和元素，而这些步骤和元素不构成一个排它性的罗列，方法或者设备也可能包含其它的步骤或元素。
本说明书中使用了流程图用来说明根据本说明书的实施例的系统所执行的操作。应当理解的是，前面或后面操作不一定按照顺序来精确地执行。相反，可以按照倒序或同时处理各个步骤。同时，也可以将其他操作添加到这些过程中，或从这些过程移除某一步或数步操作。
图1是根据本申请的一些实施例所示的骨导听力辅助设备配置装置的示意图。如图1所示，骨导听力辅助设备配置系统100可以包括骨导听力辅助设备110、处理设备120、存储器130、一个或多个终端140以及网络150。在一些实施例中，骨导听力辅助设备110、处理设备120、存储器130和/或终端140可以经由无线连接(例如，网络150)、有线连接或其组合相互连接和/或通信。骨导听力辅助设备配置系统100中的组件之间的连接是可以变化的。仅作为示例，骨导听力辅助设备110可以通过网络150连接到处理设备120，如图1所示。又例如，骨导听力辅助设备110可以直接连接到处理设备120。再例如，存储器130可以通过网络150连接到处理设备120，如图1所示，或者直接连接到处理设备120。作为又一示例，终端140可以通过网络150连接到处理设备120，如图1所示，或者直接连接到处理设备120。
骨导听力辅助设备110可以用于获取声音信息(例如，环境音、佩戴者声音、其他设备中获取的音频文件等)并将获取的声音信息进行处理后转化为振动信号，通过佩戴者的骨头等传递给佩戴者的听觉中枢，以便佩戴者可以听到该振动信号携带的声音信息。骨导听力辅助设备具体可以是骨导助听器，也可以是骨导辅听耳机。本说明书中主要以骨导听力辅助设备为骨导助听器为例进行说明。
在一些实施例中，骨导听力辅助设备110(如骨导助听器)可以包括拾音组件、扬声器组件等。拾音组件用于拾取声音信息(也可以称为第一振动信号，例如，环境音、佩戴者声音)并将拾取的第一振动信号进行处理并转化为携带声音信息的电信号。扬声器组件可以将拾音元件获取的携带声音信息的电信号转化为携带声音信息的第二振动信号并传递给佩戴者的听觉中枢。关于骨导听力辅助设备110的详细描述可以参见本申请中的其他地方描述(例如，图2以及其详细描述)。
在一些实施例中，针对不同的骨导听力辅助设备佩戴者，由于佩戴者的听力级(即听力损失的级别)不同，骨导听力辅助设备的配置可以不同。如本文中所述，骨导听力辅助设备的配置指的是与骨导听力辅助设备输出的声音信号强度相关的参数值(也可以称为参数) 和/或其确定过程，使骨导听力辅助设备可以基于参数值输出声音信号。与骨导听力辅助设备输出信号强度相关的参数值可以包括增益值(单位dB)、模拟输出值(单位dB)等。在一些实施例中，增益值可以是助听器对声音信号的强度进行放大的值，模拟输出值可以是助听器根据输入的声音信号参数(例如，声音信号的强度值)模拟的输出信号强度值。例如，模拟输出值可以等于声音信号的输入值(即强度值，单位dB)加上增益值(单位dB)。骨导听力辅助设备配置系统100可以根据佩戴者的听力级的不同，确定佩戴者的听力级对应的骨导听力辅助设备的配置。骨导听力辅助设备110可以基于该配置对获取的声音信息(例如，环境音、佩戴者声音、其他设备中获取的音频文件等)进行处理以及输出，使佩戴者听到声音。
处理设备120可以处理从骨导听力辅助设备110、存储器130和/或终端140获得的数据和/或信息。例如，处理设备120可以获取骨导听力辅助设备110佩戴者的听力损失数据。又例如，处理设备120可以基于听力损失数据，确定骨导听力辅助设备110在各个声级各个频段下的参考输出参数。还例如，处理设备120可以获取参考输出参数的调整值。再例如，处理设备120可以基于参考输出参数和调整值，配置骨导听力辅助设备110。
在一些实施例中，处理设备120可以是单个服务器或服务器组。服务器组可以是集中式或分布式的。在一些实施例中，处理设备120可以是本地的或远程的。例如，处理设备120可以经由网络150访问存储在骨导听力辅助设备110、终端140和/或存储器130中的信息和/或数据。又例如，处理设备120可以直接连接到骨导听力辅助设备110、终端140和/或存储器130以访问存储的信息和/或数据。在一些实施例中，处理设备120可以在云平台上实现。仅作为示例，该云平台可以包括私有云、公共云、混合云、社区云、分布云、内部云、多层云等或其任意组合。在一些实施例中，处理设备120可以在计算设备上来实现。在一些实施例中，处理设备120或一部分处理设备120可以集成到骨导听力辅助设备110中。在一些实施例中，处理设备120或一部分处理设备120可以集成到终端140中。
存储器130可以存储数据、指令和/或任何其他信息。在一些实施例中，存储器130可以存储从终端140和/或处理设备120获得的数据。在一些实施例中，存储器130可以存储处理设备120可以执行或用于执行本申请中描述的示例性方法的数据和/或指令。在一些实施例中，存储器130可以包括大容量存储设备、可移动存储设备、易失性读写存储器、只读存储器(ROM)等，或者它们的任意组合。在一些实施例中，存储器130可在云平台上实现。仅作为示例，该云平台可以包括私有云、公共云、混合云、社区云、分布云、内部云、多层云等或其任意组合。在一些实施例中，存储器130可以连接到网络150以与骨导听力辅助设 备配置系统100中的一个或多个其他组件(例如，处理设备120、终端140等)通信。骨导听力辅助设备配置系统100的一个或多个组件可以经由网络150访问存储在存储器130中的数据或指令。在一些实施例中，存储器130可以直接连接到骨导听力辅助设备配置系统100中的一个或多个其他部件(例如，处理设备120，终端140等)或与之通信。在一些实施例中，存储器130可以是处理设备120的一部分。
终端140可以包括移动设备141、平板电脑142、膝上计算机143、智能手表144等，或其任何组合。在一些实施例中，移动设备141可以包括智能家居设备(例如，智能电器的控制设备、智能监控设备、智能电视、智能摄像机)、可穿戴设备(例如，眼镜、头盔、配饰、衣服等)、移动设备(例如，手机、笔记本电脑等)、虚拟现实设备(例如，虚拟现实头盔、虚拟现实眼镜、虚拟现实眼罩)等，或其任意组合。在一些实施例中，骨导听力辅助设备110可以集成于终端140中，例如，集成于眼镜、配饰等。
在一些实施例中，用户(例如，骨导听力辅助设备110的佩戴者、系统操作人员、医生等)可以通过终端140与骨导听力辅助设备配置系统100进行交互。例如，用户可以通过终端140上的用户交互界面发送配置请求；处理设备120在接收配置请求后获取佩戴者的听力损失数据。例如，处理设备120可以通过用户交互界面向终端140发送听力损失数据获取请求，用户可以在接收到获取请求后通过用户交互界面上传佩戴者的听力损失数据。处理设备120可以基于听力损失数据配置骨导听力辅助设备110。
网络150可以包括可以促进骨导听力辅助设备配置系统100的信息和/或数据的交换的任何合适的网络。在一些实施例中，一个或多个骨导听力辅助设备配置系统100的组件(例如，骨导听力辅助设备110、终端140、处理设备120、存储器130等)可以通过网络150与一个或多个骨导听力辅助设备配置系统100的其他组件交换信息和/或数据。例如，处理设备120可以经由网络150从骨导听力辅助设备110获得佩戴者的听力损失数据(例如，听力级)。又例如，处理设备120可以经由网络150从终端140获得用户指令。网络150可以是和/或包括公共网络(例如，互联网)、私有网络(例如，局域网络(LAN)、广域网(WAN)等)、有线网络(例如，以太网网络)、无线网络(例如，802.11网络、Wi-Fi网络等)、蜂窝网络(例如，长期演进(LTE)网络)、帧中继网络、虚拟专用网络("VPN")、卫星网络、电话网络、路由器、集线器、交换机、服务器计算机和/或其任意组合。在一些实施例中，网络150可以包括一个或以上网络接入点。例如，网络150可以包括诸如基站和/或互联网交换点之类的有线和/或无线网络接入点，通过该接入点，骨导听力辅助设备配置系统100的一个或多个组件可以连接到网络150以交换数据和/或信息。
该描述旨在是说明性的，而不是限制本申请的范围。许多替代、修改和变化对本领域普通技术人员将是显而易见的。本申请描述的示例性实施方式的特征、结构、方法和其它特征可以以各种方式组合以获得另外的和/或替代的示例性实施例。例如，存储器130可以是包括云计算平台，例如，公共云、私有云、社区云和混合云等数据存储设备。然而，这些变化和修改不会背离本申请的范围。
图2是根据本申请一些实施例所示的骨导听力辅助设备的结构示意图。如图2所示，骨导听力辅助设备200可以包括扬声器组件210、拾音组件220以及支撑组件230。
扬声器组件210可以将含有声音信息的信号转化为振动信号。在一些实施例中，声音信息可以包括具有特定数据格式的视频、音频文件或可以通过特定途径转化为声音的数据或文件。含有声音信息的信号可以包括电信号、光信号、磁信号、机械信号等一种或多种的组合。含有声音信息的信号可以来自一个信号源或多个信号源。多个信号源可以相关也可以不相关。在一些实施例中，骨导听力辅助设备200可以以通过多种不同的方式获取含有声音信息的信号，信号的获取可以是有线的或无线的，可以是实时或延时的。例如，骨导听力辅助设备200可以通过有线或者无线的方式接收含有声音信息的电信号。又例如，骨传导助听器10中可以包括具有声音采集功能的组件(例如，拾音组件220)，通过拾取环境中的声音，将声音的机械振动转换成电信号，通过放大器处理后获得满足特定要求的电信号。
扬声器组件210将含有声音信息的信号转化为振动信号是一个能量的转换过程。转换的过程中可能包含多种不同类型能量的共存和转換。扬声器组件210可以包括一个或多个换能装置，例如，电信号通过换能装置可以直接转换成机械振动，产生声音。再例如，声音信息可以包含在光信号中，换能装置可以实现由光信号转换为振动信号的过程。其它可以在换能装置工作过程中共存和转换的能量类型包括热能、磁场能等。在一些实施例中，扬声器组件210可以通过磁路组件211与振动组件213(磁路组件211以及振动组件213可以称为换能装置)的配合而实现从声音信息的信号到振动信号的转化。其中，磁路组件211用于提供磁场，振动组件213用于在磁场受安培力机械振动。例如，磁路组件211可以包括磁铁。振动组件213可以包括磁性振子和振动片。磁性振子(例如，音圈)在磁场内受安培力的作用来回运动，并在运动过程中带动振动片振动。在上述过程中，声音信息可以与磁性振子的振动对应，可以根据声音信息的频率与强度确定磁性振子的振动频率和幅度。在一些实施例中，磁路组件与磁性振子中的一个可以为电磁铁，可以通过在电磁铁中控制线圈的个数和/或电流强度而控制磁场强度，进而控制磁性振子的振动幅度，也可以通过控制电磁铁中的线圈的电流方向变化频率控制磁性振子的振动频率。在这一过程中，还可以对声音信息进行增益，例 如，对声音信息的响度的增益可以通过提高磁性振子的振动幅度来实现。
