Hearing aid

Abstract

The present application discloses a hearing aid comprising: a front portion comprising an output transducer configured to transmit a sound signal, the front portion configured to be placed within an ear canal of a user; comprising an antenna; a middle portion comprising a rechargeable battery and a substrate carrying one or more electronic components, the substrate being disposed at the battery, the middle portion being at least partially encapsulated by a polymeric material; wherein the middle portion extends in the longitudinal direction and defines an axis between the front portion and the rear portion; wherein the front portion has a first angle relative to the axis that is not zero.

Description

Technical Field

[0001] The present invention relates to the field of hearing aids. In particular, the present invention relates to hearing aids that are configured to be placed mostly or completely within a user's ear canal. In addition, the hearing aid or parts thereof may be at least partially encapsulated. Background Art

[0002] Generally speaking, a Cartesian coordinate system in three-dimensional space consists of three ordered straight lines (i.e., coordinate axes) that pass through a common point (i.e., the origin) and are perpendicular to each other; each coordinate axis has a direction; and the three coordinate axes use a single unit of length. Summary of the Invention

[0003] The present invention generally relates to a hearing aid. The hearing aid may be configured for use in an ear canal.

[0004] A hearing aid according to the present invention can be shaped to have a specific geometry so that it is not designed to fit a specific user's ear canal. A hearing aid according to the present invention can include an adapter that acts as an interface between the hearing aid and the user's ear canal. The adapter can include a soft, dome-shaped or custom-shaped outer geometry, allowing a universally shaped hearing aid to be securely positioned within the ear canal.

[0005] A hearing aid according to the present invention may include a front portion including a speaker unit. This front portion may be referred to as a first portion. The speaker unit or output transducer may be configured to transmit sound into the ear canal. The speaker unit may be configured to have an opening at its distal end, with the opening intended to be positioned near or toward the eardrum of a person using / wearing the hearing aid. A hearing aid according to the present invention may include a central portion in which a rechargeable battery may be located. This central portion may be referred to as a second portion. Furthermore, an amplifier may be positioned within or at the central portion. The amplifier may be configured as or include a flexible circuit board wrapped around the battery. This may be achieved, for example, by providing a substrate comprising two or more portions, one of which may be positioned on one side or face of the battery, while one or more other portions may be positioned on other sides, faces, or locations of the battery. The central portion may be at least partially encapsulated by a polymer material. "Encapsulation" refers to a material surrounding the components in question, preferably applied to the components in liquid form and solidified to form the encapsulation. Unlike conventional hearing aid housings, encapsulation does not leave any, or at least not much, air between the components and the material forming the wall (i.e., the encapsulating material). This is expected to provide a shielding effect for the battery and / or amplifier against the relatively harsh environment of the ear canal. The hearing aid according to the present invention may include a rear portion. An antenna may be provided at the rear portion. The antenna may also function as a draw cord. This allows the user to pull the hearing aid out of the ear canal when required. The hearing aid according to the present invention may be configured such that the middle portion extends in a longitudinal direction around an axis between the front portion and the rear portion. The front portion may be configured to have a first angle relative to the axis. This allows the hearing aid to be placed in the ear canal so that a dome or shell provided at the tip of the speaker can help to secure the hearing aid in the ear canal.

[0006] In the hearing aid described herein, the middle portion may have a front section connected to the front portion and a rear section connected to the rear portion. The axis may extend in a longitudinal direction between the two sections as described herein.

[0007] In this specification, when an "axis" is mentioned, it is a straight line extending in space, that is, a line without curvature. When referring to the relationship between two axes, these axes are not the coordinate axes in a coordinate system, but the straight lines in a Cartesian coordinate system.

[0008] Soft, replaceable earplugs or domes, such as those made of silicone, foam, or gel, are useful for the hearing aids of the present invention. These earplugs can be fitted into the ear canal, eliminating the need for custom earplugs. Because they are form-fitting, they also increase wearing comfort and simplify the fitting process for hearing care professionals and users compared to custom devices.

[0009] Generally speaking, a hearing aid according to the present invention may include: (at least) one microphone, an amplifier, a speaker, a battery, and an ear interface. One of the at least one microphone may be positioned to face outward from the ear to pick up external sounds. Because the microphone is placed within the ear canal, the natural anatomy of the ear can be used to easily locate the source of sound. Structurally, a hearing aid according to the present invention comprises three parts: a front portion having a speaker / output transducer configured to face the ear canal, surrounded by a soft earplug that contacts the ear canal, or a housing or ear mold that may be customized to the specific shape of the user's ear canal. The hearing aid may also include a central portion that contains a battery and electronic components, including a printed circuit board with various components. The hearing aid may also include a rear portion that faces the ear canal opening and may include an antenna and at least one microphone. The hearing aid may also include additional microphones, for example, positioned near the distal end of the output transducer, i.e., facing the wearer's eardrum when in use. A second microphone may be positioned near the ambient-facing microphone, so that the hearing aid includes at least two ambient-facing microphones configured to pick up sounds in the user's surroundings rather than sounds within the ear canal. This allows the hearing aid to utilize directional or other similar processing schemes.

[0010] The hearing aid according to the invention may be configured such that the first angle is not zero. This means that the two parts are not simply aligned along the same axis.

[0011] The hearing aid according to the invention may be configured such that the front portion has a second angle (β) relative to the axis (A). By this configuration, the two portions may be better aligned relative to the ear canal of a (typical) user.

[0012] The hearing aid according to the present invention can be configured so that the second angle (β) is non-zero. By making the second angle non-zero, the two parts can be ensured to be non-parallel, thereby better fitting the ear canal of the average user. This angle also helps to improve the fit rate of the device.

[0013] The hearing aid according to the present invention can be configured to include a first microphone facing outward in the middle portion to pick up external sounds. The additional microphone helps the signal processing algorithm to improve the sound pickup effect of the hearing aid.

[0014] The hearing aid according to the present invention may be configured such that the central portion comprises a second microphone facing outwards for achieving directionality.

[0015] The hearing aid according to the present invention can be configured so that the speaker unit includes an inward-facing microphone facing into the ear canal. Such an inward-facing microphone can be used to pick up the user's own voice, detect or measure the sound pressure in the ear canal (for example, to determine or counteract the occlusion effect), or for other purposes.

[0016] Hearing aids according to the present invention can be configured to include at least one exposed metal pad in the central portion for charging. Providing one or more charging pads on the device allows for contact charging of the hearing aid. Contact charging of batteries in hearing aids can provide faster charging compared to wireless charging because the risk of inductive current heating the battery is reduced.

[0017] A hearing aid according to the present invention may be configured such that the front portion includes an earplug connected to the speaker unit. The earplug may be detachable. The earplug may be referred to as a dome or ear tip. The earplug may include a stem portion configured to connect the dome / earplug to the hearing aid, and a skirt or dome portion configured to engage / abut the user's ear canal when the hearing aid is placed in the ear canal.

[0018] The hearing aid according to the present invention can be configured so that the earplug is a replaceable earplug that contacts the ear canal. The earplug may include a stem and a dome, wherein the stem is configured to be connected to the hearing aid and the dome is configured to fit against the wall of the user's ear canal.

