EP4607960A1

EP4607960A1 - Improved sealing dome for hearing aid, and hearing aid with improved sealing dome

Info

Publication number: EP4607960A1
Application number: EP24191627.9A
Authority: EP
Inventors: Silas BRINKBÆK-HUMMELMOSE; Nicolas Kjær HØJFELDT; Søren Skall Toke
Original assignee: Oticon AS
Current assignee: Oticon AS
Priority date: 2024-07-30
Filing date: 2024-07-30
Publication date: 2025-08-27

Abstract

A sealing dome for a hearing aid is disclosed. The sealing dome comprises a shell comprising an outer surface, an inner surface, and a plurality of arms extending from the outer surface to the inner surface to define a plurality of chambers, a filler held within each of the plurality of chambers, wherein the filler has a lower shore value than the shell, a lumen extending between a proximal end of the sealing dome and a distal end of the sealing dome, wherein a radially outer edge of the lumen is defined by the inner surface of the shell, and an interface located at least partially within lumen and configured for a releasable connection to the hearing aid.

Description

TECHNICAL FIELD

The present application relates to the field of hearing aids. In particular, the present disclosure generally relates to improved sealing domes for hearing aids, and hearing aids with improved sealing domes.

SUMMARY

A sealing dome and a hearing aid with a sealing dome:

In an aspect of the present disclosure, a sealing dome for a hearing aid is disclosed. The sealing dome includes a shell. The shell comprises an outer surface, an inner surface, and a plurality of arms. The plurality of arms extend from the outer surface to the inner surface to define a plurality of chambers. The sealing dome includes a filler. The filler is held within each of the plurality of chambers. The filler has a lower shore value than the shell. The sealing dome includes a lumen. The lumen extends between a proximal end of the sealing dome and a distal end of the sealing dome. A radially outer edge of the lumen is defined by the inner surface of the shell. The sealing dome further can include an interface. The interface is located at least partially within the lumen. The interface is configured for a releasable connection to the hearing aid.
Advantageously, adding a mechanical structure, such as the chambers and/or the plurality of arms, can allow the sealing dome to at least partially collapse on itself, therefore closing any potential leaking scenarios caused by bending/buckling of the sealing dome. Further, the mechanical structure, such as the chambers and/or the plurality of arms, can also be substantial enough to retain mechanical integrity of the sealing dome to prevent full collapse when inserting the sealing dome into the ear canal, thereby improving retention of the sealing dome within the ear canal.
Advantageously, adding a mechanical structure to the sealing dome of the hearing aid, such as the chambers and/or the plurality of arms, can allow the sealing dome to at least partially collapse on itself, therefore closing any potential leaking scenarios caused by bending/buckling of the sealing dome and improving audio received by a user of the hearing aid. Further, the mechanical structure, such as the chambers and/or the plurality of arms, can also be substantial enough to retain mechanical integrity of the sealing dome to prevent full collapse when inserting the sealing dome into the ear canal, thereby improving retention of the hearing aid for the user.
The sealing dome (e.g., seal) can be configured for use with a hearing aid. For example, the sealing dome can be configured for use with a receiver-in-the-ear (RITE) and/or behind-the-ear (BTE) hearing aid. The particular type of hearing aid is not limiting. The sealing dome can be separate from the hearing aid, for example configured to connect with a hearing aid. The sealing dome can be attached to a hearing aid.
The sealing dome includes a shell. The shell can be a radially outermost surface of the sealing dome. The shell can define an outer surface, in particular a radially outer surface, of the sealing dome. The shell can extend from a proximal end of the sealing dome to a distal end of the sealing dome. The shell can be bulbous. The shell can be tapered. The shell can have a circular or ovaloid cross section. A distance between opposite radial sides of the shell can vary depending on the longitudinal location.
The shell can have an outer surface. The outer surface can be a radially outer surface. The outer surface can be a radially outermost surface of the sealing dome. The outer surface can define an outer surface, in particular a radially outer surface, of the sealing dome. The outer surface and the shell can be used interchangeably.
The shell can be a radially outermost innermost of the sealing dome. The shell can define an inner surface, in particular a radially inner surface, of the sealing dome.
The shell can have an inner surface. The inner surface can be a radially inner surface. The inner surface can be a radially innermost surface of the sealing dome. The inner surface can define an inner surface, in particular a radially inner surface, of the sealing dome. The inner surface can define a radially outer edge of the lumen.
The outer surface can be radially spaced apart from the inner surface. The outer surface can be parallel to the inner surface. A cross section of the inner surface can be circular or ovaloid. A cross section of the outer surface can be circular or ovaloid. A distance between opposite radial sides of the inner surface can vary depending on the longitudinal location.
The shell can include an arm extending from the outer surface to the inner surface. The shell can include a plurality of arms extending from the outer surface to the inner surface. The shell can include a plurality of arms extending from the outer surface to the inner surface to define a plurality of chambers. In cross section, each of the plurality of chambers can be defined by the inner surface, the outer surface, and two of the plurality of arms.
The plurality of arms may be one or more of 2, 3, 4, 5, 6, 7, 8, 9, 10, 11, or 12 arms. The plurality of chambers may be 2, 3, 4, 5, 6, 7, 8, 9, or 10 chambers.
Each of the plurality of chambers can extend a longitudinal length of the shell. In certain examples, multiple chambers can be formed in a longitudinal length of the shell. Each of the multiple chambers can be sealed at a distal longitudinal end and/or a proximal longitudinal end. In one or more example sealing domes, each of the plurality of chambers have the same radial cross section dimensions. In one or more example sealing domes, at least two of the plurality of chambers have the same radial cross section dimensions.
In one or more example, the shell can have a thickness of 0.07-0.25mm. In some examples, at least one of: the outer surface, the inner surface, and the plurality of arms can have a thickness of 0.07-0.25mm. In certain examples, each of the of the outer surface, the inner surface, or the plurality of arms have a thickness of 0.07-0.25mm.
In one or more example, the shell can have a thickness of 0. 15mm. In some examples, at least one of: the outer surface, the inner surface, and the plurality of arms can have a thickness of 0.15mm. In certain examples, each of the of the outer surface, the inner surface, or the plurality of arms have a thickness of 0.15mm.
Optionally, the shell can include one or more vents extending longitudinal along the outer surface. The one or more vents can be considered cutouts (e.g., carveouts) into the outer surface.
The sealing dome includes a filler. The filler can be held (e.g., contained, stored, accommodated by) by at least one of the plurality of chambers. The filler can be held in all of the plurality of chambers. The filler can be held in a portion of the plurality of chambers.
The filler can have a lower shore value (e.g., shore hardness) than the shell. The shore value can be defined, for example, by a shore durometer. In other words, the filler can have a lower hardness than the shell. The shell can be a polymer. The shell can be a compressible polymer. The filler can be a polymer. The filler can be a compressible polymer.
The filler can be a foam filler. The filler can be a silicone filler. The filler can be a soft silicone filler. The filler can be a silicone foam. For example, the filler can be a soft silicone filler having a short value of around A5 (or 0030). The filler can be a gel filler. For example, the filler can be a gel filler having a shore value of around A01 (or 0010). In certain examples, the filler has a shore value of 0030 to 0060 (or A06), preferably between 0030 and 0040 (or A04). In certain examples, the fille has a shore value of A3 (or 0048). In certain examples, the filler has a shore hardness of A02-A10.
The shell can be a silicone shell. The shell can have a shore hardness of A40. The shell can have a shore hardness of 0070 to 0085. The shell can have a shore hardness of 0078.
The filler can fill the plurality of chambers. The filler can bond to the shell. The filler can melt together with the shell. The filler and the shell can attract to one another so that a bonding of the filler and the shell can occur.
The sealing dome includes a lumen. The lumen can extend between a proximal end of the sealing dome and a distal end of the sealing dome. The lumen can have the same diameter along its length. The lumen can include one or more tapers. The lumen can include one or more steps. A radially outer edge of the lumen is defined by the inner surface of the shell. The lumen can be generally radially central within the sealing dome, such as within the outer surface of the shell.
The sealing dome includes an interface The interface can be located at least partially within the lumen. The interface may extend out past the distal end of the shell. The interface is configured for a releasable connection to a hearing aid. For example, the interface is configured for a releasable connection with a receiver of a hearing aid. Accordingly, the sealing dome can be removed from the hearing aid and replaced with a different sealing dome.
In one or more example sealing domes, each of the plurality arms have the same length. Each of the plurality of arms can have the same radial length. Each of the plurality of arms can have the same length between the outer surface and the inner surface. For example, the inner surface can have the same radial distance from the outer surface. The lumen can be generally circular. The lumen can be shaped the same as the shell.
In one or more example sealing domes, a first portion of the plurality of arms has a first length and a second portion of the plurality of arms has a second length different from the first length. A first portion of the plurality of arms has a first radial length and a second portion of the plurality of arms has a second radial length different from the first radial length. For example, the outer surface and the inner surface may have varying radial distances. In one or more example sealing domes, the inner surface varies in radial distance from the outer surface. The inner surface may have variable radial dimensions.
In one or more example sealing domes, each of the plurality of arms is orthogonal to the outer surface. In one or more example sealing domes, each of the plurality of arms is orthogonal to the inner surface. In one or more example sealing domes, at least one of the plurality of arms is orthogonal to the outer surface and/or the inner surface.
In one or more example sealing domes, at least one of the plurality of arms extends at an acute angle from the outer surface. The at least one of the plurality of arms can also extend at an obtuse angle from the outer surface, depending on the measured angle. The at least one of the plurality of arms can extend at an angle non-orthogonal from the outer surface. In one or more example sealing domes, at least one of the plurality of arms extends at an acute angle from the inner surface.
In one or more example sealing domes, each of the plurality of arms extends at an acute angle from the outer surface. In one or more example sealing domes, each of the plurality of arms extends at an acute angle from the inner surface.
In one or more example sealing domes, each of the plurality of arms extends straight between the outer surface and the inner surface. In certain examples, at least one of the plurality of arms includes a bend (e.g., kink, turn, angle change) between the inner surface and the outer surface. In one or more example sealing domes, each of the plurality of arms includes a bend between the inner surface and the outer surface.
In another aspect of the present disclosure, a sealing dome for a hearing aid is disclosed. The hearing dome includes a shell. The sealing dome includes a core. The core is within the shell. The core extends from the shell radially inward to a radially inward surface. The radially inward surface comprises a plurality of cutouts. The plurality of cutouts is configured to direct buckling of the sealing dome. The sealing dome includes a lumen. The lumen extends between a proximal end of the sealing dome and a distal end of the sealing dome. A radially outer edge of the lumen is defined by the radially inwards surface of the core. The sealing dome can include an interface. The interface can be located at least partially within lumen. The interface can be configured for a releasable connection to the hearing aid. The core has a lower shore value than the shell.
Advantageously, adding a mechanical structure, such as the core having the plurality of cutouts, can allow the sealing dome to at least partially collapse on itself, therefore closing any potential leaking scenarios caused by bending/buckling of the sealing dome. Further, the mechanical structure, such as the core having the plurality of cutouts, can also be substantial enough to retain mechanical integrity of the sealing dome to prevent full collapse when inserting the sealing dome into the ear canal, thereby improving retention of the sealing dome within the ear canal.
In another aspect of the present disclosure, a hearing aid is disclosed. The hearing aid includes the sealing dome disclosed above.
Advantageously, adding a mechanical structure to the sealing dome of the hearing aid, such as the core having the plurality of cutouts, can allow the sealing dome to at least partially collapse on itself, therefore closing any potential leaking scenarios caused by bending/buckling of the sealing dome and improving audio received by a user of the hearing aid. Further, the mechanical structure, such as the core having the plurality of cutouts, can also be substantial enough to retain mechanical integrity of the sealing dome to prevent full collapse when inserting the sealing dome into the ear canal, thereby improving retention of the hearing aid for the user.
The sealing dome (e.g., seal) can be configured for use with a hearing aid. For example, the sealing dome can be configured for use with a receiver-in-the-ear (RITE) and/or behind-the-ear (BTE) hearing aid. The particular type of hearing aid is not limiting. The sealing dome can be separate from the hearing aid, for example configured to connect with a hearing aid. The sealing dome can be attached to a hearing aid.
The sealing dome includes a shell. The shell can be a radially outermost surface of the sealing dome. The shell can define an outer surface, in particular a radially outer surface, of the sealing dome.
In one or more example, the shell can have a thickness of 0.07-0.25mm. In one or more example, the shell can have a thickness of 0.15mm
Optionally, the shell can include one or more vents extending longitudinal along a radially outer surface of the shell. The one or more vents can be considered cutouts (e.g., carveouts) into the outer surface.
The sealing dome can include a core. The core can bond to the shell. The core can melt together with the shell. The core and the shell can attract to one another so that a bonding of the filler and the shell can occur.
The core can have a lower shore value (e.g., shore hardness) than the shell. The shore value can be defined, for example, by a shore durometer. In other words, the core can have a lower hardness than the shell. The shell can be a polymer. The shell can be a compressible polymer. The core can be a polymer. The core can be a compressible polymer.
The core can be a foam core. The core can be a silicone core. The core can be a soft silicone core. For example, the core can be a soft core filler having a short value of around A5 (or 0030). The core can be a gel core. For example, the core can be a gel core having a shore value of around 0010. In certain examples, the core has a shore value of 0030 to 0060, preferably between 0030 and 0040.
The shell can be a silicone shell. The shell can have a short hardness of A40.
The core extends from the shell radially inward towards a radially inward surface of the core. The radially inward surface of the core can define the lumen.
The radially inward surface can include a plurality of cutouts (e.g., carveouts). In other words, the radially inward surface can be understood as a circular surface, in cross section, with a plurality of cutouts extending radially towards the shell. The cutouts can be configured to direct buckling of the sealing dome. Buckling happens due to retention of the ear canal when inserting, the radial forces are inflicting or causing the part out of the roundness/oval shape and are causing potential leak areas.
Defining in a different way, the radially inward surface can comprise a plurality of protrusions (e.g., extensions, projections, bumps, lamella). The protrusions can extend into the lumen. The protrusions can be configured to direct buckling of the sealing dome.
In one or more example sealing domes, the radially inwards surface is star-shaped. For example, the star can have 5, 6, 7, 8, 9, or 10 points. The star-shaped can be defined by rounded cutouts and/or sharp cutouts.
In one or more example sealing domes, the radially inwards surface is rounded.
In one or more example sealing domes, the radially inwards surface is irregular.
In one or more example sealing domes, each of the plurality of cutouts is triangular.
In one or more example sealing domes, each of the plurality of cutouts have the same radial dimensions.
The sealing dome includes a lumen. The lumen can extend between a proximal end of the sealing dome and a distal end of the sealing dome. The lumen can have the same diameter along its length. The lumen can include one or more tapers. The lumen can include one or more steps. A radially outer edge of the lumen is defined by the radially inwards surface of the core. The lumen can be generally radially central within the sealing dome, such as within the outer surface of the shell.
The sealing dome includes an interface The interface can be located at least partially within the lumen. The interface may extend out past the distal end of the shell. The interface is configured for a releasable connection to a hearing aid. Accordingly, the sealing dome can be removed from the hearing aid and replaced with a different sealing dome.