振动组件的具体能量转换方式具体可以包括动圈式、静电式、压电式、动铁式、气动式、电磁式等。骨导听力辅助设备200的频率响应范围以及音质会受到振动组件的影响。例如，在动圈式换能装置中，振动组件可以包括缠绕的柱状音圈和振动体(例如，振动片或振动膜)，受信号电流驱动的柱状音圈在磁场中带动振动体振动发声，振动体材质的伸展和收缩、褶皱的变形、大小、形状以及固定方式，磁场的磁密度等，都会对骨导听力辅助设备的音效质量带来很大的影响。振动组件中振动体可以是镜面对称的结构、中心对称的结构或者非对称的结构振动体上可以设置有间断的孔状结构，使振动体产生更大的位移，从而让骨导听力辅助设备200实现更高的灵敏度，提高振动与声音的输岀功率；振动体可以是圆环体结构，在圆环体内设置向中心辐辏的多个支杆，支杆的个数可以是两个或者更多。
拾音组件220可以主要是用于拾取用户的语音、用户所在环境的环境音等。对于听障者而言，拾音组件220的拾音效果，将影响听障者通过骨导听力辅助设备接收到的声音的清晰度、稳定度等。在一些实施例中，拾音组件220可以包括麦克风。在一些实施例中，拾音组件220可以将外界的声音信号转换为电信号。在一些实施例中，拾音组件220可以包括振膜、线圈和磁体。振膜可以与线圈相连，而线圈可以设于磁体产生的磁场中。外界的声波(即声音信号或振动信号)可以引起振膜振动，振膜可以带动线圈一起运动，线圈在磁体产生的磁场中运动会产生电流，以使得声音信号被转换为电信号，从而完成外界声音的拾取。
支撑组件230可以对骨导听力辅助设备200中的其他元件(例如，磁路组件、振动组件和/或存储组件、电源组件、通信组件(图中未示出)、拾音组件220)起到支撑作用。支撑组件230可以包括一个或多个壳体、一个或多个连接件。一个或多个壳体可以形成用于容纳存储组件、控制器、拾音组件220、通信组件、电池组件等的容置腔232。一个或多个连接件可以连接壳体与骨导听力辅助设备200中的其他元件(例如，磁路组件、振动组件和/或存储组件、电源组件、通信组件(图中未示出)、拾音组件220)。
骨导听力辅助设备200涉及的有线连接可以包括金属电缆、光学电缆或者金属和光学的混合电缆，例如，同轴电缆、通信电缆、软性电缆、螺旋电缆、非金属护皮电缆、金属护皮电缆、多芯电缆、双绞线电缆、带状电缆、屏蔽电缆、电信电缆、双股电缆、平行双芯导线、双绞线等种或多种的组合。以上描述的例子仅作为方便说明之用，有线连接的媒介还可以是其它类型，例如，其它电信号或光信号等的传输载体。
骨导听力辅助设备200涉及的无线连接可以包括无线电通信、自由空间光通信、声通讯、和电磁感应等。其中无线电通讯可以包括IEEE802.11系列标准、IEEE802.15系列标准(例 如蓝牙技术和紫蜂技术等)、第一代移动通信技术、第二代移动通信技术(例如FDMA、TDMA、SDMA、CDMA、和SSMA等)、通用分组无线服务技术、第三代移动通信技术(例如CDMA2000、WCDMA、TD-SCDMA、和WIMAX等)、第四代移动通信技术(例如TD-LTE和FDD-LTE等)、卫星通信(例如GPS技术等)、近场通信(NFC)和其它运行在ISM频段(例如2.4GHz等)的技术；自由空间光通信可以包括可见光、红外线讯号等；声通讯可以包括声波、超声波讯号等；电磁感应可以包括近场通讯技术等。以上描述的例子仅作为方便说明之用，无线连接的媒介还可以是其它类型，例如，Z-wave技术、其它收费的民用无线电频段和军用无线电频段等。例如，作为本技术的一些应用场景，骨导听力辅助设备200可以通过蓝牙技术从其他设备获取含有声音信息的信号。
以上对骨导听力辅助设备200结构的描述仅仅是具体的示例，不应被视为是唯一可行的实施方案。显然，对于本领域的专业人员来说，在了解骨导听力辅助设备200的基本原理后，可能在不背离这一原理的情况下，对实施骨导听力辅助设备200的具体方式与步骤进行形式和细节上的各种修正和改变，但是这些修正和改变仍在以上描述的范围之内。例如，骨导听力辅助设备200可以包括一个或多个处理器，处理器可以执行一个或多个声音信号处理算法。声音信号处理算法可以对声音信号进行修正或强化。例如对声音信号进行降噪、声反馈抑制、宽动态范围压缩、自动增益控制、主动环境识别、主动抗噪、定向处理、耳鸣处理、多通道宽动态范围压缩、主动啸叫抑制、音量控制，或其它类似的，或以上任意组合的处理，这些修正和改变仍在本发明的权利要求保护范围之内。又例如，骨导听力辅助设备可以包括一个或多个传感器，例如温度传感器、湿度传感器、速度传感器、位移传感器等。传感器可以采集用户信息或环境信息。再例如，存储组件可以不是必须的，可以从骨导听力辅助设备中移除。
在一些实施例中，骨导听力辅助设备的配置系统主要是基于佩戴者的听力损失数据，按照预设的公式或者助听器配置系统的预设算法进行配置。例如，在助听器配置系统中，将佩戴者的听力损失数据输入助听器配置系统后，助听器配置系统可以基于预设算法自动地输出助听器的相关参数值。仅通过预设算法直接配置骨导听力辅助设备，可能会使得配置的骨导听力辅助设备200在某些场景下(如佩戴者自己说话或环境声音过大)产生较剧烈的振动，造成佩戴者的不适感。
本申请提供一种骨导听力辅助设备的配置系统，图3是根据本申请一些实施例所示的骨导听力辅助设备的配置系统的模块图。如图3所示，骨导听力辅助设备的配置系统300包括获取模块310、参考输出参数确定模块320、调整值确定模块330以及配置模块340。各模 块之间的连接形式可以是有线的、无线的、或两者的结合。任何一个模块都可以是本地的、远程的、或两者的结合。模块间的对应关系可以是一对一的，或一对多的。
在一些实施例中，获取模块310可以用于获取佩戴者的听力损失数据。
在一些实施例中，参考输出参数确定模块320可以用于基于听力损失数据，确定骨导听力辅助设备在各个声级各个频段下的参考输出参数。
在一些实施例中，调整值确定模块330可以用于获取参考输出参数的调整值。在一些实施例中，在不同听力级以及相同频段下的调整值相同。在一些实施例中，在频率大于0Hz而小于或等于625Hz的频段内，调整值为1dB-12dB。在一些实施例中，在频率大于0Hz而小于或等于125Hz的频段内，调整值设定为5dB-12dB；在频率大于125Hz而小于或等于375Hz的频段内，调整值设定为3dB-9dB；和/或，在频率大于375Hz而小于或等于625Hz的频段内，调整值设定为1dB-6dB。在一些实施例中，在频率大于0Hz而小于或等于125Hz的频段内，调整值为5dB-7dB；在频率大于125Hz而小于或等于375Hz的频段内，调整值为3dB-5dB；和/或，在频率大于375Hz而小于或等于625Hz的频段内，调整值为1dB-3dB。在一些实施例中，在频率大于0Hz而小于或等于125Hz的频段内，调整值为10dB-12dB；在频率大于125Hz而小于或等于375Hz的频段内，调整值为7dB-9dB；和/或，在频率大于375Hz而小于或等于625Hz的频段内，调整值为4dB-6dB。在一些实施例中，在不同听力级以及相同频段下的调整值不同。在一些实施例中，调整值确定模块330可以用于：确定各个频段以及各个声级对应的第一阈值，第一阈值与佩戴者对各个频段各个声级的振动感受程度相关；确定各个频段以及各个声级对应的第二阈值，第二阈值与佩戴者在各个频段各个声级的言语识别率相关；以及基于参考输出参数、第一阈值和第二阈值确定调整值。在一些实施例中，调整值确定模块330可以用于：对于各个声级以及各个频段中的某一声级以及某个频段下的参考输出参数；将参考输出参数减去第一阈值而获得比较值；将比较值与第二阈值进行比较；基于比较值与第二阈值的比较结果，确定参考输出参数对应的调整值。在一些实施例中，调整值确定模块330可以用于：响应于比较值小于或等于0，调整值设置为0dB；响应于比较值大于0而小于等于第二阈值，调整值设置为比较值；响应于比较值大于第二阈值时，调整值设置为第二阈值。
在一些实施例中，在频率大于0Hz而小于等于125Hz的频段内，第一阈值在48dB-52dB范围内。在一些实施例中，在频率大于125Hz而小于等于375Hz的频段内，第一阈值在49dB-54dB范围内。在一些实施例中，在频率大于375Hz而小于等于625Hz的频段内，第一阈值在50dB 55dB范围内。在一些实施例中，在频率大于0Hz而小于等于125Hz的频段 内，第二阈值在5dB-10dB范围内。在一些实施例中，在频率大于125Hz而小于等于375Hz的频段内，第二阈值在3dB-7dB范围内。在一些实施例中，在频率大于375Hz而小于等于625Hz的频段内，第二阈值在1dB-4dB范围内。
在一些实施例中，当使用多通道宽动态范围压缩系统，配置骨导听力辅助设备时，调整值确定模块330可以用于：将参考输出参数与第一阈值进行比较；第一阈值与佩戴者对各个频段各个声级的振动感受程度相关；基于参考输出参数与第一阈值的比较结果，确定参考输出参数对应的调整值。在一些实施例中，调整值包括在各个声级中至少一个声级大于声级阈值时的增益降低值；调整值确定模块330可以用于：响应于参考输出参数小于或等于第一阈值，则设置增益降低值为0dB；响应于参考输出参数大于第一阈值，则设置增益降低值为第一阈值与参考输出参数的差值。在一些实施例中，调整值包括多通道宽动态范围压缩系统的最大输出的降低值；调整值确定模块330可以用于：响应于参考输出参数小于或等于第一阈值，则最大输出的降低值设置为0dB；响应于参考输出参数大于第一阈值，则最大输出的降低值设置为大于0dB。
在一些实施例中，配置模块340可以用于基于参考输出参数和调整值，配置骨导听力辅助设备。在一些实施例中，配置模块340还可以用于在频率大于0Hz而小于或等于625Hz的频段内，基于调整值降低参考输出参数。在一些实施例中，配置模块340可以用于基于参考输出参数和调整值，使用多通道宽动态范围压缩系统，配置骨导听力辅助设备。
需要注意的是，以上对处理模块的描述仅仅是具体的示例，不应被视为是唯一可行的实施方案。上述每个模块或单元并不是必须的，每一个模块或单元均可通过一个或多个部件实现，每个模块或单元的功能也并不局限于此。上述各个模块或单元可以根据具体实施场景或需要选择添加或删除。显然，对于本领域的专业人员来说，在了解运力调度流程的基本原理后，可能在不背离这一原理的情况下，对处理模块的具体实施方式与步骤进行形式和细节上的各种修正和改变，还可以做出若干简单推演或替换，在不付出创造性劳动的前提下，对各模块或单元的顺序做出一定调整、组合或拆分，但是这些修正和改变仍在以上描述的范围之内。
图4是根据本申请一些实施例所示的骨导听力辅助设备的配置方法的流程图。如图4所示，骨导听力辅助设备的配置方法的流程400包括下述步骤：