[0019] Hearing aids according to the present invention can be configured so that the earplug is a custom ear mold. This custom ear mold allows the hearing aid to fit more snugly within the ear canal, reducing sound leakage and, in turn, feedback when loud sounds are output to the user. Consequently, the custom ear mold allows the user to receive higher sound levels, compensating for their individual hearing loss.

[0020] A hearing aid according to the present invention may be configured to include an accelerometer in the central portion. The accelerometer may be used to measure / determine various events, such as a user tapping once, twice, or more times on or near the hearing aid to provide some control input, such as a volume change command, a program change command, a power level change command (e.g., requesting the hearing aid to enter a low-power mode, such as airplane mode, etc.).

[0021] Hearing aids according to the present invention can be configured to include non-contact sensors in the front or center portion, such as a thermal sensor, a gyroscope, and / or a PPG, and / or a galvanic skin response sensor for EEG, EMG, and / or ECG. These sensors can be used to record or detect physiological signals from the user's body. These signals can be used to control the hearing aid.

[0022] A hearing aid according to the present invention can be configured to also include a coil for binaural communication and / or wireless charging. Such a coil can simultaneously perform both functions. Another coil may also be included, such as a telecoil for picking up the baseband modulated signal from the telecoil system.

[0023] The hearing aid according to the present invention can be configured so that the middle part includes a flexible joint to adapt to any angle of the user's ear canal. This can be achieved by a soft part connecting the middle part to the front part, or alternatively, by a ball and socket joint between the two parts.

[0024] The hearing aid may be adapted to provide frequency-dependent gain and / or level-dependent compression and / or frequency transposition of one or more frequency ranges to one or more other frequency ranges (with or without frequency compression) to compensate for a user's hearing impairment. The hearing aid may include a signal processor for enhancing an input signal and providing a processed output signal.

[0025] The hearing aid may comprise an output unit for providing a stimulus perceived by the user as an acoustic signal based on the processed electrical signal. The output unit may comprise a vibrator of a bone conduction hearing aid. The output unit may comprise an output transducer. The output transducer may comprise a receiver (loudspeaker) for providing the stimulus as an acoustic signal to the user (e.g. in an acoustic (air conduction based) hearing aid). The output transducer may comprise a vibrator for providing the stimulus as a mechanical vibration of the skull to the user (e.g. in a bone attached or bone anchored hearing aid). The output unit may (in addition or as an alternative) comprise a (e.g. wireless) transmitter for transmitting the sound picked up by the hearing aid (e.g. via a network, e.g. in telephone operating mode, or in a headset configuration) to another device, such as a remote communication partner.

[0026] The hearing aid may include an input unit for providing an electrical input signal representing sound. The input unit may include an input transducer, such as a microphone, for converting the input sound into the electrical input signal. The input unit may include a wireless receiver for receiving a wireless signal including or representing sound and providing the electrical input signal representing the sound.

[0027] The wireless receiver and / or transmitter may be configured to receive and / or transmit electromagnetic signals in the radio frequency range (3 kHz to 300 GHz), for example. The wireless receiver and / or transmitter may be configured to receive and / or transmit electromagnetic signals in the optical frequency range (e.g., infrared light 300 GHz to 430 THz or visible light such as 430 THz to 770 THz), for example.

[0028] A hearing aid may include a directional microphone system adapted to spatially filter ambient sound to enhance a target sound source among multiple sound sources in the local environment of a user wearing the hearing aid. The directional system may be adapted to detect (e.g., adaptively detect) the direction from which a particular portion of the microphone signal originates. This can be achieved in a variety of different ways, such as those described in the prior art. In hearing aids, microphone array beamformers are commonly used to spatially attenuate background noise sources. The beamformer may include a linearly constrained minimum variance (LCMV) beamformer. Many beamformer variants are available in the literature. Minimum variance distortionless response (MVDR) beamformers are widely used in microphone array signal processing. Ideally, an MVDR beamformer leaves the signal from the target direction (also known as the line-of-sight direction) unchanged while maximally attenuating sound signals from other directions. The generalized sidelobe canceler (GSC) structure is an equivalent representation of the MVDR beamformer, offering computational and digital representation advantages over a direct implementation of the original form.

[0029] Most sound signal sources (except the user's own voice) are relatively small compared to the size of the hearing aid, such as the distance d between the two microphones of a directional system. mic Located away from the user. The typical microphone distance in a hearing aid is on the order of 10 mm. The minimum distance from the user's sound source of interest (e.g., the sound from the user's mouth or the sound from the audio transmission device) is 0.1 m (>10 d mic ) level. For such a minimum distance, the hearing aid (microphone) will be in the acoustic near field of the sound source and the level difference of the sound signal incident on the respective microphones may be significant. The typical distance of the communication partner is greater than 1m (>100d mic The hearing aid (microphone) will be in the acoustic far field of the sound source, and the level difference of the sound signals incident on the corresponding microphones will not be obvious. The arrival time difference of the sound incident in the direction of the microphone axis (for example, in front of or behind a normal hearing aid) is ΔT = d mic / v sound =0.01 / 343[s]=29μs, where v sound The speed of sound in air at 20°C (343 m / s).

[0030] The hearing aid may include an antenna and transceiver circuitry that enables a wireless link to an entertainment device (e.g., a television), a communication device (e.g., a telephone), a wireless microphone, a separate (external) processing device, or another hearing aid. The hearing aid may thus be configured to wirelessly receive a direct electrical input signal from another device. Similarly, the hearing aid may be configured to wirelessly transmit a direct electrical output signal to another device. The direct electrical input or output signal may represent or include an audio signal and / or a control signal and / or an information signal.

[0031] In general, the wireless link established by the antenna and transceiver circuitry of the hearing aid may be of any type. The wireless link may be a link based on near field communication, for example an inductive link based on inductive coupling between antenna coils of a transmitter part and a receiver part. The wireless link may be based on far-field electromagnetic radiation. Preferably, the frequency used to establish the communication link between the hearing aid and the other device is below 70 GHz, for example in the range from 50 MHz to 70 GHz, for example above 300 MHz, for example in the ISM range above 300 MHz, for example in the 900 MHz range or in the 2.4 GHz range or in the 5.8 GHz range or in the 60 GHz range (ISM = Industrial, Scientific and Medical, such standardized ranges are defined, for example, by the International Telecommunication Union ITU). The wireless link may be based on standardized or proprietary technologies. The wireless link may be based on Bluetooth technology (for example Bluetooth Low Energy technology, for example LE Audio) or Ultra-Wideband (UWB) technology.

[0032] The hearing aid may consist of or may form part of a portable (ie configured to be wearable) device, eg a device comprising a local energy source such as a battery, eg a rechargeable battery.

[0033] The hearing aid may for example be a low-weight, easily wearable device, for example having a total weight of less than 100 g, such as less than 20 g, for example less than 5 g.

[0034] A hearing aid may include a "forward" (or "signal") path between the input and output of the hearing aid for processing audio signals. A signal processor may be located in this forward path. The signal processor may be adapted to provide frequency-dependent gain according to the specific needs of the user (e.g., hearing loss). The hearing aid may include an "analysis" path having functional components for analyzing signals and / or controlling processing of the forward path. Some or all of the signal processing in the analysis path and / or the forward path may be performed in the frequency domain, in which case the hearing aid includes appropriate analysis and synthesis filter banks. Some or all of the signal processing in the analysis path and / or the forward path may be performed in the time domain.

