EP2750412B1 - Localisation améliorée avec rétroaction - Google Patents

Localisation améliorée avec rétroaction Download PDF

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Publication number
EP2750412B1
EP2750412B1 EP12199761.3A EP12199761A EP2750412B1 EP 2750412 B1 EP2750412 B1 EP 2750412B1 EP 12199761 A EP12199761 A EP 12199761A EP 2750412 B1 EP2750412 B1 EP 2750412B1
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EP
European Patent Office
Prior art keywords
btec
hearing aid
output
bte
microphone
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EP12199761.3A
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German (de)
English (en)
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EP2750412A1 (fr
Inventor
Karl-Fredrik Johan Gran
Guilin Ma
Jacob Ulrik Telcs
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GN Hearing AS
Original Assignee
GN Resound AS
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Publication date
Application filed by GN Resound AS filed Critical GN Resound AS
Priority to DK12199761.3T priority Critical patent/DK2750412T3/en
Priority to EP12199761.3A priority patent/EP2750412B1/fr
Priority to US13/872,459 priority patent/US9148733B2/en
Priority to JP2013263656A priority patent/JP5624202B2/ja
Priority to CN201310744757.7A priority patent/CN103916807B/zh
Publication of EP2750412A1 publication Critical patent/EP2750412A1/fr
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Publication of EP2750412B1 publication Critical patent/EP2750412B1/fr
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    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R25/00—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception
    • H04R25/40—Arrangements for obtaining a desired directivity characteristic
    • H04R25/405—Arrangements for obtaining a desired directivity characteristic by combining a plurality of transducers
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R25/00—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception
    • H04R25/45—Prevention of acoustic reaction, i.e. acoustic oscillatory feedback
    • H04R25/453—Prevention of acoustic reaction, i.e. acoustic oscillatory feedback electronically
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R2225/00—Details of deaf aids covered by H04R25/00, not provided for in any of its subgroups
    • H04R2225/021—Behind the ear [BTE] hearing aids
    • H04R2225/0216—BTE hearing aids having a receiver in the ear mould
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R2225/00—Details of deaf aids covered by H04R25/00, not provided for in any of its subgroups
    • H04R2225/025—In the ear hearing aids [ITE] hearing aids
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R25/00—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception
    • H04R25/40—Arrangements for obtaining a desired directivity characteristic
    • H04R25/407—Circuits for combining signals of a plurality of transducers
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04S—STEREOPHONIC SYSTEMS 
    • H04S2420/00—Techniques used stereophonic systems covered by H04S but not provided for in its groups
    • H04S2420/01—Enhancing the perception of the sound image or of the spatial distribution using head related transfer functions [HRTF's] or equivalents thereof, e.g. interaural time difference [ITD] or interaural level difference [ILD]

Definitions

  • a new hearing aid is provided with improved localization of sound sources with relation to the wearer of the hearing aid.
  • Hearing aid users have been reported to have poorer ability to localize sound sources when wearing their hearing aids than without their hearing aids. This represents a serious problem for the mild-to-moderate hearing impaired population.
  • hearing aids typically reproduce sound in such a way that the user perceives sound sources to be localized inside the head. The sound is said to be internalized rather than being externalized.
  • a common complaint for hearing aid users when referring to the "hearing speech in noise problem" is that it is very hard to follow anything that is being said even though the signal to noise ratio (SNR) should be sufficient to provide the required speech intelligibility.
  • SNR signal to noise ratio
  • a significant contributor to this fact is that the hearing aid reproduces an internalized sound field. This adds to the cognitive loading of the hearing aid user and may result in listening fatigue and ultimately that the user removes the hearing aid(s).
  • the new hearing aid preserves information of the directions and distances of respective sound sources in the sound environment with relation to the orientation of the head of the wearer of the hearing aid.
  • Human beings detect and localize sound sources in three-dimensional space by means of the human binaural sound localization capability.
  • the input to the hearing consists of two signals, namely the sound pressures at each of the eardrums, in the following termed the binaural sound signals.
  • the human auditory system extracts information about distance and direction to a sound source, but it is known that the human auditory system uses a number of cues in this determination. Among the cues are spectral cues, reverberation cues, interaural time differences (ITD), interaural phase differences (IPD) and interaural level differences (ILD).
  • HRTF Head-Related Transfer Function
  • the HRTF contains all information relating to the sound transmission to the ears of the listener, including diffraction around the head, reflections from shoulders, reflections in the ear canal, etc., and therefore, the HRTF varies from individual to individual.
  • the hearing aid related transfer function is defined similar to a HRTF, namely as the ratio between a sound pressure p generated by the hearing aid at a specific point in the appertaining ear canal in response to a plane wave and a reference.
  • the reference traditionally chosen is the sound pressure p I that would have been generated by a plane wave at a position right in the middle of the head with the listener absent.
  • the HRTF changes with direction and distance of the sound source in relation to the ears of the listener. It is possible to measure the HRTF for any direction and distance and simulate the HRTF, e.g. electronically, e.g. by filters. If such filters are inserted in the signal path between a playback unit, such as a tape recorder, and headphones used by a listener, the listener will achieve the perception that the sounds generated by the headphones originate from a sound source positioned at the distance and in the direction as defined by the transfer functions of the filters simulating the HRTF in question, because of the true reproduction of the sound pressures in the ears.
  • a playback unit such as a tape recorder
  • Binaural processing by the brain when interpreting the spatially encoded information, results in several positive effects, namely better signal-to-noise ratio (SNR); direction of arrival (DOA) estimation; depth/distance perception and synergy between the visual and auditory systems.
  • SNR signal-to-noise ratio
  • DOA direction of arrival
  • the complex shape of the ear is a major contributor to the individual spatial-spectral cues (ITD, ILD and spectral cues) of a listener. Devices which pick up sound behind the ear will, hence, be at a disadvantage in reproducing the HRTF since much of the spectral detail will be lost or heavily distorted.
  • FIGs. 1 and 2 This is exemplified in Figs. 1 and 2 where the angular frequency spectrum of an open ear, i.e. non-occluded, measurement is shown in Fig. 1 for comparison with Fig. 2 showing the corresponding measurement on the front microphone on a behind the ear device (BTE) using the same ear.
  • BTE behind the ear device
  • US 2009/0097681 discloses systems, devices and methods for communication that include an ear canal microphone configured for placement in the ear canal to detect high frequency sound localization cues.
  • An external microphone positioned away from the ear canal can detect low frequency sound, such that feedback can be substantially reduced.
  • the canal microphone and the external microphone are coupled to a transducer, such that the user perceives sound from the external microphone and the canal microphone with high frequency localization cues and decreased feedback.