步骤410，获取佩戴者的听力损失数据。具体地，步骤410可以由获取模块310执行。
在一些实施例中，佩戴者的听力损失数据可以理解为与佩戴者的听力损失情况相关的数据。听力损失数据可以包括佩戴者的各个频段内以及各个声级下的听力级(也叫听阈或听 力损失级别)，在本说明书中，听力级所使用的单位为dBHL。听力级的值越高，则佩戴者的听力损失情况越严重。在一些实施例中，听力损失数据可以包括佩戴者的历史上佩戴的助听器相关的数据。例如，佩戴者的历史上佩戴的助听器相关的数据可以包括该佩戴者历史上使用的骨导听力辅助设备的配置数据。
在一些实施例中，听力级可以在0dBHL-80dBHL范围内。例如，听力级可以在0dBHL-25dBHL内表示正常听力；听力级可以在26dBHL-40dBHL，轻度听力下降；听力级41dBHL-60dBHL中度听力下降，表现为听正常的声音有困难；61dBHL-80dBHL重度听力下降，表现为听大声有困难；听力级大于80dBHL，表示极重度听力下降，表现为听响声有困难。
在一些实施例中，骨导听力辅助设备的佩戴者在相同声级(声级的具体说明请参见步骤420的相关内容)下不同频段的听力级可以相同。例如，在20dBC声级下，佩戴者在不同频段下的听力级可以都等于41dBHL-60dBHL范围内某一值；在40dBC声级下，佩戴者在不同频段下的听力级可以都等于26dBHL-40dBHL范围内某一值；在60dBC声级下，佩戴者在不同频段下的听力级可以都等于0dBHL-25dBHL范围内某一值。
在一些实施例中，骨导听力辅助设备的佩戴者相同声级下不同频段的听力级可以不相同。例如，在20dBC声级下，佩戴者在高频段(例如，8000Hz-12000Hz下)的听力级可以都等于41dBHL-60dBHL范围内某一值；在低频段下的听力级可以都等于26dBHL-40dBHL范围内某一值。
在一些实施例中，骨导听力辅助设备的佩戴者在相同频段下不同声级对应的听力级可以相同。例如，在250Hz-500Hz频段下，佩戴者在不同声级的听力级可以都等于0dBHL-25dBHL中的某个值；在500Hz-1000Hz频段下，佩戴者在不同频段下的听力级可以都等于26dBHL-40dBHL范围内某一值；在1000Hz-2000Hz频段下，佩戴者在不同频段下的听力级可以都等于41dBHL-60dBHL范围内某一值。
在一些实施例中，骨导听力辅助设备的佩戴者在在相同频段下不同声级对应的听力级可以不同。例如，在250Hz-500Hz频段下，佩戴者在20dBC声级下听力级可以等于41dBHL-60dBHL范围内某一值；在40dBC声级下听力级可以都等于26dBHL-40dBHL范围内某一值；在60dBC声级下听力级可以等于0dBHL-25dBHL范围内某一值。
在一些实施例中，获取佩戴者的听力损失数据可以通过对佩戴者进行实时听力测试而获取到。例如，助听器验配师可以使用听力测试设备来对佩戴者进行听力测试(如播放各个频段下、各个声级下的声音信号)，从而获得佩戴者的听力损失数据。听力测试设备采集的 听力损失数据可以直接通过网络(例如，网络150)上传至处理设备(例如，处理设备120)或上传至存储设备，处理设备可以从存储设备中获取听力损失数据。在另一些实施例中，佩戴者可以通过终端(例如，终端140)自行上传自身的听力损失数据，骨导听力辅助设备配置系统(例如，骨导听力辅助设备配置系统100)或设备(例如，处理设备120)可以通过有线或无线的方式接收到佩戴者自行上传的听力损失数据。在一些实施例中，骨导听力辅助设备配置系统或设备可以从相关存储器(例如，存储器130)中调取佩戴者的听力损失数据。
步骤420，基于听力损失数据，确定骨导听力辅助设备在各个声级各个频段下的参考输出参数。具体地，步骤420可以由参考输出参数确定模块320执行。
在一些实施例中，参考输出参数可以是骨导听力辅助设备在各个声级各个频段下的参考模拟输出值(即骨导听力辅助设备模拟输出的信号的强度值，单位dB)。在一些实施例中，参考输出参数可以是骨导听力辅助设备各个声级各个频段的参考增益值(即骨导听力辅助设备对声音信号进行放大的强度值，单位dB)。需注意的是，当骨导听力辅助设备在参考输出参数下(例如，参考增益值)输入的声音信号满足特定声级以及频段，则骨导听力辅助设备输出该声音信号的强度值可以等于该特定声级以及频段下的参考模拟输出值。在一些实施例中，参考输出参数与听力损失级别、声级、频率等有关。在一些实施例中，骨导听力辅助设备的参考模拟输出值进一步与骨导听力辅助设备的参考增益值有关。例如，可以基于增益值对声级对应的信号强度进行放大以确定模拟输出值。在一些实施例中，对于不同的佩戴者，由于其听力损失数据(如，各个声级下的听力损失程度)不同，参考输出参数会不同。在一些实施例中，声音信号的声级和频率会影响骨导听力辅助设备的参考输出参数，不同的声级和/或不同的频段可能会对应不同的参考输出参数。也就是说，相同听力损失级别以及相同的声级下，不同的频段可能会对应不同的参考输出参数；相同听力损失级别以及相同的频段下，不同的声级可能会对应不同的参考输出参数；相同声级以及相同频段下，不同的听力损失级别可能会对应不同的参考输出参数。
本说明书中涉及的声级表示声音信号的强度，单位为分贝。在本说明书中，声级的计量主要采用C频率计权测量，即本说明书中声级的单位为dBC。频段在本说明书中指声音信号的频率范围。在一些实施例中，可以将声音信号的频率分为多个连续的范围，以形成不同的频段。
在一些实施例中，确定骨导听力辅助设备在各个声级各个频段下的参考输出参数可以指的是确定骨导听力辅助设备在预设声级和/或预设频率下以及该预设声级以及预设频率下对应的骨导听力辅助设备的佩戴者的听力损失级别对应的参数输出参数。在一些实施例中， 确定骨导听力辅助设备在各个声级各个频段下的参考输出参数可以指的是确定骨导听力辅助设备在预设声级范围和/或预设频段下以及该预设声级范围以及预设频段下对应的骨导听力辅助设备的佩戴者的听力损失级别对应的参数输出参数。基于该确定的参考输出参数，骨导听力辅助设备可以将输入骨导听力辅助设备的声音信号(即声音输入信号)进行放大并转化成振动信号，传递给骨导听力辅助设备的佩戴者，以便佩戴者可以听到声音。在一些实施例中，预设声级、预设频率、预设声级范围和/或预设频段可以是系统(例如，骨导听力辅助设备配置系统100)的默认设置或由用户设定。在一些实施例中，预设声级可以包括20dBC、30dBC、40dBC、50dBC、60dBC、70dBC、80dBC等或其组合。在一些实施例中，预设频率可以包括250Hz、500Hz、1000Hz、2000Hz、3000Hz、4000Hz、8000Hz、10000Hz等或其组合。在一些实施例中，预设声级范围可以包括10dBC-20dBC(可以不包括20dBC)、20dBC-30dBC(可以不包括30dBC)、30dBC-40dBC(可以不包括40dBC)、40dBC-50dBC(可以不包括50dBC)、50dBC-60dBC(可以不包括60dBC)、60dBC-70dBC(可以不包括70dBC)、70dBC-80dBC(可以不包括80dBC)等或其组合。在一些实施例中，预设频段可以包括20Hz-250Hz(可以不包括250Hz)、250Hz-500Hz(可以不包括500Hz)、500Hz-1000Hz(可以不包括1000Hz)、1000Hz-2000Hz(可以不包括2000Hz)、2000Hz-3000Hz(可以不包括3000Hz)、3000Hz-4000Hz(可以不包括4000Hz)、4000Hz-6000Hz(可以不包括6000Hz)、6000Hz-10000Hz(可以不包括10000Hz)等或其组合。在一些实施例中，预设频段可以包括0Hz-125Hz(可以不包括125Hz)、125Hz-375Hz(可以不包括375Hz)、375Hz-625Hz(可以不包括625Hz)、625Hz-875Hz(可以不包括875Hz)、875Hz-1375Hz(可以不包括1375Hz)、1375Hz-1875Hz(可以不包括1875Hz)、1875Hz-2625Hz(可以不包括2625Hz)、2625Hz-4875Hz(可以不包括4875Hz)等或其组合。在一些实施例中，预设声级、预设频率、预设声级范围和/或预设频段可以是由系统(例如，骨导听力辅助设备配置系统100)或用户进行调整。例如，可以根据骨导听力辅助设备的佩戴者的听力级进行调整。例如，若佩戴者的听力级在声级为80dBC的情况下为10dBHL(表明佩戴者在该声级下听力正常)，则可以预设声级的最大值可以不超过80dBC。
在一些实施例中，参考输出参数可以是骨导听力辅助设备的参考增益值，处理设备120可以基于听力损失数据中各个声级以及各个频段下的听力级以及各个声级以及各个频段的值，确定骨导听力辅助设备在各个声级各个频段下的参考增益值。例如，可以基于声级20dBC、375Hz-625Hz频段以及基于声级20dBC以及375Hz-625Hz频段下骨导听力辅助设备的佩戴者的听力级确定该骨导听力辅助设备在声级20dBC以及375Hz-625Hz频段下的参考增 益值。在一些实施例中，参考输出参数可以是骨导听力辅助设备的参考模拟输出信号强度值(即参考模拟输出值)。处理设备120可以基于听力损失数据中各个声级以及各个频段下的听力级以及各个声级以及各个频段的值，确定骨导听力辅助设备在各个声级各个频段下的参考模拟输出信号强度值(即参考模拟输出值)。例如，可以声级30dBC、125Hz-375Hz频段以及基于声级30dBC以及125Hz-375Hz频段下骨导听力辅助设备的佩戴者的听力级确定该骨导听力辅助设备在声级30dBC以及125Hz-375Hz频段下的参考模拟输出信号强度值(即参考模拟输出值)。
在一些实施例中，处理设备120(参考输出参数确定模块320)可以是基于听力损失数据，先确定骨导听力辅助设备在各个声级各个频段下的参考增益值，再基于上述在各个声级各个频段下的增益值确定骨导听力辅助设备在对应声级以及对应频段下的参考模拟输出信号强度值(即参考模拟输出值)。
在一些实施例中，处理设备120(参考输出参数确定模块320)可以通过预设公式确定参考输出参数。例如，可以根据佩戴者的听力损失数据，通过预设公式确定各个声级各个频段下的参考增益值。在一些实施例中，预设公式可以为由Lybarger提出的“1/2增益原则”，即感音神经性聋要达到舒适听觉，所需增益值应是听阈提高程度的一半。也就是说，骨导听力辅助设备的参考增益值可以相当于佩戴者的听力损失的二分之一左右。
