CN115334435A - Hearing assisting device - Google Patents

Abstract

The application discloses hearing assistance device, this hearing assistance device can include: a signal input module configured to receive an initial sound and convert the initial sound into an electrical signal; a signal processing module configured to process the electrical signal and generate a control signal; and at least one output transducer configured to convert the control signal into a bone-conducted sound wave of the user and an air-conducted sound wave that can be heard by the ear of the user, wherein, within a target frequency range, the air-conducted sound wave is delivered to the ear of the user such that the sound intensity of the air-conducted sound heard by the ear of the user is greater than the sound intensity of the initial sound received by the signal input module.

Description

A hearing aid device

technical field

The present application relates to the field of acoustics, in particular to a hearing aid device.

Background technique

Existing hearing aids can usually provide hearing compensation for users through bone conduction or air conduction. In some hearing aids (for example, hearing aids), the bone conduction sound transmission method will cause insufficient vibration signal strength in certain frequency bands due to the performance of the bone conduction vibrator, so that hearing compensation through bone conduction The effect is not ideal. In addition, for people with conductive hearing loss, traditional air conduction hearing aids will have a large air conduction sound threshold difference in certain frequency bands, which makes it difficult to perform hearing compensation through air conduction. When the user needs to hear the frequency When using wide-ranging or multi-band sounds, the above problems will lead to poor listening experience for users.

Therefore, it is desired to provide a hearing aid device that combines bone conduction and air conduction for hearing compensation, which can improve the hearing compensation effect of the user in a specific frequency band.

Contents of the invention

One of the embodiments of the present application provides a hearing aid device, which includes: a signal input module configured to receive an initial sound and convert the initial sound into an electrical signal; a signal processing module configured to process the electrical signal and generate a control signal; and at least one output transducer configured to convert the control signal into bone-conducted sound waves of the user and air-conducted sound waves that can be heard by the user's ears, wherein, within the target frequency range, the The air conduction sound wave is transmitted to the user's ear, so that the sound intensity of the air conduction sound heard by the user's ear is greater than the sound intensity of the initial sound received by the signal input module.

In some embodiments, the target frequency range is 200Hz-8000Hz.

In some embodiments, the target frequency range is 500Hz-6000Hz.

In some embodiments, the target frequency range is 750Hz-1000Hz.

In some embodiments, the signal processing module includes a signal processing unit, and the signal processing unit includes: a frequency division module configured to decompose the electrical signal into a high-frequency component and a low-frequency component; a high-frequency signal processing module , coupled to the frequency division module and configured to generate a high frequency output signal according to the high frequency component; and a low frequency signal processing module, coupled to the frequency division module and configured to generate a low frequency output signal according to the low frequency component .

In some embodiments, the electrical signal includes a high-frequency output signal corresponding to a high-frequency component in the initial sound, and a low-frequency output signal corresponding to a low-frequency component in the initial sound, and the signal processing unit includes: A high-frequency signal processing module configured to generate a high-frequency output signal according to the high-frequency component; and a low-frequency signal processing module configured to generate a low-frequency output signal according to the low-frequency component.

In some embodiments, the signal processing module further includes a power amplifier configured to amplify the high frequency output signal or the low frequency output signal into the control signal.

In some embodiments, the output transducer includes: a first vibration component, the first vibration component is electrically connected to the signal processing module to receive the control signal, and generates the bone vibration based on the control signal. a conductive sound wave; and a casing, the casing is coupled to the first vibrating component and driven by the first vibrating component to generate the air-conducting sound wave.

In some embodiments, the connection between the housing and the first vibrating component is a rigid connection.

In some embodiments, the housing and the first vibrating component are connected to the first vibrating component through an elastic member.

In some embodiments, the first vibrating component includes: a magnetic circuit system configured to generate a first magnetic field; a vibrating plate connected to the housing; and a coil connected to the vibrating plate and connected to the signal The processing module is electrically connected, the coil receives the control signal and generates a second magnetic field based on the control signal, the first magnetic field interacts with the second magnetic field, so that the vibration plate generates the bone-conducted sound wave .

In some embodiments, the vibrating plate and the casing define a cavity, and the magnetic circuit system is located in the cavity, wherein the magnetic circuit system is connected to the casing through an elastic member.

In some embodiments, the vibration output force level corresponding to the bone-conducted sound wave is greater than 55 dB.

In some embodiments, at least one second vibrating component configured to generate additional air-conducted sound waves that enhance the sound intensity of the air-conducted sound heard by the user's ears in the target frequency range may also be included.

In some embodiments, the at least one second vibrating component is a diaphragm structure, the diaphragm structure is connected to the housing, and the at least one output transducer excites the diaphragm structure to generate the additional air Conduct sound waves.

In some embodiments, the at least one second vibration component is an air-conducted speaker configured to generate the additional air-conducted sound waves according to the control signal.

In some embodiments, the hearing aid device further includes a fixing structure configured to carry the hearing aid device so that the hearing aid device is positioned on the mastoid process, temporal bone, parietal bone, frontal bone, auricle, In the ear canal or on the concha of the ear.

One of the embodiments of the present application provides a hearing aid device, which includes: a signal input module configured to receive an initial sound and convert the initial sound into an electrical signal; a signal processing module configured to process the electrical signal and generate a control signal; and at least one output transducer configured to convert the control signal into bone-conducted sound waves of the user and air-conducted sound waves that can be heard by the user's ears, wherein the hearing aid device includes a working state and a non-working state, the working state produces the air-conducted sound wave, the non-working state does not produce the air-conducted sound wave, and within the target frequency range, the sound of the air-conducted sound heard by the user's ear in the working state Stronger than the sound intensity of the air conduction sound heard by the user's ear in the non-working state.

Description of drawings

The present application will be further illustrated by means of exemplary embodiments, which will be described in detail by means of the accompanying drawings. These examples are non-limiting, and in these examples, the same number indicates the same structure, wherein:

Fig. 1 is an exemplary framework diagram of a hearing aid device provided according to some embodiments of the present application;

Fig. 2 is a frame diagram of a signal processing unit provided according to some embodiments of the present application;

Fig. 3 is a schematic structural diagram of an output transducer provided according to some embodiments of the present application;

Fig. 4 is a full scale force level (OFL60) frequency response diagram of a bone conduction component output by a hearing aid device in a reference acoustic environment according to some embodiments of the present application;

Fig. 5 is a frequency response diagram of the full-scale acoustic-mechanical sensitivity level (AMSL) of the output bone conduction component in the reference environment of the hearing aid device provided according to some embodiments of the present application;

Fig. 6 is a graph showing the sound pressure level of the air conduction components output by the hearing aid device in the reference environment according to some embodiments of the present application;

Fig. 7 is a gain diagram of an air conduction component output by a hearing aid device in a reference environment according to some embodiments of the present application; and

Fig. 8 is a position distribution diagram of a hearing aid device when worn according to some embodiments of the present application.

