hearing aids

Abstract

To provide a hearing aid that improves the effect of hearing compensation.SOLUTION: A hearing aid 10 includes a signal input module 100 that receives an initial sound and converts the initial sound into an electrical signal, a signal processing module 200 that processes the electrical signal to generate a control signal, and at least one output transducer 300 that converts the control signal into user's bone-conducted sound waves and air-conducted sound waves that can be heard by user's ears. The sound intensity of the air-conducted sound audible to the user's ear is within a target frequency range. The air-conducted sound wave is transmitted to the user's ear, so that it is higher than the sound intensity of the initial sound received by the signal input module.SELECTED DRAWING: Figure 1

Description

[Technical Field]

[0001] This application relates to the field of acoustics, and in particular to hearing aids. [Background technology]

[0002] Conventional hearing aids typically provide users with hearing compensation through bone conduction or air conduction. In some hearing aids (e.g., hearing aids), bone conduction sound transmission can cause the generated vibration signal to be insufficient in some frequency bands due to the performance of the bone conduction vibrator, resulting in less than ideal hearing compensation results. Furthermore, for conductive hearing-loss sufferers, conventional air conduction hearing aids can experience large differences in air conduction sound thresholds in some frequency bands, making it difficult to provide hearing compensation through air conduction. When users need to hear sounds across a wide frequency range or multiple frequency bands, these problems can result in a poor listening experience. Summary of the Invention [Problem to be solved by the invention]

[0003] Therefore, it is desirable to provide a hearing aid device that performs hearing compensation using a combination of bone conduction and air conduction methods, which can improve the hearing compensation effect in a specific frequency band of the user. [Means for solving the problem]

[0004] A hearing assistance device according to one embodiment of the present application 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 to generate a control signal, and at least one output transducer configured to convert the control signal into a user's bone-conducted sound wave and an air-conducted sound wave heard by the user's ear, wherein within a target frequency range, the air-conducted sound waves are transmitted to the user's ear, so that the sound intensity of the air-conducted sound heard by the user's ear is higher than the sound intensity of the initial sound received by the signal input module.

[0005] In some embodiments, the target frequency range is between 200 Hz and 8000 Hz.

[0006] In some embodiments, the target frequency range is between 500 Hz and 6000 Hz.

[0007] In some embodiments, the target frequency range is between 750 Hz and 1000 Hz.

[0008] In some embodiments, the signal processing module includes a signal processing unit including a frequency division module configured to divide the electrical signal into high-frequency band components and low-frequency band components, a high-frequency signal processing module coupled to the frequency division module and configured to generate a high-frequency output signal based on the high-frequency band components, and a low-frequency signal processing module coupled to the frequency division module and configured to generate a low-frequency output signal based on the low-frequency components.

[0009] In some embodiments, the electrical signal includes a high-frequency output signal corresponding to a high-frequency band component of the initial sound and a low-frequency output signal corresponding to a low-frequency band component of the initial sound, and the signal processing unit includes a high-frequency signal processing module configured to generate the high-frequency output signal based on the high-frequency band component, and a low-frequency signal processing module configured to generate the low-frequency output signal based on the low-frequency band component.

[0010] In some embodiments, the signal processing module further comprises a power amplifier configured to amplify the high frequency output signal or the low frequency output signal into the control signal.

[0011] In some embodiments, the output transducer includes a first vibrating component electrically connected to the signal processing module to receive the control signal and generate the bone-conducted sound waves based on the control signal, and a housing coupled to the first vibrating component to generate the air-conducted sound waves upon driving the first vibrating component.

[0012] In some embodiments, the connection between the housing and the first vibrating component is a rigid connection.

[0013] In some embodiments, the housing and the first vibrating component are connected to the first vibrating component by a resilient member.

[0014] In some embodiments, the first vibrating component includes a magnetic circuit system configured to generate a first magnetic field, a diaphragm connected to the housing, and a coil connected to the diaphragm, electrically connected to the signal processing module, receiving the control signal, and generating a second magnetic field based on the control signal, wherein the interaction between the first magnetic field and the second magnetic field causes the diaphragm to generate the bone conduction sound waves.

[0015] In some embodiments, the diaphragm and the housing define a cavity, the magnetic circuit system is located within the cavity, and the magnetic circuit system is connected to the housing by an elastic member.

[0016] In some embodiments, the vibration output force level corresponding to the bone-conducted sound waves is greater than 55 dB.

[0017] In some embodiments, the hearing aid device further includes at least one second vibrating component configured to generate additional air-conducted sound waves, which, in a target frequency range, increase the sound intensity of the air-conducted sound heard by the user's ear.

[0018] In some embodiments, the at least one second vibrating component is a vibrating membrane structure connected to the housing, and the at least one output transducer excites the vibrating membrane structure to generate the additional air-conducted sound waves.

[0019] In some embodiments, the at least one second vibratory component is an air-conducted speaker configured to generate the additional air-conducted sound waves based on the control signal.

[0020] In some embodiments, the hearing aid device further includes a fixation structure configured to mount the hearing aid device so that the hearing aid device is positioned on the mastoid process, temporal bone, parietal bone, frontal bone, pinna, within the ear canal or concha of the user's head. [Effects of the Invention]

[0021] An auditory assistance device according to one embodiment of the present application includes a signal input module configured to receive initial sound and convert the initial sound into an electrical signal, a signal processing module configured to process the electrical signal to generate a control signal, and at least one output transducer configured to convert the control signal into a user's bone-conducted sound waves and air-conducted sound waves heard by the user's ear, wherein the auditory assistance device includes an operating state and a non-operating state, generates the air-conducted sound waves in the operating state and does not generate the air-conducted sound waves in the non-operating state, and within a target frequency range, the sound intensity of the air-conducted sound heard by the user's ear in the operating state is higher than the sound intensity of the air-conducted sound heard by the user's ear in the non-operating state.

[0022] The present application will be further illustrated by exemplary embodiments, which are not limiting and are illustrated in detail in the drawings, in which like numerals refer to like structures. [Brief explanation of the drawings]

[0023] [Figure 1] 1 is an exemplary block diagram of a hearing aid device according to some embodiments of the present application; [Figure 2] FIG. 2 is a block diagram of a signal processing unit according to some embodiments of the present application. [Figure 3] FIG. 1 is a schematic diagram of an output transducer according to some embodiments of the present application. [Figure 4] FIG. 10 is a frequency response diagram of the maximum force level (OFL60) of the bone conduction component output from a hearing aid device according to some embodiments of the present application in a reference sound environment. [Figure 5] FIG. 1 is a frequency response diagram of the maximum sound-power sensitivity level (AMSL) of the bone-conducted component output from a hearing aid according to some embodiments of the present application in a reference environment. [Figure 6] FIG. 10 is a diagram illustrating the sound pressure level of the air conduction component output from the hearing aid device shown in some embodiments of the present application in a reference environment. [Figure 7] FIG. 10 is a gain diagram of the air conduction component output from a hearing aid device according to some embodiments of the present application in a reference environment. [Figure 8] 1 is a diagram showing the position distribution of hearing aids according to some embodiments of the present application when worn; DETAILED DESCRIPTION OF THE INVENTION

[0024] In order to more clearly describe the technical means of the embodiments of the present application, the following will briefly describe the drawings necessary for describing the embodiments. Obviously, the drawings described below are only some examples or embodiments of the present application, and those skilled in the art can apply the present application to other similar scenarios based on these drawings without any creative effort. Unless otherwise clear from the language environment or otherwise described, the same numbers in the drawings indicate the same structures or operations.