[0035] The analog electrical signal representing the acoustic signal can be converted into a digital audio signal in an analog-to-digital (AD) conversion process, where the analog signal is sampled at a predetermined frequency or sampling rate f. s Sampling, f s For example, in the range from 8 kHz to 48 kHz (adapted to the specific needs of the application) at discrete time points t n (or n) provides digital samples x n (or x[n]), each audio sample is passed through a predetermined N b The bit represents the sound signal at t n The value when N bFor example, in the range from 1 to 48 bits, such as 24 bits. Each audio sample thus uses N b bit quantization (resulting in 2 Nb different possible values). A digital sample x has a 1 / f s The length of time, such as 50μs, for f s = 20kHz. Multiple audio samples can be arranged in time frames. A time frame can include 64 or 128 audio data samples. Other frame lengths can be used depending on the actual application.

[0036] The hearing aid may include an analog-to-digital (AD) converter to digitize an analog input (e.g., from an input transducer such as a microphone) at a predetermined sampling rate, such as 20 kHz. The hearing aid may also include a digital-to-analog (DA) converter to convert the digital signal into an analog output signal, such as for presentation to the user via an output transducer.

[0037] The hearing aid, such as the input unit and / or the antenna and the transceiver circuit, may comprise a transform unit for converting a time domain signal into a signal in a transform domain (e.g. the frequency domain or the Laplace domain, a Z transform, a wavelet transform, etc.). The transform unit may be constituted by or include a time-frequency (TF) transform unit for providing a time-frequency representation of the input signal. The time-frequency representation may comprise an array or mapping of corresponding complex or real values ​​of the signal in question in a specific time and frequency range. The TF transform unit may comprise a filter bank for filtering the (time-varying) input signal and providing a plurality of (time-varying) output signals, each output signal comprising a distinct frequency range of the input signal. The TF transform unit may comprise a Fourier transform unit (e.g. a discrete Fourier transform (DFT) algorithm, a short-time Fourier transform (STFT) algorithm, or a similar algorithm) for converting the time-varying input signal into a (time-varying) signal in the (time-)frequency domain. The frequency domain considered by the hearing aid, from the minimum frequency f min To the maximum frequency f max The frequency range of may include a portion of the typical human hearing range from 20 Hz to 20 kHz, for example a portion of the range from 20 Hz to 12 kHz. Typically, the sampling rate f s Greater than or equal to the maximum frequency f max twice, that is, f s ≥2f max The signals of the forward and / or analysis paths of the hearing aid may be split into NI frequency bands (e.g., of uniform width), where NI is, for example, greater than 5, such as greater than 10, such as greater than 50, such as greater than 100, such as greater than 500, at least parts of which are processed separately. The hearing aid may be adapted to process the signals of the forward and / or analysis paths in NP different frequency channels (NP ≤ NI). The frequency channels may be of uniform or non-uniform width (e.g., increasing width with frequency), overlapping or non-overlapping.

[0038] A hearing aid can be configured to operate in different modes, such as a normal mode and one or more special modes, which can be selected by the user or automatically. The operating modes can be optimized for specific acoustic situations or environments, such as a communication mode, for example, a telephone mode. The operating modes can include a low-power mode, in which the functionality of the hearing aid is reduced (e.g., to save energy), such as disabling wireless communication and / or disabling specific features of the hearing aid.

[0039] The hearing aid may include a plurality of detectors or sensors configured to provide status signals related to the current network environment of the hearing aid (e.g., the current acoustic environment), and / or the current state of the user wearing the hearing aid, and / or the current state or operating mode of the hearing aid. Alternatively or additionally, one or more of the detectors may form part of an external device that communicates with the hearing aid (e.g., wirelessly). The external device may include, for example, another hearing aid, a remote control, an audio transmission device, a phone (e.g., a smartphone), an external sensor, etc.

[0040] One or more of the plurality of detectors may operate on a full-band signal (time domain). One or more of the plurality of detectors may operate on a band-split signal ((time-)frequency domain), eg in a limited number of frequency bands.

[0041] The plurality of detectors may include a level detector for estimating the current level of the signal in the forward path. The detector may be configured to determine whether the current level of the signal in the forward path is above or below a given (L-)threshold. The level detector operates on the full-band signal (time domain). The level detector operates on the band-split signal ((time-)frequency domain).

[0042] A hearing aid may include a voice activity detector (VAD) for estimating whether (or with what probability) an input signal (at a given point in time) includes a voice signal. In this specification, a voice signal may be understood to include a speech signal from a human. It may also include other forms of vocalizations (such as singing) produced by the human speech system. The voice activity detector unit may be adapted to classify the user's current acoustic environment as a "voice" or "no-voice" environment. This has the advantage that time periods containing electrical microphone signals of human vocalizations (such as speech) in the user's environment can be identified and thus separated from time periods containing only (or primarily) other sound sources (such as artificially generated noise). The voice activity detector may be adapted to also detect the user's own voice as "voice." Alternatively, the voice activity detector may be adapted to exclude the user's own voice from the "voice" detection.

[0043] A hearing aid may include a self-voice detector for estimating whether (or with what probability) a particular input sound (e.g., voice, such as speech) originates from the voice of a user of the hearing system. The microphone system of the hearing aid may be adapted to be able to distinguish the user's own voice from the voice of another person and possibly from unvoiced sounds.

[0044] The plurality of detectors may include a motion detector such as an accelerometer. The motion detector may be configured to detect movement of the user's facial muscles and / or bones, such as due to speech or chewing (eg, jaw movement), and provide a detector signal indicative of the movement.

[0045] The hearing aid may comprise a classification unit configured to classify a current situation based on an input signal from (at least part of) the detector and possibly other inputs. In this specification, a "current situation" may be defined by one or more of the following:

[0046] a) the physical environment (e.g., including the current electromagnetic environment, such as the presence of electromagnetic signals (including audio and / or control signals) intended or unintended for reception by the hearing aid, or other properties of the current environment other than acoustics);

[0047] b) Current acoustic conditions (input level, feedback, etc.);

[0048] c) the user’s current mode or state (motion, temperature, cognitive load, etc.);

[0049] d) The current mode or status of the hearing aid and / or another device communicating with the hearing aid (selected program, time elapsed since last user interaction, etc.).

[0050] The classification unit may be based on or may comprise a neural network, such as a recurrent neural network, such as a trained neural network.

[0051] Hearing aids may include acoustic (and / or mechanical) feedback control (e.g., suppression) or an echo cancellation system. Adaptive feedback cancellation has the ability to track changes in the feedback path over time. It is typically based on a linear time-invariant filter to estimate the feedback path, but the filter weights are updated over time. The filter updates can be calculated using a stochastic gradient algorithm, including some form of least mean square (LMS) or normalized LMS (NLMS) algorithm. They all have the property of minimizing the difference signal in terms of mean square, with NLMS additionally normalizing the filter updates by the square of the Euclidean norm of a reference signal.

[0052] The hearing aid may also include other appropriate functions for the application in question, such as compression, noise reduction, etc.