Detailed ways

In order to more clearly illustrate the technical solutions of the embodiments of the present application, the following briefly introduces the drawings that need to be used in the description of the embodiments. Obviously, the accompanying drawings in the following description are only some examples or embodiments of the present application, and those skilled in the art can also apply the present application to other similar scenarios. Unless otherwise apparent from context or otherwise indicated, like reference numerals in the figures represent like structures or operations.

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

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

In the field of hearing aids, air conduction hearing aids or bone conduction hearing aids are usually used to compensate for hearing loss. Traditional air-conduction loudspeakers provide hearing compensation for hearing loss by amplifying air-conduction sound signals. However, for people with conductive hearing loss, the air conduction sound threshold difference in some frequency bands may be large, which makes it difficult to use air conduction sound for hearing compensation. Bone conduction hearing aids can compensate hearing loss by converting sound signals into vibration signals (bone conduction sound). The ideal compensation effect, or if the bone conduction hearing aid generates excessive vibrations in certain frequency bands, it will bring discomfort to the user.

In order to improve the hearing compensation effect of the hearing aid device, the hearing aid device provided by the present application provides hearing compensation for the user simultaneously through bone conduction and air conduction. In some embodiments, the hearing assistance device may include a signal input module, a signal processing module, and at least one output transducer. Wherein, the signal input module is configured to receive an initial sound and convert the initial sound into an electrical signal, the signal processing module is configured to process the electrical signal and generate a control signal, and at least one output transducer is configured to convert the The control signal is converted into bone-conducted sound waves of the user and air-conducted sound waves that can be heard by the user's ears. In the target frequency range (for example, 200Hz-8000Hz), the air-conducted sound wave is transmitted to the user's ear, so that the sound intensity of the air-conducted sound heard by the user's ear is greater than the sound intensity of the initial sound received by the signal input module. In this case, the superimposition of air-conducted sound waves generated by the hearing aid device and bone-conducted sound waves can increase the intensity of the listening sound perceived by the user's ears, thereby improving the hearing compensation effect of the hearing aid device.

In some embodiments, the aforementioned bone-conducted sound waves and air-conducted sound waves can be generated by the same output transducer (eg, a bone-conducted vibration component). The output transducer converts the control signal into an air-conducted sound wave that is heard by the user's ear. sound). In addition, the housing of the hearing aid device may also be provided with sound guide holes meeting certain conditions. The sound guide hole can lead out the sound in the hearing aid device housing, and superimpose with the leakage sound generated by the vibration of the housing, jointly forming the air-conducted sound wave heard by the user's ear.

In some embodiments, the hearing aid device may also include a bone conduction vibration component (also referred to as a first vibration component) and an air conduction vibration component (also referred to as a second vibration component). The aforementioned bone-conducted sound waves and air-conducted sound waves can be generated by bone-conducted vibration components and air-conducted vibration components, respectively. During use, the signal processing module can separately process the electrical signals used to generate air-conducted sound waves and the electrical signals used to generate bone-conducted sound waves according to actual conditions, so as to meet the needs of different hearing-impaired people or the same hearing-impaired person in different environments. Different requirements for hearing compensation.

Fig. 1 is an exemplary framework diagram of a hearing aid device provided according to some embodiments of the present application. As shown in FIG. 1 , the hearing aid device 10 may include a signal input module 100 , a signal processing module 200 and at least one output transducer 300 .

The signal input module 100 is configured to receive an initial sound and convert the received initial sound into an electrical signal. In some embodiments, the signal input module 100 may include a microphone 110 or/and an audio interface 120 . In some embodiments, the microphone 110 may include an air conduction microphone, a bone conduction microphone, a remote microphone, a digital microphone, etc., or any combination thereof. In some embodiments, the remote microphone may include a wired microphone, a wireless microphone, a broadcast microphone, etc., or any combination thereof. In some embodiments, the number of microphones 110 may be one or more, and when the number of microphones 110 is more than one, the types of microphones 110 may be one or more. In some embodiments, the initial sound may include sound transmitted from the external environment to the signal input module 100 through air conduction. For example, the microphone 110 can convert the collected air vibration into an analog signal (electrical signal). The audio interface 120 is configured to receive digital or analog signals from the microphone 110 . In some embodiments, audio interface 120 may include an analog audio interface, a digital audio interface, a wired audio interface, a wireless audio interface, etc., or any combination thereof. In some embodiments, the signal input module 100 can directly receive electrical signals transmitted by wires or wirelessly. For example, the audio interface 120 can receive any digital or analog signal corresponding to sound from an external device in a wired or wireless manner.

The signal processing module 200 may be configured to process the electrical signal output by the signal input module 100 and generate a control signal. The control signal may be used to control the output transducer 300 to output bone-conducted sound waves and/or air-conducted sound waves. In the embodiments of this specification, the bone-conducted sound wave refers to the sound wave (also known as "bone-conducted sound") that the mechanical vibration conducts to the user's cochlea through the bone and is perceived by the user, and the air-conducted sound wave refers to the mechanical vibration conducted to the cochlea through the air Sound waves perceived by the user through the user's cochlea (also known as "air conduction sound").

In some embodiments, the signal processing module 200 may include a signal processing unit 210 . The signal processing unit 210 can process the received electrical signal. For example, the signal processing unit 210 may perform frequency-based processing on electrical signals, and classify electrical signals in different frequency bands. For another example, the signal processing unit 210 may perform noise reduction processing on the electrical signal to remove noise in the electrical signal (eg, the electrical signal corresponding to the noise received by the signal input module 100 ). In some embodiments, the signal processing module 200 may further include at least one power amplifier 220 . The power amplifier 220 can amplify the received electrical signal. In some embodiments, the order in which the signal processing unit 210 and the power amplifier 220 process signals in the signal processing module 200 is not limited here. For example, in some embodiments, the signal processing unit 210 may first process the electrical signal output by the signal input module 100 into one or more signals, and then the power amplifier 220 amplifies the one or more signals to generate a control signal. In some alternative embodiments, the power amplifier 220 may amplify the electrical signal output by the signal input module 100 first, and the signal processing unit 210 then processes the amplified electrical signal to generate one or more control signals. In some embodiments, the signal processing unit 210 may be located between a plurality of power amplifiers 220 . For example, the power amplifier 220 may include a first power amplifier and a second power amplifier, the signal processing unit 210 is located between the first power amplifier and the second power amplifier, and the first power amplifier may first process the electrical signal output by the signal input module 100 After amplifying, the signal processing unit 210 performs processing based on the amplified electrical signal to generate one or more control signals, and the second power amplifier performs power method processing based on the one or more control signals. In other embodiments, the signal processing module 200 may only include the signal processing unit 210 instead of the power amplifier 220 . More descriptions about the signal processing module 200 can be found elsewhere in this application (for example, FIG. 2 and its related descriptions), and will not be repeated here.