[0025] It should be understood that the terms "system," "device," "unit," and / or "module" used herein are ways of distinguishing between various levels of assemblies, elements, parts, portions, or assemblies, however, other terms may be used in place of the above terms if they achieve the same purpose.

[0026] As used in this application and the claims, unless the context clearly dictates otherwise, terms such as "a," "one," "one kind," and / or "the" do not specifically refer to the singular but may also include the plural. In general, the terms "comprise" and "containing" are intended to indicate only the inclusion of explicitly identified steps and elements, and these steps and elements are not an exclusive listing; a method or apparatus may also include other steps or elements.

[0027] In the field of hearing aids, hearing compensation for hearing loss is typically achieved using air conduction hearing aids or bone conduction hearing aids. Conventional air conduction speakers compensate for hearing loss by amplifying air conduction sound signals. However, for conductive hearing loss, there may be large differences in air conduction sound thresholds in some frequency bands, making it difficult to compensate for hearing loss using air conduction sound. Bone conduction hearing aids compensate for hearing loss by converting sound signals into vibration signals (bone conduction sound). However, bone conduction hearing aids are subject to performance issues, such as insufficient vibration signals in some frequency bands, making it difficult to achieve ideal compensation results. Furthermore, excessive vibrations in some frequency bands can cause discomfort to users.

[0028] To improve the hearing compensation effect of a hearing aid device, the hearing aid device according to the present application provides hearing compensation to a user simultaneously through bone conduction and air conduction. In some embodiments, the hearing aid device may include a signal input module, a signal processing module, and at least one output transducer. 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 to generate a control signal, and the at least one output transducer is configured to convert the control signal into a bone-conducted sound wave and an air-conducted sound wave heard by the user's ear. Within a target frequency range (e.g., 200 Hz to 8000 Hz), the air-conducted sound waves are transmitted to the user's ear, so that the sound intensity of the air-conducted sound heard by the user's ear is higher than the sound intensity of the initial sound received by the signal input module. In this case, the air-conducted sound waves generated by the hearing aid device are superimposed on the bone-conducted sound waves, thereby increasing the sound intensity of the sound perceived by the user's ear, thereby improving the hearing compensation effect of the hearing aid device.

[0029] In some embodiments, the bone-conducted sound waves and air-conducted sound waves may be generated by the same output transducer (e.g., a bone-conducted vibration component). The output transducer converts a control signal into air-conducted sound waves audible to the user's ear, which may be understood as the housing of the hearing aid device generating air-conducted sound waves (which may also be referred to as leakage sound from the hearing aid device) by driving the output transducer. The housing of the hearing aid device may further include a sound guide hole that meets certain conditions. The sound guide hole can conduct sound within the housing of the hearing aid device, and the sound can be superimposed with leakage sound due to vibration of the housing to jointly form air-conducted sound waves audible to the user's ear.

[0030] In some embodiments, the hearing aid device may 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 bone conduction sound waves and the air conduction sound waves may be generated by the bone conduction vibration component and the air conduction vibration component, respectively. During use, the signal processing module processes the electrical signals for generating the air conduction sound waves and the electrical signals for generating the bone conduction sound waves according to actual conditions, so as to meet different hearing compensation needs of different hearing-impaired individuals or the same hearing-impaired individual in different environments.

[0031] 1 is an exemplary block diagram of a hearing aid device 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.

[0032] Signal input module 100 is configured to receive initial sound and convert the received initial sound into an electrical signal. In some embodiments, signal input module 100 may include microphone 110 or / and audio interface 120. In some embodiments, 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 there are multiple microphones 110, the type of microphones 110 may be one or more. In some embodiments, the initial sound may include sound transmitted from the external environment to signal input module 100 via air conduction. For example, microphone 110 may convert collected air vibrations into an analog signal (electrical signal). Audio interface 120 is configured to receive the digital or analog signal from 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, signal input module 100 may directly receive electrical signals transmitted in a wired or wireless manner. For example, audio interface 120 may receive any digital or analog signal corresponding to audio from an external device in a wired or wireless manner.

[0033] The signal processing module 200 may be configured to process the electrical signal input by the signal input module 100 to generate a control signal. The control signal controls the bone-conducted sound waves and / or air-conducted sound waves output by the output transducer 300. In the embodiments herein, bone-conducted sound waves refer to sound waves in which mechanical vibrations are conducted through bone to the user's cochlea and perceived by the user (also referred to as "bone-conducted sound"), and air-conducted sound waves refer to sound waves in which mechanical vibrations are conducted through air to the user's cochlea and perceived by the user (also referred to as "air-conducted sound").

[0034] In some embodiments, the signal processing module 200 may include a signal processing unit 210. The signal processing unit 210 may process the received electrical signal. For example, the signal processing unit 210 may perform frequency-based processing on the electrical signal to classify the electrical signal in different frequency bands. For example, the signal processing unit 210 may perform noise reduction processing on the electrical signal to remove noise in the electrical signal (e.g., 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 may amplify the received electrical signal. In some embodiments, the order in which the signal processing unit 210 and the power amplifier 220 process the signals in the signal processing module 200 is not limited. For example, in some embodiments, the signal processing unit 210 may process the electrical signal output by the signal input module 100 into one or more signals, and then the power amplifier 220 may amplify 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, and then the signal processing unit 210 may process the amplified electrical signal to generate one or more control signals. In some embodiments, the signal processing unit 210 may be located between multiple power amplifiers 220. For example, the power amplifier 220 may include a first power amplifier and a second power amplifier, and the signal processing unit 210 may be located between the first power amplifier and the second power amplifier. The first power amplifier may amplify the electrical signal output by the signal input module 100, then the signal processing unit 210 may process the amplified electrical signal to generate one or more control signals, and then the second power amplifier may perform power method processing based on the one or more control signals. In other embodiments, the signal processing module 200 may include only the signal processing unit 210 and not the power amplifier 220. A more detailed description of the signal processing module 200 can be found elsewhere in this application (e.g., FIG. 2 and its related descriptions), and therefore will not be repeated here.

[0035] At least one output transducer 300 may be configured to convert the control signals generated by the signal processing module 200 into bone-conducted sound waves and air-conducted sound waves that are heard by the user's ear. As used herein, a transducer refers to a component that can convert an electrical signal into a vibration signal.

[0036] In some embodiments, at least one output transducer 300 includes a bone-conduction vibration component. The bone-conduction vibration component fits to the user's face and transmits a vibration signal to the cochlea through the skull. At the same time, the vibration signal vibrates the housing of the bone-conduction vibration component, generating air-conducted sound waves that are heard by the user's ear. In some embodiments, by designing the structure of the bone-conduction vibration component and adjusting the electrical signal processing methods of different modules of the signal processing module 200, the air-conducted sound waves generated by the bone-conduction vibration component can meet certain requirements. For example, within a target frequency range (e.g., 200 Hz to 8000 Hz), the air-conducted sound waves generated by the bone-conduction vibration component are transmitted to the user's ear (cochlea) so that the sound intensity of the air-conducted sound heard by the user when wearing the hearing aid 10 is higher than the sound intensity of the air-conducted sound heard by the user when not wearing the hearing aid 10. In other words, the bone conduction vibration component generates bone conduction sound waves and amplifies the air conduction sound heard by the user, thereby simultaneously providing the user with hearing compensation through both bone conduction and air conduction. When the user is wearing the hearing aid 10, the hearing aid 10 may be considered to be in an operating state, and when the user is not wearing the hearing aid 10, the hearing aid 10 may be considered to be in a non-operating state. For a detailed description of the operating and non-operating states, please refer to Figure 5 and related content of the present application, and no further limitations will be provided here.