Hearing aid

Further disclosed are embodiments of hearing aids including the sealing dome(s) discussed above. The hearing aid can be a RITE or a BTE hearing aid including the sealing dome(s) discussed herein.
The hearing aid may be adapted to provide a frequency dependent gain and/or a level dependent compression and/or a transposition (with or without frequency compression) of one or more frequency ranges to one or more other frequency ranges, e.g. to compensate for a hearing impairment of a user. The hearing aid may comprise a signal processor for enhancing the input signals and providing a processed output signal.
The hearing aid may comprise an output unit for providing a stimulus perceived by the user as an acoustic signal based on a processed electric signal. The output unit may a vibrator of a bone conducting 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 mechanical vibration of a skull bone to the user (e.g. in a bone-attached or bone-anchored hearing aid). The output unit may (additionally or alternatively) comprise a (e.g. wireless) transmitter for transmitting sound picked up-by the hearing aid to another device, e.g. a far-end communication partner (e.g. via a network, e.g. in a telephone mode of operation).
The hearing aid may comprise an input unit for providing an electric input signal representing sound. The input unit may comprise an input transducer, e.g. a microphone, for converting an input sound to an electric input signal. The input unit may comprise a wireless receiver for receiving a wireless signal comprising or representing sound and for providing an electric input signal representing said sound.
The wireless receiver and/or transmitter may e.g. be configured to receive and/or transmit an electromagnetic signal in the radio frequency range (3 kHz to 300 GHz). The wireless receiver and/or transmitter may e.g. be configured to receive and/or transmit an electromagnetic signal in a frequency range of light (e.g. infrared light 300 GHz to 430 THz, or visible light, e.g. 430 THz to 770 THz).
The hearing aid may comprise a directional microphone system adapted to spatially filter sounds from the environment, and thereby enhance a target acoustic source among a multitude of acoustic sources in the local environment of the user wearing the hearing aid. The directional system may be adapted to detect (such as adaptively detect) from which direction a particular part of the microphone signal originates. This can be achieved in various different ways as e.g. described in the prior art. In hearing aids, a microphone array beamformer is often used for spatially attenuating background noise sources. The beamformer may comprise a linear constraint minimum variance (LCMV) beamformer. Many beamformer variants can be found in literature. The minimum variance distortionless response (MVDR) beamformer is widely used in microphone array signal processing. Ideally the MVDR beamformer keeps the signals from the target direction (also referred to as the look direction) unchanged, while attenuating sound signals from other directions maximally. The generalized sidelobe canceller (GSC) structure is an equivalent representation of the MVDR beamformer offering computational and numerical advantages over a direct implementation in its original form.
Most sound signal sources (except the user's own voice) are located far away from the user compared to dimensions of the hearing aid, e.g. a distance d_mic between two microphones of a directional system. A typical microphone distance in a hearing aid is of the order 10 mm. A minimum distance of a sound source of interest to the user (e.g. sound from the user's mouth or sound from an audio delivery device) is of the order of 0.1 m (> 10 d_mic). For such minimum distances, the hearing aid (microphones) would be in the acoustic near-field of the sound source and a difference in level of the sound signals impinging on respective microphones may be significant. A typical distance for a communication partner is more than 1 m (>100 d_mic). The hearing aid (microphones) would be in the acoustic far-field of the sound source and a difference in level of the sound signals impinging on respective microphones is insignificant. The difference in time of arrival of sound impinging in the direction of the microphone axis (e.g. the front or back of a normal hearing aid) is ΔT= d_mic/v_sound=0.01/343 [s]=29 µs, where v_sound is the speed of sound in air at 20°C (343 m/s).
The hearing aid may comprise antenna and transceiver circuitry allowing a wireless link to an entertainment device (e.g. a TV-set), a communication device (e.g. a telephone), a wireless microphone, a separate (external) processing device, or another hearing aid, etc. The hearing aid may thus be configured to wirelessly receive a direct electric input signal from another device. Likewise, the hearing aid may be configured to wirelessly transmit a direct electric output signal to another device. The direct electric input or output signal may represent or comprise an audio signal and/or a control signal and/or an information signal.
In general, a wireless link established by antenna and transceiver circuitry of the hearing aid can be of any type. The wireless link may be a link based on near-field communication, e.g. an inductive link based on an inductive coupling between antenna coils of transmitter and receiver parts. The wireless link may be based on far-field, electromagnetic radiation. Preferably, frequencies used to establish a communication link between the hearing aid and the other device is below 70 GHz, e.g. located in a range from 50 MHz to 70 GHz, e.g. above 300 MHz, e.g. in an ISM range above 300 MHz, e.g. 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 being e.g. defined by the International Telecommunication Union, ITU). The wireless link may be based on a standardized or proprietary technology. The wireless link may be based on Bluetooth technology (e.g. Bluetooth Low-Energy technology, e.g. LE audio), or Ultra WideBand (UWB) technology.
The hearing aid may be constituted by or form part of a portable (i.e. configured to be wearable) device, e.g. a device comprising a local energy source, e.g. a battery, e.g. a rechargeable battery. The hearing aid may e.g. be a low weight, easily wearable, device, e.g. having a total weight less than 100 g, such as less than 20 g, such as less than 5 g.
The hearing aid may comprise a 'forward' (or `signal') path for processing an audio signal between an input and an output of the hearing aid. A signal processor may be located in the forward path. The signal processor may be adapted to provide a frequency dependent gain according to a user's particular needs (e.g. hearing impairment). The hearing aid may comprise an 'analysis' path comprising functional components for analyzing signals and/or controlling processing of the forward path. Some or all signal processing of the analysis path and/or the forward path may be conducted in the frequency domain, in which case the hearing aid comprises appropriate analysis and synthesis filter banks. Some or all signal processing of the analysis path and/or the forward path may be conducted in the time domain.
An analogue electric signal representing an acoustic signal may be converted to a digital audio signal in an analogue-to-digital (AD) conversion process, where the analogue signal is sampled with a predefined sampling frequency or rate f_s, f_s being e.g. in the range from 8 kHz to 48 kHz (adapted to the particular needs of the application) to provide digital samples x_n (or x[n]) at discrete points in time t_n (or n), each audio sample representing the value of the acoustic signal at t_n by a predefined number N_b of bits, N_b being e.g. in the range from 1 to 48 bits, e.g. 24 bits. Each audio sample is hence quantized using N_b bits (resulting in 2^Nb different possible values of the audio sample). A digital sample x has a length in time of 1/f_s, e.g. 50 µs, for f_s = 20 kHz. A number of audio samples may be arranged in a time frame. A time frame may comprise 64 or 128 audio data samples. Other frame lengths may be used depending on the practical application.
The hearing aid may comprise an analogue-to-digital (AD) converter to digitize an analogue input (e.g. from an input transducer, such as a microphone) with a predefined sampling rate, e.g. 20 kHz. The hearing aids may comprise a digital-to-analogue (DA) converter to convert a digital signal to an analogue output signal, e.g. for being presented to a user via an output transducer.
The hearing aid, e.g. the input unit, and or the antenna and transceiver circuitry may comprise a transform unit for converting a time domain signal to a signal in the transform domain (e.g. frequency domain or Laplace domain, Z transform, wavelet transform, etc.). The transform unit may be constituted by or comprise a TF-conversion unit for providing a time-frequency representation of an input signal. The time-frequency representation may comprise an array or map of corresponding complex or real values of the signal in question in a particular time and frequency range. The TF conversion unit may comprise a filter bank for filtering a (time varying) input signal and providing a number of (time varying) output signals each comprising a distinct frequency range of the input signal. The TF conversion unit may comprise a Fourier transformation unit (e.g. a Discrete Fourier Transform (DFT) algorithm, or a Short Time Fourier Transform (STFT) algorithm, or similar) for converting a time variant input signal to a (time variant) signal in the (time-)frequency domain. The frequency range considered by the hearing aid from a minimum frequency f_min to a maximum frequency f_max may comprise a part of the typical human audible frequency range from 20 Hz to 20 kHz, e.g. a part of the range from 20 Hz to 12 kHz. Typically, a sample rate f_s is larger than or equal to twice the maximum frequency f_max, f_s ≥ 2f_max. A signal of the forward and/or analysis path of the hearing aid may be split into a number NI of frequency bands (e.g. of uniform width), where NI is e.g. larger than 5, such as larger than 10, such as larger than 50, such as larger than 100, such as larger than 500, at least some of which are processed individually. The hearing aid may be adapted to process a signal of the forward and/or analysis path in a number NP of different frequency channels (NP ≤ NI). The frequency channels may be uniform or non-uniform in width (e.g. increasing in width with frequency), overlapping or non-overlapping.
The hearing aid may be configured to operate in different modes, e.g. a normal mode and one or more specific modes, e.g. selectable by a user, or automatically selectable. A mode of operation may be optimized to a specific acoustic situation or environment, e.g. a communication mode, such as a telephone mode. A mode of operation may include a low-power mode, where functionality of the hearing aid is reduced (e.g. to save power), e.g. to disable wireless communication, and/or to disable specific features of the hearing aid.
The hearing aid may comprise a number of detectors configured to provide status signals relating to a current physical environment of the hearing aid (e.g. the current acoustic environment), and/or to a current state of the user wearing the hearing aid, and/or to a current state or mode of operation of the hearing aid. Alternatively or additionally, one or more detectors may form part of an external device in communication (e.g. wirelessly) with the hearing aid. An external device may e.g. comprise another hearing aid, a remote control, and audio delivery device, a telephone (e.g. a smartphone), an external sensor, etc.
One or more of the number of detectors may operate on the full band signal (time domain). One or more of the number of detectors may operate on band split signals ((time-) frequency domain), e.g. in a limited number of frequency bands.
The number of detectors may comprise a level detector for estimating a current level of a signal of the forward path. The detector may be configured to decide whether the current level of a signal of the forward path is above or below a given (L-)threshold value. The level detector operates on the full band signal (time domain). The level detector operates on band split signals ((time-) frequency domain).
The hearing aid may comprise a voice activity detector (VAD) for estimating whether or not (or with what probability) an input signal comprises a voice signal (at a given point in time). A voice signal may in the present context be taken to include a speech signal from a human being. It may also include other forms of utterances generated by the human speech system (e.g. singing). The voice activity detector unit may be adapted to classify a current acoustic environment of the user as a VOICE or NO-VOICE environment. This has the advantage that time segments of the electric microphone signal comprising human utterances (e.g. speech) in the user's environment can be identified, and thus separated from time segments only (or mainly) comprising other sound sources (e.g. artificially generated noise). The voice activity detector may be adapted to detect as a VOICE also the user's own voice. Alternatively, the voice activity detector may be adapted to exclude a user's own voice from the detection of a VOICE.
The hearing aid may comprise an own voice detector for estimating whether or not (or with what probability) a given input sound (e.g. a voice, e.g. speech) originates from the voice of the user of the system. A microphone system of the hearing aid may be adapted to be able to differentiate between a user's own voice and another person's voice and possibly from NON-voice sounds.
The number of detectors may comprise a movement detector, e.g. an acceleration sensor. The movement detector may be configured to detect movement of the user's facial muscles and/or bones, e.g. due to speech or chewing (e.g. jaw movement) and to provide a detector signal indicative thereof.
The hearing aid may comprise a classification unit configured to classify the current situation based on input signals from (at least some of) the detectors, and possibly other inputs as well. In the present context `a current situation' may be taken to be defined by one or more of