  • Wireless circuitry can be configured to connect to many devices with a wireless protocol, such that the user can receive and transmit audio signals.
  • a bone conduction sensor can detect near-end speech of the user for transmission with the wireless circuitry in noisy environment. Noise cancellation of background sounds near the user can improve the user's hearing of desired sounds.
  • one or more microphones of the hearing aid at position(s) with relation to a user wearing the hearing aid in which spatial cues of sounds arriving at the user is preserved. It is for example advantageous to position a microphone in the outer ear of the user in front of the pinna, for example at the entrance to the ear canal; or, inside the ear canal, in order to preserve spatial cues of sounds arriving at the ear to a much larger extent than what is possible with the microphone behind the ear. A position below the triangular fossa has also proven advantageous with relation to preservation of spatial cues.
  • Positioning of a microphone at the entrance to the ear canal or inside the ear canal leads to the problem that the microphone is moved close to the sound emitting device of the hearing aid, whereby the risk of feedback generation is increased, which in turn limits the maximum stable gain which can be prescribed with the hearing aid.
  • a BTE hearing aid with front and rear microphones positioned behind the ear and an In-The-Ear (ITE) hearing aid with an open fitted microphone positioned in the ear canal is shown in Fig. 2 . It can be seen that the ITE hearing aid has much lower maximum stable gain (MSG) than the front and rear BTE microphones for nearly all frequencies.
  • MSG maximum stable gain
  • output signals of an arbitrary configuration of microphones undergo signal processing in such a way that spatial cues are preserved and conveyed to the user of the hearing aid.
  • the output signals are filtered with filters that are configured to preserve spatial cues.
  • the new hearing aid provides improved localization to the user by providing, in addition to conventionally positioned microphones as in a BTE hearing aid, at least one ITE microphone intended to be positioned in the outer ear of the user in front of the pinna, e.g. at the entrance to the ear canal or immediately below the triangular fossa; or, inside the ear canal, when in use in order to record sound arriving at the ear of the user and containing the desired spatial information relating to localization of sound sources in the sound environment.
  • the processor of the new hearing aid combines an audio signal of the at least one ITE microphone residing in the outer ear of the user with the microphone signal(s) of the conventionally positioned microphone(s) as in a BTE hearing aid in such a way that spatial cues are preserved.
  • An audio signal of the at least one ITE microphone may be formed as a weighted sum of the output signals of each microphone of the at least one ITE microphone.
  • Other forms of signal processing may be included in the formation of the audio signal of the at least one ITE microphone.
  • a hearing aid comprising a BTE hearing aid housing configured to be worn behind the pinna of a user, at least one BTE sound input transducer, such as an omni-directional microphone, a directional microphone, a transducer for an implantable hearing aid, a telecoil, a receiver of a digital audio datastream, etc., accommodated in the BTE hearing aid housing, each of which is configured for conversion of sound into a respective audio signal, an ITE microphone housing configured to be positioned in the outer ear of the user for fastening and retaining, in its intended position, at least one ITE microphone accommodated in the ITE microphone housing, each of which is configured for conversion of acoustic sound into a respective audio signal, at least one adaptive cue filter, each of which having
  • the hearing aid further comprises a feedback and cue controller with inputs connected to the at least one output of the adaptive feedback canceller and the output of the at least one adaptive cue filter, and configured to control the at least one adaptive cue filter so that the difference between an output of the at least one ITE microphone and a combined output of the at least one adaptive cue filter is reduced, preferably minimized, taking feedback into account.
  • a feedback and cue controller with inputs connected to the at least one output of the adaptive feedback canceller and the output of the at least one adaptive cue filter, and configured to control the at least one adaptive cue filter so that the difference between an output of the at least one ITE microphone and a combined output of the at least one adaptive cue filter is reduced, preferably minimized, taking feedback into account.
  • the hearing aid may further have a sound signal transmission member for transmission of a sound signal from a sound output in the BTE hearing aid housing at a first end of the sound signal transmission member to the ear canal of the user at a second end of the sound signal transmission member, and an earpiece configured to be inserted in the ear canal of the user for fastening and retaining the sound signal transmission member in its intended position in the ear canal of the user.
  • the "output signals of the at least one ITE microphone” may be used to identify any analogue or digital signal forming part of the signal path from the output of the at least one ITE microphone to an input of the processor, including pre-processed output signals of the at least one ITE microphone.
  • the "output signals of the at least one BTE sound input transducer" may be used to identify any analogue or digital signal forming part of the signal path from the at least one BTE sound input transducer to an input of the processor, including pre-processed output signals of the at least one BTE sound input transducer.
  • the at least one ITE microphone is positioned so that the output signal of the at least one ITE microphone generated in response to the incoming sound has a transfer function that constitutes a good approximation to the HRTFs of the user.
  • the at least one ITE microphone may be constituted by a single microphone positioned at the entrance to the ear canal.
  • the processor conveys the directional information contained in the output signal of the at least one ITE microphone to the resulting hearing loss compensated output signal of the processor so that the hearing loss compensated output signal of the processor also attains a transfer function that constitutes a good approximation to the HRTFs of the user whereby improved localization is provided to the user.
  • a BTE hearing aid has a BTE housing that is shaped to be worn behind the pinna of the user.
  • the BTE housing accommodates components for hearing loss compensation.
  • a sound signal transmission member i.e. a sound tube or an electrical conductor, transmits a signal representing the hearing loss compensated sound from the BTE housing into the ear canal of the user.
  • an earpiece, shell, or earmould may be provided for insertion into the ear canal of the user constituting an open solution.
  • the earpiece, shell, or earmould does not obstruct the ear canal when it is positioned in its intended operational position in the ear canal.
  • the earpiece, shell, or earmould is individually custom manufactured or manufactured in a number of standard sizes to fit the user's ear to sufficiently secure the sound signal transmission member in its intended position in the ear canal and prevent the earpiece from falling out of the ear, e.g., when the user moves the jaw.
  • the output transducer may be a receiver positioned in the BTE hearing aid housing.
  • the sound signal transmission member comprises a sound tube for propagation of acoustic sound signals from the receiver positioned in the BTE hearing aid housing and through the sound tube to an earpiece positioned and retained in the ear canal of the user and having an output port for transmission of the acoustic sound signal to the eardrum in the ear canal.
  • the output transducer may be a receiver positioned in the earpiece.
  • the sound signal transmission member comprises electrical conductors for propagation of audio signals from the output of a processor in the BTE hearing aid housing through the conductors to a receiver positioned in the earpiece for emission of sound through an output port of the earpiece.