在一些实施例中，步骤320中的参考输出参数可以通过下表(表1)的经验数据确定。例如，可以通过下表所示的经验数据确定各个频段各个听损级别(基于听力损失数据确定)下的参考增益值，再通过参考增益值进一步确定对应频段对应听损级别下的参考模拟输出值。下表以声级为60dBSPL为例，说明各个听力级下以及各个频段下的参考增益值。如表1所示，当声级为60dBSPL，听力级为20dBHL，各个频段下的的参考增益值为0；听力级为40dBHL，125-375Hz频段下的的参考增益值为5。在一些实施例中，当声级以及听力级一定时，随着频段的增加，参考增益值可以先增大后减小。在一些实施例中，当频段一定时，参考增益值随着听力级的增加而增大。
表1是以声级为60dB SPL为例，说明各个听力级下以及各个频段下的参考增益值。
Figure PCTCN2021090136-appb-000001
在一些实施例中，处理设备120可以根据配置模型进行确定参考输出参数。配置模型可以表示参考输出参数与频段、声级以及听力级之间的关系。
步骤430，获取参考输出参数的调整值。其中，调整值至少与频段相关。具体地，步骤430可以由参考输出调整值确定模块330执行。
调整值是指用于对参考输出参数进行调整的数值。在一些实施例中，通过调整值可以调整参考输出参数，调整后的参考输出参数可以作为骨导听力辅助设备的实际模拟输出参数。以参考输出参数为参考模拟输出值和参考增益值为例分别进行说明。例如，可以通过调整值调整参考模拟输出值(模拟输出的信号的强度值)，以将调整后的参考模拟输出值作为骨导听力辅助设备的实际模拟输出值(实际的模拟输出的信号强度值)。又例如，可以通过调整值调整骨导听力辅助设备的参考增益值(对声音信号进行放大的强度值)，以将调整后的参考增益值作为骨导听力辅助设备的实际增益值。
在一些实施例中，调整值用于降低参考输出参数。例如，调整值可以是用于对参考模拟输出值进行衰减的数值，即可以在参考输出参数的基础上减去调整值。又例如，调整值也可以是用于对参考增益值进行衰减的数值，即可以在参考增益值的基础上减去调整值。还例如，调整值可以为小于1的比例值，即可以在参考输出参数的基础上乘以调整值。
骨导听力辅助设备的振动较为强烈的情况出现在输入骨导听力辅助设备的声音信号的频率较低时，例如，骨传导耳机在125Hz～625Hz频段易产生振动。因此，可以在0Hz～625Hz频段内(或者在125Hz～625Hz频段内)设定调整值(例如，在该频段内使用调整值降低参考输出参数)，以改善骨导听力辅助设备在该频段内振动强烈的情况。
图8是实验测定的佩戴者佩戴骨导听力辅助设备时在各个频率下的振动感知阈值图。在图8中，振动感知阈值(单位dBV)可以是指佩戴者能够感知到振动时骨导助听辅助设备的驱动电压值(单位V)进行数值换算后得到数值。如果骨导助听辅助设备的驱动电压值是X(单位V)；则换算成振动感知阈值为20*log10(X/1)(单位dBV)。仅作为示例，骨导助听辅助设备的驱动电压值是1V时，对应振动感知阈值为0dBV；骨导助听辅助设备的驱动电压值是0.5V时，对应振动感知阈值为-6dBV。从图8可以看出，骨导听力辅助设备在1000Hz以下的频段下的振动感知阈值较小，表示骨导听力辅助设备在1000Hz以下的频段容易产生振动，尤其是125Hz～600Hz的频段最易产生振动。其中，骨导听力辅助设备在125Hz、250Hz、400Hz、500Hz时最易产生振动。因此，基于上述实验测定的数据，可以在0Hz～625Hz频段内(或者在125Hz～625Hz频段内)设定调整值。
在一些实施例中，在不同听力级下相同频段和/或相同声级可以对应相同的调整值。 例如，听力级在26dBHL-40dBHL、频率在0Hz-625Hz的频段内以及20dBC声级下的调整值与听力级在41dBHL-60dBHL、频率在0Hz-625Hz的频段内以及20dBC声级下的调整值相同。又例如，听力级可以在26dBHL-40dBHL、频率在0Hz-125Hz的频段内以及20dBC声级下的调整值与听力级在41dBHL-60dBHL、频率在0Hz-125Hz的频段内以及20dBC声级下的调整值相同。又例如，听力级在26dBHL-40dBHL、频率在125Hz-375Hz的频段内以及20dBC声级下的调整值与听力级在41dBHL-60dBHL频率在125Hz-375Hz的频段内以及20dBC声级下的调整值相同。
在一些实施例中，在不同听力级下相同频段和/或相同声级可以对应不相同的调整值。例如，听力级可以在26dBHL-40dBHL、频率在0Hz-625Hz的频段内以及20dBC声级下的调整值与听力级在41dBHL-60dBHL、频率在0Hz-625Hz的频段内以及20dBC声级下的调整值不相同。又例如，听力级可以在26dBHL-40dBHL、频率在20Hz-125Hz的频段内以及20dBC声级下的调整值与听力级在41dBHL-60dBHL频率、在20Hz-125Hz的频段内以及20dBC声级下的调整值不相同。又例如，听力级可以在26dBHL-40dBHL、频率在125Hz-375Hz的频段内以及20dBC声级下的调整值与听力级在41dBHL-60dBHL频率在125Hz-375Hz的频段内以及20dBC声级下的调整值不相同。
在一些实施例中，在不同声级下相同频段和/或相同听力级可以对应相同的调整值。例如，声级在20dBC-40dBC、频率在0Hz-125Hz的频段内以及听力级41dBHL-60dBHL的调整值与声级在40dBC-60dBC、频率0Hz-125Hz的频段内以及听力级41dBHL-60dBHL的调整值可以相同。又例如，声级在20dBC-40dBC、频率在125Hz-375Hz的频段内以及听力级26dBHL-40dBHL的调整值与声级在40dBC-60dBC、频率在125Hz-375Hz的频段内以及听力级26dBHL-40dBHL的调整值可以相同。
在一些实施例中，在不同声级下相同频段和/或相同听力级可以对应不相同的调整值。例如，声级在26dBC-40dBC、频率在0Hz-125Hz频段内以及听力级41dBHL-60dBHL的调整值与声级在40dBC-60dBC、频率0Hz-125Hz频段内以及听力级41dBHL-60dBHL的调整值可以不相同。又例如，声级在26dBC-40dBC、频率在125Hz-375Hz频段内以及听力级26dBHL-40dBHL的调整值与声级在40dBC-60dBC、频率在125Hz-375Hz频段内以及听力级26dBHL-40dBHL的调整值可以不相同。
在一些实施例中，在不同频段相同声级和/或相同听力级可以对应相同的调整值。例如，频率在0Hz-125Hz频段内(可以不包含125Hz)、声级在20dBC-40dBC以及听力级41dBHL-60dBHL的调整值与频率125Hz-375Hz频段内、声级在20dBC-40dBC以及听力级 41dBHL-60dBHL的调整值可以相同。又例如，频率在125Hz-375Hz频段内(可以不包含375Hz)、声级在40dBC-60dBC以及听力级26dBHL-40dBHL的调整值与频率在375Hz-625Hz频段内、声级在40dBC-60dBC以及听力级26dBHL-40dBHL的调整值可以相同。
在一些实施例中，在不同频段相同声级和/或相同听力级可以对应不相同的调整值。例如，频率在0Hz-125Hz频段内(可以不包含125Hz)、声级在20dBC-40dBC以及听力级41dBHL-60dBHL的调整值与频率125Hz-375Hz频段内、声级在20dBC-40dBC以及听力级41dBHL-60dBHL的调整值可以不相同。又例如，频率在125Hz-375Hz频段内(可以不包含375Hz)、声级在40dBC-60dBC以及听力级26dBHL-40dBHL的调整值与频率在375Hz-625Hz频段内、声级在40dBC-60dBC以及听力级26dBHL-40dBHL的调整值可以不相同。
在一些实施例中，调整值至少与频段有关，在不同的频段内，调整值可以不同。在一些实施例中，不同频段可以对应不同的调整值，相同频段内的频率可以对应相同的调整值；在一些实施例中，不同频率可以对应不同的调整值。在一些实施例中，在频率大于0Hz而小于或等于625Hz的频段内，调整值在1dB-12dB范围内。通过在上述频率范围内将调整值设为上述值，再进行骨导听力辅助设备的配置，可以改善佩戴者在佩戴骨导听力辅助设备时在某些场景下振动较为强烈的问题，且还能够保证对言语可懂度的影响较小。在一些实施例中，随着频率的增大，调整值降低。例如，频率125Hz对应的调整值可以为5dB；频率250Hz对应的调整值可以为3dB；频率500Hz对应的调整值可以为1dB。又例如，频率125Hz对应的调整值可以为10dB；频率250Hz对应的调整值可以为7dB；频率500Hz对应的调整值可以为4dB。在一些实施例中，在频率大于625Hz而小于等于8000Hz的频段内，调整值可以为0dB-4dB。在一些实施例中，在频率大于625Hz而小于等于8000Hz的频段内，调整值可以为0。
在一些实施例中，在频率大于0Hz而小于或等于125Hz的频段内，调整值设定为5dB-12dB。在一些实施例中，在频率大于125Hz而小于或等于375Hz的频段内，调整值设定为3dB-9dB。在一些实施例中，在频率大于375Hz而小于或等于625Hz的频段内，调整值设定为1dB-6dB。进一步划分频段，在上述频段几个频段内分别设定上述调整值，可以使得骨导听力辅助设备降低振动的效果更好。
在一些实施例中，在频率大于0Hz而小于或等于125Hz的频段内，调整值为5dB-7dB。在频率大于125Hz而小于或等于375Hz的频段内，调整值为3dB-5dB。在一些实施例中，在频率大于375Hz而小于或等于625Hz的频段内，调整值为1dB-3dB。通过在上述频率范围内将调整值设为上述值，再进行骨导听力辅助设备的配置，可以解决听力级为30dBL的佩戴者 在对应频段内佩戴骨导听力辅助设备时的振动问题，且还能够对言语可懂度几乎无影响，保证佩戴者的助听效果。
在一些实施例中，在频率大于0Hz而小于或等于125Hz的频段内，调整值为10dB-12dB。在一些实施例中，在频率大于125Hz而小于或等于375Hz的频段内，调整值为7dB-9dB。在一些实施例中，在频率大于375Hz而小于或等于625Hz的频段内，调整值为4dB-6dB。通过在上述频率范围内将调整值设为上述值，再进行骨导听力辅助设备的配置，可以解决听力级为40dBL的佩戴者在对应频段内佩戴骨导听力辅助设备时的振动问题，且还能够对言语可懂度的影响较小，保证佩戴者的助听效果。
图9-11是分别对3位佩戴者(佩戴者1、佩戴者2和佩戴者3)进行言语识别率测试的实验结果图。图9-11均以参考输出参数为参考模拟输出值为例，示出了对参考模拟输出值降低前佩戴者的言语识别率、振动感及音量，以及在各个频段下参考模拟输出值对应不同的调整值时佩戴者的言语识别率、振动感及音量。图9-11均针对每个测试者进行了6组测试，表格中，负数表示调整值降低了参考输出参数(如参考模拟输出值)，例如，-5表示调整值为5dB，将参考模拟输出值降低了5dB；又例如，-15表示调整值为15dB，将参考模拟输出值降低了15dB。