[0053] A hearing aid may comprise a hearing instrument, such as a hearing instrument adapted to be positioned at the ear of a user or fully or partially positioned in the ear canal, an ear protection device, or a combination thereof. A hearing system may comprise a loudspeaker amplifier (comprising a plurality of input transducers (e.g. a microphone array) and a plurality of output transducers, such as one or more loudspeakers, and one or more audio (and possibly video) transmitters, such as for use in audio conferencing situations), such as comprising a beamformer filter unit, such as to provide multiple beamforming capabilities.

[0054] In one aspect, uses of the hearing aids described herein are also provided. These may be used in systems comprising one or more hearing aids (e.g., hearing instruments), active ear protection systems, and the like, for example, in hands-free telephone systems, teleconferencing systems (e.g., including a speakerphone), public address systems, karaoke systems, classroom sound reinforcement systems, and the like.

[0055] In one aspect, the present invention provides a hearing aid comprising a first portion connected to a second portion. The second portion comprises a battery and a substrate, wherein the substrate carries electronic components. The electronic components are at least one of the following: a sound processor and a wireless communication component. The second portion is preferably encapsulated by a material. The encapsulation provides a barrier for the battery and electronic components against earwax, water, and the like, thereby extending the life of the electronic components and / or battery. An antenna is connected to and extends from the second portion such that, when the hearing aid is placed in the ear canal of a user, the antenna is located within the outer ear of the user wearing the hearing aid. An angle is formed between the first portion and the second portion, allowing the first portion to bend in a manner similar to the curvature of the ear canal, thereby enabling deeper placement within the user's ear canal. A dome, a flexible component, or even a custom-shaped component may be connected to the first portion. Such a component can provide a more comfortable wearing experience for the user and increase the retention of the hearing aid in the ear canal, making it less likely to fall out of the ear canal during use. The features described in conjunction with this aspect may be combined with the features mentioned and described in conjunction with the other aspects, as well as with the features disclosed herein.

[0056] Hearing system

[0057] In another aspect, there is provided a hearing aid comprising the device described above, in detail in the "Detailed Description of the Invention" and in the claims, and a hearing system comprising an auxiliary device.

[0058] The hearing system may be adapted to establish a communication link between the hearing aid and the auxiliary device so that information (eg control and status signals, possibly audio signals) can be exchanged or forwarded from one device to the other.

[0059] The auxiliary device may include or may consist of a remote control, a smart phone, or other portable or wearable electronic device such as a smart watch.

[0060] The auxiliary device may consist of or include a remote control for controlling the functions and operation of the hearing aid. The functions of the remote control are implemented in a smartphone, which may run an app that enables the functions of the audio processing device to be controlled via the smartphone (the hearing aid includes a suitable wireless interface to the smartphone, for example based on Bluetooth or some other standardized or proprietary solution).

[0061] The auxiliary device may be constituted by or include an audio gateway device, which is suitable for receiving multiple audio signals (for example from an entertainment device such as a TV or music player, from a telephone device such as a mobile phone, or from a computer such as a PC, a wireless microphone, etc.) and is suitable for selecting and / or combining appropriate signals (or signal combinations) from the received audio signals for transmission to the hearing aid.

[0062] The auxiliary device may consist of or may comprise a further hearing aid.The hearing system may comprise two hearing aids adapted to implement a binaural hearing system, eg a binaural hearing aid system.

[0063] definition

[0064] As used herein, a hearing aid, such as a hearing instrument, refers to a device adapted to improve, enhance, and / or protect a user's hearing ability by receiving acoustic signals from the user's environment, generating corresponding audio signals, possibly modifying the audio signals, and providing the possibly modified audio signals as audible signals to at least one ear of the user. The audible signals may be provided, for example, in the form of acoustic signals radiated into the user's outer ear and / or acoustic signals transmitted as mechanical vibrations through the bony structure of the user's head and / or through portions of the middle ear to the user's inner ear.

[0065] The hearing aid can be configured to be worn in any known manner, such as as a unit worn behind the ear (with a tube that directs the radiated acoustic signal into the ear canal or with an output transducer, such as a loudspeaker, arranged close to or in the ear canal), as a unit arranged entirely or partially in the auricle and / or ear canal, as a unit connected to a fixed structure implanted in the skull, such as a vibrator, etc. The hearing aid can comprise a single unit or several units that communicate with each other (e.g., acoustically, electrically, or optically). The loudspeaker can be arranged in the housing together with the other components of the hearing aid, or it can itself be an external unit (possibly in combination with a flexible guiding element, such as a dome-shaped element).

[0066] Hearing aids can be adapted to the needs of specific users, such as hearing loss. The configurable signal processing circuitry of the hearing aid can be adapted to apply frequency- and level-dependent compression and amplification of the input signal. The customized frequency- and level-dependent gain (amplification or compression) can be determined during the fitting process by the fitting system based on the user's hearing data, such as an audiogram, using basic fitting principles (e.g., adaptation to speech). The frequency- and level-dependent gain can, for example, be reflected in processing parameters, uploaded to the hearing aid via an interface to a programming device (fitting system), and used by a processing algorithm executed by the configurable signal processing circuitry of the hearing aid.

[0067] A "hearing system" refers to a system that includes one or two hearing aids. A "binaural hearing system" refers to a system that includes two hearing aids and is adapted to collaboratively provide audible signals to both ears of a user. A hearing system or binaural hearing system may also include one or more "auxiliary devices" that communicate with the hearing aids and influence and / or benefit from the hearing aids' functionality. Such auxiliary devices may include at least one of the following: a remote control, a remote microphone, an audio gateway device, an entertainment device such as a music player, a wireless communication device such as a mobile phone (e.g., a smartphone) or a tablet, or another device, such as one that includes a graphical interface. A hearing aid, hearing system, or binaural hearing system may be used, for example, to compensate for the hearing loss of a hearing-impaired person, enhance or protect the hearing ability of a person with normal hearing, and / or transmit electronic audio signals to a person. A hearing aid or hearing system may, for example, form part of or interact with a public address system, active ear protection system, hands-free phone system, car audio system, entertainment (e.g., television, music playback, or karaoke) system, teleconferencing system, classroom amplification system, and the like. BRIEF DESCRIPTION OF THE DRAWINGS

[0068] Various aspects of the present invention will be best understood from the following detailed description in conjunction with the accompanying drawings. For clarity, the drawings are schematic and simplified, showing only the details necessary for understanding the present invention and omitting other details. Throughout the specification, the same reference numerals are used for identical or corresponding parts. The various features of each aspect may be combined with any or all features of the other aspects. These and other aspects, features, and / or technical effects will be apparent from and elucidated in conjunction with the following figures, in which:

[0069] Figure 1 schematically shows a block diagram of a hearing aid;

[0070] Figure 2 schematically shows a block diagram of a hearing aid with external processing;

[0071] Figure 3 Schematically illustrates a hearing aid as described herein;

[0072] Figure 4 Schematically shows Figure 3 Different views of hearing aids;

[0073] Figure 5 Schematically shows Figure 3 and Figure 4 different views of hearing aids; and

[0074] Figure 6 A hearing aid with an antenna having an overmolded first portion and a thinner second portion is schematically shown.