  • the ITE microphone housing accommodating at least one ITE microphone may be combined with, or be constituted by, the earpiece so that the at least one microphone is positioned proximate the entrance to the ear canal when the earpiece is fastened in its intended position in the ear canal.
  • the ITE microphone housing may be connected to the BTE hearing aid housing with an arm, possibly a flexible arm that is intended to be positioned inside the pinna, e.g. around the circumference of the conchae abutting the antihelix and at least partly covered by the antihelix for retaining its position inside the outer ear of the user.
  • the arm may be pre-formed during manufacture, preferably into an arched shape with a curvature slightly larger than the curvature of the antihelix, for easy fitting of the arm into its intended position in the pinna.
  • the arm has a length and a shape that facilitate positioning of the at least one ITE microphone in an operating position immediately below the triangular fossa.
  • the processor may be accommodated in the BTE hearing aid housing, or in the ear piece, or part of the processor may be accommodated in the BTE hearing aid housing and part of the processor may be accommodated in the ear piece.
  • the link may be wired or wireless.
  • the link may be wired or wireless.
  • the processor operates to perform hearing loss compensation while maintaining spatial information of the sound environment for optimum spatial performance of the hearing aid and while at the same time providing as large maximum stable gain as possible.
  • the output signal of the at least one ITE microphone of the earpiece may be a combination of several pre-processed ITE microphone signals or the output signal of a single ITE microphone of the at least one ITE microphone.
  • One or more output signals of the at least one BTE sound input transducers are provided.
  • the output signals may be pre-processed. Pre-processing may include, without excluding any form of processing; adaptive and/or static feedback suppression, adaptive or fixed beamforming and pre-filtering.
  • Adaptive cue filters may be configured to adaptively filter the audio signals of the at least one BTE sound input transducer so that they correspond to the output signal of the at least one ITE microphone as closely as possible.
  • the adaptive cue filters G 1 , G 2 , ... , G n have the respective transfer functions: G 1 ( f,t ) , G 2 ( f,t ) , ... , G n ( f , t ).
  • the at least one ITE microphone may operate as monitor microphone(s) for generation of an audio signal with the desired spatial information of the current sound environment.
  • Each output signal of the at least one BTE sound input transducer is filtered with a respective adaptive cue filter, the filter coefficients of which are adapted to provide a combined output signal of the adaptive cue filter(s) that resembles the audio signal provided by the at least one ITE microphone as closely as possible.
  • LMS least mean square
  • RLS recursive least squares
  • Various weights may be incorporated into the minimization problems above so that the solution is optimized as specified by the values of the weights.
  • frequency weights W(f) may optimize the solution in certain one or more frequency ranges while information in other frequency ranges may be disregarded.
  • the minimization problem may be modified into: min G 1 f t ... G n f t ⁇ W f ( S IEC f t ⁇ G 1 f t S 1 BTEC f t ⁇ ... ⁇ G n f t S n BTEC f t ⁇ p
  • only magnitude of the transfer functions may be taken into account during minimization while phase is disregarded, i.e. in the one or more selected frequency range, the transfer function is substituted by its absolute value.
  • the combined output signal of the adaptive cue filter(s) is passed on for further hearing loss compensation processing, e.g. with a compressor.
  • the adaptive cue filters i.e. the algorithm adjusting the filter coefficients, adapt towards the new minimum of minimization problem (2).
  • the time constants of the adaptation are set to appropriately respond to changes of the current sound environment.
  • Feedback may be taken into account by performing the solution of the minimization problem (2) subject to the condition that the gain of the feedback loops must be less than one, i.e. subject to the condition that 1 ⁇ G 1 BTEC f t H FB , 1 BTEC f + ... + G n BTEC f t H FB , n BTEC ⁇ 2 ⁇ MSG f
  • H FB , 1 BTEC f , H FB , 2 BTEC f , ... , H FB , n BTEC f are the transfer functions of the feedback path associated with the n'th BTE microphone of the at least one BTE microphone
  • MSG(f) is the maximum stable gain
  • the requirement of spatial cue preservation and feedback cancellation may be balanced by solving: min G 1 BTEC f t ... G n BTEC f t ⁇ S IEC f t ⁇ G 1 BTEC f t S 1 BTEC f t ⁇ ... ⁇ G n f t S n BTEC f t ⁇ p + ⁇ ⁇ G 1 BTEC f t H FB , 1 BTEC f + ... + G n BTEC f t H FB , n BTEC ⁇ p wherein
  • the transfer functions H FB , 1 BTEC f , H FB , 2 BTEC f , ... , H FB , n BTEC f of the feedback paths may be modelled or approximated by an adaptive feedback cancellation circuit well-known in the art.
  • Various weights may be incorporated into the minimization problems above so that the solution is optimized as specified by the values of the weights.
  • frequency weights W(f) may optimize the solution in certain one or more frequency ranges.
  • the minimization problem may be modified into: Min G 1 BTEC f t ... G n BTEC f t ⁇ W f S IEC f t ⁇ G 1 BTEC f t S 1 BTEC f t ⁇ ... ⁇ G n f t S n BTEC f t ⁇ p subject to the condition that 1 ⁇ G 1 BTEC f t H FB , 1 BTEC f + ... + G n BTEC f t H FB , n BTEC ⁇ 2 ⁇ MSG f or min G 1 BTEC f t ... G n BTEC f t ⁇ W f S IEC f t ⁇ G 1 BTEC f t S 1 BTEC f t ⁇ ... ⁇ G
  • the target transfer function need not be defined by the HRTF for the various directions I. Any transfer function that includes spatial cues may be used as the target transfer function.
  • processor As used herein, the terms "processor”, “signal processor”, “controller”, “system”, etc., are intended to refer to CPU-related entities, either hardware, a combination of hardware and software, software, or software in execution.
  • a "processor”, “signal processor”, “controller”, “system”, etc. may be, but is not limited to being, a process running on a processor, a processor, an object, an executable file, a thread of execution, and/or a program.
  • processor designate both an application running on a processor and a hardware processor.
  • processors may reside within a process and/or thread of execution, and one or more "processors”, “signal processors”, “controllers”, “systems”, etc., or any combination hereof, may be localized on one hardware processor, possibly in combination with other hardware circuitry, and/or distributed between two or more hardware processors, possibly in combination with other hardware circuitry.
  • the hearing aid may be a multi-channel hearing aid in which signals to be processed are divided into a plurality of frequency channels, and wherein signals are processed individually in each of the frequency channels.
  • the adaptive feedback cancellation circuitry may also be divided into the plurality of frequency channels; or, the adaptive feedback cancellation circuitry may still operate in the entire frequency range; or, may be divided into other frequency channels, typically fewer frequency channels, than the other circuitry is divided into.