[0037] In some embodiments, at least one output transducer 300 includes a bone conduction vibration component and an air conduction vibration component, which converts the control signal generated by the signal processing module 200 into additional air-conducted sound waves, and can further provide hearing compensation to the user in an air conduction manner. A more detailed description of the output transducer 300 can be found elsewhere in this application (e.g., FIG. 3 and related descriptions), and therefore will not be repeated here.

[0038] 2 is a block diagram of a signal processing unit 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 division module 211, a high-frequency signal processing module 212, and a low-frequency signal processing module 213. The frequency division module 211 can directly divide an electrical signal into corresponding different frequency band components. For example, the frequency division module 211 can divide an initial sound into high-frequency band components and low-frequency band components. The high-frequency signal processing module 212 is coupled to the frequency division module 211 and configured to generate a high-frequency output signal (high-frequency electrical signal) based on the high-frequency band components. The low-frequency signal processing module 213 is coupled to the frequency division module 211 and configured to generate a low-frequency output signal (low-frequency electrical signal) based on the low-frequency band components. In embodiments of the present application, the high-frequency components may refer to high-frequency electrical signals, and the low-frequency components may refer to low-frequency electrical signals. The high-frequency signal processing module 212 can process or condition 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 can be equalizers, dynamic range controllers, phase processors, etc. In other embodiments, the hearing aid device may only include the frequency division module 211, and whether the high-frequency signal processing module 212 and the low-frequency signal processing module 213 are installed may be determined based on actual conditions. In the embodiments herein, the low frequency may refer to a frequency range of approximately 20 Hz to 150 Hz, the mid frequency may refer to a frequency range of approximately 150 Hz to 5 kHz, the high frequency band may refer to a frequency range of approximately 5 kHz to 20 kHz, the mid-low frequency may refer to a frequency range of approximately 150 Hz to 500 Hz, and the mid-high frequency may refer to a frequency range of 500 Hz to 5 kHz. It should be noted that the above frequency band classification is merely an example for providing a range, and the definition of the above frequency band can be changed according to different industries, different application scenarios, and different classification standards.For example, in some other application scenarios, low frequency may refer to a frequency band of approximately 20 Hz to 80 Hz, mid-low frequency may refer to a frequency band of approximately 80 Hz to 160 Hz, mid frequency may refer to a frequency band of approximately 160 Hz to 1280 Hz, mid-high frequency may refer to a frequency band of approximately 1280 Hz to 2560 Hz, and high frequency band may refer to a frequency band of approximately 2560 Hz to 20 kHz.

[0039] In some embodiments, the frequency division module 211 can also directly divide the electrical signal into frequency components corresponding to multiple frequency bands, and at the same time, the signal processing unit 210 may include signal processing units corresponding to multiple frequency bands, so as to obtain frequency output signals corresponding to multiple frequency bands. For example, the frequency division module 211 can divide the electrical signal into one or more of a low frequency band component, a mid frequency band component, and a high frequency band component, or divide the initial sound into a mid-low frequency band component, a mid-high frequency band component, etc.

[0040] In some embodiments, the signal processing module 200 may only include a frequency division module 211, which can perform frequency division processing on the electrical signal output by the signal input module 100 to obtain electrical signals of each frequency band (e.g., low-frequency electrical signals, high-frequency electrical signals, etc.), and then directly output them to a power amplifier for amplification.

[0041] It should be noted that the division of the electrical signal by the frequency division module 211 may be performed according to actual conditions or user settings, and is not limited to the manner described above. In some embodiments, the frequency division module may process the electrical signal to output a control signal including different frequency components, and further include several filters / filter groups to respectively control the output of air-conducted sound or bone-conducted sound. In some embodiments, the filters / filter groups include, but are not limited to, analog filters, digital filters, passive filters, active filters, etc.

[0042] In some embodiments, the signal input module 100 may perform frequency division processing on the initial sound beforehand. For example, the signal input module 100 may include a high-frequency microphone and a low-frequency microphone. The high-frequency microphone can receive high-frequency audio of the initial sound and convert the high-frequency audio into high-frequency components, and the low-frequency microphone can receive low-frequency audio of the initial sound and convert the low-frequency audio into low-frequency components, so that the frequency division processing is completed before the electrical signal is transmitted to the signal processing module 200. In some embodiments, the signal processing unit 210 may also include a high-frequency signal processing module and a low-frequency signal processing module directly coupled to the signal input module 100 to generate corresponding high-frequency output signals and low-frequency output signals based on the high-frequency components and low-frequency components, respectively.

[0043] In some embodiments, the signal processing unit 210 may include only a full-frequency signal processing module, and frequency division processing is not required for the electrical signal input by the signal input module 100. That is, the frequency division module 211, the high-frequency signal processing module 212, and the low-frequency signal processing module 213 can be replaced with a full-frequency signal processing module. The full-frequency signal processing module may include an equalizer, a dynamic range controller, a phase processor, etc. The equalizer may be configured to apply individual gain or attenuation to the electrical signal according to a specific frequency band. The dynamic range controller may be configured to compress and amplify the electrical signal, for example, so that a voice sounds softer or louder. The phase processor may be configured to adjust the phase of the electrical signal. In some embodiments, the electrical signal may be processed through the equalizer, the dynamic range controller, and the phase processor to become an output signal. For example, in some scenes, the user's ears may be more sensitive to air-conducted sounds in certain frequency ranges (e.g., low frequencies, low-mid frequencies, or high frequencies), so the output transducer 300 outputs air-conducted sounds with higher sound intensity within those frequency ranges by emphasizing the electrical signals in those frequency ranges using the full-frequency signal processing module. In other scenes, strong bone-conducted sound waves in low frequencies may cause discomfort to the user, so the full-frequency signal processing module attenuates the low-frequency electrical signals to alleviate such discomfort. Preferably, the full-frequency signal processing module further appropriately emphasizes electrical signals in other frequency ranges than low frequencies to compensate for the attenuated low-frequency signals and avoid a decrease in the overall sound intensity of the sounds heard by the user.

[0044] In some embodiments, the signal processing module 200 may further include at least one power amplifier 220. The power amplifier 220 may 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 (e.g., 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, where the first power amplifier is configured to amplify the high-frequency output signal into a corresponding control signal, and the second power amplifier amplifies the low-frequency output signal into a corresponding control signal. In some embodiments, when the frequency division module 211 can divide the electrical signal into frequency components corresponding to multiple frequency bands, the signal processing module 200 may include multiple power amplifiers 220 to amplify output signals corresponding to frequency components corresponding to multiple frequency bands, respectively, into control signals. In some embodiments, a power amplifier may be used in combination with the full frequency signal processing module to selectively amplify specific frequency ranges of the initial sound for final transmission to the user via bone-conducted and air-conducted sound waves.