a) the physical environment (e.g. including the current electromagnetic environment, e.g. the occurrence of electromagnetic signals (e.g. comprising audio and/or control signals) intended or not intended for reception by the hearing aid, or other properties of the current environment than acoustic);
b) the current acoustic situation (input level, feedback, etc.), and
c) the current mode or state of the user (movement, temperature, cognitive load, etc.);
d) the current mode or state of the hearing aid (program selected, time elapsed since last user interaction, etc.) and/or of another device in communication with the hearing aid.

The classification unit may be based on or comprise a neural network, e.g. a recurrent neural network, e.g. a trained neural network.
The hearing aid may comprise an acoustic (and/or mechanical) feedback control (e.g. suppression) or echo-cancelling system. Adaptive feedback cancellation has the ability to track feedback path changes over time. It is typically based on a linear time invariant filter to estimate the feedback path but its filter weights are updated over time. The filter update may be calculated using stochastic gradient algorithms, including some form of the Least Mean Square (LMS) or the Normalized LMS (NLMS) algorithms. They both have the property to minimize the error signal in the mean square sense with the NLMS additionally normalizing the filter update with respect to the squared Euclidean norm of some reference signal.
The hearing aid may further comprise other relevant functionality for the application in question, e.g. compression, noise reduction, etc.
The hearing aid may comprise a hearing instrument, e.g. a hearing instrument adapted for being located at the ear or fully or partially in the ear canal of a user.

Definitions:

In the present context, a hearing aid, e.g. a hearing instrument, refers to a device, which is adapted to improve, augment and/or protect the hearing capability of a user by receiving acoustic signals from the user's surroundings, generating corresponding audio signals, possibly modifying the audio signals and providing the possibly modified audio signals as audible signals to at least one of the user's ears. Such audible signals may e.g. be provided in the form of acoustic signals radiated into the user's outer ears and/or acoustic signals transferred as mechanical vibrations to the user's inner ears through the bone structure of the user's head and/or through parts of the middle ear.
The hearing aid may be configured to be worn in any known way, e.g. as a unit arranged behind the ear with a tube leading radiated acoustic signals into the ear canal or with an output transducer, e.g. a loudspeaker, arranged close to or in the ear canal, as a unit entirely or partly arranged in the pinna and/or in the ear canal, as a unit, e.g. a vibrator, attached to a fixture implanted into the skull bone, etc. The hearing aid may comprise a single unit or several units communicating (e.g. acoustically, electrically or optically) with each other. The loudspeaker may be arranged in a housing together with other components of the hearing aid, or may be an external unit in itself (possibly in combination with a flexible guiding element, e.g. a dome-like element).
A hearing aid may be adapted to a particular user's needs, e.g. a hearing impairment. A configurable signal processing circuit of the hearing aid may be adapted to apply a frequency and level dependent compressive amplification of an input signal. A customized frequency and level dependent gain (amplification or compression) may be determined in a fitting process by a fitting system based on a user's hearing data, e.g. an audiogram, using a fitting rationale (e.g. adapted to speech). The frequency and level dependent gain may e.g. be embodied in processing parameters, e.g. 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 circuit of the hearing aid.
A `hearing system' refers to a system comprising one or two hearing aids, and a `binaural hearing system' refers to a system comprising two hearing aids and being adapted to cooperatively provide audible signals to both of the user's ears. Hearing systems or binaural hearing systems may further comprise one or more `auxiliary devices', which communicate with the hearing aid(s) and affect and/or benefit from the function of the hearing aid(s). Such auxiliary devices may include at least one of a remote control, a remote microphone, an audio gateway device, an entertainment device, e.g. a music player, a wireless communication device, e.g. a mobile phone (such as a smartphone) or a tablet or another device, e.g. comprising a graphical interface. Hearing aids, hearing systems or binaural hearing systems may e.g. be used for compensating for a hearing-impaired person's loss of hearing capability, augmenting or protecting a normal-hearing person's hearing capability and/or conveying electronic audio signals to a person. Hearing aids or hearing systems may e.g. form part of or interact with public-address systems, active ear protection systems, handsfree telephone systems, car audio systems, entertainment (e.g. TV, music playing or karaoke) systems, teleconferencing systems, classroom amplification systems, etc.
The invention is set out in the appended set of claims.