At least one output transducer 300 may be configured to convert the control signal generated by the signal processing module 200 into bone-conducted sound waves and air-conducted sound waves that can be heard by the user's ears. In this application, a transducer refers to a component that can convert an electrical signal into a vibration signal.

In some embodiments, at least one output transducer 300 includes a bone-conducted vibration assembly. The bone conduction vibration component is attached to the user's face to transmit the vibration signal to the cochlea through the skull. At the same time, the vibration signal can cause the shell of the bone conduction vibration assembly to vibrate, generating air-conducted sound waves heard by the user's ears. In some embodiments, by designing the structure of the bone conduction vibration component and adjusting the processing methods of different modules in the signal processing module 200 for electrical signals, the air-conducted sound waves generated by the bone conduction vibration component can meet certain requirements, for example, In the target frequency range (for example, 200Hz-8000Hz), the air-conducted sound wave generated by the bone conduction vibration component is transmitted to the user's ear (the cochlea), so that the air-conducted sound heard by the user's ear when wearing the hearing aid device 10 is strong. The sound intensity of the air conduction sound heard by the ear when the hearing aid device 10 is not worn. That is to say, while the bone conduction vibration component generates bone conduction sound waves, it also amplifies the air conduction sound heard by the user, thereby achieving hearing compensation for the user through both bone conduction and air conduction. It should be noted that, when the user wears the hearing aid device 10 , the hearing aid device 10 can be regarded as being in the working state, and when the user is not wearing the hearing aid device 10 , the hearing aid device 10 can be regarded as being in the non-working state. For a specific description of the working state and the non-working state, reference may be made to FIG. 5 of the present application and its related contents, which will not be further limited here.

In some embodiments, at least one output transducer 300 includes a bone conduction vibration assembly and an air conduction vibration assembly. The air-conduction vibration component can convert the control signal generated by the signal processing module 200 into additional air-conduction sound waves, and further perform hearing compensation to the user in an air-conduction manner. Further descriptions of the output transducer 300 can be found elsewhere in this application (eg, FIG. 3 and its related descriptions), and will not be repeated here.

Fig. 2 is a block diagram of a signal processing unit provided according to some embodiments of the present application. As shown in FIG. 2 , in some embodiments, the signal processing unit 210 may include a frequency dividing module 211 , a high frequency signal processing module 212 and a low frequency signal processing module 213 . The frequency division module 211 can directly decompose the electrical signal into corresponding different frequency band components, for example, the frequency division module 211 can decompose the original sound into a high frequency band component and a low frequency band component. The high frequency signal processing module 212 can be coupled to the frequency division module 211 and is configured to generate a high frequency output signal (high frequency electrical signal) according to the high frequency band component; the low frequency signal processing module 213 can be coupled to the frequency division module 211 and is configured to The low-band components generate a low-frequency output signal (low-frequency electrical signal). In the embodiments of this specification, the high-frequency component may refer to a high-frequency electrical signal, and the low-frequency component may refer to a low-frequency electrical signal. Wherein, the high-frequency signal processing module 212 can process or adjust high-frequency electrical signals, and the low-frequency signal processing module 213 can process low-frequency electrical signals. In some embodiments, the high-frequency signal processing module 212 and the low-frequency signal processing module 213 may refer to equalizers, dynamic range controllers, or phase processors. It should be noted that, in other embodiments, the hearing aid device may only include the frequency dividing module 211, and whether the high frequency signal processing module 212 and the low frequency signal processing module 213 are installed can be determined according to actual conditions. In the embodiments of this specification, the low frequency can refer to the frequency band of generally 20Hz to 150Hz, the intermediate frequency can refer to the frequency band of generally 150Hz to 5kHz, the high frequency can refer to the frequency band of generally 5kHz to 20kHz, and the middle and low frequency It can refer to the frequency band from 150Hz to 500Hz in general, and the medium and high frequency refers to the frequency band from 500Hz to 5kHz. It should be noted that the division of the above frequency bands is only given as an example to give an approximate interval. The definition of the above frequency bands may vary with different industries, different application scenarios and different classification standards. For example, in some other application scenarios, the low frequency refers to the frequency band generally between 20Hz and 80Hz, the medium and low frequency refers to the frequency band between 80Hz and 160Hz, the intermediate frequency refers to the frequency range between 160Hz and 1280Hz, and the medium and high frequency refers to the general In the frequency band of 1280Hz-2560Hz, the high frequency band can generally refer to the frequency band from 2560Hz to 20kHz.

In some embodiments, the frequency division module 211 can also directly decompose the electrical signal into frequency components corresponding to multiple frequency bands, and at the same time, the signal processing unit 210 can include signal processing units corresponding to multiple frequency bands to obtain the frequency components corresponding to multiple frequency bands. frequency output signal. For example, the frequency division module 211 may decompose the electrical signal into one or more of low frequency components, mid frequency components, and high frequency components, or decompose the original sound into mid and low frequency components, mid and high frequency components, and the like.

In some embodiments, the signal processing module 200 may only include a frequency division module 211, and the frequency division module 211 may perform frequency division processing on the electrical signal output by the signal input module 100 to obtain electrical signals of various frequency bands (for example, low-frequency electrical signals, High-frequency electrical signals, etc.), and directly output to the power amplifier for amplification.

It should be known that the division method of the frequency division module 211 for the electrical signal can be performed according to the actual situation or the setting of the user, and is not limited to the above-described method. In some embodiments, the frequency division module may include several filters/filter banks to process the electrical signal to output control signals containing different frequency components, thereby controlling the output of air conduction sound or bone conduction sound respectively. In some embodiments, the filters/filter banks include, but are not limited to, analog filters, digital filters, passive filters, active filters, and the like.

In some embodiments, the signal input module 100 may perform frequency division processing on the initial sound in advance. For example, the signal input module 100 may include a high frequency microphone and a low frequency microphone. Among them, the high-frequency microphone can receive the high-frequency sound in the initial sound and convert the high-frequency sound into a high-frequency component, and the low-frequency microphone can receive the low-frequency sound in the initial sound and convert the low-frequency sound into a low-frequency component, so that the electrical signal is transmitted The frequency division processing is completed before the signal processing module 200 . In some embodiments, the signal processing unit 210 may further include a high-frequency signal processing module and a low-frequency signal processing module directly coupled to the signal input module 100, so as to generate corresponding high-frequency output signals and low-frequency signals according to the high-frequency components and low-frequency components, respectively. output signal.