如图9-11所示，当基于调整值降低参考模拟输出值时，言语识别率可能会降低，振动感可能会减小但音量可能会减小。从表格可以看出，在125Hz的频率下，如果调整值为5dB(或小于该数值)，即参考模拟输出值降低5dB，言语识别率没有显著变化；在250Hz的频率下，如果调整值为3dB(或小于该数值)，即参考模拟输出值降低3dB，言语识别率没有显著变化；在500Hz的频率下，如果调整值为1dB(或小于该数值)，即参考模拟输出值降低1dB，言语识别率没有显著变化。同时，按照上述数值设置调整值，测试者可以在自己说话时感觉振动，但音量还好(即音量大小为佩戴者能够基本听清的音量范围)。
在125Hz的频率下，如果调整值为10dB(或大于5dB而小于10dB范围内)，即参考模拟输出值降低10dB，言语识别率的降低量小于或等于5％；在250Hz的频率下，如果调整值为7dB(或大于3dB而小于7dB范围内)，即参考模拟输出值降低7dB，言语识别率的降低量小于或等于5％；在500Hz的频率下，如果调整值为4dB(或大于1dB而小于4dB范围内)，参考模拟输出值降低4dB，言语识别率的降低量小于或等于5％。同时，按照上述数值设置调整值，测试者可能感觉较为舒适，但感觉声音较为低沉(即佩戴者可能感觉音量太低)。
在125Hz的频率下，如果调整值为17dB(或大于10dB而小于17dB范围内)，即参 考模拟输出值降低17dB，言语识别率的降低量可能大于5％(如为10％)；在250Hz的频率下，如果调整值为15dB(或大于7dB而小于15dB范围内)，即参考模拟输出值降低15dB，言语识别率的降低量可能大于5％(如为10％)；在500Hz的频率下，如果调整值为10dB(或大于4dB而小于10dB范围内)，即参考模拟输出值降低10dB，言语识别率的降低量可能大于5％(如为10％)。同时，按照上述数值设置调整值，测试者可能感觉音量较小(即佩戴者很可能因音量太低而无法听清)。
在一定范围内(如调整值小于17dB的范围内)，调整值的数量越大，则减小骨导听力辅助设备的振动的效果越好，但是由图9-11可以得知，调整值的数量越大可能会导致骨导听力辅助设备输出信号强度较低，会导致言语识别率受到较大影响(如可能导致言语识别率降低)，而当调整值为上述实施例中的上述范围内的值时，既可以解决听力级为30dBL-40dBL的佩戴者在对应频段内佩戴骨导听力辅助设备时的振动问题，同时又能够保证对言语可懂度的影响较小。
在一些实施例中，参考输出参数的调整值可以仅与频段相关。参考输出参数在不同听力级、相同频段内对应的调整值可以相同(如上文的实施例中的调整值)，在相同听力级、不同频段内对应的调整值可以不相同；参考输出参数在不同声级下相同频段内对应的调整值可以相同，相同声级下不同频段内的调整值可以不相同；参考输出参数的在不同声级不同听力级的相同频段内对应的调整值可以相同，相同声级相同听力级不同频段内的调整值不同。
在一些实施例中，参考输出参数的调整值可以与频段和佩戴者的听力级相关。参考输出参数在不同听力级相同频段内对应的调整值不同；参考输出参数在相同听力级、相同频段、不同声级下对应的调整值可以相同，该实施例的详细描述请参见图5及其相关说明。
在一些实施例中，参考输出参数的调整值可以与频段和声级相关。参考输出参数在不同声级下相同频段内对应的调整值不同；但是参考输出参数在不同听力级、相同声级、相同频段内对应的调整值可以相同，该实施例对的详细描述请参加图6及其相关说明。
步骤440，基于参考输出参数和调整值，配置骨导听力辅助设备。具体地，步骤440可以由配置模块340执行。
在一些实施例中，处理设备120(配置模块340)可以基于调整值调整参考输出参数，以获得实际输出参数，并通过实际输出参数来配置骨导听力辅助设备。
在一些实施例中，处理设备120(配置模块340)可以根据调整值降低参考输出参数，以获得实际输出参数，并基于降低后的参考输出参数(即实际输出参数)配置骨导听力辅助设备。根据调整值降低参考输出参数可以是直接使用参考输出参数减去调整值，也可以是通 过调整值来调整其他骨导听力辅助设备的相关设置参数，以达到降低参考输出参数的目的。
在一些实施例中，处理设备120(配置模块340)可以基于调整值和参考输出值来配置磁路组件，以实现对骨导听力辅助设备的配置。在一些实施例中，配置骨导听力辅助设备包括对骨导听力辅助设备的各项参数进行设置，以使得骨导听力辅助设备与信号输出强度相关的参数(例如，增益值、模拟输出值)为预设值，例如，基于调整值调整后的参考参数。例如，可以通过调节磁路组件中电磁铁的电流大小、调节拾音组件的放大电路的电阻大小等方式来调节骨导听力辅助设备对声音信号的参考增益值，调节骨导听力辅助设备的参考模拟输出值，以实现对骨导听力辅助设备的配置。
在一些实施例中，基于参考输出参数和调整值，可以使用均衡调节系统(EQ系统)或自动增益控制系统(AGC系统)等来配置骨导听力辅助设备。
在另一些实施例中，基于参考输出参数和调整值，可以使用多通道宽动态范围压缩系统(WDRC系统)来配置骨导听力辅助设备。多通道宽动态范围压缩系统可以先用滤波器组将声音信号按照频段划分为多个通道，对每个通道的信号单独进行压缩处理，这样可以根据该频段对应的听力损失情况设计合适的压缩比和压缩阈值，然后再将处理后的各通道信号综合成一路信号。多通道宽动态范围压缩系统可以更灵活地进行听力补偿。在多通道宽动态范围压缩系统中，通过调节每个参考输出参数和调整值，可以调节各个通道的信号的压缩比和压缩阈值，从而调节各个通道的参考输出参数。
图5是根据该获取参考输出参数的调整值的方法的示例性流程图。使用图5所示的方法确定的调整值与佩戴者的听力级相关。如图5所示，流程500包括下述步骤。
步骤510，确定各个频段以及各个声级对应的第一阈值，其中，第一阈值与佩戴者对各个频段各个声级的振动感受程度相关。
振动感受程度可以用于表示用户佩戴骨导听力辅助设备时候感知到振动的程度。在一些实施例中，振动感受程度可以包括多个等级用于表示感知到振动的程度。等级越高，用户可以感知到振动的程度越大。在一些实施例中，等级可以包括第一等级、第二等级、第三等级、第四等级以及第五等级，分别对应的振动感受程度可以包括“没有振动”、“极其轻微振动”、“轻微振动”、“振动明显，但能接收”、“振动剧烈，不能接受”。在一些实施例中，不同的等级可以通过分数进行表示。例如，第一等级可以是1分，第二等级可以是2分，第三等级可以是3分，第四等级可以是4分，第五等级可以是5分。
在一些实施例中，第一阈值可以为佩戴者在振动感受程度处于某一等级下时对应骨导听力辅助设备的输出信号强度，也就是说，当骨导听力辅助设备的输出信号的强度达到该第 一阈值时，佩戴者能够感受到该等级的振动。例如，第一阈值可以为佩戴者在振动感受程度处于第三等级下时对应骨导听力辅助设备的输出信号强度(即参考输出参数)，也就是说，当骨导听力辅助设备的输出信号强度达到该第一阈值时，佩戴者能够感受到第三等级对应的轻微振动。又例如，第一阈值可以为佩戴者在振动感受程度处于第四等级下时对应骨导听力辅助设备的输出信号强度，也就是说，当骨导听力辅助设备的输出信号强度达到该第一阈值时，佩戴者能够感受到第四等级对应的明显振动，但是可以接收的振动强度。在一些实施例中，当骨导听力辅助设备的输出信号强度大于该第一阈值，则佩戴者可能会感受到第一阈值对应的等级下的振动(例如，第三等级对应的轻微振动)更强烈的振动，佩戴体验较差，则需要调整(降低)参考输出参数，以使得骨导听力辅助设备的输出信号强度小于第一阈值。
在一些实施例中，可以获取骨导听力辅助设备佩戴者在各个声级各个频段下对应的初步参考输出参数。关于获取参考输出参数的详细描述可以参照图4中的420操作。在一些实施例中，对于不同的佩戴者而言，第一阈值可以不同。例如，可以对骨导听力辅助设备的佩戴者进行测试，以确定骨导听力辅助设备佩戴者在各个声级各个频段下在该初步参考输出参数下的输出信号强度以及对应的振动感受程度，并通过调整初步参考输出参数获得参考输出参数，以调整输出信号强度以及振动感受程度，使得佩戴者的振动感受程度达到一定等级(例如，第三等级，轻微振动)，进而确定各个频段以及各个声级对应的第一阈值。在一些实施例中，调整后的初步参考输出参数(即参考输出参数，例如参考模拟输出值)可以等于调整后的信号输出强度。第一阈值可以等于佩戴者的振动感受程度达到一定等级(例如，第三等级，轻微振动)时对应的调整输出信号强度或者参考模拟输出值。
在一些实施例中，对于不同的佩戴者而言，第一阈值可以相同。例如，第一阈值具体可以按照以下方法来确定：对多个测试者进行测试，以确定各个测试者在各个声级以及各个频段下主观感受到第二等级的轻微振动时的信号输出强度，将上述信号输出强度作为测试数据；对测试数据进行整合和挑选，以得到第一阈值。该第一阈值可以适用于不同的佩戴者。在一些实施例中，对测试数据进行整合和挑选可以是：对于某一频段而言，仅仅考虑每个测试者在该频段下各个声级中主观感受到轻微振动时的输出参数的最低值，并从各个测试者的各个声级中主观感受到轻微振动时的输出参数的最低值中进一步挑选最低值作为第一阈值。
在一些实施例中，骨导听力辅助设备在低频段(如0Hz-625Hz的频段)的剧烈振动现象较为明显，可以在低频段设置参考输出参数的调整值，以降低参考输出参数，降低用户可以感知的振动强度；相应的，可以在低频段(如0Hz-625Hz的频段)设置第一阈值，以便基于第一阈值确定参考输出参数的调整值。在一些实施例中，可以在0Hz-625Hz的频段内 设定第一阈值，并在该频段确定调整值。在一些实施例中，不同频段对应的第一阈值不同。例如，在频率大于0Hz而小于等于125Hz的频段内，第一阈值在48dB-52dB范围内。在一些实施例中，在频率大于125Hz而小于等于375Hz的频段内，第一阈值在49dB-54dB范围内。在一些实施例中，在频率大于375Hz而小于等于625Hz的频段内，第一阈值在50dB-55dB范围内。在一些实施例中，相同声级下频段越高，第一阈值越大。
在一些实施例中，不同声级相同频段对应的第一阈值可以相同，例如，可以在上述各个频段内对应的第一阈值的范围内选择一个最小值(例如，48dB)作为该频段的第一阈值，以使得骨导听力辅助设备在接收到的声音信号为不同声级相同频段下均不会产生较剧烈的振动。例如，在频率大于0Hz而小于等于125Hz的频段内，第一阈值为48dB。在频率大于125Hz而小于等于375Hz的频段内，第一阈值为49dB。在频率大于375Hz而小于等于625Hz的频段内，第一阈值为50dB。