[0045] The signal processing module 200 can improve the hearing compensation effect of a hearing aid. For illustrative purposes only, if the hearing aid is a bone conduction hearing aid, the hearing aid can output vibration or bone-conducted sound across the entire frequency range using an output transducer (e.g., a vibration speaker) to provide human hearing through bone conduction. In some cases, the bone conduction hearing aid has a high sound compensation effect within a specific frequency range (e.g., 200 Hz to 8000 Hz). In some embodiments, an amplification process can be applied to electrical signals within the specific frequency range to further enhance the sound compensation effect of the hearing aid in the specific frequency range. In some embodiments, an amplification process can be applied to electrical signals outside the specific frequency range (e.g., 20 Hz to 200 Hz, 8000 Hz to 20 kHz). In this way, the hearing aid can achieve a high sound compensation effect within the specific range while also ensuring sound compensation effects in other frequency bands. This allows the sound compensation effect of the hearing aid to have good uniformity across all frequencies, improving the user experience. In some embodiments, the output transducer of the hearing aid device generates bone-conducted sound waves and corresponding air-conducted sound waves. The air-conducted sound waves may be used to compensate for sounds other than bone-conducted sound waves in the hearing aid device. By power amplifying the electrical signal in a specific frequency range, the amount of bone-conducted sound waves in that frequency range can be improved and the air-conducted sound waves can be additionally increased, thereby further improving the sound compensation effect of the hearing aid device. Note that the frequency ranges selected for power amplification are merely exemplary. Those skilled in the art can adjust the frequency ranges corresponding to power amplification according to actual application situations, and no further limitations are provided herein.

[0046] It should be noted that the signal processing unit 210 may not perform frequency division processing, and in this case, 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 subbands 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, etc. The equalizer may be configured to apply individual gain or attenuation to the electrical signal according to a specific frequency band. The dynamic range controller may be configured to compress and amplify the electrical signal, for example, so that a voice sounds softer or louder. The phase processor may be configured to adjust the phase of the electrical signal. The nonlinear processor may be configured to reduce noise signals in the electrical signal. In some embodiments, the electrical signal may be processed to become an output signal via the equalizer, the dynamic range controller, the phase processor, and the nonlinear processor.

[0047] FIG. 3 is a schematic diagram of an output transducer according to some embodiments of the present application.

[0048] As shown in FIG. 3 , the output transducer 300 may include a first vibrating component and a housing 350. The first vibrating component is electrically connected to the signal processing module 200 to receive a control signal generated by the signal processing module 200 and generate bone-conducted sound waves based on the control signal. Specifically, the first vibrating component can generate mechanical vibrations based on the control signal, which can generate bone-conducted sound waves. For example, the first vibrating component may be any element (e.g., a vibration motor, an electromagnetic vibrating device, etc.) that converts an electrical signal (e.g., a control signal from the signal processing module 200) into a mechanical vibration signal. The signal conversion method may include, but is not limited to, electromagnetic (moving coil, moving iron, magnetostrictive), piezoelectric, electrostatic, etc. The internal structure of the first vibrating component may be a single resonance system or a multi-resonance system. When a user wears the hearing aid device, a portion of the first vibrating component fits against the skin of the user's head, thereby conducting bone-conducted sound waves to the user's cochlea through the user's skull. The housing 350 is coupled to a first vibrating component, and is capable of generating air-conducted sound waves upon activation of the first vibrating component.

[0049] In some embodiments, housing 350 may be connected to the first vibrating component by connecting member 330. In some embodiments, adjusting connecting member 330 between housing 350 and the first vibrating component can adjust the response of housing 350 to the vibration of the first vibrating component, i.e., adjusting connecting member 330 adjusts the effectiveness of housing 350 in generating air-conducted sound waves. In some embodiments, connecting member 330 may be rigid or flexible. If connecting member 330 is rigid, the connection between housing 350 and the first vibrating component may be a rigid connection. In other embodiments, connecting member 330 may be an elastic member, such as a spring or a dome.

[0050] In some embodiments, the first vibration component may include a magnetic circuit system 310, a diaphragm 320, and a coil 340. The magnetic circuit system 310 may be configured to generate a first magnetic field, the diaphragm 320 may be connected to the housing 350 by a connecting member 330, and the coil 340 may be connected to the diaphragm 320 and electrically connected to the signal processing module 200. Specifically, the coil 340 receives a control signal generated by the signal processing module 200 and generates a second magnetic field based on the control signal, and the first magnetic field and the second magnetic field interact with each other, causing the coil 340 to receive a biasing force F, thereby exciting the diaphragm 320 to vibrate and generate bone-conducted sound waves at the user's face. In addition, the vibration of the diaphragm 320 can drive the housing 350 to vibrate, thereby generating air-conducted sound waves. Specifically, in the mid-low frequency band, the vibration amplitude of the housing 350 is greater than or equal to the vibration amplitude of the diaphragm 320. Because the housing 350 does not directly contact the skin, the vibration of the housing 350 cannot transmit sound via bone conduction. However, the vibration of the housing 350 generates air-conducted sound waves, which are transmitted to the eardrum via the ear canal so that the user can hear the sound, thereby improving the sound compensation effect. At the same time, because the vibration sensation of the housing 350 is stronger than that of the diaphragm 320 in the mid-low frequency band, a small vibration amplitude of the diaphragm 320 can effectively reduce the vibration sensation during use and improve comfort. In the high frequency band, the vibration amplitude of the diaphragm 320 is significantly greater than that of the housing 350. Thus, the first vibrating component can effectively transmit sound via bone conduction through the vibration of the diaphragm 320. At the same time, because the vibration amplitude of the housing 350 is much smaller than that of the diaphragm 320, the leakage sound from the housing 350 in the high frequency band can be effectively reduced. In some embodiments, the frequency range and width over which sound is transmitted by air or bone conduction can be adjusted by adjusting the mass and elastic modulus of each portion of the first vibrating component.

[0051] In some embodiments, the diaphragm 320 and the housing 350 define a cavity, and the magnetic circuit system 310 is positioned within the cavity and connected to the housing 350 by a connecting member 330 or other elastic member (not shown in FIG. 3 ). Under 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 promotes air vibration within the cavity. In some embodiments, when one or more sound guide holes are formed in the housing 350, the air within the cavity can be guided out of the housing 350 and superimposed with the sound generated by the vibration of the housing 350 to jointly form air-conducted sound waves audible to the user's ear. The number, position, shape, and / or size of the sound guide holes in the housing 350 can satisfy certain conditions so that the sound transmitted through the sound guide holes and the sound generated by the vibration of the housing 350 interfere with and enhance each other at the user's ear, thereby further enhancing the air-conducted sound heard by the user.

[0052] 3 and its associated description, bone-conducted sound waves are generated by the diaphragm 320 of the output transducer 300, and air-conducted sound waves are generated by the housing 350 (or the sound-guiding holes in the housing 350). In some embodiments, the control signal may include different frequency components, and the vibration of the diaphragm 320 based on the control signal may include vibrations of different frequencies. Therefore, the bone-conducted sound waves and air-conducted sound waves generated by the hearing aid device cover different frequency ranges, allowing the hearing aid device to provide consistent sound compensation effects within the different frequency ranges.