  • the processor may be configured for processing the output signals of the at least one ITE microphone and the at least one BTE sound input transducer in such a way that the hearing loss compensated output signal substantially preserves spatial cues in a selected frequency band.
  • the selected frequency band may comprise one or more of the frequency channels, or all of the frequency channels.
  • the selected frequency band may be fragmented, i.e. the selected frequency band need not comprise consecutive frequency channels.
  • the plurality of frequency channels may include warped frequency channels, for example all of the frequency channels may be warped frequency channels.
  • the at least one ITE microphone may be connected conventionally as an input source to the processor of the hearing aid and may cooperate with the processor of the hearing aid in a well-known way.
  • the at least one ITE microphone supplies the input to the hearing aid at frequencies where the hearing aid is capable of supplying the desired gain with this configuration.
  • the microphones of BTE hearing aid housing are included in the signal processing as disclosed above. In this way, the gain can be increased while simultaneously maintain the spatial information about the sound environment provided by the at least one ITE microphone.
  • the hearing aid may for example comprise a first filter connected between the processor input and the at least one ITE microphone, and a second complementary filter connected between the processor input and a combined output of the at least one BTE sound input transducer, the filters passing and blocking frequencies in complementary frequency bands so that one of the at least one ITE microphone and the combined output of at least one BTE sound input transducer constitutes the main part of the input signal supplied to the processor input in one frequency band, and the other one of the at least one ITE microphone and the combined output of at least one BTE sound input transducer constitutes the main part of the input signal supplied to the processor input in the complementary frequency band.
  • the at least one ITE microphone may be used as the sole input source to the processor in a frequency band wherein the required gain for hearing loss compensation can be applied to the output signal of the at least one ITE microphone. Outside this frequency band, the combined output signal of the at least one BTE sound input transducer is applied to the processor for provision of the required gain.
  • the combination of the signals could e.g. be based on different types of band pass filtering.
  • Fig. 4 schematically illustrates a BTE hearing aid 10 comprising a BTE hearing aid housing 12 (not shown - outer walls have been removed to make internal parts visible) to be worn behind the pinna 100 of a user.
  • the BTE housing 12 accommodates at least one BTE sound input transducer 14, 16 with a front microphone 14 and a rear microphone 16 for conversion of a sound signal into a microphone audio signal, optional pre-filters (not shown) for filtering the respective microphone audio signals, A/D converters (not shown) for conversion of the respective microphone audio signals into respective digital microphone audio signals that are input to a processor 18 configured to generate a hearing loss compensated output signal based on the input digital audio signals.
  • the hearing loss compensated output signal is transmitted through electrical wires contained in a sound signal transmission member 20 to a receiver 22 for conversion of the hearing loss compensated output signal to an acoustic output signal for transmission towards the eardrum of a user and contained in an earpiece 24 that is shaped (not shown) to be comfortably positioned in the ear canal of a user for fastening and retaining the sound signal transmission member in its intended position in the ear canal of the user as is well-known in the art of BTE hearing aids.
  • the earpiece 24 also holds one ITE microphone 26 that is positioned at the entrance to the ear canal when the earpiece is positioned in its intended position in the ear canal of the user.
  • the ITE microphone 26 is connected to an A/D converter (not shown) and optional to a pre-filter (not shown) in the BTE housing 12, with electrical wires (not visible) contained in the sound transmission member 20.
  • the BTE hearing aid 10 is powered by battery 28.
  • processor 18 Various possible functions of the processor 18 are disclosed above and some of these in more detail below.
  • Fig. 5 schematically illustrates another BTE hearing aid 10 similar to the hearing aid shown in Fig. 1 , except for the difference that in Fig. 5 , the receiver 22 is positioned in the hearing aid housing 12 and not in the earpiece 24, so that acoustic sound output by the receiver 22 is transmitted through the sound tube 20 and towards the eardrum of the user when the earpiece 24 is positioned in its intended position in the ear canal of the user.
  • the positioning of the ITE microphone 26 proximate the entrance to the ear canal of the user when the BTE hearing aids 10 of Figs. 4 and 5 are used is believed to lead to a good reproduction of the HRTFs of the user.
  • Fig. 6 shows a BTE hearing aid 10 in its operating position with the BTE housing 12 behind the ear, i.e. behind the pinna 100, of the user.
  • the illustrated BTE hearing aid 10 is similar to the hearing aids shown in Figs. 4 and 5 except for the fact that the ITE microphone 26 is positioned in the outer ear of the user outside the ear canal at the free end of an arm 30.
  • the arm 30 is flexible and the arm 30 is intended to be positioned inside the pinna 100 , e.g. around the circumference of the conchae 102 behind the tragus 104 and antitragus 106 and abutting the antihelix 108 and at least partly covered by the antihelix for retaining its position inside the outer ear of the user.
  • the arm may be pre-formed during manufacture, preferably into an arched shape with a curvature slightly larger than the curvature of the antihelix 104, for easy fitting of the arm 30 into its intended position in the pinna.
  • the arm 30 contains electrical wires (not visible) for interconnection of the ITE microphone 26 with other parts of the BTE hearing aid circuitry.
  • the arm 30 has a length and a shape that facilitate positioning of the ITE microphone 26 in an operating position below the triangular fossa.
  • Fig. 7 is a block diagram illustrating one example of signal processing in the new hearing aid 10.
  • the illustrated hearing aid 10 has a front microphone 14 and a rear microphone 16 accommodated in the BTE hearing aid housing configured to be worn behind the pinna of the user, for conversion of sound signals arriving at the microphones 14, 16 into respective audio signals 33, 35.
  • the illustrated hearing aid 10 has an ITE microphone 26 accommodated in an earpiece (not shown) to be positioned in the outer ear of the user, for conversion of sound signals arriving at the microphone 26 into audio signal 31.
  • the microphone audio signals 31, 33, 35 are digitized and pre-processed, such as pre-filtered, in respective pre-processors 32, 34, 36.
  • the pre-processed audio signals 38, 40 of the front and rear microphones 14, 16 are filtered in respective adaptive cue filters 42, 44, and the adaptively filtered signals 46, 48 are added to each other in adder 50 and the combined signal 52 is input to processor 18 for hearing loss compensation.
  • the hearing loss compensated signal 54 is output to the receiver 22 that converts the signal 54 to an acoustic output signal for transmission towards the ear drum of the user.
  • Adaptation of the filter coefficients of adaptive cue filters 42, 44 are controlled by adaptive controller 56 that controls the adaptation of the filter coefficients to reduce, and preferably eventually minimize, the difference 58 between the output 52 of adder 46 and the pre-processed ITE microphone audio signal 60, output by subtractor 62.