In some embodiments, the signal processing unit 210 may only include a full-frequency signal processing module, and does not need to perform frequency division processing on the electrical signal input by the signal input module 100 . That is to say, the frequency dividing module 211 , the high frequency signal processing module 212 and the low frequency signal processing module 213 can be replaced by a full frequency signal processing module. The full-frequency signal processing module may include an equalizer, a dynamic range controller, a phase processor, and the like. Wherein, the equalizer can be configured to individually gain or attenuate the electrical signal according to a specific frequency band. Dynamic range controllers can be configured to compress and amplify electrical signals, for example, to make sounds sound softer or louder. The phase processor may be configured to adjust the phase of the electrical signal. In some embodiments, the electrical signal can be processed into an output signal via an equalizer, a dynamic range controller, or a phase processor. For example, in some scenarios, the user's ears may be more sensitive to air conduction sounds in certain frequency ranges (for example, low frequency, mid-low frequency, or high frequency), then the full-frequency signal processing module can be used to enhance the electrical signal in this frequency range, In order to make the output transducer 300 output air conduction sound with greater sound intensity in this frequency range. In other scenarios, the strong low-frequency bone-conducted sound waves may bring discomfort to the user, and the full-frequency signal processing module can be used to attenuate the low-frequency electrical signal to alleviate the uncomfortable feeling. Optionally, the full-frequency signal processing module can also appropriately enhance electrical signals in other frequency ranges other than the low frequency, so as to compensate for the attenuated low-frequency signal, and prevent the user from hearing a decrease in the overall sound intensity.

In some embodiments, the signal processing module 200 may further include at least one power amplifier 220 . The power amplifier 220 can amplify and generate a control signal based on the electrical signal output by the signal input module 100 or the electrical signal processed by the signal processing unit 210 (for example, a high-frequency output signal or a low-frequency output signal). In some embodiments, the signal processing module 200 may include two power amplifiers 220 . For example, the power amplifier may include a first power amplifier and a second power amplifier, wherein the first power amplifier is configured to amplify a high frequency output signal into a corresponding control signal, and the second power amplifier is configured to amplify a low frequency output signal into a corresponding control signal Signal. In some embodiments, when the frequency division module 211 can decompose the electrical signal into frequency components corresponding to multiple frequency bands, the signal processing module 200 can include multiple power amplifiers 220 to output frequency components corresponding to multiple frequency bands The signals are respectively amplified as control signals. In some embodiments, the power amplifier can also be used in conjunction with the above-mentioned full-frequency signal processing module to selectively amplify the sound in a specific frequency range in the initial sound, and finally deliver it to the user as bone-conducted sound waves and air-conducted sound waves.

Through the above-mentioned signal processing module 200, the hearing compensation effect of the hearing aid device can be enhanced. As an example only, when the hearing aid is a bone conduction hearing aid, the hearing aid can use an output transducer (eg, a vibrating speaker) to output full-range vibration or bone conduction sound to enable people to hear through bone conduction. In some cases, bone conduction hearing aids have a better sound compensation effect in a specific frequency range (eg, 200Hz-8000Hz). In some embodiments, in order to further highlight the sound compensation effect of the hearing aid device in the specific frequency range, the electrical signal in the specific frequency range may be amplified. In some embodiments, electrical signals outside the specific range (for example, 20Hz-200Hz, 8000Hz-20kHz) can be amplified, so that the hearing aid device can have a better sound compensation effect within the specific range , and ensure the sound compensation effect of other frequency bands, so that the sound compensation effect of the hearing aid device has better balance in the whole frequency band, and improves the user experience. In some embodiments, the output transducer of the hearing aid device generates corresponding air-conducted sound waves as well as bone-conducted sound waves. Air-conducted sound waves can be used as sound compensation in addition to bone-conducted sound waves in hearing aids. By performing power amplification processing on electrical signals in a specific frequency range, it is possible to increase the compensation amount of bone-conducted sound waves in this frequency band while additionally increasing air-conducted sound waves, thereby further improving the sound compensation effect of hearing aids. It should be noted that the above frequency range selected by the power amplifier is only used as an example, and those skilled in the art can adjust the corresponding frequency range of the power amplifier according to actual application conditions, which is not further limited here.

It should be noted that the signal processing unit 210 may not perform frequency division processing. Here, the signal processing unit 210 may not include the frequency division module 211 , the high frequency signal processing module 212 and the low frequency signal processing module 213 . In some embodiments, the signal processing unit 210 may process the electrical signal based on the time-frequency, frequency domain or sub-band of the electrical signal. In some embodiments, the signal processing unit 210 may include an equalizer, a dynamic range controller, a phase processor, a nonlinear processor, and the like. Wherein, the equalizer can be configured to individually gain or attenuate the electrical signal according to a specific frequency band. Dynamic range controllers can be configured to compress and amplify electrical signals, for example, to make sounds sound softer or louder. The phase processor may be configured to adjust the phase of the electrical signal. The non-linear processor can be configured to reduce noise signals in the electrical signal. In some embodiments, the electrical signal can be processed into an output signal through an equalizer, a dynamic range controller, a phase processor, or a nonlinear processor.

Fig. 3 is a schematic structural diagram of an output transducer provided according to some embodiments of the present application.

As shown in FIG. 3 , the output transducer 300 may include a first vibration assembly and a housing 350 . Wherein, the first vibration component can be electrically connected with the signal processing module 200 to receive the control signal generated by the signal processing module 200, and generate bone-conducted sound waves based on the control signal. Specifically, the first vibration component can perform mechanical vibration according to the control signal, and the mechanical vibration can generate bone-conducted sound waves. For example, the first vibration component can be any element (such as a vibration motor, electromagnetic vibration equipment, etc.) that converts an electrical signal (for example, a control signal from the signal processing module 200) into a mechanical vibration signal, wherein the signal conversion mode Including but not limited to: electromagnetic (moving coil, moving iron, magnetostrictive), piezoelectric, electrostatic, etc. The internal structure of the first vibrating component can be a single resonance system or a composite resonance system. When the user wears the hearing aid device, part of the structure of the first vibrating component can be attached to the skin of the user's head, so that bone-conducted sound waves are conducted to the user's cochlea via the user's skull. The housing 350 can be coupled with the first vibrating component and driven by the first vibrating component to generate air-conducted sound waves.

In some embodiments, the housing 350 can be connected to the first vibrating component through the connecting piece 330 . In some embodiments, the response of the shell 350 to the vibration of the first vibrating component can be adjusted by adjusting the connecting piece 330 between the shell 350 and the first vibrating component, that is, the vibration generated by the shell 350 can be adjusted by adjusting the connecting piece 330. The effect of air conducting sound waves. In some embodiments, connector 330 may be rigid or flexible. When the connecting member 330 is rigid, the connection between the housing 350 and the first vibrating component may be rigid. In other embodiments, the connecting member 330 may be an elastic member, such as a spring or a shrapnel.