[0053] Furthermore, because the diaphragm 320 and the housing 350 respond differently to vibrations of different frequencies, the sound compensation effects provided by the generated bone-conducted sound waves and air-conducted sound waves differ. Taking air-conducted sound waves as an example, the vibration of the housing 350 can increase the sound intensity of air-conducted sound heard by the user within a target frequency range. That is, within the target frequency range, the air-conducted sound waves generated by the vibration of the housing 350 are transmitted to the user's ear, and the sound intensity of the air-conducted sound heard by the user's ear is higher than the sound intensity of the initial sound received by the signal input module. The target frequency range depends on the structure of the housing 350 and the signal processing method used by the signal processing module 200. In some embodiments, the target frequency range may be 200 Hz to 8000 Hz, 500 Hz to 6000 Hz, 750 Hz to 1000 Hz, or any other frequency range. The hearing aid device can be considered to have a high sound compensation effect within the target frequency range. In some specific scenarios, the sound compensation effect within the target frequency range can be further improved by amplifying the control signal corresponding to the target frequency range in signal processing module 200. In other application scenarios, for example, when the frequency range of the sound received by the user is wider than the target frequency range, the sound compensation effect of the hearing aid device within the target frequency range is obvious. In this case, by amplifying the control signal outside the target frequency range more, the hearing effect of the user in each frequency band can be made uniform, while also reducing the energy consumption of the hearing aid device and ensuring the usage time of the hearing aid device.

[0054] For example, when amplifying high-frequency and low-frequency electrical signals, the amplification levels of the high-frequency and low-frequency electrical signals may be the same or different. For example, under the premise that the high-frequency sound compensation effect of the hearing aid device is higher than the low-frequency sound compensation effect, the low-frequency electrical signals may be amplified, i.e., the low-frequency output signals may be stronger than the high-frequency output signals, thereby ensuring that the hearing aid device has a uniform sound compensation effect across the entire frequency band. Also, under the premise that the high-frequency sound compensation effect of the hearing aid device is higher than the low-frequency sound compensation effect, the amplification level of the high-frequency electrical signals may be greater than the amplification level of the low-frequency electrical signals to further enhance the hearing effect of the hearing aid device with the high-frequency output signals. In some embodiments, the same level of amplification may be applied to all frequency bands of electrical signals. Note that in some embodiments, the high-frequency output signals or the low-frequency output signals may be determined relative to a target frequency. For example, if the target frequency range is 20 Hz to 1000 Hz, the low frequency may be a frequency band of 20 Hz to 100 Hz, a frequency band of 20 Hz to 150 Hz, a frequency band of 20 Hz to 200 Hz, etc., and the high frequency may be a frequency band of 900 Hz to 1000 Hz, a frequency band of 850 Hz to 1000 Hz, a frequency band of 800 Hz to 1000 Hz, etc. In some embodiments, the high frequency output signal and the low frequency output signal may be determined for the entire frequency band as described elsewhere herein. Furthermore, the high frequency output signal and the low frequency output signal herein are described in terms of both, and those skilled in the art can adjust them according to the actual application scenario, so no further limitations are provided here.

[0055] To further explain the hearing effect of the hearing aid device within a certain frequency range (for example, 200 Hz to 8000 Hz), the following describes the test results of the hearing aid device in combination with the bone conduction component and the air conduction component.

[0056] FIG. 4 shows the maximum force level (OFL) output from a hearing aid according to some embodiments of the present application in a reference environment. 60) Frequency response diagram. In the examples of the present specification, the reference environment may be the sound intensity value (also called reference sound pressure level) received by the ear simulator of the artificial head when the hearing aid is in an inoperative state. 60 is the output power level of the hearing aid device under the condition that the reference sound pressure level is 60 dB. For ease of explanation, the sound intensity value corresponding to the reference environment in the examples of this specification is set to 60 dB. As can be seen from FIG. 4, when the sound intensity of the sound in the reference environment is 60 dB, the vibration power levels of the bone conduction components output by the hearing aid device are all 76 dB or higher in the frequency range of 250 Hz to 8000 Hz. When the frequency range is 250 Hz to 2000 Hz, the vibration power levels of the bone conduction components output by the hearing aid device are all 85 dB or higher. When the frequency range is 500 Hz to 1500 Hz, the vibration power levels of the bone conduction components output by the hearing aid device are all 90 dB or higher. When the frequency range is 750 Hz to 1000 Hz, the vibration power levels of the bone conduction components output by the hearing aid device are all 92 dB or higher. In some embodiments, signal processing module 200 may amplify electrical signals of different frequencies to different degrees, taking into account that the vibration power levels of bone conduction components at different frequencies vary for a given reference sound pressure level (e.g., 60 dB). For example, because the vibration power level of bone conduction components in the 1000 Hz to 1500 Hz range exceeds the vibration power levels in other ranges, signal processing module 200 may amplify frequency band components in the 1000 Hz to 1500 Hz range more to further improve the bone conduction sound compensation effect of the hearing aid device. Alternatively, because the vibration power level of bone conduction components at approximately 4000 Hz is smaller than the vibration power levels in other ranges, signal processing module 200 may amplify frequency band components in the approximately 4000 Hz range more to uniformly compensate for bone conduction sound in each frequency range of the hearing aid device.

[0057] 5 is a frequency response diagram of the maximum sound-force sensitivity level (AMSL) of the bone-conducted component output from a hearing aid according to some embodiments of the present application. In the embodiments of the present application, the sound-force sensitivity level is the difference between the maximum force level and the reference sound pressure level, e.g., OFL in FIG. 60 and a reference sound pressure level (e.g., 60 dB). As can be seen from FIG. 5, when the reference sound pressure level of the hearing aid is 60 dB and the frequency range is 250 Hz to 8000 Hz, the sound-force sensitivity levels of the bone conduction components are 15 dB or higher. When the frequency range is 250 Hz to 2000 Hz, the sound-force sensitivity levels of the bone conduction components are all 25 dB or higher. When the frequency range is 500 Hz to 1500 Hz, the sound-force sensitivity levels of the bone conduction components are all 30 dB or higher. When the frequency range is 750 Hz to 1000 Hz, the sound-force sensitivity levels of the bone conduction components are all 32 dB or higher. In some embodiments, considering that the sound-force sensitivity levels of the bone conduction components of different frequencies (or frequency bands) differ for sound of a certain sound intensity (e.g., 60 dB), the signal processing module 200 can amplify electrical signals of different frequencies to different degrees. For example, because the sound-force sensitivity level of the bone-conduction component in the 1000 Hz to 1500 Hz range exceeds the sound-force sensitivity levels in other ranges, the signal processing module 200 can amplify the frequency band components in the 1000 Hz to 1500 Hz range more to further improve the bone-conduction sound compensation effect of the hearing aid device. Alternatively, because the sound-force sensitivity level of the bone-conduction component at approximately 8000 Hz is lower than the sound-force sensitivity levels in other ranges, the signal processing module 200 can amplify the frequency band components at approximately 8000 Hz more to uniformly compensate the bone-conduction sound in each frequency range of the hearing aid device. Note that the sound intensity value corresponding to the reference environment in the embodiments of this specification is not limited to the above 60 dB. Setting the sound intensity value corresponding to the reference environment here to 60 dB is merely for illustrative purposes. In other embodiments, the sound intensity value corresponding to the reference environment can be adaptively adjusted according to actual conditions, and no further limitations are provided herein.