BRIEF DESCRIPTION OF DRAWINGS

The aspects of the disclosure may be best understood from the following detailed description taken in conjunction with the accompanying figures. The figures are schematic and simplified for clarity, and they just show details to improve the understanding of the claims, while other details are left out. Throughout, the same reference numerals are used for identical or corresponding parts. The individual features of each aspect may each be combined with any or all features of the other aspects. These and other aspects, features and/or technical effect will be apparent from and elucidated with reference to the illustrations described hereinafter in which:

FIG. 1 schematically shows a second RITE-style embodiment of a hearing aid according to the present disclosure,
FIGS. 2A-2C illustrate cross sections of example sealing domes according to the disclosure,
FIGS. 3A-3C illustrate cross sections of example sealing domes according to the disclosure,
FIGS. 4A-4D illustrate cross sections of example sealing domes according to the disclosure,
FIGS. 5A-5C illustrate cross sections of example sealing domes according to the disclosure,
FIGS. 6A-6G illustrate cross sections of example sealing domes according to the disclosure, and
FIG. 7 illustrates a photograph of a cross section of an example sealing dome according to the disclosure.

The figures are schematic and simplified for clarity, and they just show details which are essential to the understanding of the disclosure, while other details are left out. Throughout, the same reference signs are used for identical or corresponding parts.
Further scope of applicability of the present disclosure will become apparent from the detailed description given hereinafter. However, it should be understood that the detailed description and specific examples, while indicating preferred embodiments of the disclosure, are given by way of illustration only. Other embodiments may become apparent to those skilled in the art from the following detailed description.