在一些实施例中，不同声级相同频段对应的第一阈值可以不相同。在一些实施例中，相同频段下声级越高，第一阈值可以越大。例如，在频率大于0Hz而小于等于125Hz的频段内，声级为20dBC-40dBC，第一阈值为48dB；在0Hz而小于等于125Hz的频段内，声级为40dBC-50dBC，第一阈值为49dB；在0Hz而小于等于125Hz的频段内，声级为50dBC-60dBC，第一阈值为50dB。
在一些实施例中，不同听力级不同声级相同频段对应的第一阈值可以相同，例如，可以在上述各个频段内对应的第一阈值的范围内选择一个最小值(例如，48dB)作为该频段的第一阈值，以使得在骨导听力辅助设备在接收到的声音信号为相同频段下，无论声音信号为任何声级以及无论佩戴者为任何听力级，均不会产生较剧烈的振动。
在一些实施例中，不同听力级不同声级相同频段对应的第一阈值不同。例如，听力级在40dBHL频率在大于125Hz而小于等于375Hz的频段内以及60dBC的声级下，第一阈值在可以为49dB。而听力级在10dBHL频率在大于125Hz而小于等于375Hz的频段内以及75dBC的声级下，第一阈值在可以为50dB。又例如，听力级在30dBHL频率在大于375Hz而小于等于625Hz的频段内以及70dBC的声级下，第一阈值在可以为55dB。例如，听力级在20dBHL频率在大于375Hz而小于等于625Hz的频段内以及75dBC的声级下，第一阈值在可以为56dB。在一些实施例中，不同频段不同声级不同听力级对应的第一阈值可以相同，例如，可以在上述各个频段内对应的第一阈值的范围内选择一个最小值(例如，48dB)作为所有频段不同声级对应的第一阈值，以使得骨导听力辅助设备在接收到的声音信号为不同声级不同频段下均不会产生较剧烈的振动。例如，在频率大于0Hz-625Hz的频段内，第一阈 值为48dB。
步骤520，确定各个频段以及各个声级对应的第二阈值，其中，第二阈值与佩戴者在各个频段的言语识别率相关。
言语识别率(即言语可懂度)可以是听懂或听清楚的字词与听到的字词的比值。言语识别率可以用于表征佩戴者佩戴助听器后对所听到的语言的听觉敏感度和清晰度，进而在一定程度上反映佩戴者的助听效果。言语识别率越高，标识佩戴者佩戴助听器后听觉敏感度更高，以及听觉清晰度更高，助听效果越好。在一些实施例中，如果言语识别率大于或等于70％，则可以认为助听效果为佳；而如果言语识别率小于或等于50％，则可以认为助听效果不理想，需重新调试或配置骨导听力辅助设备。
在一些实施例中，对参考输出参数的调整(如降低)可以影响骨导听力辅助设备输出信号的强度，进而可能影响骨导听力辅助设备的言语识别率。例如，基于图9-11的实验结果可以得知，在一定范围内(如调整值小于17dB的范围内)，调整值越大，言语识别率可能越低。第二阈值可以用于保证参考输出参数调整后的言语识别率在一定范围内(如高于某一阈值)。也就是说，第二阈值可以用于将参考输出参数调整后的言语识别率的降低量控制在一定范围内。例如，当调整值不超过第二阈值时，佩戴者佩戴助听器的言语识别率相对于参考输出参数未调整时的降低量可以较小，例如，言语识别率的降低量可以小于或等于5％。言语识别率的降低量可以为参考输出参数未调整时的言语识别率减去参考输出参数调整后的言语识别率。
在一些实施例中，第二阈值可以为佩戴者佩戴骨导听力辅助设备时预设言语识别率下对应的骨导听力辅助设备的参考输出参数对应的调整值的最大值，也就是说，当骨导听力辅助设备的参考输出参数对应的调整值达到该第二阈值时，佩戴者佩戴骨导听力辅助设备时言语识别率为预设阈值。当调整值大于该第二阈值，则佩戴者佩戴骨导听力辅助设备时言语识别率将小于预设言语识别率。
例如，如图10所示，第二阈值可以为佩戴者佩戴骨导听力辅助设备时在125Hz下言语识别率为80％时的参考输出参数对应的调整值，即第二阈值为5dB。也就是说，当骨导听力辅助设备在125Hz下的参考输出参数对应的调整值为第二阈值时，佩戴者佩戴骨导听力辅助设备时言语识别率可以为80％。又例如，如图11所示，第二阈值可以为佩戴者佩戴骨导听力辅助设备时在250Hz下言语识别率为60％的参考输出参数对应的调整值，即第二阈值为12dB。也就是说，当骨导听力辅助设备在250Hz下的参考输出参数对应的调整值为第二阈值时，佩戴者佩戴骨导听力辅助设备时言语识别率可以为60％。
在一些实施例中，可以根据预设言语识别率的阈值来确定第二阈值。例如，可以基于图9-11中对佩戴者进行言语识别率测试的实验结果确定第二阈值。仅作为示例，参考图10，当基于未调整时的参考输出参数配置骨导听力辅助设备时佩戴者的言语识别率为80％，如果设置降低参考输出参数后言语识别率要不小于75％(即言语识别率的降低量小于或等于5％)，则第二阈值可以为10dB；如果设置言语识别率要不小于80％(即言语识别率几乎不降低)，则第二阈值可以为5dB。
在一些实施例中，骨导听力辅助设备在低频段(如0Hz-625Hz的频段)的剧烈振动现象较为明显，可以在低频段设置参考输出参数的调整值，以降低参考输出参数，降低用户可以感知的振动强度；相应的，可以在低频段(如0Hz-625Hz的频段)设置第二阈值，以便基于第一阈值确定参考输出参数的调整值。在一些实施例中，不同频段对应的第二阈值不同。例如，在频率大于0Hz而小于等于125Hz的频段内，第二阈值在5dB-10dB范围内。在一些实施例中，在频率大于125Hz而小于等于375Hz的频段内，第二阈值在3dB-7dB范围内。在一些实施例中，在频率大于375Hz而小于等于625Hz的频段内，第二阈值在1dB-4dB范围内。在一些实施例中，相同声级下频段越高，第二阈值越小。
在一些实施例中，不同听力级相同频段对应的第二阈值可以相同。例如，无论佩戴者的听力级是30dBHL或者是40dBHL，都可以按照上述范围设置第二阈值。在一些实施例中，不同听力级相同频段对应的第二阈值可以不同。例如，在频率大于0Hz而小于等于125Hz的频段内，听力级为30dBHL，第二阈值为5dB；在0Hz而小于等于125Hz的频段内，听力级为40dBHL，第二阈值为15dB。在一些实施例中，不同声级相同频段对应的第二阈值可以相同。在一些实施例中，可以在上述范围内选择一个最小值作为第二阈值，以使得骨导听力辅助设备在接收到的声音信号为不同声级下均不会过多影响言语识别率。例如，在频率大于125Hz而小于等于375Hz的频段内，第二阈值可以为3dB。在一些实施例中在频率大于0Hz而小于等于125Hz的频段内，第二阈值可以为5dB。在一些实施例中，在频率大于375Hz而小于等于625Hz的频段内，第二阈值可以为1dB。
在一些实施例中，不同声级相同频段对应的第二阈值可以不同。例如，在频率大于0Hz而小于等于125Hz的频段内，声级为60dBC，第二阈值为5dB；在0Hz而小于等于125Hz的频段内，声级为75dBC，第二阈值为10dB。
步骤530，基于参考输出参数、第一阈值和第二阈值确定调整值。
在一些实施例中，当参考输出参数大于第一阈值时，可以先设定一个初始调整值。该初始调整值可以基于经验或预设公式来确定。然后可以将该初始调整值与第二阈值进行比较， 如果该初始调整值大于第二阈值，则减小该初始调整值，以使得初始调整值小于等于第二阈值。如果该初始调整值小于或等于第二阈值，则将该初始调整值确定为调整值。
在一些实施例中，可以将特定频段以及特定声级下对应的参考输出参数减去该特定频段以及特定声级对应的第一阈值而获得比较值；然后，将比较值与该特定频段以及特定声级对应的第二阈值进行比较；基于比较值与第二阈值的比较结果，确定该特定频段以及特定声级下的参考输出参数对应的调整值。
第一阈值和第二阈值的确定方法请参见上文的相关说明。比较值可以为正数、负数或零。将比较值与第二阈值进行比较，可以是进行数值大小的比较，以确定比较值和第二阈值的大小关系。比较值与第二阈值的比较结果可以包括比较值小于第二阈值、比较值等于第二阈值或者比较值大于第二阈值。基于比较值与第二阈值的比较结果，确定参考输出参数对应的调整值，可以是基于比较值与第二阈值的大小关系，确定调整值。
在一些实施例中，基于比较值与第二阈值的比较结果，确定参考输出参数对应的调整值可以包括当比较值小于或等于0时，调整值为0；当比较值大于0而小于等于第二阈值时，调整值为比较值；当比较值大于第二阈值时，调整值为第二阈值。
当参考输出参数小于或等于第一阈值时，按照参考输出参数配置骨导听力辅助设备后，佩戴者佩戴该骨导听力辅助设备后感受到振动的可能性较低，无需对参考输出参数进行调整。当参考输出参数大于第一阈值时，按照参考输出参数配置骨导听力辅助设备后，佩戴者佩戴该骨导听力辅助设备后感受到较强烈振动的可能性较高，需要对参考输出参数进行调整。进一步地，在确定调整值时，不但要考虑参考输出参数所带来的骨导听力辅助设备的振动风险，还要考虑对调节后的参考输出参数对骨导助听的言语识别率的影响。由于第二阈值是与言语识别率相关的阈值，通过将上述比较值与第二阈值进行比较，尽量保证调整值小于或等于第二阈值，尽可能减小因参考输出参数的调整造成的对言语识别率的影响。
图6是根据该获取参考输出参数的调整值的方法的示例性流程图。在一些实施例，当使用多通道宽动态范围压缩系统配置骨导听力辅助设备时，可以采用图6所示的流程600确定参考输出参数对应的调整值。如图6所示，确定参考输出参数对应的调整值的流程600可以包括下述步骤：
步骤610，将参考输出参数与第一阈值进行比较。其中，第一阈值与佩戴者对各个频段各个声级的振动感受程度相关。
本步骤中的第一阈值的相关说明以及确定第一阈值的方法，可以参见步骤510中关于第一阈值的相关内容。将参考输出参数与第一阈值进行比较可以是将参考输出参数与第一阈 值进行数值大小的比较。
步骤620，基于参考输出参数与第一阈值的比较结果，确定参考输出参数对应的调整值。
参考输出参数对应的调整值的相关说明，请参见步骤430的相关内容。参考输出参数与第一阈值的比较结果可以包括参考输出参数大于第一阈值、参考输出参数等于第一阈值以及参考输出参数等于第一阈值的比较结果。在一些实施例中，可以基于参考输出参数是否大于第一阈值，确定调整值是否为0。例如，当参考输出参数小于第一阈值时，调整值为0；当参考输出参数大于第一阈值时，调整值大于0。
在一些实施例中，当使用多通道宽动态范围压缩系统配置骨导听力辅助设备时，调整值可以包括在各个声级中至少一个声级大于声级阈值时多通道宽动态范围压缩系统的增益降低值。在一些实施例中，该声级阈值可以是70dB。在佩戴者使用骨导听力辅助设备过程中，日常对话的声音信号的声级一般为60dB左右。声音信号的声级大于或等于70dBC的情况可能发生在佩戴者自己说话时或环境较为嘈杂时，此时骨导听力辅助设备可能产生较为强烈的振动，因此设置调整值用于在该声级范围内调节(如降低)参考输出参数，可以改善骨导听力辅助设备的振动情况，又能够使得佩戴者在日常对话时言语识别率几乎不受到影响。