[0058] In some embodiments, the air conduction component output of the hearing prosthesis can be tested using an artificial head with an ear simulator. Only the air conduction component output is tested against the ear simulator. When testing the air conduction component output, a single frequency sound (e.g., 250 Hz, 500 Hz, 750 Hz, 1000 Hz, 1500 Hz, 2000 Hz, 3000 Hz, 4000 Hz, 6000 Hz, 8000 Hz) at a specific sound pressure level (e.g., a reference sound pressure level of 60 dB) can be used as the test sound source. During testing, an artificial head with an ear simulator is placed at a test point without wearing a hearing aid. The test sound source is then activated, and the sound pressure level (air conduction component output) measured at the ear simulator in this state is obtained. This may also be referred to as the "non-operating state" sound pressure level. Additionally, the hearing aid is placed on the artificial head according to the actual wearing style, and the test sound source is activated. This sound pressure level measured at the ear simulator in this state is obtained. This may also be referred to as the "operating state" sound pressure level. The gain of the air conduction component of the hearing aid is the difference between the "operating state" sound pressure level and the "non-operating state" sound pressure level. In some embodiments, the test point is set 1.5 m away from the test sound source, and the face of the artificial head is positioned directly in the direction of the test sound source. Note that the above-described method for testing air conduction sound pressure of a hearing aid is merely illustrative, and those skilled in the art can adapt the experimental method to suit actual conditions.

[0059] By testing the output of the air conduction component of a hearing aid device, sound pressure level diagrams and gain diagrams can be obtained for the operating and non-operating states of the hearing aid device at a reference sound pressure level. Specifically, FIG. 6 is a sound pressure level diagram of the air conduction component output from a hearing aid device described in some embodiments of the present application in a reference environment, and FIG. 7 is a gain diagram of the air conduction component output from a hearing aid device according to some embodiments of the present application in a reference environment. In the embodiments of the present application, the gain of the output air conduction component may be the difference between the sound pressure level of the air conduction component output by the hearing aid device in the operating state and the sound pressure level of the air conduction component output by the hearing aid device in the non-operating state at each frequency. As shown in FIGS. 6 and 7, when the hearing aid device is in the non-operating state, in the frequency range of 250 Hz to 8000 Hz, and the reference sound pressure level is 60 dB, the sound pressure level of the air conduction component measured by the ear simulator inside the artificial head is approximately 60 dB. That is, the sound pressure level of the air conduction component measured by the ear simulator inside the artificial head is essentially equal to the sound pressure level of the test sound source. When the hearing prosthesis is in operation and the frequency range is 250 Hz to 6000 Hz, the sound pressure levels of the air-conducted components measured at the ear simulator inside the artificial head are all greater than 60 dB, and when the frequency range is 6000 Hz to 8000 Hz, the sound pressure level of the air-conducted components measured at the bone simulator inside the artificial head is approximately 60 dB. Therefore, when the hearing prosthesis is in operation and the frequency range is 250 Hz to 6000 Hz, the hearing prosthesis can generate air-conducted sound waves that are different from the test sound source, and the air-conducted sound waves can generate higher sound intensities than the test sound source, thereby improving the air-conducted hearing compensation effect of the hearing prosthesis. In some embodiments, signal processing module 200 can amplify electrical signals of different frequencies (or frequency bands) to different degrees, taking into account that the gains of air-conducted components of different frequencies are different for a given sound intensity (e.g., 60 dB SPL). For example, since the gain of the air conduction component at approximately 750 Hz exceeds the gain in other ranges, the signal processing module 200 can amplify the frequency band components within the 750 Hz range more to further improve the air conduction sound compensation effect of the hearing aid device.Alternatively, since the gain of the air conduction components above 6000 Hz is smaller than the gain in other ranges, the signal processing module 200 can amplify the frequency band components above 6000 Hz more to equalize the compensation effect of the air conduction sound in each frequency range of the hearing aid device.

[0060] Combining the details shown in FIGS. 4 to 7, it can be seen that in a specific frequency range, bone-conducted sound waves and air-conducted sound waves output by the hearing aid device have a high hearing compensation effect. For example, in a frequency range of 250 Hz to 8000 Hz, bone-conducted sound waves output by the hearing aid device have a high gain effect relative to a reference sound pressure level. For example, in a frequency range of 250 Hz to 6000 Hz, air-conducted sound waves output by the hearing aid device have a high gain effect relative to a reference sound pressure level (e.g., 60 dB SPL). From the above, it can be seen that the hearing aid device has high bone-conducted gain and air-conducted gain within the target frequency range. In some embodiments, the target frequency range is 200 Hz to 8000 Hz. Preferably, the target frequency range is 500 Hz to 6000 Hz. More preferably, the target frequency range is 750 Hz to 1000 Hz. Adjusting the frequency range can improve the sound compensation effect of the hearing aid device for bone-conducted sound waves and / or air-conducted sound waves. For example, in the frequency range from 250 Hz to 500 Hz, the hearing aid device's sound compensation effect for bone-conducted sound waves is high, but in this frequency range, the hearing aid device's sound compensation effect for air-conducted sound waves is low. In this case, power amplifier 220 can be used to power amplify the electrical signal in that frequency range to improve the hearing aid device's sound compensation effect for bone-conducted sound waves in that frequency range. Also, in the frequency range from 3000 Hz to 4000 Hz, the hearing aid device's sound compensation effect for air-conducted sound waves is high, but in this frequency range, the hearing aid device's sound compensation effect for bone-conducted sound waves is low. In this case, power amplifier 220 can be used to amplify the electrical signal in that frequency range to improve the hearing aid device's sound compensation effect for air-conducted sound waves in that frequency range. Furthermore, for example, in the range of 750 Hz to 1500 Hz, the hearing aid device has a high sound compensation effect for both air-conducted sound waves and bone-conducted sound waves. In this case, the power amplifier 220 can amplify the electrical signal in this frequency band to improve the sound compensation effect of the hearing aid device for bone-conducted sound waves and air-conducted sound waves in this frequency band, thereby emphasizing the sound compensation effect of the hearing aid device in this frequency band.In another embodiment, to ensure uniformity of the listening experience in each frequency band of the hearing aid device, power amplification processing can be performed on signals in a frequency band other than 750 Hz to 1500 Hz. In another embodiment, the frequency range and width in which sound is transmitted by air conduction or bone conduction can be adjusted by adjusting the mass and elastic modulus of each part of the first vibration component (e.g., magnetic circuit system 310, diaphragm 320, connection member 330).

[0061] In some further embodiments, the hearing prosthesis may include additional vibrating components to improve the compensation effect of the air-conducted sound waves in the hearing prosthesis. Referring again to Figure 3, in some embodiments, the hearing prosthesis 10 may further include at least one second vibrating component (not shown) configured to generate additional air-conducted sound waves that further increase the sound intensity of the air-conducted sound heard by the user's ear within a target frequency range.