[0075] By the detailed description provided below, the further scope of application of the present invention will be apparent. However, it should be understood that while the detailed description and specific examples indicate the preferred embodiments of the present invention, they are provided for illustrative purposes only. For those skilled in the art, based on the following detailed description, other embodiments of the present invention will be apparent. DETAILED DESCRIPTION

[0076] The detailed description presented below in conjunction with the accompanying drawings serves as a description of a variety of different configurations. The detailed description includes specific details for providing a thorough understanding of a plurality of different concepts. However, it will be apparent to those skilled in the art that these concepts can be implemented without these specific details. Several aspects of the apparatus and method are described by a plurality of different blocks, functional units, modules, components, circuits, steps, processes, algorithms, etc. (collectively referred to as "elements"). Depending on the specific application, design limitations or other reasons, these elements may be implemented using electronic hardware, computer programs or any combination thereof.

[0077] The electronic hardware may include microelectromechanical systems (MEMS), (e.g., application specific) integrated circuits, microprocessors, microcontrollers, digital signal processors (DSPs), field programmable gate arrays (FPGAs), programmable logic devices (PLDs), gating logic, discrete hardware circuits, printed circuit boards (PCBs) (e.g., flexible PCBs), and other suitable hardware configured to perform the various functions described in this specification, such as sensors for sensing and / or recording physical properties of the environment, device, user, etc. A computer program shall be construed broadly to mean instructions, an instruction set, code, a code segment, program code, a program, a subroutine, a software module, an application, a software application, a software package, a routine, a subroutine, an object, an executable, a thread of execution, a program, a function, or the like, whether referred to as software, firmware, middleware, microcode, a hardware description language, or otherwise.

[0078] The present application relates to the field of hearing aids. Figure 1 An exemplary block diagram of a hearing device HD, such as a hearing aid, is shown, comprising a noise reduction system NRS for compensating for hearing impairment of a user of the hearing device and a hearing aid (audio) processor HAG. The hearing device comprises an input unit IU for picking up sound s from the environment (e.g. via M input transducers such as microphones). in And provide multiple (M, M>1) electrical input signals (S1,…,S M ), the noise reduction system NRS is used to estimate the input sound s based on the electric input signal and optionally further information such as a mode control signal ("mode") in The target signal in The mode selection input ("mode") may be configured to indicate an operating mode and / or filter coefficient update strategy of a beamformer of a system, e.g., a noise reduction system NRS, e.g., depending on whether the target signal is the user's own voice or a target signal from the user's environment (possibly also indicating the direction or position of the target sound source). The mode control signal may, for example, be provided from a user interface, e.g., from a remote control (e.g., implemented as an APP on a smartphone or similar device, such as a smartwatch). The mode control signal ("mode") may, for example, be automatically generated, e.g., using one or more sensors, e.g., activated by receiving a wireless signal, e.g., from a phone. The output of the noise reduction system NRS may be an estimate of the user's voice. or an estimate of the target sound from the environment The hearing device, such as a hearing aid, further comprises an (audio) processor PRO for applying one or more processing algorithms to the signal in the forward path from the input to the output, for example (here) to an estimate of the target signal provided by the noise reduction system (For example, by time-frequency representation This can be done, for example, by a corresponding analysis filter bank (forming, for example, the input unit IU MIC part, possibly together with a corresponding analog-to-digital converter, as appropriate), thereby providing an electrical input signal (S1, ..., S) in a time-frequency representation (k, n) M ), k and n are frequency index and time index respectively. One or more processing algorithms may include, for example, a compression algorithm configured to amplify (or attenuate) the signal according to the needs of the user, for example to compensate for the user's hearing loss. Other processing algorithms may include frequency shifting, feedback control, etc. The processor PRO provides a processed output OUT, which is fed to the synthesis filter bank FBS to convert from a time-frequency representation (frequency domain) to the time domain. The time domain output signal out is fed to the output unit OU to be converted into a stimulus s that can be perceived by the user as sound out ("output sound") such as acoustic vibrations (e.g., in the air and / or in the skull), the synthesis filter bank FBS may be omitted. The target signal may be the user's own voice, and / or a target sound in the user's environment (e.g., a person (different from the user) speaking, e.g., communicating with the user).

[0079] The hearing aid further comprises a configurable signal processor (DSP), such as a digital (audio) signal processor, e.g., a processor that applies frequency- and level-dependent gain, e.g., to provide hearing loss compensation, beamforming, noise reduction, filter bank functionality, and other digital functions of the hearing device. The configurable signal processor (DSP) is adapted to access a memory (MEM). The configurable signal processor (DSP) is further configured to process one or more electrical input audio signals and / or one or more directly received auxiliary audio input signals based on currently selected (e.g., automatically selected, e.g., based on one or more sensors, or based on input from a user interface) (enabled) hearing aid program / parameter settings. The aforementioned functional units (and other components) can be divided into circuits and components depending on the application involved (e.g., for size, power consumption, analog-to-digital processing, acceptable latency, etc.), e.g., integrated into one or more integrated circuits, or as a combination of one or more integrated circuits and one or more separate electronic components (e.g., inductors, capacitors, etc.). The configurable signal processor (DSP) provides a processed audio signal, which is intended for presentation to the user. The hearing aid also includes a front-end IC (FE) that interfaces a configurable signal processor (DSP) to input and output transducers, among other things. This typically includes interfaces between analog and digital signals (e.g., to a microphone and / or speaker). The input and output transducers can be separate components or integrated with other electronic circuitry (e.g., based on MEMS).

[0080] The hearing device HD further comprises an output unit (eg an output transducer) which provides stimuli perceivable as sound by the user based on the processed audio signal from the processor or a signal derived therefrom.

[0081] The hearing devices described herein may comprise an output transducer in the form of a loudspeaker (also referred to as a "receiver") SPK for converting an electrical signal into an acoustic (air-borne) signal which (when the hearing aid is mounted at the ear of a user) is directed towards the eardrum, thereby providing a sound signal S at the eardrum. ED The hearing aid or hearing device further comprises a guiding element such as a dome DO for guiding and positioning the hearing aid in the ear canal of the user. The hearing aid may further comprise an additional (first) input transducer such as a microphone M ITE,env , which is directed towards the environment to provide a signal S representing the input sound at the ear canal ITE The hearing aid may also include an additional (second) input transducer such as a microphone M ITE,ed , which is directed towards the eardrum to provide a sound signal representing the sound at the eardrum (S ED =S dir +S HI) is a (second) electrical input audio signal. Sound propagates from the environment to the residual cavity at the eardrum via a direct acoustic path through the semi-open dome DO (often referred to as direct path sound). The directly propagated sound is mixed with the sound from the hearing device HD to form a composite sound field at the eardrum. The sound output S of the hearing aid is HI Sound transmitted directly from the environment to the eardrum may be taken into account (at least in certain operating modes) for modification to provide adaptive noise cancellation (ANC) and / or adaptive occlusion control (AOC).

[0082] In addition to the (acoustic) output and input transducers, the hearing aid may also include other functional elements, such as (additional) detectors, such as electrodes for collecting signals from the user's body (e.g., brain wave signals, temperature indications, blood-related parameters, heartbeat indications, muscle vibrations, etc.). Such detectors may include one or more of the following: an electroencephalogram (EEG) sensor, an electromyogram (EMG) sensor, a motion sensor, a temperature sensor, a photoplethysmogram (PPG) sensor, an electrooculogram (EOG) sensor, etc.