  • the input signal 52 to the processor 18 models the microphone audio signal 60 of the ITE microphone 26, and thus also substantially models the HRTFs of the user.
  • Pre-processing may include, without excluding any form of processing; adaptive and/or static feedback suppression, adaptive or fixed beamforming and pre-filtering.
  • the adaptive controller 56 is configured to control the filter coefficients of adaptive cue filters 42, 44 so that their summed output 52 corresponds to the pre-processed output signal 60 of the ITE microphone 26 as closely as possible.
  • the adaptive cue filters 42, 44 have the respective transfer functions: G 1 ( f,t ) , and G 2 ( f,t ) .
  • the ITE microphone 26 operates as monitor microphone for generation of an audio signal 60 with the desired spatial information of the current sound environment due to its positioning in the outer ear of the user.
  • LMS least mean square
  • RLS recursive least squares
  • the combined output signal 52 of the adaptive cue filters 42, 44 is passed on for further hearing loss compensation processing, e.g. in a compressor.
  • hearing loss compensation processing e.g. in a compressor.
  • signals from the front and rear microphones 14, 16 are possibly amplified as a result of hearing loss compensation while the audio signal 60 of the ITE microphone 26 is not processed in the processor 18 configured for hearing loss processing, whereby possible feedback from the output transducer 22 to the ITE microphone 26 is reduced, preferably minimized, and a large maximum stable gain can be provided.
  • the adaptive cue filters 42, 44 i.e. the adaptive controller 56 by adjusting the filter coefficients, adapt towards the new minimum of the minimization problem (11).
  • the time constants of the adaptation are set to appropriately respond to changes of the current sound environment.
  • adaptation may be stopped, i.e. the filter coefficients may be prevented from changing, or the adaptation rate may be slowed down, in order to avoid that feedback is transferred from the audio signal of the at least one ITE microphone to the output signal(s) of the at least one BTE sound input transducer during presence of feedback.
  • the filter coefficients of the adaptive cue filters 42, 44 may be predetermined so that a set of filter coefficients is provided for a specific HRTF.
  • the sets of filter coefficients may be determined using a manikin, such as KEMAR.
  • the filter coefficients are determined for at number of direction of arrivals for the hearing aid as disclosed above; however under controlled conditions and allowing adaptation of long duration. In this way, an approximation to the individual HRTFs is provided that can be of sufficient accuracy for the hearing aid user to maintain sense of direction when wearing the hearing aid.
  • the set of filter coefficients is selected that reduces, and preferably eventually minimizes, the difference between the combined output signal, possibly pre-processed, of the at least one BTE sound input transducer and the output signal, possibly pre-processed, of the at least one ITE microphone.
  • the adaptive cue filter may be allowed to further adapt to the individual HRTF of the user in question. The adaptation may be stopped when the filter coefficients have become stable so that the at least one ITE microphone is no longer used for the HRTF in question.
  • the new hearing aid circuitry shown in Fig. 7 may operate in the entire frequency range of the hearing aid 10.
  • the hearing aid 10 shown in Fig. 7 may be a multi-channel hearing aid in which microphone audio signals 38, 40, 60 to be processed are divided into a plurality of frequency channels, and wherein signals are processed individually in each of the frequency channels.
  • Fig. 7 may illustrate the circuitry and signal processing in a single frequency channel.
  • the circuitry and signal processing may be duplicated in a plurality of the frequency channels, e.g. in all of the frequency channels.
  • the signal processing illustrated in Fig. 7 may be performed in a selected frequency band, e.g. selected during fitting of the hearing aid to a specific user at a dispenser's office.
  • the selected frequency band may comprise one or more of the frequency channels, or all of the frequency channels.
  • the selected frequency band may be fragmented, i.e. the selected frequency band need not comprise consecutive frequency channels.
  • the plurality of frequency channels may include warped frequency channels, for example all of the frequency channels may be warped frequency channels.
  • the ITE microphone 26 may be connected conventionally as an input source to the processor 18 of the hearing aid 10 and may cooperate with the processor 18 of the hearing aid 10 in a well-known way.
  • the ITE microphone supplies the input to the hearing aid at frequencies where the hearing aid is capable of supplying the desired gain with this configuration.
  • the microphones 14, 16 of BTE hearing aid housing are included in the signal processing as disclosed above. In this way, the gain can be increased while the spatial information of the sound environment as provided by the ITE microphone is simultaneously maintained.
  • Fig. 8 is a block diagram illustrating a new hearing aid 10 similar to the hearing aid 10 shown in Fig. 7 except for the fact that adaptive feedback cancellation circuitry has been added, including an adaptive feedback filter 70 with an input 72 connected to the output of the hearing aid processor 18 and with outputs 74-1, 76-1, 76-2, each of which is connected to a respective subtractor 78-1, 80-1, 80-2 for subtraction of each output 74-1, 76-1, 76-2 from a respective microphone output 31, 33, 35 to provide a respective feedback compensated signal 82-1, 84-1, 84-2 as is well-known in the art.
  • an adaptive feedback filter 70 with an input 72 connected to the output of the hearing aid processor 18 and with outputs 74-1, 76-1, 76-2, each of which is connected to a respective subtractor 78-1, 80-1, 80-2 for subtraction of each output 74-1, 76-1, 76-2 from a respective microphone output 31, 33, 35 to provide a respective feedback compensated signal 82-1, 84-1, 84-2 as
  • Each feedback compensated signal 82-1, 84-1, 84-2 is fed to the corresponding preprocessor 32, 34, 36, and also to the adaptive feedback filter 70 for control of the adaption of the adaptive feedback filter 70.
  • the adaptive feedback filter outputs 74-1, 76-1, 76-2 provide signals that constitute approximations of corresponding feedback signals travelling from the output transducer 22 to the respective microphone 14, 16, 26 as is well-known in the art.
  • the outputs 76-1, 76-2 approximating feedback signals of the BTE microphones are further connected to the adaptive controller 56.
  • the adaptive controller 56 of Fig. 8 controls adjustment of the filter coefficients of adaptive cue filters 38, 40 by solving minimization problem (11) subject to the condition that 1 ⁇ G 1 f t H FB , 1 BTEC f + G 2 f t H FB , n BTEC ⁇ 2 ⁇ MSG f or by solving minimization problem min G 1 f t G 2 f t ⁇ W f S IEC f t ⁇ G 1 f t S 1 BTEC f t ⁇ G 2 f t S 2 BTEC f t ⁇ p + ⁇ ⁇ G 1 f t H FB , 1 BTEC f + ... + G 2 f t H FB , 2 BTEC ⁇ p
  • the new hearing aid circuitry shown in Fig. 8 may operate in the entire frequency range of the hearing aid 10.