DETAILED DESCRIPTION OF EMBODIMENTS

The detailed description set forth below in connection with the appended drawings is intended as a description of various configurations. The detailed description includes specific details for the purpose of providing a thorough understanding of various concepts. However, it will be apparent to those skilled in the art that these concepts may be practiced without these specific details. Several aspects of the apparatus and methods are described by various blocks, functional units, modules, components, circuits, steps, processes, algorithms, etc. (collectively referred to as "elements"). Depending upon particular application, design constraints or other reasons, these elements may be implemented using electronic hardware, computer program, or any combination thereof.
The electronic hardware may include micro-electronic-mechanical systems (MEMS), integrated circuits (e.g. application specific), microprocessors, microcontrollers, digital signal processors (DSPs), field programmable gate arrays (FPGAs), programmable logic devices (PLDs), gated logic, discrete hardware circuits, printed circuit boards (PCB) (e.g. flexible PCBs), and other suitable hardware configured to perform the various functionality described throughout this disclosure, e.g. sensors, e.g. for sensing and/or registering physical properties of the environment, the device, the user, etc. Computer program shall be construed broadly to mean instructions, instruction sets, code, code segments, program code, programs, subprograms, software modules, applications, software applications, software packages, routines, subroutines, objects, executables, threads of execution, procedures, functions, etc., whether referred to as software, firmware, middleware, microcode, hardware description language, or otherwise.
The present application relates to the field of sealing domes, in particular for a hearing aid.
FIG. 1 illustrates an example embodiment of a BTE hearing aid including a sealing dome according to the disclosure. In particular, FIG. 1 shows an embodiment of a hearing aid (HA) (e.g., hearing device) according to the present disclosure. The exemplary hearing aid (HA, is of a particular style (sometimes termed receiver-in-the ear, or RITE, style) comprising a BTE-part (BTE) adapted for being located at or behind an ear of a user, and an ITE-part (ITE) adapted for being located in or at an ear canal of the user's ear and comprising a receiver (loudspeaker). The BTE-part and the ITE-part are connected (e.g. electrically connected) by a connecting element (IC) and internal wiring in the ITE- and BTE-parts (cf. e.g. wiring Wx in the BTE-part). The connecting element may alternatively be fully or partially constituted by a wireless link between the BTE- and ITE-parts (or by an acoustic tube, if the loudspeaker is located in the BTE-part).
In the embodiment of a hearing aid in FIG. 1, the BTE part comprises an input unit comprising two (first) input transducers (e.g. microphones) (M_BTE1, M_BTE2), each for providing an (first) electric input audio signal representative of an input sound signal (S_BTE) (originating from a sound field S around the hearing aid). The input unit further comprises two wireless receivers (WLR₁, WLR₂) (or transceivers) for providing respective directly received auxiliary audio and/or control input signals (and/or allowing transmission of audio and/or control signals to other devices, e.g. to another hearing aid, or to a remote control or processing device, or a telephone). The hearing aid (HA) comprises a substrate (SUB) whereon a number of electronic components are mounted, including a memory (MEM), e.g. storing different hearing aid programs (e.g. parameter settings defining such programs, or parameters of algorithms) and/or hearing aid configurations, e.g. input source combinations (M_BTE1, M_BTE2, M_ITE,env, M_ITE,ed, WLR₁, WLR₂), e.g. optimized for a number of different listening situations. In a specific mode of operation, one or more directly received auxiliary electric signals may be used together with one or more of the electric input signals from the microphones to provide a beamformed signal provided by applying appropriate complex weights to (at least some of) the respective signals, e.g. to provide an enhanced target signal to the user (or an estimate of the user's own voice to another application, e.g. a communication partner, or a voice control interface).
The substrate (SUB) further comprises a configurable signal processor (DSP, e.g. a digital (audio) signal processor), e.g. including a processor for applying a frequency and level dependent gain, e.g. providing hearing loss compensation, beamforming, noise reduction, filter bank functionality, and other digital functionality of a hearing aid. The configurable signal processor (DSP) is adapted to access the memory (MEM. The configurable signal processor (DSP) is further configured to process one or more of the electric input audio signals and/or one or more of the directly received auxiliary audio input signals, based on a currently selected (activated) hearing aid program/parameter setting (e.g. either automatically selected, e.g. based on one or more sensors, or selected based on inputs from a user interface). The mentioned functional units (as well as other components) may be partitioned in circuits and components according to the application in question (e.g. with a view to size, power consumption, analogue vs. digital processing, acceptable latency, etc.), e.g. integrated in one or more integrated circuits, or as a combination of one or more integrated circuits and one or more separate electronic components (e.g. inductor, capacitor, etc.). The configurable signal processor (DSP) provides a processed audio signal, which is intended to be presented to a user. The substrate further comprises a front-end IC (FE) for interfacing the configurable signal processor (DSP) to the input and output transducers, etc., and typically comprising interfaces between analogue and digital signals (e.g. interfaces to microphones and/or loudspeaker(s)). The input and output transducers may be individual separate components, or integrated (e.g. MEMS-based) with other electronic circuitry.
The hearing aid (HA) further comprises an output unit (e.g. an output transducer) providing stimuli perceivable by the user as sound based on a processed audio signal from the processor or a signal derived therefrom. In the embodiment of a hearing aid in FIG. 1, the ITE part comprises the output transducer in the form of a loudspeaker (also termed a 'receiver') (SPK) for converting an electric signal to an acoustic (air borne) signal, which (when the hearing aid is mounted at an ear of the user) is directed towards the ear drum (Ear drum), where sound signal (S_ED) is provided.
As shown, the ITE-part further comprises sealing dome, (DO) for guiding and positioning the ITE-part in the ear canal (Ear canal) of the user. The sealing dome can be any of the sealing domes discussed herein.
The ITE-part may (as shown in FIG. 1) further comprise a further (first) input transducer, e.g. a microphone (M_ITE,env), facing the environment for providing an electric input audio signal representative of an input sound signal (S_ITE) at the ear canal. The ITE-part may (as shown in FIG. 1) further comprise a further (second) input transducer, e.g. a microphone (M_ITE,ed), facing the eardrum for providing an (second) electric input audio signal representative of the sound signal (S_ED = S_dir + S_HI) at the eardrum.
Propagation of sound (S_ITE) from the environment to a residual volume at the ear drum via direct acoustic paths through the sealing dome (DO) are indicated in FIG. 1 by dashed arrows (denoted Direct path). The directly propagated sound (indicated by sound fields S_dir) is mixed with sound from the hearing aid (HA) (indicated by sound field S_HI) to a resulting sound field (S_ED) at the ear drum. The sound output S_HI of the hearing aid may (at least in a specific mode of operation) be modified in view of the directly propagated sound from the environment to the ear drum to provide adaptive noise cancellation (ANC) and/or adaptive occlusion control (AOC).
Apart from the (acoustic) output and input transducers, the ITE part may comprise other functional components, e.g. (further) detectors, such as electrodes for picking up signals from the user's body (such as brainwave signals, temperature indications, blood-related parameters, heartbeat indications, muscular vibrations, etc.). Such detectors may include one or more of an electroencephalography (EEG) sensor, an electromyography (EMG) sensor, a movement sensor, a temperature sensor, a photoplethysmography (PPG) sensor, an electrooculography (EOG) sensor, etc.