[0083] (from (first and / or second) input converter M BTE1 ,M BTE2 ,M ITE,env ,M ITE,ed The electrical input signal may be processed in the time domain or in the (time-)frequency domain (or partly in the time domain and partly in the frequency domain, as is advantageous for the application in question).

[0084] Figure 1 The embodiment of a hearing device (HD), such as a hearing aid, illustrated in the accompanying drawings is a portable device comprising a battery BAT, such as a rechargeable battery, such as a battery based on lithium-ion battery technology, for powering the electronic components of the hearing aid. In an embodiment, the hearing device, such as a hearing aid, is adapted to provide frequency-dependent gain and / or level-dependent compression and / or frequency transposition of one or more frequency ranges to one or more other frequency ranges (with or without frequency compression) to compensate for a hearing impairment of a user.

[0085] Figure 2 An embodiment of a hearing device HD hearing aid configured to be worn at or in an ear of a user is shown, together with a separate, external, possibly body-worn audio processing device APD configured to be worn or carried by the user (or at least positioned sufficiently close to the user to maintain communication with the earpiece via a wireless link WL implemented by transceivers Tx / Rx of the respective devices). The audio processing device APD comprises a computing device CPD apd For example, an audio signal processor or similar device.

[0086] The hearing device comprises (at least one) input transducer (here a microphone M for converting a sound in the environment of the hearing device into an acoustically received electrical input signal y(n) (n being a possible time variation) representing the sound). The hearing device further comprises a wireless transmitter Tx for transmitting the acoustically received electrical input signal y(n) or a part thereof (e.g. a filtered part, such as a low-pass filtered part) to an audio processing device APD. The hearing device further comprises a wireless receiver Rx for receiving a processed signal z(n) from the audio processing device, at least in a normal operating mode of the hearing device. The wireless transmitter and receiver (Tx, Rx) may be provided as an antenna and a transceiver circuit for establishing an audio communication link WL in accordance with a standardized or proprietary (short-range) protocol. The hearing device further comprises an output transducer (here a loudspeaker SPK) for outputting the (final) processed signal (s') to the audio processing device APD. out (n) is converted into a stimulus perceived by the user as sound. The processed signal s' out (n) may consist of or may comprise at least a portion of the processed signal z(n) provided by the audio processing device, at least in a normal operating mode of the hearing device. Alternatively (or in a separate "stand-alone" mode), the processed signal s' out (n) may be formed by a processed signal provided by the earpiece itself (in which case it may comprise suitable means for processing the electrical input signal y(n) and converting the processed signal s' out Optional processing of the acoustically received signal y(n) may, for example, be of interest in operating modes in which no contact with the audio processing device APD can be established (e.g. in order to provide the user with basic functionality of the hearing device (e.g. hearing loss compensation)).

[0087] The audio processing device APD comprises a wireless receiver Rx for receiving an acoustically received electric input signal y(n) or a part thereof from the earpiece EP and is configured to provide a received signal representative of the signal. apd ) further comprises a (hearing aid) processor part HAP for applying a processing algorithm (e.g. comprising a neural network) to the received signal or a signal derived therefrom, such as a transformed version Y thereof (e.g. provided by a transformation unit TRF, such as a Fourier transformation unit), and providing a modified signal Y'. The processor part HAP may for example be configured to compensate for a hearing impairment of the user (e.g. by applying a compression-amplification algorithm, e.g. providing a frequency and / or level dependent gain (or attenuation) to be applied to the input signal (y'(n) or Y)). In Figure 2 In an embodiment of the present invention, the audio processing device APD (eg, the computing device CPD apd) comprises corresponding transform domain units and inverse transform domain units (TRF, I-TRF) for converting a time domain signal (here the signal y'(n) received from the earpiece) into a transform domain (e.g. the time-frequency domain), see signal Y, and then converting it back into the time domain again (here the processed signal Y' in the transform domain into z(n) in the time domain).

[0088] The signal transmitted from the hearing device to the (external) audio processing device APD and / or from the audio processing device APD to the hearing device via the wireless link WL does not necessarily have to be the aforementioned "audio signal." It can also be a feature derived from the audio signal. For example, instead of transmitting the audio signal back to the hearing device, a gain derived from the predicted signal can be transmitted back to the earpiece and applied to a suitably processed version (e.g., a delayed version) of the electrical input signal y(n).

[0089] The term "processed version" may, for example, cover features extracted from an original audio signal. The term "processed version" may also, for example, cover an original audio signal that has been subjected to a processing algorithm that applies a gain or attenuation and / or a delay to the original audio signal and results in a modified audio signal (preferably enhanced in some way, e.g., noise reduced relative to a target signal, or simply delayed).

[0090] Figure 3 A hearing device according to the present invention is schematically shown.

[0091] The hearing device 10 comprises a front part 2. The front part is configured to be inserted into an ear canal of a user. The front part 2 comprises a speaker unit / output transducer 3 for transmitting sound into the ear canal of a user.

[0092] Here, the front portion 2 is equipped with a dome or earplug 11. This dome provides an interface with the user's ear canal. The earplug or dome 11 is replaceable and will (at least partially) contact the ear canal during use. The dome's exterior is soft, so that when the hearing device 10 is inserted into the ear canal, it will (at least partially) conform to the shape of the ear canal. The dome 11 also provides retention, preventing the hearing device 10 from easily slipping out of the ear canal. The dome or earplug 11 is connected to the front portion of the hearing aid. In an alternative embodiment (not shown), the earplug 11 can be made of a custom ear mold. The outer surface of such an ear mold is generally shaped according to the shape of (a portion of) the ear canal of a specific user. Compared to a hearing aid equipped with a (soft) dome at the same volume level, a custom ear mold can provide higher sound pressure to the user's ear while reducing the risk of feedback. The dome 11 includes a relatively rigid stem portion that is configured to connect to the tip / end of the hearing device, where the output transducer is located.

[0093] Hearing device 10 includes a central portion 4 containing a rechargeable battery and an amplifier or amplifier section. The amplifier section is formed of or includes a (possibly flexible) circuit board that is at least partially wrapped around a portion of the battery. For example, it may be arranged on two or more sides of the battery, along these sides, or parallel to these sides. The circuit board may include several sections, with one section arranged on one side of the battery, another on the other side, and so on. Two of the multiple sections may be connected by a flexible member or flexible section, which may themselves be more rigid or less flexible. The flexible section may be implemented using a different substrate or by making a thinner portion of the substrate. The central portion of the hearing device is at least partially encapsulated by a polymer material. This provides a protective barrier for the battery and amplifier from the hearing device's environment and also provides mechanical stability for the hearing device. The substrate may carry one or more electronic components, such as a sound processor, a wireless interface, filters, decoupling elements, a sensor processor, and so on. The wireless interface may perform encoding and decoding during wireless communication.

[0094] Hearing device 10 includes a rear portion 5, which contains an antenna 6. Antenna 6 can be said to constitute rear portion 5. As can be seen in the figure, antenna 6 is connected so that antenna 6, the middle portion, and the front portion together form a hearing aid. Antenna 6 is attached to the rear portion and can be detached from the rear portion. Antenna 6 also functions as a drawstring, meaning the user can grasp the antenna and pull it to disengage the hearing device from the ear canal and remove it.