[0062] In some embodiments, the at least one second vibrating component may be a vibrating membrane structure (e.g., a passive vibrating membrane) and may be connected to the housing 350 so that the vibration of the first vibrating component excites the vibrating membrane structure to generate additional air-conducted sound waves. Specifically, when the diaphragm 320 of the output transducer vibrates to generate bone-conducted sound waves, it drives the vibration of the air inside the housing 350 to act on the vibrating membrane structure, and the vibrating membrane structure vibrates in response to the vibration of the air inside the housing 350, thereby generating additional air-conducted sound waves, which are then emitted to the outside through at least one sound emission hole provided in the housing 350. The additional air-conducted sound waves can be transmitted to the user's ear together with the air-conducted sound waves generated by the vibration of the housing 350, thereby further increasing the sound intensity of the air-conducted sound received by the user.

[0063] In some embodiments, the second vibrating component may be an air conduction speaker configured to generate additional air conduction sound waves based on a control signal. The additional air conduction sound waves generated by the air conduction speaker may be emitted to the outside through at least one sound emission hole provided in the housing 350. In some embodiments, the at least one sound emission hole is proximate to the ear of the user when the hearing aid is worn by the user. In some embodiments, the control signal controlling the air conduction speaker may be the same as or different from the control signal controlling the output transducer. For example, if the control signal controlling the air conduction speaker is the same as the control signal controlling the output transducer, the air conduction speaker can enhance the hearing effect in the same frequency range as the output transducer by supplementing the hearing aid with sound waves in that frequency range. For example, if the control signal controlling the air conduction speaker is different from the control signal controlling the output transducer, the air conduction speaker can enhance the hearing effect in another frequency range of the hearing aid by supplementing the hearing aid with sound waves in a different frequency range than the output transducer.

[0064] In some embodiments, the hearing aid device may further include a fixation structure configured to mount the hearing aid device such that the hearing aid device (shaded area in FIG. 8 ) is positioned on the mastoid process 1, temporal bone 2, parietal bone 3, frontal bone 4, pinna 5, concha 6, or within the ear canal (not shown) of the user's head as shown in FIG. 8. In other embodiments, the hearing aid device may be positioned on other areas of the user's head, without further limitation herein.

[0065] In some embodiments, the hearing aid device may be combined with a product such as glasses, headphones, a head-mounted display, or an AR / VR helmet. In this case, the securing structure may be a component (e.g., a connecting member) of the product. The hearing aid device may be secured near the user's ear by a hanging or clamping mechanism. In some alternative embodiments, the securing structure may be a hook, and the shape of the hook may conform to the shape of the pinna, allowing the hearing aid device to be independently attached to the user's ear by the hook. The independently worn hearing aid device may be communicatively connected to a signal source (e.g., a computer, a mobile phone, or another mobile device) via a wired or wireless (e.g., Bluetooth®) mechanism. For example, both the left and right hearing aid devices may be directly communicatively connected to the signal source via a wireless mechanism. For example, the left and right hearing aid devices may include a first output device and a second output device, where the first output device is communicatively connected to the signal source and the second output device is wirelessly connected to the first output device via a wireless mechanism, and the first output device and the second output device synchronize audio playback via one or more synchronization signals. The wireless connection method includes, but is not limited to, Bluetooth, a local area network, a wide area network, a wireless personal area network, near field communication, etc., or any combination thereof.

[0066] In some embodiments, the securing structure may be a housing structure having a shape that conforms to the human ear, such as a ring, ellipse, polygon (regular or irregular), U-shape, V-shape, or semicircle, so that it can be directly attached to the user's ear. In some embodiments, the securing structure may include an ear hook, a head beam, or an elastic band to better secure the hearing prosthesis to the user and prevent it from falling off during use. Simply by way of example, the elastic band may be a headband configured to be worn around a head region. In some embodiments, the elastic band may be a continuous band that can be elastically stretched and attached to the user's head, simultaneously applying pressure to the user's head to securely secure the hearing prosthesis to a specific position on the user's head. In some embodiments, the elastic band may be a discontinuous band. For example, the elastic band may include a rigid portion and a flexible portion, and the rigid portion may be made of a rigid material (e.g., plastic or metal) and may be secured to the housing of the hearing prosthesis by a physical connection (e.g., a lock, a screw connection, etc.). The flexible portion may be made of an elastic material (eg, fabric, composite material or / and chloroprene rubber).

[0067] Although the basic concepts have been described above, it will be apparent to those skilled in the art that the detailed disclosure above has been presented by way of example only and is not intended to limit the present application. Although not expressly described herein, those skilled in the art may make various changes, improvements, and modifications to the present application. These changes, improvements, and modifications are intended to be suggested by the present application and are therefore within the spirit and scope of the exemplary embodiments of the present application.

[0068] Furthermore, certain terms are used herein to describe embodiments of the present application. For example, "one embodiment," "one embodiment," and / or "some embodiments" refer to particular features, structures, or characteristics associated with at least one embodiment of the present application. Therefore, it is emphasized and understood that references to "one embodiment" or "one embodiment" or "one alternative embodiment" more than once in various parts of this specification do not necessarily all refer to the same embodiment. Furthermore, particular features, structures, or characteristics of one or more embodiments of the present application may be combined as appropriate.

[0069] Additionally, as will be appreciated by those skilled in the art, aspects of the present application may be illustrated and described in several patentable classes or contexts, including any new and useful process, machine, manufacture, or combination of matter, or any new and useful improvement thereto. Accordingly, aspects of the present application may be implemented entirely in hardware, entirely in software (including firmware, resident software, microcode, etc.), or a combination of hardware and software. Such hardware or software may be referred to as a "data block," "module," "engine," "unit," "assembly," or "system." Additionally, aspects of the present application may take the form of a computer program product embodied in one or more computer-readable medium(s) containing computer-readable program code.

[0070] A computer storage medium may include a propagated data signal, propagated in baseband or as part of a carrier wave, for carrying computer program code. The propagated signal may take various forms, such as an electromagnetic signal, an optical signal, or a suitable combination. A computer storage medium may be any computer-readable medium other than a computer-readable storage medium, which can be coupled to an instruction execution system, device, or apparatus to enable communication, propagation, or transmission of a program used therein. The program code on a computer storage medium may be transmitted via any suitable medium, including wireless, cable, fiber optic cable, RF, or similar media, or any combination of the above media.

[0071] Computer program code necessary for the operation of portions of this application may be coded in one or more programming languages, including object-oriented programming languages ​​such as Java, Scala, Smalltalk, Eiffel, JADE, Emerald, C++, C#, VB.NET, Python, etc.; traditional procedural programming languages ​​such as C, Visual Basic, Fortran 2003, Perl, COBOL 2002, PHP, ABAP, etc.; dynamic programming languages ​​such as Python, Ruby, and Groovy, or other programming languages. The program code may run entirely on the user's computer, on the user's computer as a separate software package, partially on the user's computer and partially on a remote computer, or entirely on a remote computer or server. In the latter case, the remote computer may be connected to the user's computer by any form of network, such as a local area network (LAN) or wide area network (WAN), connected to an external computer (e.g., via the Internet), in a cloud computing environment, or used as a service, such as Software as a Service (SaaS).