  • the hearing aid 10 shown in Fig. 8 may be a multi-channel hearing aid in which microphone audio signals 38, 40, 60 to be processed are divided into a plurality of frequency channels, and wherein signals are processed individually in each of the frequency channels possibly apart from the adaptive feedback cancellation circuitry 70, 72, 74-1, 74-2, 76-1, 76-2, 78-1, 78-2, 80-1, 80-2, 82-1, 82-2, 84-1, 84-2 that may still operate in the entire frequency range; or, may be divided into other frequency channels, typically fewer frequency channels than the remaining illustrated circuitry.
  • the part of Fig. 8 corresponding to the circuitry of Fig. 7 may illustrate the circuitry and signal processing in a single frequency channel, while the adaptive circuitry that may still operate in the entire frequency range; or, may be divided into other frequency channels, typically fewer frequency channels than the remaining illustrated circuitry.
  • the circuitry and signal processing may be duplicated in a plurality of the frequency channels, e.g. in all of the frequency channels.
  • the signal processing illustrated in Fig. 8 may be performed in a selected frequency band, e.g. selected during fitting of the hearing aid to a specific user at a dispenser's office.
  • the selected frequency band may comprise one or more of the frequency channels, or all of the frequency channels.
  • the selected frequency band may be fragmented, i.e. the selected frequency band need not comprise consecutive frequency channels.
  • the plurality of frequency channels may include warped frequency channels, for example all of the frequency channels may be warped frequency channels.
  • the at least one ITE microphone may be connected conventionally as an input source to the processor of the hearing aid and may cooperate with the processor of the hearing aid in a well-known way.
  • the at least one ITE microphone supplies the input to the hearing aid at frequencies where the hearing aid is capable of supplying the desired gain with this configuration.
  • the microphones of BTE hearing aid housing are included in the signal processing as disclosed above. In this way, the gain can be increased while simultaneously maintain the spatial information about the sound environment provided by the at least one ITE microphone.
  • Fig. 9 is a block diagram illustrating a new hearing aid 10 similar to the hearing aid 10 shown in Fig. 7 and operating in a way similar to the hearing aid 10 shown in Fig. 7 , except for the fact that the circuit has been generalized to include an arbitrary number N of ITE microphones 26-1, 26-2, ... , 26-N, and an arbitrary number M of BTE microphones 14-1, 14-2, ... , 14-M.
  • N and M can be any non-negative integer.
  • the output signals 31-1, 31-2, ... , 31-N from the N ITE microphones 26-1, 26-2, ... , 26-N are delayed by delays 41-1, 41-2, ... , 41-N after pre-processing in pre-processors 32-1, 32-2, ... , 32-N to compensate for the delays of the output signals 33-1, 33-2, ... , 33-M from the M BTE microphones 14-1, 14-2, ... , 14-M, caused by the adaptive cue filters 42-1, 42-2, ... , 42-M.
  • the delays 41-1, 41-2, ... , 41-N may also be used for beamforming.
  • the output signals 33-1, 33-2, ... , 33-M from the M BTE microphones are pre-processed in pre-processors 34-1, 34-2, ... , 34-M and filtered in the respective adaptive cue filters 42-1, 42-2, ... , 42-M and combined in the signal combiner 50, e.g. as a weighted sum, and the output 52 of the signal combiner 50 is fed to the subtractor 62 and the hearing aid processor 18 as in the circuit of Fig. 7 .
  • the adaptive controller 56 controls the adaptation of the filter coefficients of adaptive cue filters 42-1, 42-2, ... , 42-M to reduce, and preferably eventually minimize, the difference 58 between the output of BTE signal combiner 50 and ITE signal combiner 64, provided by subtractor 62, e.g. by solving the minimization problem (2) already mentioned above: min G 1 f t ... G m f t ⁇ W f ( S IEC f t ⁇ G 1 f t S 1 BTEC f t ⁇ ... ⁇ G m f t S m BTEC f t ⁇ p
  • S IEC is the output signal 60 of signal combiner 64
  • G 1 (f,t), G 2 (f,t), ... , G n (f,t) are the transfer functions of the respective adaptive cue filters 42-1, 42-2, ... , 42-M.
  • Possible weights in the signal combination performed by the signal combiner 58 are included in the transfer functions G 1 (f,t), G 2 (f,t) G n (f,t). These weights may be frequency dependent.
  • the output signal 52 of the BTE signal combiner 50 models the combined ITE microphone audio signal 60 of the ITE microphones 26-1, 26-2, ... , 26-N, and thus also substantially models the HRTFs of the user.
  • the new hearing aid circuitry shown in Fig. 9 may operate in the entire frequency range of the hearing aid 10.
  • the hearing aid 10 shown in Fig. 9 may be a multi-channel hearing aid in which microphone audio signals 31-1, 31-2, ... , 31-N, 33-1, 33-2, ... , 33-M to be processed are divided into a plurality of frequency channels, and wherein signals are processed individually in each of the frequency channels.
  • Fig. 9 may illustrate the circuitry and signal processing in a single frequency channel.
  • the circuitry and signal processing may be duplicated in a plurality of the frequency channels, e.g. in all of the frequency channels.
  • the signal processing illustrated in Fig. 9 may be performed in a selected frequency band, e.g. selected during fitting of the hearing aid to a specific user at a dispenser's office.
  • the selected frequency band may comprise one or more of the frequency channels, or all of the frequency channels.
  • the selected frequency band may be fragmented, i.e. the selected frequency band need not comprise consecutive frequency channels.
  • the plurality of frequency channels may include warped frequency channels, for example all of the frequency channels may be warped frequency channels.
  • the at least one ITE microphone 26-1, 26-2, ... , 26-N may be connected conventionally as an input source to the processor 18 of the hearing aid 10 and may cooperate with the processor 18 of the hearing aid 10 in a well-known way.
  • the at least one ITE microphone 26-1,26-2, ... , 26-N supply the input to the hearing aid at frequencies where the hearing aid is capable of supplying the desired gain with this configuration.
  • the microphones 14-1, 14-2, ... , 14-M of BTE hearing aid housing are included in the signal processing as disclosed above. In this way, the gain can be increased while simultaneously maintain the spatial information about the sound environment provided by the at least one ITE microphone.
  • adaptive feedback cancellation has been added to the hearing aid shown in Fig. 9 similar to the way illustrated in Fig. 8 in comparison with Fig. 7 , i.e. an adaptive feedback filter 70 is added with an input 72 connected to the output of the hearing aid processor 18 and outputs 74-1, 74-2, ... , 74-N, 76-1. 76-2, ... , 76-M connected to subtractors 78-1, 78-2, ... , 78-N, 80-1, 80-2, ... , 80-M for subtraction of each output from a respective microphone output to provide a feedback compensated signal 82-1, 82-2, ... , 82-N, 84-1, 84-2, ...