In some embodiments, the first vibration component may include a magnetic circuit system 310 , a vibration plate 320 and a coil 340 . The magnetic circuit system 310 can be configured to generate a first magnetic field; the vibrating plate 320 can be connected to the housing 350 through the connecting piece 330 ; the coil 340 can be connected to the vibrating plate 320 and electrically connected to the signal processing module 200 . Specifically, the coil 340 can receive the control signal generated by the signal processing module 200 and generate a second magnetic field based on the control signal. Through the interaction between the first magnetic field and the second magnetic field, the coil 340 will be subjected to an active force F, thereby exciting the vibrating plate 320 to vibrate. , to generate bone-conducted sound waves in the user's face. In addition, the vibration of the vibrating plate 320 can drive the shell 350 to vibrate, thereby generating air-conducted sound waves. Specifically, in the middle and low frequency bands, the vibration amplitude of the housing 350 is greater than or equivalent to that of the vibrating plate 320. Since the housing 350 is not in direct contact with the skin, the vibration of the housing 350 cannot transmit sound through bone conduction, but the housing 350 The vibration can generate air-conducted sound waves, and conduct the eardrum through the path of the external auditory canal, allowing the user to hear the sound, thereby increasing the sound compensation effect. At the same time, since the vibration of the housing 350 is stronger than that of the vibrating plate 320 in the middle and low frequency bands, the smaller vibration amplitude of the vibrating plate 320 can effectively reduce the vibration of the user during use and improve comfort. In the higher frequency band, the vibration amplitude of the vibrating plate 320 is significantly greater than that of the housing 350, so that the first vibrating component can effectively transmit sound through the vibration of the vibrating plate 320 in a bone conduction manner; meanwhile, the vibration amplitude of the housing 350 is much smaller than that of the vibrating shell 350. The vibration of the plate 320 can effectively reduce the sound leakage of the shell 350 in the higher frequency band. In some embodiments, the frequency range and amplitude of sound transmitted through air conduction or bone conduction can be adjusted by adjusting the mass and elastic coefficient of each part of the first vibration component.

In some embodiments, the vibrating plate 320 and the housing 350 define a cavity, and the magnetic circuit system 310 is located in the cavity, and can be connected to the housing 350 through the connecting member 330 or other elastic members (not shown in FIG. 3 ). . Under the interaction with the coil 340, the magnetic circuit system 310 also generates corresponding vibrations. The vibration of the magnetic circuit system 310 relative to the housing 350 will push the air in the cavity to vibrate. In some embodiments, one or more sound guide holes are provided on the casing 350 to guide the air in the cavity out of the casing 350, and superimpose with the sound generated by the vibration of the casing 350 to jointly form the sound heard by the user's ears. Air conducts sound waves. The number, position, shape and/or size of the sound guide holes on the housing 350 need to meet certain conditions, so that the sound derived from the sound guide holes and the sound generated by the vibration of the housing 350 interfere and increase at the user's ear, thereby further Enhances the air conduction sound heard by the user.

As can be seen from FIG. 3 and its related descriptions, the bone-conducted sound wave is generated by the vibrating plate 320 of the output transducer 300 , and the air-conducted sound wave is generated by the housing 350 (or the sound guide hole on the housing 350 ). In some embodiments, the control signal includes different frequency components, and the vibration of the vibrating plate 320 based on the control signal may include vibrations of different frequencies. Therefore, the bone-conducted sound waves and the air-conducted sound waves emitted by the hearing aid device can cover different frequency ranges, so that the hearing aid device can provide certain sound compensation effects in different frequency ranges.

It should be known that since the vibrating plate 320 and the casing 350 respond differently to vibrations of different frequencies, the bone-conducted sound waves and air-conducted sound waves generated by them have different sound compensation effects at different frequencies. Taking air-conducted sound waves as an example, the vibration of the housing 350 can amplify the sound intensity of the air-conducted sound heard by the user within the target frequency range. That is, within the target frequency range, the air-conducted sound wave generated by the vibration of the casing 350 is transmitted to the user's ear, so that the sound intensity of the air-conducted sound heard by the user's ear is greater than the sound intensity of the initial sound received by the signal input module. The target frequency range is related to the structure of the casing 350 and the signal processing method of the signal processing module 200 . In some embodiments, the target frequency range may be 200Hz-8000Hz, or 500Hz-6000Hz, or 750Hz-1000Hz, or any other frequency range. It can be considered that the hearing aid device has a better sound compensation effect in the target frequency range. In some specific scenarios, the control signal corresponding to the target frequency range can be amplified more in the signal processing module 200, so as to further improve the sound compensation effect in the target frequency range. In other application scenarios, for example, when the frequency range of the sound received by the user is greater than the target frequency range, since the sound compensation effect of the hearing aid device in the target frequency range is more obvious, it can be more amplified at this time except for the target frequency range. Control the signal, so as to balance the hearing effect of the user in each frequency band, reduce the energy consumption of the hearing aid device at the same time, and ensure the use time of the hearing aid device.

For example, when amplifying the high-frequency electrical signal and the low-frequency electrical signal, the amplification degrees of the high-frequency electrical signal and the low-frequency electrical signal may be the same or different. For example, under the premise that the high-frequency sound compensation effect of the hearing aid device is better than that of the low-frequency sound compensation effect, the low-frequency electrical signal can be amplified, that is, the low-frequency output signal is stronger than the high-frequency output signal, so as to ensure that the hearing aid device works well in all frequency bands. It has a more balanced sound compensation effect. For another example, on the premise that the high-frequency sound compensation effect of the hearing aid device is better than that of the low-frequency sound compensation effect, in order to further highlight the hearing effect of the hearing aid device under the high-frequency output signal, the amplification degree of the high-frequency electrical signal can also be greater than that of the low-frequency band Amplification of electrical signals. In some embodiments, the same degree of amplification can also be performed on the electrical signals of the whole frequency band. It should be noted that, in some embodiments, the high frequency output signal or the low frequency output signal may be determined relative to the target frequency. For example, when the target frequency range is 20Hz-1000Hz, the low frequency can be the frequency range of 20Hz-100Hz, the frequency range of 20Hz-150Hz, the frequency range of 20Hz-200Hz, etc., and the high frequency can be the frequency range of 900Hz-1000Hz, 850Hz-1000Hz , 800Hz-1000Hz frequency band, etc. In some embodiments, the high frequency output signal and the low frequency output signal may also be determined relative to a full band of frequencies as described elsewhere in this application. In addition, the high-frequency output signal and the low-frequency output signal here are relative to each other, and those skilled in the art can make corresponding adjustments according to actual application scenarios, which are not further limited here.

In order to further illustrate the auditory effect of the hearing aid device in a certain frequency range (for example, 200 Hz-8000 Hz), the test results of the bone conduction component and the air conduction component of the hearing aid device are now described.