[0095] A cover can be placed where the antenna 6 connects to the hearing aid 10. This cover covers the area where the antenna is connected, such as where the antenna is soldered to a connector or pins. The pins or connectors are further soldered to the substrate on the other side. This establishes an electrical connection between the antenna and the substrate / electronic components / transceiver. The transceiver / radio is configured to communicate with external devices via the antenna. The radio can implement various communication protocols, such as Bluetooth, Bluetooth Low Energy, Auracast, and others.

[0096] The antenna is flexible, meaning it conforms to the shape of the user's ear when the hearing aid is properly positioned in the user's ear canal. The antenna bends when the hearing aid is placed in the user's ear canal, retaining some of its bent shape. This allows the antenna to better conform to the user's shape over time and makes it less noticeable to the user because it applies less force to the ear / concha when the hearing aid is in the ear canal.

[0097] like Figure 4 As shown, the middle portion 4 extends in the longitudinal direction around the axis A between the front portion 2 and the rear portion 5. Here, "around" can be understood as along the axis or surrounding a part of the axis, that is, the middle portion extends along the axis and the axis passes through the middle portion 4, as shown in FIG. Figure 4 As shown. Figure 4 As shown, the first angle (α) of the front portion relative to the axis A is 34.13 degrees. The first angle (α) is measured or determined relative to the longitudinal extension of the front portion, which is Figure 4 In the embodiment of the present invention, a straight line A is determined. In different versions of the hearing aid, this angle may be different. In general, it has been found that this angle is preferably in the range of 10 degrees to 40 degrees, for example in the range of 20 degrees to 35 degrees, such as about 35 degrees.

[0098] like Figure 4 As shown, the middle portion 4 includes at least one exposed metal pad 10 for charging. Figure 4 As shown, hearing aid 10 includes two charging pads. These two charging pads are located on the same side or surface of the hearing aid, rather than on opposite or adjacent sides. Here, both charging pads are located on the same side of central portion 4. This allows the hearing aid 10 to be charged in a charger while placed on its side. Charging via exposed metal pads can reduce the size of the device and improve charging efficiency, such as enabling faster charging speeds, such as charging speeds exceeding 1C (>20 mA).

[0099] The hearing aid 10 also includes a magnet disposed on one side so that when the hearing aid 10 is placed in a charger, the magnet helps align the hearing aid 10 relative to the charger, thereby establishing an effective electrical connection with the metal pads. If the metal pads are not aligned with the corresponding charging pins in the charger, the efficiency of the charging process will be reduced. A metal sheet may also be embedded in the hearing aid so that the corresponding magnet in the charger can be arranged to generate an attractive force to attract the metal sheet. The metal sheet / magnet combination provides a force that causes the hearing aid to be pressed against the surface of the charger, thereby increasing the contact force between the charging pads in the hearing aid and the charging pins in the charger.

[0100] Figure 5 It is also shown that the middle portion 4 extends along or around the axis B. Figure 5 In FIG, the hearing aid 10 is viewed from a different angle. Here, it can be seen that the receiver in the front portion 2 has a second angle of 43.72 degrees relative to the second axis B, which helps the hearing aid adapt to the relative shape of the ear canal. The second angle can be measured relative to the axis A. As can be seen from the figure, the second angle (β) is not zero.

[0101] The middle part 4 includes a first microphone 7 facing outwards to pick up external sounds. Figure 3 As shown, the first microphone can be placed in a side area of ​​the end surface of the middle part 4.

[0102] Although not shown, the central portion 4 can be configured to include a second, outward-facing microphone for directional functionality. The second microphone can be positioned adjacent to the first microphone. When the hearing aid is placed in the user's ear canal, the first and second microphones can be positioned (substantially) in a horizontal line. This helps the signal processor establish a directional signal.

[0103] Although not shown, a microphone can be arranged near the speaker unit 3, i.e., at the front, facing into the ear canal. This is an inward-facing microphone. The inward-facing microphone can be formed by an accelerometer, and the signal from there is processed to detect the user's own voice or other sounds present in the space between the hearing aid / dome and the eardrum. The signal from the inward-facing microphone can be used to counteract the occlusion effect. The inward-facing microphone can be directed toward the ear canal wall rather than toward the eardrum.

[0104] The hearing aid may be equipped with an accelerometer. Such an accelerometer may be placed in the central portion 4, possibly together with other electronic components on the substrate.

[0105] A non-contact sensor may be located on the front 2 or center 4 of the hearing aid. Suitable sensors include one or more of the following: a thermal sensor, a gyroscope, and / or a PPG, and / or a galvanic skin response sensor for measuring EEG, EMG, and / or ECG. The appropriate sensor is selected based on the physiological value to be monitored or determined. If multiple sensors are present in the hearing device, one or more of them can be selectively activated to perform one or more measurements.

[0106] Although not shown, a hearing aid according to the present invention may include a flexible joint in or within the middle portion to accommodate changes in the angle of the user's ear canal. This may be a ball-and-socket joint, or a flexible portion or connection structure, for example made of different materials, that allows the two portions to be (slightly) adjusted relative to each other to provide a more comfortable wearing experience for the user.

[0107] One goal of the hearing aids disclosed herein is to provide a ready-to-wear, completely in-the-canal hearing aid that provides an instant, customized fitting experience. With the disclosed hearing aids, the wearer does not need to sacrifice hearing aid size for performance. Ready-to-wear, completely in-the-canal (CIC) devices may include the following key features:

[0108] - Completely invisible due to its small size and location in the ear canal;

[0109] - Rechargeable battery;

[0110] -2.4GHz Bluetooth wireless connection;

[0111] - Wireless / inductive communication between two hearing aids;

[0112] - Built-in accelerometer for tap control and other future uses.

[0113] This hearing aid allows for immediate and hassle-free fitting, eliminating the long wait times associated with other custom-fitted hearing aids. From the perspective of a hearing healthcare professional, the fitting process for this hearing aid is similar to that of currently available Receiver-in-the-Ear (RITE) devices. The hearing aid is secured in the ear canal using a dome or custom-fitted ear mold shell, and the hearing aid utilizes an interface for this purpose. To achieve a high fit rate, this hearing aid is designed to be as compact as possible. Thin walls are achieved through epoxy potting technology, which encapsulates the internal electronics and eliminates the need for a traditional plastic housing. The amplifier includes a flexible circuit board that wraps around the battery to minimize the overall size of the hearing aid. "Wrapped around the battery" should be understood as meaning that portions of the flexible circuit board are shaped, such as bent, and placed adjacent to the battery, such that two or more portions of the flexible circuit board are adjacent to different sides of the battery. A flexible circuit board does not necessarily mean that the entire substrate is flexible; rather, it means that the substrate comprising the flexible circuit board can be bent or folded at least in the required areas or locations to allow the flexible circuit board to be wrapped around the battery. The hearing aid is placed in the ear canal, and the connection is achieved by placing the antenna on the outer ear. The antenna also acts as a pull cord. The microphone's inlet faces the outside of the ear and picks up external sound.