  • the adaptive feedback filter outputs 74-1, 74-2, ... , 74-N, 76-1. 76-2, ... , 76-M provide signals that constitute approximations of corresponding feedback signals travelling from the output transducer 22 to the respective microphones 26-1, 26-2, ... , 26-N, 14-1, 14-2, ... , 14-M as is well-known in the art.
  • outputs 76-1, 76-2, ... , 76-M approximating feedback signals of the BTE microphones 14-1, 14-2, ... , 14-M are connected to the adaptive controller 56 that controls the filter coefficients of adaptive cue filters 42-1, 42-2, ... , 42-M.
  • equation 1 subject to condition 1, or equation 5, in order to preserve spatial cue and simultaneously take feedback into account.
  • the adaptive controller 56 controls the adaptation of the filter coefficients of adaptive cue filters 42-1, 42-2, ... , 42-M to reduce, and preferably eventually minimize, the difference 58 between the output 60 of the ITE signal combiner 64 and the output 52 of BTE signal combiner 50, provided by subtractor 62, e.g.
  • Possible weights in the signal combination performed by the signal combiner 58 are included in the transfer functions G 1 (f,t), G 2 (f,t), ..., G n (f,t). These weights may be frequency dependent.
  • the output signal 52 of the BTE signal combiner 50 models the combined ITE microphone audio signal 60 of the ITE microphones 26-1, 26-2, ... , 26-N, and thus also substantially models the HRTFs of the user.
  • the new hearing aid circuitry shown in Fig. 10 may operate in the entire frequency range of the hearing aid 10.
  • the hearing aid 10 shown in Fig. 10 may be a multi-channel hearing aid in which microphone audio signals 31-1, 31-2, ... , 31-N, 33-1, 33-2, ... , 33-M to be processed are divided into a plurality of frequency channels, and wherein signals are processed individually in each of the frequency channels, possibly apart from the adaptive feedback cancellation circuitry 70, 72, 74-1, 74-2, ... , 74-N, 76-1, 76-2, ... , 76-M, 78-1, 78-2, ... , 78-N, 80-1, 80-2, ... , 80-M, 82-1, 82-2, ... , 82-N, 84-1, 84-2, ... , 84-M, 86 that may still operate in the entire frequency range; or, may be divided into other frequency channels, typically fewer frequency channels than the remaining illustrated circuitry.
  • Fig. 10 may also illustrate the circuitry and signal processing in a single frequency channel of a multi-channel hearing aid 10.
  • the circuitry and signal processing may be duplicated in a plurality of the frequency channels, e.g. in all of the frequency channels apart from the adaptive circuitry that may still operate in the entire frequency range; or, may be divided into its own frequency channels, typically with fewer frequency channels than the remaining illustrated circuitry.
  • the part of Fig. 10 corresponding to the circuitry of Fig. 9 may illustrate the circuitry and signal processing in a single frequency channel, while the adaptive circuitry may still operate in the entire frequency range; or, may be divided into other frequency channels, typically fewer frequency channels than the remaining illustrated circuitry.
  • the illustrated circuitry and signal processing may be duplicated in a plurality of the frequency channels, e.g. in all of the frequency channels.
  • the signal processing illustrated in Fig. 10 may be performed in a selected frequency band, e.g. selected during fitting of the hearing aid to a specific user at a dispenser's office.
  • the selected frequency band may comprise one or more of the frequency channels, or all of the frequency channels.
  • the selected frequency band may be fragmented, i.e. the selected frequency band need not comprise consecutive frequency channels.
  • the plurality of frequency channels may include warped frequency channels, for example all of the frequency channels may be warped frequency channels.
  • the at least one ITE microphone may be connected conventionally as an input source to the processor 18 of the hearing aid and may cooperate with the processor 18 of the hearing aid in a well-known way.
  • the at least one ITE microphone 26-1, 26-1, ... , 26-N supply the input to the hearing aid at frequencies where the hearing aid is capable of supplying the desired gain with this configuration.
  • the microphones of BTE hearing aid housing are included in the signal processing as disclosed above. In this way, the gain can be increased while simultaneously maintain the spatial information about the sound environment provided by the at least one ITE microphone.
  • the hearing aid 10 shown in Fig. 11 is similar to the hearing aid 10 shown in Fig. 10 and operates in the same way, apart from the fact that, in Fig. 11 , a signal combiner 66 has been inserted in front of the processor 18.
  • the added signal combiner 66 comprises first filters connected between the processor input and the output 60 of the signal combiner 64 of the at least one ITE microphone 26-1, 26-2, ... , 26-N, and second complementary filters connected between the processor input and the output 52 of the signal combiner 50 of the at least one BTE microphone 14-1, 14-2, ... , 14-M, the filters passing and blocking, respectively, frequencies in complementary frequency bands so that the output 60 of the signal combiner 64 of the at least one ITE microphone 26-1, 26-2, ...
  • 26-N constitutes the main part of the input signal 68 supplied to the processor input in one or more first frequency bands
  • the output 52 of the signal combiner 50 of the at least one BTE microphone 14-1, 14-2, ... , 14-M constitutes the main part of the input signal 68 supplied to the processor input in one or more complementary second frequency bands.
  • the at least one ITE microphone 26-1, 26-2, ... , 26-N may be used as the sole input source to the processor 18 in one or more frequency bands wherein the required gain for hearing loss compensation can be applied to the output signal 60 of the at least one ITE microphone 26-1, 26-2, ... , 26-N. Outside these one or more frequency bands, the combined output signal 52 of the at least one BTE sound input transducer 14-1, 14-2, ... , 14-M is applied to the processor 18 for provision of the required gain.
  • the combination of the signals performed in signal combiner 66 could e.g. be based on different types of band pass filtering.
  • the hearing aid 10 shown in Fig. 11 may be a multi-channel hearing aid in which microphone audio signals 31-1, 31-2, ... , 31-N, 33-1, 33-2, ... , 33-M to be processed are divided into a plurality of frequency channels, and wherein signals are processed individually in each of the frequency channels possibly apart from the adaptive feedback cancellation circuitry 70, 72, 74-1, 74-2, ... , 74-N, 76-1, 76-2, ... , 76-M, 78-1, 78-2, ... , 78-N, 80-1, 80-2, ... , 80-M, 82-1, 82-2, ... , 82-N, 84-1, 84-2, ...