Fig. 4 is a frequency response graph of full-range force level (OFL ₆₀ ) output by a hearing aid device in a reference environment according to some embodiments of the present application. In the embodiment of this description, the reference environment may refer to the sound intensity value (also referred to as reference sound pressure level) received by the ear simulator of the artificial head when the hearing aid device is in a non-working state. OFL ₆₀ refers to the output force level of hearing aids under the condition that the reference sound pressure level is 60dB. For ease of description, the sound intensity value corresponding to the reference environment in the embodiments of this specification is 60 dB. It can be seen from Figure 4 that when the sound intensity of the reference environment is 60dB, the vibration force level of the bone conduction component output by the hearing aid device is above 76dB at frequencies between 250Hz and 8000Hz. When the frequency range is 250Hz-2000Hz, the vibration force level of the bone conduction component output by the hearing aid device is above 85dB. When the frequency range is 500Hz-1500Hz, the vibration force level of the bone conduction component output by the hearing aid device is above 90dB. When the frequency range is 750Hz-1000Hz, the vibration force level of the bone conduction component output by the hearing aid device is above 92dB. In some embodiments, for a sound with a certain reference sound pressure level (for example, 60dB), considering that the vibration force levels of bone conduction components at different frequencies are different, the signal processing module 200 can be used to perform different levels of electrical signals at different frequencies. enlarge. For example, since the vibration force level of the bone conduction component in the range of 1000Hz-1500Hz exceeds the vibration force level of other ranges, in order to further improve the bone conduction sound compensation effect of the hearing aid device, the signal processing module 200 can be more amplified in the range of 1000Hz-1500Hz Inner frequency components. Or, since the vibration force level of the bone conduction component at about 4000 Hz is smaller than that in other ranges, in order to balance the compensation effect of the bone conduction sound in each frequency range of the hearing aid device, the signal processing module 200 can be more amplified at about 4000 Hz frequency band components.

Fig. 5 is a frequency response diagram of the full-scale acoustic-mechanical sensitivity level (AMSL) of the bone conduction component output by the hearing aid device according to some embodiments of the present application. In the embodiments of this specification, the sound-force sensitivity level may refer to the difference between the full-scale force level and the reference sound pressure level, for example, the difference between OFL ₆₀ in FIG. 5 and the reference sound pressure level (eg, 60dB) . It can be seen from Figure 5 that when the reference sound pressure level of the hearing aid device is 60dB and the frequency range is 250Hz-8000Hz, the sound-force sensitivity level of the bone conduction component is above 15dB. When the frequency range is 250Hz-2000Hz, the sound-force sensitivity level of the bone conduction component is above 25dB. When the frequency range is 500Hz-1500Hz, the sound-force sensitivity level of the bone conduction component is above 30dB. When the frequency range is 750Hz-1000Hz, the sound-force sensitivity level of the bone conduction component is above 32dB. In some embodiments, for a sound with a certain sound intensity (for example, 60dB), considering that the acoustic-force sensitivity levels of the bone conduction components of different frequencies (or frequency bands) are different, the signal processing module 200 can be used for electrical signals of different frequencies. different levels of magnification. For example, since the sound-force sensitivity level of the bone conduction component in the range of 1000Hz-1500Hz exceeds the sound-force sensitivity level of other ranges, in order to further improve the bone conduction sound compensation effect of the hearing aid device, the signal processing module 200 can be amplified more Frequency band components in the range of 1000Hz-1500Hz. Or, since the sound-force sensitivity level of the bone conduction component around 8000 Hz is smaller than that of other ranges, in order to balance the compensation effect of the bone conduction sound in each frequency range of the hearing aid device, the signal processing module 200 can be made more Amplify the frequency band components around 8000Hz. It should be noted that the sound intensity value corresponding to the reference environment in the embodiments of this specification is not limited to the above-mentioned 60dB, and the sound intensity value corresponding to the reference environment here is set to 60dB for illustrative purposes only. The corresponding sound intensity value can be adaptively adjusted according to the actual situation, which is not further limited here.

In some embodiments, the output to the air conduction component of the hearing assistance device may be tested using an artificial head with an ear simulator. Among them, what the ear simulator measures is only the output of the air conduction component. When testing the output of air conduction components, single-frequency tones (for example, 250Hz, 500Hz, 750Hz, 1000Hz, 1500Hz, 2000Hz, 3000Hz, 4000Hz, 6000Hz) of a specific sound pressure level (for example, a reference sound pressure level of 60dB) can be used , 8000Hz) as the test sound source for testing. During the test, an artificial head with an ear simulator can be placed at the test point without wearing a hearing aid, and then the test sound source is turned on to obtain the sound pressure level (air conduction) measured by the ear simulator under this condition. component output), which can also be called "non-working state" sound pressure level; in addition, the hearing aid device can be placed on the artificial head according to the actual wearing method in use, and when the test sound source is turned on, the hearing aid can be obtained. The sound pressure level measured by the simulator in this situation can also be called the "working state" sound pressure level, where the gain of the air conduction component of the hearing aid device is the "working state" sound pressure level and the "non-working state" difference in sound pressure level. In some embodiments, the test point can be selected at 1.5m directly in front of the test sound source, while the artificial head and face are facing the direction of the test sound source. It should be noted that the above-mentioned method of air conduction sound pressure test for hearing aids is only for illustration, and those skilled in the art can make adaptive adjustments to the experimental method according to the actual situation.

By testing the output of the air conduction component of the hearing aid device, the sound pressure level diagram and the gain diagram of the hearing aid device in the working state and non-working state at the reference sound pressure level can be obtained. Specifically, Fig. 6 is a sound pressure level diagram of the air conduction component output by the hearing aid device according to some embodiments of the present application in the reference environment; Fig. 7 is a hearing aid device provided according to some embodiments of the present application in the reference environment Gain plot of the output air conduction component in the environment. In the embodiment of this specification, the gain of the output air conduction component may refer to the difference between the sound pressure level of the hearing aid device outputting the air conduction component in the working state and the sound pressure level of the non-working state outputting the air conduction component at each frequency . As shown in Figure 6 and Figure 7, when the hearing aid device is in the non-working state, when the frequency range is 250Hz-8000Hz and the reference sound pressure level is 60dB, the sound pressure of the air conduction component measured by the ear simulator inside the artificial head The level is roughly 60dB, that is, the sound pressure level of the air conduction component measured by the ear simulator inside the artificial head is basically equal to the sound pressure level of the test sound source. When the hearing aid device is in working condition, when the frequency range is 250Hz-6000Hz, the sound pressure level of the air conduction component measured by the ear simulator inside the artificial head is greater than 60dB, and when the frequency range is 6000Hz-8000Hz, the artificial head The sound pressure level of the air conduction component measured by the bone simulator inside the head is roughly 60dB. From this, it can be concluded that when the hearing aid device is in working condition and the frequency range is 250Hz-6000Hz, the hearing aid device can produce a difference from The air conduction sound wave of the test sound source can generate a sound intensity higher than that of the test sound source, thereby improving the air conduction hearing compensation effect of the hearing aid device. In some embodiments, for a sound with a certain sound intensity (for example, 60dBSPL), considering that the gains of air conduction components at different frequencies are different, the signal processing module 200 can be used to perform different degrees of electrical signal processing at different frequencies (or frequency bands). enlarge. For example, since the gain of the air conduction component around 750 Hz exceeds the gain of other ranges, in order to further improve the air conduction sound compensation effect of the hearing aid device, the signal processing module 200 can be made to amplify the frequency band components in the range of 750 Hz more. Or, since the gain of the air conduction component above 6000 Hz is smaller than that of other ranges, in order to balance the compensation effect of the air conduction sound of the hearing aid device in each frequency range, the signal processing module 200 can be made to amplify the frequency band components above 6000 Hz more.