The electric input signals (from (first and/or second) input transducers M_BTE1, M_BTE2, M_ITE,env, M_ITE,ed) 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 considered advantageous for the application in question).
The embodiments of a hearing aid (HA), e.g. a hearing aid, exemplified in 1 is a portable device comprising a battery (BAT), e.g. a rechargeable battery, e.g. based on Li-Ion battery technology, e.g. for energizing electronic components of the BTE- and possibly ITE-parts. In an embodiment, the hearing aid, e.g. a hearing aid, is adapted to provide a frequency dependent gain and/or a level dependent compression and/or a transposition (with or without frequency compression) of one or more frequency ranges to one or more other frequency ranges, e.g. to compensate for a hearing impairment of a user. The BTE-part may e.g. comprise a connector (e.g. a DAI or USB connector) for connecting a 'shoe' with added functionality (e.g. an FM-shoe or an extra battery, etc.), or a programming device, or a charger, or a separate processing device, etc., to the hearing aid (HA).
FIGS. 2A-2C illustrate cross sections of example sealing domes according to the disclosure. The sealing dome can be for a hearing aid, such as the hearing aid of FIG. 1.
As shown, the sealing dome 100 can include a shell 102. The shell 102 includes an outer surface 104 and an inner surface 106. The outer surface 104 and the inner surface 106 are spaced radially apart from one another. The shell 102 further includes a plurality of arms 108 extending from the outer surface 104 to the inner surface 106. This defines a plurality of chambers 110. The shell can have a thickness of 0.07-0.25mm.
A filler 112 can be held within each of the plurality of chambers 110. The filler 112 has a lower shore value than the shell 102.
The sealing dome 100 can further include a lumen 120 extending between a proximal end 101 of the sealing dome 100 and a distal end 103 of the sealing dome 100 (shown in FIG. 2A). A radially outer edge of the lumen 120 is defined by the inner surface 106 of the shell 102.
The sealing dome 100 further includes an interface 130 (simplified for convenience) located at least partially within lumen 120 and configured for a releasable connection to the hearing aid.
As shown in FIG. 2A, each of the plurality of arms 108 has the same length, for example the distance between the outer surface 104 and the inner surface 106. Further, as shown, each of the plurality of arms 108 is orthogonal to the outer surface 104. In this way, each of the plurality of chambers 110 has approximately the same shape. For example, each of the plurality of chambers 108 have the same radial cross section dimensions.
FIGS. 3A-3C illustrate cross sections of example sealing domes according to the disclosure. The sealing dome can be for a hearing aid, such as the hearing aid of FIG. 1. FIGS. 3A-3C can include any and/or all of the features of the sealing dome 100 of FIGS. 2A-2C.
FIGS. 3A-3C illustrate different numbers of chambers of the plurality of chambers 110, depending on the number of arms of the plurality of arms 108. For example, the sealing dome 100 can include 2 chambers, 4 chambers, 12 chambers, etc.
FIGS. 4A-4D illustrate cross sections of example sealing domes according to the disclosure. The sealing dome can be for a hearing aid, such as the hearing aid of FIG. 1. FIGS. 4A-4D can include any and/or all of the features of the sealing dome 100 of FIGS. 2A-3C.
In particular, the sealing dome 100 of FIGS. 4A-4D illustrate where the inner surface 106 varies in radial distance from the outer surface 104. While, for example the sealing dome 100 of FIGS. 3A-3C have an inner surface 106 that forms a circular shape, the inner surface 106 of the sealing dome 100 of FIGS. 4A-4D varies in different ways, allowing for different types of buckling and/or sealing of the sealing dome 100.
Further, FIGS. 4A-4D illustrates a first portion of the plurality of arms 108 has a first length and a second portion of the plurality of arms 108 has a second length different from the first length. This can be due to the variability of the inner surface 106.
FIGS. 5A-5C illustrate cross sections of example sealing domes according to the disclosure. The sealing dome can be for a hearing aid, such as the hearing aid of FIG. 1. FIGS. 5A-5C can include any and/or all of the features of the sealing dome 100 of FIGS. 2A-4D.
FIGS. 5A-5B show a sealing dome 100 where at least one of the plurality of arms 108 extends at an acute angle from the outer surface 104.
FIG. 5C illustrates a sealing dome 100 where each of the plurality of arms 108 includes a bend 502 between the inner surface 106 and the outer surface 104.
FIGS. 6A-6G illustrate cross sections of example sealing domes according to the disclosure. The sealing dome can be for a hearing aid, such as the hearing aid of FIG. 1.
As shown, the sealing dome 600 can include a shell 602. The sealing dome 600 includes a core 610 within the shell 602 (e.g., radially within). The core 610 extends from the shell 602 radially inward to a radially inward surface 612, wherein the radially inward surface 612 comprises a plurality of cutouts 614 configured to direct buckling of the sealing dome 600.
The sealing dome 600 includes a lumen 620 extending between a proximal end of the sealing dome 600 and a distal end of the sealing dome 600. A radially outer edge of the lumen 620 is defined by the radially inwards surface 612 of the core 610.
The sealing dome 600 further includes an interface located at least partially within lumen 620 and configured for a releasable connection to the hearing aid.
The core 610 has a lower shore value than the shell 602.
As shown in FIG. 6A, the radially inwards surface 612 is star-shaped.
FIGS. 6A-6D all show a radially inwards surface 612 that is rounded. Further, FIGS. 6A-6D all show a radially inwards surface 612 that is regular around a circumference.
FIGS. 6A-6F show where each of the plurality of cutouts 614 is triangular. In other words, the edges are pointed rather than rounded. In FIG. 6E, each of the plurality of cutouts 614 have the same radial dimensions.
FIGS. 6F-6G illustrate where the radially inwards surface 612 is irregular. In other words, the radially inwards surface 612 is irregular around the circumference.
FIG. 7 illustrates a photograph of a cross section of an example sealing dome according to the disclosure. The sealing dome can be for a hearing aid, such as the hearing aid of FIG. 1.
It is intended that the structural features of the devices described above, either in the detailed description and/or in the claims, may be combined with steps of the method, when appropriately substituted by a corresponding process.
As used, the singular forms "a," "an," and "the" are intended to include the plural forms as well (i.e. to have the meaning "at least one"), unless expressly stated otherwise. It will be further understood that the terms "includes," "comprises," "including," and/or "comprising," when used in this specification, specify the presence of stated features, integers, steps, operations, elements, and/or components, but do not preclude the presence or addition of one or more other features, integers, steps, operations, elements, components, and/or groups thereof. It will also be understood that when an element is referred to as being "connected" or "coupled" to another element, it can be directly connected or coupled to the other element, but an intervening element may also be present, unless expressly stated otherwise. Furthermore, "connected" or "coupled" as used herein may include wirelessly connected or coupled. As used herein, the term "and/or" includes any and all combinations of one or more of the associated listed items. The steps of any disclosed method are not limited to the exact order stated herein, unless expressly stated otherwise.
It should be appreciated that reference throughout this specification to "one embodiment" or "an embodiment" or "an aspect" or features included as "may" means that a particular feature, structure or characteristic described in connection with the embodiment is included in at least one embodiment of the disclosure. Furthermore, the particular features, structures or characteristics may be combined as suitable in one or more embodiments of the disclosure. The previous description is provided to enable any person skilled in the art to practice the various aspects described herein. Various modifications to these aspects will be readily apparent to those skilled in the art.
The claims are not intended to be limited to the aspects shown herein but are to be accorded the full scope consistent with the language of the claims, wherein reference to an element in the singular is not intended to mean "one and only one" unless specifically so stated, but rather "one or more." Unless specifically stated otherwise, the term "some" refers to one or more.