在各个声级中至少一个声级大于声级阈值时的增益可以被称为高水平增益(High Level Gain)，调整值可以包括多通道宽动态范围压缩系统的高水平增益(High Level Gain)的降低值。多通道宽动态范围压缩系统的高水平增益(High Level Gain)可以是在声音信号的声级大于声级阈值(例如70dB)时的增益。多通道宽动态范围压缩系统在各个声级中至少一个声级大于声级阈值时的增益可以基于佩戴者的听力损失数据来确定，例如，可以根据经验公式来确定。例如，经验公式可以是基于佩戴者的听力级来确定多通道宽动态范围压缩系统的高水平增益(High Level Gain)。调整值可以是对经验公式得出的高水平增益进行降低的具体数值。
在一些实施例中，可以基于参考输出参数是否大于第一阈值，确定增益降低值是否为0(即是否降低在各个声级中至少一个声级大于声级阈值时的增益)。例如，当参考输出参数小于第一阈值时，增益降低值为0；当参考输出参数大于第一阈值时，增益降低值大于0。
在一些实施例中，在确定在各个声级中至少一个声级大于声级阈值时的增益降低值后，可以用该增益降低值降低声级大于声级阈值时的增益值，并将降低后的增益值作为多通道宽动态范围压缩系统的输入参数。在各个声级中至少一个声级大于声级阈值时，骨导听力辅助设备易产生振动，通过在设定的频段内(频率大于0Hz而小于或等于625Hz的频段内)以及 在声级高于声级阈值时设定按照上述方式确定增益降低值，并将该增益降低值作为调整值，可以保证在声音信号的声级小于声级阈值时的参考输出参数不受到影响，而当声音信号的声级小于声级阈值时，参考输出参数得到降低。这样可以在保证骨导听力辅助设备的言语识别率的情况下，又改善骨导听力辅助设备在某些场景下振动剧烈的情况。
在一些实施例中，当调整值包括在各个声级中至少一个声级大于声级阈值时多通道宽动态范围压缩系统的增益降低值时，步骤620具体可以包括以下步骤：如果参考输出参数小于或等于第一阈值，则增益降低值为0；如果参考输出参数大于第一阈值，则增益降低值为第一阈值与参考输出参数的差值。
在本实施例中，如果参考输出参数小于或等于第一阈值，则佩戴者在佩戴骨导听力辅助设备时感受到剧烈振动的概率较小，无需调整(降低)高水平增益，因此将高水平增益降低值设为0。如果参考输出参数大于第一阈值，则佩戴者在佩戴骨导听力辅助设备时有较大概率会感受到剧烈振动，则需要调整(降低)高水平增益，从而降低参考输出参数，以使得参考输出参数能够小于第一阈值。
在一些实施例中，当使用多通道宽动态范围压缩系统配置骨导听力辅助设备时，调整值可以包括在各个声级中至少一个声级大于声级阈值时多通道宽动态范围压缩系统的最大输出(Output Limit)的降低值。在一些实施例中，该声级阈值可以是70dB。在本实施例中，声音信号的声级大于或等于70dBC的情况可能发生在佩戴者自己说话时或环境较为嘈杂时，此时骨导听力辅助设备可能产生较为强烈的振动，因此设置调整值用于在该声级范围内调节参考输出参数(多通道宽动态范围压缩系统的最大输出)，可以改善骨导听力辅助设备的振动情况，又能够使得佩戴者在日常对话时言语识别率几乎不受到影响。
最大输出可以理解为对各个频段下的参考输出参数的限定值，当参考输出参数大于最大输出时，骨导听力辅助设备的参考输出参数即等于最大输出。多通道宽动态范围压缩系统的最大输出(Output Limit)可以基于佩戴者的听力损失数据，根据经验公式来确定。例如，经验公式可以是基于佩戴者的听力级来确定多通道宽动态范围压缩系统的最大输出(Output Limit)。调整值可以是对经验公式得出的最大输出进行降低的具体数值。经验公式可以是由用户设定或是骨导听力辅助设备配置系统的默认设置。
在一些实施例中，当调整值可以包括在各个声级中至少一个声级大于声级阈值时多通道宽动态范围压缩系统的最大输出(Output Limit)的降低值时，步骤620可以进一步包括以下步骤：如果参考输出参数小于或等于第一阈值，则最大输出的降低值为0dB；如果参考输出参数大于第一阈值，则最大输出的降低值大于0dB。
也就是说，如果参考输出参数小于或等于第一阈值，则佩戴者在佩戴骨导听力辅助设备时感受到剧烈振动的概率较小，无需调整(降低)最大输出；如果参考输出参数大于第一阈值，则佩戴者在佩戴骨导听力辅助设备时有较大概率会感受到剧烈振动，需要调整(降低)最大输出，从而降低参考输出参数，以使得参考输出参数能够小于第一阈值。
进一步地，当确定最大输出的降低值大于0时，可以进一步确定最大输出参数的降低值的具体数值。在一些实施例中，例如，可以在等步长地逐步降低最大输出，以使得参考输出参数最终小于第一阈值。例如，等步长地逐步降低最大输出可以是每次将最大输出降低的数值相同(如每次将最大输出降低2dB)，以逐步减小参考输出参数，并最终使得参考输出参数小于第一阈值。
由于佩戴者一般在自己说话或者环境声音较大时感受到较强烈的振动，此时的声级较大，例如，大于等于70dB，通过方法600和调节参考输出参数，可以使得当中声级(如70dB以下声级)的声音信号输入骨导听力辅助设备时，骨导听力辅助设备的参考输出参数不受到影响，而当高声级(如70dB及以上声级)的声音信号输入骨导听力辅助设备时，骨导听力辅助设备的参考输出参数低于第一阈值，从而改善佩戴者在自己说话或者环境声音较大时感受到较强烈的振动的情况。
在一些实施例中，调整值可以仅包括在各个声级中至少一个声级大于声级阈值时的增益降低值。在另一些实施例中，调整值可以仅包括在各个声级中至少一个声级大于声级阈值时的最大输出(Output Limit)的降低值。在一些实施例中，调整值可以既包括各个声级中至少一个声级大于声级阈值时的增益降低值，又包括调整值可以仅包括在各个声级中至少一个声级大于声级阈值时的最大输出(Output Limit)的降低值。
在一些实施例中，多通道宽动态范围压缩系统的设置参数还包括分频频率(Crossover Frequency)、下限阈值(Lower Threshold)、低水平增益(Low Level Gain)、上限阈值(Upper Threshold)、放大阈值(Expansion Threshold)、放大比例(Expansion Ratio)、效果器产生时间(Compressor Attack)、效果器释放时间(Compressor Release)、增益算法产生时间(AGCo Attack)、增益算法释放时间(AGCo Release)。其中，分频频率(Crossover Frequency)可以是音频频谱被分割的频率，即各个频段的分割点。下限阈值可以是该频段下声级下限阈值。低水平增益可以是输入声级小于下限阈值时的增益。上限阈值可以是该频段下声级的上限阈值，即高水平增益对应的阈值。放大阈值可以是频段下声级放大阈值，放大比例可以是对放大阈值的声音的增益比例。效果器产生时间可以是当效果器侦测到有高于阈值的声音，效果器完全产生作用的过渡时间，过渡时间内增益逐渐增加至预设增益。效果器释放时间可以是 当声音低于阈值时，效果器完全产生作用的过渡时间，过渡时间内增益逐渐降低至预设增益。增益算法为根据输出的自动增益控制算法(Automatic Gain Control according to Output,AGCo)，增益算法产生时间可以是2ms。增益算法释放时间可以是64ms。
图7是根据本申请一些实施例所示的骨导听力辅助设备在使用过程中所执行操作的流程图。如图7所示，骨导听力辅助设备使用过程中骨导听力辅助设备可以执行下述步骤：
步骤710，获取声音输入信号。在一些实施例中，声音输入信号可以包括骨导听力辅助设备从存储设备(例如，存储器130)、终端(例如，终端140)等设备中获取的音频信号(例如，歌曲、语音等)。在一些实施例中，输入骨导听力辅助设备的声音信号可以包括骨导听力辅助设备的拾音组件拾取的声音信号。例如，拾音组件可以拾取声音(第一振动信号)，并将第一振动信号进行处理后转化为电信号。电信号可以传递给骨导听力辅助设备的扬声器组件，扬声器组件用于将该电信号基于参考输出参数进行处理转化为第二振动信号，传递给佩戴者。
步骤720，基于声音输入信号的声级以及频率成分和参考输出参数，确定频率成分对应的参考输出参数。在一些实施例中，骨导听力辅助设备可以获取存储于骨导听力辅助设备中的存储设备中的预设的参考输出参数。该预设的参考输出参数可以对应不同的频段、声级以及听力级。骨导听力辅助设备可以根据声音输入信号的声级以及频率成分从预设的参考输出参数中确定与该声级以及频率成分对应的参考输出参数。在一些实施例中，骨导听力辅助设备可以根据声音输入信号的声级、频率成分以及佩戴者的听力级从预设的参考输出参数中确定与该声级、频率成分以及听力级对应的参考输出参数。在一些实施例中，不同的频段、声级以及听力级对应的预设的参考输出参数可以根据图4中的420步骤确定。
步骤730，基于频率成分对应的参考输出参数以及频率成分的参考输出参数对应的调整值，获取频率成分在声级下对应的实际输出参数。在一些实施例中，骨导听力辅助设备可以获取存储于骨导听力辅助设备中的存储设备中的预设的参考输出参数的调整值。该预设的调整值可以对应不同的频段、声级以及听力级下的参考输出参数。骨导听力辅助设备可以根据声音输入信号的声级以及频率成分从预设的调整值中确定与该声级以及频率成分对应的参考输出参数对应的调整值。在一些实施例中，骨导听力辅助设备可以根据声音输入信号的声级、频率成分以及佩戴者的听力级从预设的调整值中确定与该声级、频率成分以及听力级下的参考输出参数对应的调整值。在一些实施例中，不同的频段、声级以及听力级对应的预设的参考输出参数对应的调整值可以根据图4中的430步骤确定。
步骤740，基于实际输出参数，控制骨导听力辅助设备输出声音信号。
参考输出参数可以理解为在配置骨导听力辅助设备的过程中进行初始设置的参数，实际输出参数可以理解为骨导听力辅助设备基于调整值调整后的输出参数。在一些实施例中，实际输出参数可以包括增益值和/或实际模拟输出值。在一些实施例中，实际增益值可以是助听器在佩戴过程中对声音信号的强度实际进行放大的值，实际模拟输出值可以是助听器根据输入的声音信号参数(例如，声音信号的强度值)模拟的实际输出信号强度值。例如，实际模拟输出值可以等于声音信号的输入值(即强度值，单位dB)加上实际增益值(单位dB)。在一些实施例中，某一特定声级以及特定频段下对应的实际模拟输出值可以等于骨导听力辅助设备使用过程中的实际输出值(即骨导听力辅助设备实际输出的信号的强度值，单位dB)，例如，当骨导听力辅助设备输入声音信号在该特定声级以及特定频段下。在一些实施例中，当佩戴者佩戴上骨导听力辅助设备时，骨导听力辅助设备的拾音组件220可以执行步骤710，骨导听力辅助设备的磁路组件可以执行步骤720和730。骨导听力辅助设备的振动组件可以执行步骤740，振动组件可以将磁路组件确定的实际输出参数转换为对应的振动强度，以使得骨导听力辅助设备通过机械振动的方式输出声音信号。在一些实施例中，当佩戴者佩戴上骨导听力辅助设备时，骨导听力辅助设备的拾音组件220可以执行步骤710，骨导听力辅助设备的中的处理设备可以执行步骤720和730。骨导听力辅助设备的处理设备可以控制磁路组件以及振动组件可以执行步骤740。例如，处理设备可以基于确定的实际输出参数控制振动组件产生与实际输出参数对应的振动强度，以使得骨导听力辅助设备通过机械振动的方式输出声音信号。又例如，处理设备可以基于确定的实际输出参数控制音圈中的电流大小，以控制音圈产生的机械振动强度，从而控制骨导听力辅助设备输出信号强度。