Combining the contents of Figures 4-7, in a specific frequency range, the bone-conducted sound waves and air-conducted sound waves output by the hearing aid device have a better hearing compensation effect. For example, when the frequency range is 250 Hz-8000 Hz, the bone-conducted sound wave output by the hearing aid device has a better gain effect relative to the reference sound pressure level. For another example, when the frequency range is 250 Hz-6000 Hz, the air-conducted sound wave output by the hearing aid device has a better gain effect relative to the reference sound pressure level (eg, 60 dBSPL). To sum up, it can be known that the hearing aid device has better bone conduction gain and air conduction gain in the target frequency range. In some embodiments, the target frequency range is 200Hz-8000Hz. Preferably, the target frequency range is 500Hz-6000Hz. More preferably, the target frequency range is 750Hz-1000Hz. It should be noted that the sound compensation effect of the hearing aid device in terms of bone-conducted sound waves and/or air-conducted sound waves can be improved by adjusting the frequency range. For example, at 250Hz-500Hz, the sound compensation effect of the hearing aid device on bone-conducted sound waves is better, but the sound compensation effect of the hearing aid device on air-conducted sound waves in this frequency band is poor, and the power amplifier 220 can be used here. The electrical signal is amplified to enhance the sound compensation effect of the hearing aid device in terms of bone-conducted sound waves in this frequency band. For another example, at 3000Hz-4000Hz, the sound compensation effect of the hearing aid device in the air-conducted sound wave is better, but in this frequency band, the sound compensation effect of the hearing aid device in the bone-conducted sound wave is poor. Here, the power amplifier 220 can be used for this frequency band. The electrical signal is amplified to enhance the sound compensation effect of the hearing aid device in terms of air-conducted sound waves in this frequency band. For another example, at 750Hz-1500Hz, the sound compensation effect of the hearing aid device on air-conducted sound waves and bone-conducted sound waves is relatively good. Here, the electric signal in this frequency band can be amplified by the power amplifier 220 to enhance the hearing aid device in this frequency band. The sound compensation effect of bone-conducted sound waves and air-conducted sound waves to highlight the sound compensation effect of hearing aids in this frequency band. In other embodiments, in order to ensure the balanced listening effect of the hearing aid device in each frequency band, power amplification processing may be performed on signals in frequency bands other than 750 Hz-1500 Hz. In other embodiments, the quality and elastic coefficient of each part of the first vibrating component (for example, the magnetic circuit system 310, the vibrating plate 320, and the connecting piece 330) can also be adjusted to adjust the sound transmission rate through air conduction or bone conduction. frequency range and amplitude.

In some further embodiments, in order to improve the compensation effect of the hearing aid device on air-conducted sound waves, an additional vibrating component may be provided in the hearing aid device. Referring again to FIG. 3 , in some embodiments, the hearing aid device 10 may further include at least one second vibrating component (not shown in the figure), which is configured to generate additional air-conducted sound waves within the target frequency range, so The additional air-conducted sound waves can further enhance the sound intensity of the air-conducted sound heard by the user's ears.

In some embodiments, the at least one second vibrating component can be a diaphragm structure (for example, a passive diaphragm), and is connected to the housing 350, so that the vibration of the first vibrating component can excite the diaphragm structure to generate additional air Conduct sound waves. Specifically, when the vibrating plate 320 of the output transducer vibrates to generate bone-conducted sound waves, it will also drive the air inside the housing 350 to vibrate and act on the diaphragm structure, and the diaphragm structure vibrates with the vibration of the air inside the housing 350, As a result, additional air-conducted sound waves are generated, and the additional air-conducted sound waves are radiated to the outside through at least one sound outlet provided on the casing 350 . The additional air-conducted sound waves can be transmitted to the user's ears together with the air-conducted sound waves generated by the vibration of the shell 350, further increasing the sound intensity of the air-conducted sound received by the user.

In some embodiments, the second vibration component may be an air-conducted speaker configured to generate additional air-conducted sound waves according to the control signal. The additional air-conducted sound waves emitted by the air-conducted speaker can also be radiated to the outside through at least one sound outlet provided on the casing 350 . In some embodiments, when the user wears the hearing aid device, at least one sound outlet is close to the ear of the human body. In some embodiments, the control signal controlling the air conduction speaker may be the same or different than the control signal controlling the output transducer. For example, when the control signal controlling the air conduction speaker is the same as the control signal controlling the output transducer, the air conduction speaker can supplement the hearing aid device with sound waves in the same frequency range as the output transducer, thereby enhancing the hearing effect in that frequency range . For another example, when the control signal for controlling the air-conduction speaker is different from the control signal for controlling the output transducer, the air-conduction speaker can supplement the hearing aid device with sound waves in a different frequency range from that of the output transducer, thereby compensating for the hearing aid device's sound waves in other frequency ranges. Hearing effects in the frequency range.

In some embodiments, the assistive hearing device may further include a fixed structure configured to carry the assistive hearing device such that the assistive hearing device (shaded area in FIG. 8 ) may be positioned on the user's head as shown in FIG. 8 . Mastoid 1, temporal bone 2, parietal bone 3, frontal bone 4, auricle 5, concha concha 6 or the vicinity of the ear canal (not shown in the figure). In other embodiments, the hearing aid device may also be located in other areas of the user's head, which is not further limited here.

In some embodiments, the hearing assistance device can be combined with glasses, headphones, head-mounted display devices, AR/VR helmets, etc., in which case, the fixed structure can be used as a part of the above products (for example, connectors). The hearing aid device can be fixed near the user's ear in a hanging or clamping manner. In some alternative embodiments, the fixing structure may be a hook, and the shape of the hook matches the shape of the auricle, so that the hearing aid device can be independently worn on the user's ear through the hook. A hearing aid device worn independently can communicate with a signal source (eg, a computer, a mobile phone or other mobile devices) in a wired or wireless (eg, Bluetooth) manner. For example, the hearing aids at the left and right ears may both communicate directly with the signal source in a wireless manner. For another example, the hearing aids at the left and right ears may include a first output device and a second output device, wherein the first output device may communicate with the signal source, and the second output device may be wirelessly connected to the first output device , Synchronization of audio playback is implemented between the first output device and the second output device through one or more synchronization signals. The way of wireless connection may include but not limited to Bluetooth, local area network, wide area network, wireless personal area network, near field communication, etc. or any combination thereof.