[0072] Additionally, unless expressly stated in the claims, the enumerated order, use of alphanumeric characters, or use of other designations of processing elements or sequences described herein does not limit the order of the procedures and methods herein. While the above disclosure has set forth through various examples what are presently believed to be various useful embodiments of the invention, it should be understood that such details are for illustrative purposes only, and that the appended claims are not limited to the disclosed embodiments, but rather are intended to cover all modifications and equivalent combinations within the spirit and scope of the embodiments herein. For example, the system assembly described above may be implemented by a hardware device, or may be implemented as a software-only solution, e.g., by installing the described system on an existing server or mobile device.

[0073] Similarly, in the foregoing description of embodiments of the present application, it should be understood that various features may be grouped together in a single embodiment, drawing, or description for the purpose of simplifying the disclosure and facilitating an understanding of one or more embodiments of the present invention. However, this method of disclosure should not be interpreted as reflecting an intention that the claimed subject matter requires more features than are recited in each claim. In fact, an embodiment may include fewer than all features of a single embodiment disclosed above.

[0074] In some examples, numbers describing the number of components and attributes are used; it should be understood that the numbers describing such examples are, in some instances, modified by the modifiers "about," "approximately," or "generally." Unless otherwise specified, "about," "approximately," or "generally" indicates that the number may vary by ±20%. Thus, in some examples, all numerical parameters used in the specification and claims are approximations that may vary depending on the specific requirements of a particular example. In some examples, numerical parameters should be calculated with the stated number of significant digits in mind and with ordinary rounding techniques. While in some examples, the numerical ranges and parameters used to determine ranges are approximations, in specific examples, such numerical values ​​are determined as precisely as possible.

[0075] All patents, patent applications, published patent applications, and other materials, such as papers, books, specifications, publications, and documents, referenced in this application are incorporated herein by reference in their entirety, except for prosecution history documents that are inconsistent with or inconsistent with the content of this application and documents that may have a limiting effect on the broadest scope of the claims of this application (now or later related to this application). Further, in the event that an explanation, definition, and / or term usage in the accompanying materials of this application is inconsistent with or inconsistent with the content set forth in this application, the explanation, definition, and / or term usage in this application shall control.

[0076] Finally, it should be understood that the embodiments described herein are merely illustrative of the principles of the present embodiments. Other variations may be within the scope of the present application. Thus, by way of example, and not of limitation, alternative configurations of the present embodiments may be considered consistent with the teachings of the present application. Thus, the present embodiments are not limited to the embodiments expressly introduced and described herein. [Explanation of symbols]

[0077] 10. Hearing assistive devices 100 Signal Input Module 110 Microphone 120 Audio Interface 200 Signal Processing Module 210 Signal Processing Unit 211 Frequency Division Module 212 High Frequency Signal Processing Module 213 Low-Frequency Signal Processing Module 220 Power Amplifier 300 Output Transducer 310 Magnetic Circuit System 320 diaphragm 350 Housing 330 Connecting member 340 coil

Claims

1. A hearing aid, comprising: 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 to generate a control signal; 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 ear; a fixation structure configured to mount the hearing aid device so that the hearing aid device is positioned on a temporal bone of a user's head; 1. A hearing aid device comprising an operating state and a non-operating state, wherein the air-conducted sound waves are generated in the operating state and the air-conducted sound waves are not generated in the non-operating state, wherein within a target frequency range, the sound intensity of air-conducted sound heard by the user's ear in the operating state is higher than the sound intensity of air-conducted sound heard by the user's ear in the non-operating state, and the target frequency range covers at least a frequency range in which sound compensation is high for the air-conducted sound waves but low for the bone-conducted sound waves.

2. The signal processing module includes a signal processing unit, the signal processing unit comprising: a frequency division module configured to divide the electrical signal into a high frequency band component and a low frequency band component; a high frequency signal processing module coupled to the frequency division module and configured to generate a high frequency output signal based on the high frequency band components; 2. The hearing aid device of claim 1, further comprising: a low-frequency signal processing module coupled to the frequency division module and configured to generate a low-frequency output signal based on the low-frequency band components.

3. The signal processing module includes a signal processing unit, the electrical signal includes a high-frequency output signal corresponding to a high-frequency band component of the initial sound and a low-frequency output signal corresponding to a low-frequency band component of the initial sound, and the signal processing unit: a high frequency signal processing module configured to generate a high frequency output signal based on the high frequency band components; and a low-frequency signal processing module configured to generate a low-frequency output signal based on the low-frequency band components.

4. 4. A hearing aid device according to claim 2 or 3, characterized in that the signal processing module further comprises a power amplifier configured to amplify the high frequency output signal or the low frequency output signal into the control signal.

5. 4. The hearing aid device according to claim 2, wherein the power amplifier amplifies the high-frequency output signal to a different degree than the low-frequency output signal.

6. The output transducer comprises: a first vibrating component electrically connected to the signal processing module to receive the control signal and generate the bone-conducted sound waves based on the control signal; 2. The hearing aid device of claim 1, further comprising: a housing coupled to the first vibrating component, the housing generating the air-conducted sound waves upon activation of the first vibrating component.

7. The hearing aid device according to claim 6, wherein the housing and the first vibrating component are connected to the first vibrating component by an elastic member.

8. The first vibrating component is a magnetic circuit system configured to generate a first magnetic field; a diaphragm connected to the housing; 7. The hearing assistance device of claim 6, further comprising: a coil connected to the diaphragm, electrically connected to the signal processing module, receiving the control signal, and generating a second magnetic field based on the control signal, wherein the first magnetic field and the second magnetic field interact with each other to cause the diaphragm to generate the bone conduction sound waves.

9. 9. The hearing aid device of claim 8, wherein the diaphragm and the housing define a cavity, the magnetic circuit system is located within the cavity, and the magnetic circuit system is connected to the housing by an elastic member.

10. 2. The hearing aid device of claim 1, wherein the vibration output force level corresponding to the bone-conducted sound waves is greater than 55 dB.

11. 7. The hearing aid device of claim 6, further comprising at least one second vibrating component configured to generate additional air-conducted sound waves, wherein in the target frequency range, the additional air-conducted sound waves increase the sound intensity of air-conducted sound heard by the user's ear.

12. 12. The hearing aid device of claim 11, wherein the at least one second vibrating component is a vibrating membrane structure connected to a housing, and the at least one output transducer excites the vibrating membrane structure to generate the additional air-conducted sound waves.

13. 12. The hearing aid device of claim 11, wherein the at least one second vibratory component is an air conduction speaker configured to generate the additional air conduction sound waves based on the control signal.

14. 10. A hearing aid device as described in claim 9, wherein the housing has one or more sound conducting holes formed therein to guide air within the cavity out of the housing.

15. 8. The hearing aid device of claim 7, wherein the target frequency range is from 200 Hz to 8000 Hz.

16. A hearing aid, comprising: 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 to generate a control signal; 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 ear; a fixation structure configured to mount the hearing aid device so that the hearing aid device is positioned on a temporal bone of a user's head; The device includes an operating state and a non-operating state, wherein the air-conducted sound waves are generated in the operating state and the air-conducted sound waves are not generated in the non-operating state, and within a target frequency range, the sound intensity of the air-conducted sound heard by the user's ear in the operating state is higher than the sound intensity of the air-conducted sound heard by the user's ear in the non-operating state, and the target frequency range covers at least 3000 Hz to 4000 Hz. Assistive hearing devices.

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