[0114] Based on the different shapes and curvatures of the ear canal, the angle, inclination and height affect the fit rate. The optimal angle depends on the length, width and height of the device before and after the angle change. When the size of the hearing aid body, receiver housing or earplug changes, the angle, inclination, height and fit rate of the receiver should be re-evaluated. The angle of the receiver around the first axis relative to the insertion side can be around 20 degrees to 40 degrees, such as around 25 degrees to 35 degrees, such as around 34.5 degrees, to accommodate the first bend in the ear canal. The angle of the receiver around the second axis can be around 20 degrees to 50 degrees, such as around 30 degrees to 45 degrees, such as around 45 degrees, to accommodate the relative shape of the ear canal.

[0115] The antenna may be configured such that a first portion has a first thickness and a second portion has a second, smaller thickness. This helps maintain a minimum distance between the antenna and the outer ear when the device is inserted into the ear canal of a user. The thickness may be tapered so that the transition from the first thickness to the second thickness is gradually decreasing across a certain length of the antenna. Thicker portions of the antenna, such as those closest to the connection point of the antenna to the hearing aid body / housing, help maintain a minimum distance between the antenna and the outer ear / skin of the user's ear. Additionally, the increased stiffness helps maintain the antenna in a predetermined orientation relative to the ear canal, while the reduced stiffness helps the antenna conform to the shape of the outer ear at its distal end while the hearing aid is being worn by the user.

[0116] Figure 6 A hearing aid antenna is schematically shown, having an overmolded first portion and a thinner second portion. The portion closest to the hearing aid housing / body is the overmolded portion and at least partially tapers. The first portion exits the housing at a specific angle. The ear canal is generally elliptical, with a major axis and a minor axis. The hearing aid does not completely fill the ear canal, thereby preventing occlusion. The antenna deflects / steers when it contacts the bottom of the outer ear.

[0117] The hearing aid according to the present invention, Figure 6 As shown, the antenna can be configured so that the transition from a first thickness to a second thickness gradually changes across a certain length of the antenna. The first portion of the antenna, i.e., the portion that connects to the hearing aid body / housing, can have a first thickness, while the second portion can have a second, smaller thickness. Due to its greater thickness, the first portion of the antenna is stiffer than the second portion. Therefore, the first portion of the antenna is better able to maintain its shape than the second portion. However, the first portion of the antenna should still be able to deform to conform to the outer ear when the outer ear is close to the antenna. However, the increased thickness will ensure a minimum distance between the antenna and the outer ear / skin. This minimum distance helps improve the performance of the antenna, for example, by reducing coupling between the antenna and the user's skin / ear / head.

[0118] The structural features of the apparatus described above, described in detail in the "Detailed Description of the Invention" and defined in the claims may be combined with the steps of the method of the present invention when appropriately replaced by corresponding processes.

[0119] Unless expressly stated otherwise, the singular forms "a", "the" and "the" used herein include the plural form (i.e., having the meaning of "at least one"). It should be further understood that the terms "having", "including" and / or "comprising" used in the specification indicate the presence of the described features, integers, steps, operations, elements and / or parts, but do not exclude the presence or addition of one or more other features, integers, steps, operations, elements, parts and / or combinations thereof. It should be understood that, unless expressly stated otherwise, when an element is referred to as being "connected" or "coupled" to another element, it may be directly connected or coupled to the other element, or there may be an intermediate intervening element. The term "and / or" as used herein includes any and all combinations of one or more listed related items. Unless expressly stated otherwise, the steps of any method disclosed herein do not have to be performed in the exact order disclosed.

[0120] It should be understood that references in this specification to "an embodiment," "an embodiment," "an aspect," or features that "may" include, mean that the specific features, structures, or characteristics described in conjunction with that embodiment are included in at least one embodiment of the present invention. Furthermore, the specific features, structures, or characteristics may be combined as appropriate in one or more embodiments of the present invention. The foregoing description is provided to enable those skilled in the art to practice the various aspects described herein. Various modifications will be apparent to those skilled in the art.

[0121] The claims are not limited to the aspects shown herein, but rather have the full scope consistent with the claim language in which, unless expressly stated otherwise, elements referred to in the singular do not mean "one and only one" but rather "one or more." Unless expressly stated otherwise, the term "some" means one or more.

[0122] Reference numerals

[0123] 1-Hearing aids

[0124] 2-Front

[0125] 3-speaker unit

[0126] 4-Central

[0127] 5-Rear

[0128] 6-antenna

[0129] 7-First Microphone

[0130] 8-Second microphone

[0131] 9-Inward-facing microphone

[0132] 10-Metal pad

[0133] 11- Dome or earplugs

[0134] A-axis

[0135] B-Second axis

[0136] α-first angle

[0137] β - second angle.

Claims

1. A hearing aid (1) configured to be placed in an ear canal of a user, the hearing aid comprising: a front portion (2) comprising an output transducer (3) configured to transmit an acoustic signal, the front portion being configured to be placed in an ear canal of a user; a rear portion (5) including an antenna (6); a central part (4) comprising a rechargeable battery and a substrate carrying one or more electronic components, the substrate being arranged at the battery, the central part being at least partially encapsulated by a polymeric material; wherein the middle portion (4) extends longitudinally and defines an axis (A) between the front portion (2) and the rear portion (5); The front portion (2) has a first non-zero angle (α) relative to the axis (A). 2 . The hearing aid of claim 1 , wherein the antenna in the rear portion is connected to an outer surface configured to extend substantially parallel to an opening of a user's ear canal when worn.

3. The hearing aid according to claim 1, wherein the front part (2) has a second angle (β) with respect to the axis (A). The hearing aid according to claim 3 , wherein the second angle (β) is non-zero.

5. The hearing aid according to claim 1, wherein the middle part (4) comprises a first microphone (7) facing outside the ear canal to pick up external sounds.

6. The hearing aid according to claim 5, wherein the middle part (4) comprises a second microphone (8) facing outwards, the hearing aid being configured to create a directional signal based on the signals from the first microphone and the second microphone.

7. The hearing aid according to claim 1, wherein the speaker unit (3) comprises an inwardly facing microphone (9) arranged to face into the ear canal.

8. The hearing aid according to claim 1, wherein the middle portion (4) comprises at least one exposed metal pad (10) configured to receive a charging signal from a charging unit.

9. The hearing aid according to claim 1, wherein the front part (2) comprises an earplug or dome (11) connected to a speaker unit (3).

10. The hearing aid according to claim 9, wherein the earplug (11) is a replaceable earplug configured to be in contact with the ear canal when the hearing aid is placed in the ear canal.

11. The hearing aid according to claim 9, wherein the earplug (11) is a custom-made ear mold.

12. The hearing aid according to claim 1, wherein the middle part (4) comprises an accelerometer.

13. The hearing aid according to claim 1, wherein the front part (2) or the middle part (4) comprises a contactless sensor, such as a thermal sensor, a gyroscope, and / or a PPG, and / or a galvanic skin response sensor for measuring EEG, EMG and / or ECG.

14. The hearing aid according to claim 1, wherein the hearing aid (1) further comprises a coil for binaural communication and / or wireless charging.

15. The hearing aid according to claim 1, wherein the middle portion (4) comprises a flexible joint for adapting to any angular changes of the user's ear canal.

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