In some embodiments, the fixing structure can be a shell structure with a shape suitable for the human ear, such as circular, elliptical, polygonal (regular or irregular), U-shaped, V-shaped, semicircular, so that the fixed structure It can be directly attached to the user's ear. In some embodiments, the fixing structure may include ear hooks, head beams or elastic bands, etc., so that the hearing aid device can be better fixed on the user and prevent the user from falling during use. For example only, the elastic band may be a headband that may be configured to be worn around the head region. In some embodiments, the elastic band can be a continuous ribbon, and can be elastically stretched to be worn on the user's head, and at the same time, the elastic band can also apply pressure to the user's head, so that the hearing aid device is firmly fixed. Fixed to a specific position on the user's head. In some embodiments, the elastic band may be a discontinuous strip. For example, the elastic band may include a rigid part and a flexible part, wherein the rigid part may be made of a rigid material (eg, plastic or metal), and the rigid part may be physically connected to the housing of the hearing aid device (eg, snap fit, thread connection, etc.) to fix. The flexible portion may be made of elastic material (eg, cloth, composite, or/and neoprene).

The basic concept has been described above, obviously, for those skilled in the art, the above detailed disclosure is only an example, and does not constitute a limitation to the present application. Although not expressly stated here, various modifications, improvements and amendments to this application may be made by those skilled in the art. Such modifications, improvements, and amendments are suggested in this application, so such modifications, improvements, and amendments still belong to the spirit and scope of the exemplary embodiments of this application.

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

In addition, those skilled in the art will understand that various aspects of the present application may be illustrated and described in several patentable categories or circumstances, including any new and useful process, machine, product or combination of substances, or any combination of them Any new and useful improvements. Correspondingly, various aspects of the present application may be entirely executed by hardware, may be entirely executed by software (including firmware, resident software, microcode, etc.), or may be executed by a combination of hardware and software. The above hardware or software may be referred to as "block", "module", "engine", "unit", "component" or "system". Additionally, aspects of the present application may be embodied as a computer product comprising computer readable program code on one or more computer readable media.

A computer storage medium may contain a propagated data signal embodying a computer program code, for example, in baseband or as part of a carrier wave. The propagated signal may have various manifestations, including electromagnetic form, optical form, etc., or a suitable combination. A computer storage medium may be any computer-readable medium, other than a computer-readable storage medium, that can be used to communicate, propagate, or transfer a program for use by being coupled to an instruction execution system, apparatus, or device. Program code residing on a computer storage medium may be transmitted over any suitable medium, including radio, electrical cable, fiber optic cable, RF, or the like, or combinations of any of the foregoing.

The computer program codes required for the operation of each part of this application can be written in any one or more programming languages, including object-oriented programming languages such as Java, Scala, Smalltalk, Eiffel, JADE, Emerald, C++, C#, VB.NET, Python etc., conventional procedural programming languages such as C language, Visual Basic, Fortran 2003, Perl, COBOL 2002, PHP, ABAP, dynamic programming languages such as Python, Ruby and Groovy, or other programming languages, etc. The program code may run entirely on the user's computer, or as a stand-alone software package, or run partly on the user's computer and partly on a remote computer, or entirely on the remote computer or server. In the latter case, the remote computer can be connected to the user computer through any form of network, such as a local area network (LAN) or wide area network (WAN), or to an external computer (such as through the Internet), or in a cloud computing environment, or as a service Use software as a service (SaaS).

In addition, unless explicitly stated in the claims, the order of processing elements and sequences described in the application, the use of numbers and letters, or the use of other designations are not used to limit the order of the flow and methods of the application. While the foregoing disclosure has discussed by way of various examples some embodiments of the invention that are presently believed to be useful, it should be understood that such detail is for illustrative purposes only and that the appended claims are not limited to the disclosed embodiments, but rather, the claims The claims are intended to cover all modifications and equivalent combinations that fall within the spirit and scope of the embodiments of the application. For example, although the system components described above may be implemented by hardware devices, they may also be implemented by a software-only solution, such as installing the described system on an existing server or mobile device.

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

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

The entire contents of each patent, patent application, patent application publication, and other material, such as article, book, specification, publication, document, etc., cited in this application are hereby incorporated by reference into this application. Application history documents that are inconsistent with or conflict with the content of this application are excluded, as are documents (currently or hereafter appended to this application) that limit the broadest scope of the claims of this application. It should be noted that if there is any inconsistency or conflict between the descriptions, definitions, and/or terms used in the attached materials of this application and the contents of this application, the descriptions, definitions and/or terms used in this application shall prevail .

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

Claims (10)

1. A hearing aid device, characterized in that it comprises: a signal input module configured to receive an initial sound and convert the initial sound into an electrical signal; a signal processing module configured to process the electrical signal and generate a control signal; and at least one output transducer configured to convert the control signal into bone-conducted sound waves of the user and air-conducted sound waves audible to the user's ears; The output transducers include: a first vibration component, electrically connected to the signal processing module to receive the control signal, and generate the bone-conducted sound wave based on the control signal; and a casing, coupled to the first vibration component, and driven by the first vibration component to generate the air-conducted sound wave; Wherein, the air-conducted sound wave generated by the hearing aid device is superimposed on the bone-conducted sound wave, so that the listening sound perceived by the user's ear is stronger than the sound intensity of the initial sound received by the signal input module. 2. The hearing aid device according to claim 1, wherein the housing is rigidly connected to the first vibrating component. 3. The hearing aid device according to claim 1, wherein the housing is connected to the first vibrating component through an elastic member. 4. The hearing aid device according to claim 1, wherein the first vibrating component comprises: a magnetic circuit system configured to generate a first magnetic field; a vibrating plate connected to the housing; and a coil, connected to the vibrating plate and electrically connected to the signal processing module, the coil receives the control signal and generates a second magnetic field based on the control signal, and the first magnetic field interacts with the second magnetic field , so that the vibrating plate generates the bone-conducted sound waves. 5. The hearing aid device according to claim 4, wherein the vibrating plate and the housing define a cavity, the magnetic circuit system is located in the cavity, and the magnetic circuit system passes through the elastic member connected to the housing. 6. The hearing aid device according to claim 1, wherein the vibration output force level corresponding to the bone-conducted sound wave is greater than 55 dB. 7. The hearing aid device of claim 1, wherein the output transducer further comprises a second vibration assembly configured to generate an additional air-conducted sound wave, the additional air-conducted sound wave The sound waves amplify the intensity of the air conduction sound heard by the user's ears. 8. The hearing aid device according to claim 7, wherein the second vibrating component is a diaphragm structure, the diaphragm structure is connected to the housing, and the output transducer excites the vibrating The membrane structure generates the additional air-conducted sound waves. 9. The hearing aid device according to claim 7, wherein the second vibrating component is an air-conduction speaker configured to generate the additional air-conduction sound wave according to the control signal. 10. The hearing aid device according to claim 1, wherein the hearing aid device further comprises a fixed structure configured to carry the hearing aid device so that the hearing aid device is positioned on the head of the user. mastoid, temporal bone, parietal bone, frontal bone, pinna, ear canal, or concha.

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