在一些实施例中，骨导听力辅助设备中可以存储有各个频段以及各个声级下的实际输出参数。当骨导听力辅助设备获取到声音输入信号，骨导听力辅助设备可以基于声音输入信号的声级以及频段，直接确定骨导听力辅助设备在对应声级和对应频段下的实际输出参数，并基于该实际输出参数输出声音信号。
上文已对基本概念做了描述，显然，对于本领域技术人员来说，上述详细披露仅仅作为示例，而并不构成对本申请的限定。虽然此处并没有明确说明，本领域技术人员可能会对本申请进行各种修改、改进和修正。该类修改、改进和修正在本申请中被建议，所以该类修改、改进、修正仍属于本申请示范实施例的精神和范围。
同时，本申请使用了特定词语来描述本申请的实施例。如“一个实施例”、“一实施例”、和/或“一些实施例”意指与本申请至少一个实施例相关的某一特征、结构或特点。因此，应强调并注意的是，本说明书中在不同位置两次或多次提及的“一实施例”或“一个实施例”或“一个 替代性实施例”并不一定是指同一实施例。此外，本申请的一个或多个实施例中的某些特征、结构或特点可以进行适当的组合。
此外，除非权利要求中明确说明，本申请所述处理元素和序列的顺序、数字字母的使用、或其他名称的使用，并非用于限定本申请流程和方法的顺序。尽管上述披露中通过各种示例讨论了一些目前认为有用的发明实施例，但应当理解的是，该类细节仅起到说明的目的，附加的权利要求并不仅限于披露的实施例，相反，权利要求旨在覆盖所有符合本申请实施例实质和范围的修正和等价组合。例如，虽然以上所描述的系统组件可以通过硬件设备实现，但是也可以只通过软件的解决方案得以实现，如在现有的服务器或移动设备上安装所描述的系统。
同理，应当注意的是，为了简化本申请披露的表述，从而帮助对一个或多个发明实施例的理解，前文对本申请实施例的描述中，有时会将多种特征归并至一个实施例、附图或对其的描述中。但是，这种披露方法并不意味着本申请对象所需要的特征比权利要求中提及的特征多。实际上，实施例的特征要少于上述披露的单个实施例的全部特征。
一些实施例中使用了描述成分、属性数量的数字，应当理解的是，此类用于实施例描述的数字，在一些示例中使用了修饰词“大约”、“近似”或“大体上”来修饰。除非另外说明，“大约”、“近似”或“大体上”表明所述数字允许有±20％的变化。相应地，在一些实施例中，说明书和权利要求中使用的数值参数均为近似值，该近似值根据个别实施例所需特点可以发生改变。在一些实施例中，数值参数应考虑规定的有效数位并采用一般位数保留的方法。尽管本申请一些实施例中用于确认其范围广度的数值域和参数为近似值，在具体实施例中，此类数值的设定在可行范围内尽可能精确。
针对本申请引用的每个专利、专利申请、专利申请公开物和其他材料，如文章、书籍、说明书、出版物、文档等，特此将其全部内容并入本申请作为参考。与本申请内容不一致或产生冲突的申请历史文件除外，对本申请权利要求最广范围有限制的文件(当前或之后附加于本申请中的)也除外。需要说明的是，如果本申请附属材料中的描述、定义、和/或术语的使用与本申请所述内容有不一致或冲突的地方，以本申请的描述、定义和/或术语的使用为准。
最后，应当理解的是，本申请中所述实施例仅用以说明本申请实施例的原则。其他的变形也可能属于本申请的范围。因此，作为示例而非限制，本申请实施例的替代配置可视为与本申请的教导一致。相应地，本申请的实施例不仅限于本申请明确介绍和描述的实施例。

Claims (20)

  1. 一种骨导听力辅助设备的配置方法，其包括以下步骤：
    获取佩戴者的听力损失数据；
    基于所述听力损失数据，确定骨导听力辅助设备在各个声级各个频段下的参考输出参数；
    获取所述参考输出参数的调整值，所述调整值至少与所述频段相关；以及
    基于所述参考输出参数和所述调整值，配置所述骨导听力辅助设备。
  2. 如权利要求1所述的配置方法，其中，所述基于所述参考输出参数和所述调整值，配置所述骨导听力辅助设备，包括：
    在频率大于0Hz而小于或等于625Hz的频段内，基于所述调整值降低所述参考输出参数。
  3. 如权利要求1所述的配置方法，其中，在不同听力级以及相同频段下的所述调整值相同。
  4. 如权利要求2所述的配置方法，其中，在频率大于0Hz而小于或等于625Hz的频段内，所述调整值为1dB-12dB。
  5. 如权利要求2所述的配置方法，其中，
    在频率大于0Hz而小于或等于125Hz的频段内，所述调整值设定为5dB-12dB；
    在频率大于125Hz而小于或等于375Hz的频段内，所述调整值设定为3dB-9dB；和/或，
    在频率大于375Hz而小于或等于625Hz的频段内，所述调整值设定为1dB-6dB。
  6. 如权利要求2所述的配置方法，其中，
    在频率大于0Hz而小于或等于125Hz的频段内，所述调整值为5dB-7dB；
    在频率大于125Hz而小于或等于375Hz的频段内，所述调整值为3dB-5dB；和/或，
    在频率大于375Hz而小于或等于625Hz的频段内，所述调整值为1dB-3dB。
  7. 如权利要求2所述的配置方法，其中，
    在频率大于0Hz而小于或等于125Hz的频段内，所述调整值为10dB-12dB；
    在频率大于125Hz而小于或等于375Hz的频段内，所述调整值为7dB-9dB；和/或，
    在频率大于375Hz而小于或等于625Hz的频段内，所述调整值为4dB-6dB。
  8. 如权利要求1所述的配置方法，其中，在不同听力级以及相同频段下的所述调整值不同。
  9. 如权利要求8所述的配置方法，其中，所述获取所述参考输出参数的调整值包括：
    确定所述各个频段以及所述各个声级对应的第一阈值，所述第一阈值与所述佩戴者对所述各个频段所述各个声级的振动感受程度相关；
    确定所述各个频段以及所述各个声级对应的第二阈值，所述第二阈值与所述佩戴者在所述各个频段各个声级的言语识别率相关；以及
    基于所述参考输出参数、所述第一阈值和所述第二阈值确定所述调整值。
  10. 如权利要求9所述的配置方法，其中，所述基于所述参考输出参数、所述第一阈值和所述第二阈值确定所述调整值包括：
    对于所述各个声级以及所述各个频段中的某一声级以及某个频段下的参考输出参数；
    将所述参考输出参数减去所述第一阈值而获得比较值；
    将所述比较值与所述第二阈值进行比较；
    基于所述比较值与所述第二阈值的比较结果，确定所述参考输出参数对应的调整值。
  11. 如权利要求10所述的配置方法，其中，所述基于所述比较值与所述第二阈值的比较结果，确定所述参考输出参数对应的调整值包括：
    当所述比较值小于或等于0时，所述调整值为0dB；
    当所述比较值大于0而小于等于所述第二阈值时，所述调整值为所述比较值；
    当所述比较值大于所述第二阈值时，所述调整值为所述第二阈值。
  12. 如权利要求9所述的配置方法，其中，在频率大于0Hz而小于等于125Hz的频段内，所述第一阈值在48dB-52dB范围内；
    在频率大于125Hz而小于等于375Hz的频段内，所述第一阈值在49dB-54dB范围内；和/或，
    在频率大于375Hz而小于等于625Hz的频段内，所述第一阈值在50dB-55dB范围内。
  13. 如权利要求9所述的配置方法，其中，在频率大于0Hz而小于等于125Hz的频段内，所述第二阈值在5dB-10dB范围内；
    在频率大于125Hz而小于等于375Hz的频段内，所述第二阈值在3dB-7dB范围内；和/或，
    在频率大于375Hz而小于等于625Hz的频段内，所述第二阈值在1dB-4dB范围内。
  14. 如权利要求1所述的配置方法，其中，基于所述参考输出参数和所述调整值，配置所述骨导听力辅助设备包括：
    基于所述参考输出参数和所述调整值，使用多通道宽动态范围压缩系统，配置所述骨导听力辅助设备。
  15. 如权利要求14所述的配置方法，所述获取所述参考输出参数的调整值，包括：
    将所述参考输出参数与第一阈值进行比较，所述第一阈值与所述佩戴者对所述各个频段所述各个声级的振动感受程度相关；
    基于所述参考输出参数与所述第一阈值的比较结果，确定所述参考输出参数对应的所述调整值。
  16. 如权利要求15所述的配置方法，其中，所述调整值包括在所述各个声级中至少一个声级大于声级阈值时所述多通道宽动态范围压缩系统的增益降低值；基于所述参考输出参数与所述第一阈值的比较结果，确定所述参考输出参数对应的所述调整值，包括：
    如果所述参考输出参数小于或等于所述第一阈值，则所述增益降低值为0dB；
    如果所述参考输出参数大于所述第一阈值，则所述增益降低值为所述第一阈值与所述参考输出参数的差值。
  17. 如权利要求15所述的配置方法，其中，所述调整值包括在所述各个声级中至少一个声级大于声级阈值时所述多通道宽动态范围压缩系统的最大输出的降低值；基于所述参考输出参数与所述第一阈值的比较结果，确定所述参考输出参数对应的调整值，包括：
    如果所述参考输出参数小于或等于所述第一阈值，则所述最大输出的降低值为0dB；
    如果所述参考输出参数大于所述第一阈值，则所述最大输出的降低值大于0dB。
  18. 一种骨导听力辅助设备的配置系统，其包括：
    获取模块，用于获取佩戴者的听力损失数据；
    参考输出参数确定模块，用于基于听力损失数据，确定骨导听力辅助设备在各个声级各个频段下的参考输出参数；
    调整值确定模块，用于获取参考输出参数的调整值；以及
    配置模块，用于基于参考输出参数和调整值，配置骨导听力辅助设备。
  19. 一种骨导听力辅助设备的配置装置，其包括：
    处理设备；
    与所述处理设备通信的存储设备，用于存储指令，当所述处理设备执行所述存储指令，所述处理设备执行权利要求1-17中任一项所述的骨导听力辅助设备的配置方法。
  20. 一种计算机可读存储介质，所述存储介质存储计算机指令，当计算机读取所述存储介质中的计算机执指令时，所述计算机执行如权利要求1-17中任一项所述的骨导听力辅助设备的配置方法。
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