Claims

A sealing dome for a hearing aid, the sealing dome comprising:
a shell comprising an outer surface, an inner surface, and a plurality of arms extending from the outer surface to the inner surface to define a plurality of chambers;

a filler held within each of the plurality of chambers, wherein the filler has a lower shore value than the shell;

a lumen extending between a proximal end of the sealing dome and a distal end of the sealing dome, wherein a radially outer edge of the lumen is defined by the inner surface of the shell; and

an interface located at least partially within lumen and configured for a releasable connection to the hearing aid.
The sealing dome of claim 1, wherein each of the plurality of arms have the same length.
The sealing dome of claim 1, wherein a first portion of the plurality of arms has a first length and a second portion of the plurality of arms has a second length different from the first length.
The sealing dome of any one of the previous claims, wherein each of the plurality of arms is orthogonal to the outer surface.
The sealing dome of any one of claims 1-3, wherein at least one of the plurality of arms extends at an acute angle from the outer surface.
The sealing dome of any one of the previous claims, wherein each of the plurality of arms includes a bend between the inner surface and the outer surface.
The sealing dome of any one of the previous claims, wherein the inner surface varies in radial distance from the outer surface.
The sealing dome of any one of the previous claims, wherein the shell has a thickness of 0.07-0.25mm.
The sealing dome of any one of the previous claims, wherein each of the plurality of chambers have the same radial cross section dimensions.
A sealing dome for a hearing aid, the sealing dome comprising:
a shell;

a core within the shell, wherein the core extends from the shell radially inward to a radially inward surface, wherein the radially inward surface comprises a plurality of cutouts configured to direct buckling of the sealing dome;

a lumen extending between a proximal end of the sealing dome and a distal end of the sealing dome, wherein a radially outer edge of the lumen is defined by the radially inwards surface of the core; and

an interface located at least partially within lumen and configured for a releasable connection to the hearing aid;

wherein the core has a lower shore value than the shell.
The sealing dome of claim 10, wherein the radially inwards surface is star-shaped.
The sealing dome of claim 10 or 11, wherein the radially inwards surface is rounded.
The sealing dome of any of claims 10-13, wherein the radially inwards surface is irregular.
The sealing dome of any one of claims 10-13, wherein each of the plurality of cutouts is triangular.
Hearing aid comprising the sealing dome of any one of the previous claims.