  • the signal combiner 66 may connect the audio signal 60 of the at least one ITE microphone 26-1, 26-2, ... , 26-N as the sole input source to the processor 18 in one or more frequency channels in which no feedback is expected, and the combined output signal 52 of the at least one BTE sound input transducer 14-1, 14-2, ... , 14-M in frequency channels with risk of feedback.
  • the hearing aid 10 shown in Fig. 12 is similar to the hearing aid 10 shown in Fig. 11 and operates in the same way, apart from the fact that, in Fig. 12 , the signal combiner 66 is adaptive, e.g. so that the interconnections of the output 60 of the signal combiner 64 of the at least one ITE microphone 26-1, 26-2, ... , 26-N and the output 52 of the signal combiner 50 of the at least one BTE microphone 14-1, 14-2, ... , 14-M can be changed during operation of the hearing aid 10, e.g. in response to the status of the feedback loops, whereby, the at least one ITE microphone 26-1, 26-2, ...
  • 26-N may be used as the sole input source to the processor 18 in one or more frequency bands in which no feedback is currently present, whereas in one or more frequency bands in which feedback is evolving, the combined output signal 52 of the at least one BTE sound input transducer 14-1, 14-2, ... , 14-M is applied to the processor 18 for provision of the required gain without feedback.
  • the hearing aid 10 shown in Fig. 12 may be a multi-channel hearing aid in which microphone audio signals 31-1, 31-2, ... , 31-N, 33-1, 33-2, ... , 33-M to be processed are divided into a plurality of frequency channels, and wherein signals are processed individually in each of the frequency channels possibly apart from the adaptive feedback cancellation circuitry 70, 72, 74-1, 74-2, ..., 74-N, 76-1, 76-2, ... , 76-M, 78-1, 78-2, ... , 78-N, 80-1, 80-2, ... , 80-M, 82-1, 82-2, ... , 82-N, 84-1, 84-2, ...
  • the signal combiner 66 may adaptively connect the audio signal 60 of the at least one ITE microphone 26-1, 26-2, ... , 26-N as the sole input source to the processor 18 in one or more frequency channels in which no feedback instability is currently present, and the combined output signal 52 of the at least one BTE sound input transducer 14-1, 14-2, ... , 14-M in frequency channels with current risk of feedback.

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Claims (14)

  1. Prothèse auditive (10) comprenant
    un boîtier de prothèse auditive BTE (12) configuré pour être porté derrière la pinna (100) d'un utilisateur,
    au moins un transducteur d'entrée acoustique BTE logé dans le boîtier de prothèse auditive BTE (12) et comprenant au moins un microphone BTE (14, 16, 14-1, ..., 14-M), dont chacun est configuré pour la conversion de son acoustique en un signal audio respectif (33, 35, 33-1, ..., 33-M),
    un boîtier de microphone ITE configuré pour être positionné dans l'oreille externe de l'utilisateur pour fixer et retenir, dans sa position prévue,
    au moins un microphone ITE (26, 26-1, ..., 26-N) logé dans le boîtier de microphone ITE, dont chacun est configuré pour la conversion du son acoustique en un signal audio respectif (31, 31-1, ..., 31-N),
    un processeur (18) configuré pour générer un signal de sortie (54) compensé de la perte auditive,
    un transducteur de sortie (22) pour la conversion du signal de sortie (54) compensé de la perte auditive en un signal de sortie acoustique qui peut être reçu par le système auditif humain,
    un annuleur de rétroaction adaptative (70) pour la suppression de rétroaction et ayant
    une entrée (72) reliée à une sortie du processeur pour la réception du signal de sortie compensé de la perte auditive,
    au moins une sortie (76-1, ..., 76-M) modelant le trajet de rétroaction de la sortie du transducteur de sortie à l'au moins un microphone BTE respectif et reliée à
    un soustracteur (80-1, ..., 80-M) pour la soustraction de l'au moins une sortie de la sortie de l'au moins un microphone BTE respectif et faisant sortir la différence à l'au moins un filtre de repérage adaptatif respectif (42, 44, 42-1, ..., 42-M),
    caractérisée en ce que la prothèse auditive comprend en outre au moins un filtre de repérage adaptatif (42, 44, 42-1, ..., 42-M), dont chacun comportant
    une entrée qui est pourvue d'un signal de sortie de l'un respectif de l'au moins un transducteur d'entrée acoustique BTE, et
    dont les coefficients de filtre sont adaptés si bien que la différence entre une sortie de l'au moins un microphone ITE et une sortie combinée (52) de l'au moins un filtre de repérage adaptatif est réduite,
    dans laquelle le processeur (18) est configuré pour générer le signal de sortie (54) compensé de la perte auditive basé sur une combinaison des signaux audio filtrés sortis par l'au moins un filtre de repérage, et
    une commande de rétroaction et de repérage (56) avec des entrées connectées à l'au moins une sortie de l'annuleur de rétroaction adaptive (70) et la sortie de l'au moins un filtre de repérage adaptif (42, 44, 42-1, ..., 42-M), et configurée pour commander l'au moins un filtre de repérage adaptif (42, 44, 42-1, ..., 42-M) si bien que la différence entre la sortie de l'au moins un microphone ITE (26, 26-1, ..., 26-N) et la sortie combinée (52) de l'au moins un filtre de repérage adaptatif (42, 44, 42-1, ..., 42-M) est réduite et si bien que la rétroaction est réduite.
  2. Prothèse auditive selon la revendication 1, dans laquelle les coefficients de filtre de l'au moins un filtre de repérage adaptatif (42, 44, 42-1, ..., 42-M) sont adaptés vers une solution de: min G 1 BTEC f t … G n BTEC f t ‖ W f S IEC f t − G 1 BTEC f t S 1 BTEC f t − … − G n f t S n BTEC f t ‖ p + α ‖ G 1 BTEC f t H FB , 1 BTEC f + … + G n BTEC f t H FB , n BTEC ‖ p
    Figure imgb0045
     dans laquelle
    SIEC (f,t) est le spectre de courte durée à un temps t du signal de sortie de l'au moins un microphone ITE, et
    S 1 BTEC f t t ) , S 2 BTEC f t , … , S n BTEC f t
    Figure imgb0046
     sont les spectres de courte durée à un tempes t des signaux de sortie de l'au moins un transducteur d'entrée acoustique BTE, et
    G 1 BTEC f t , G 2 BTEC f t , … , G n BTEC f t
    Figure imgb0047
     sont les fonctions de transfert de filtres de prétraitement (34, 36, 34-1, ..., 34-M) connectés aux sorties respectives de l'au moins un transducteur d'entrée acoustique BTE et
    H FB , 1 BTEC f , H FB , 2 BTEC f , … , H FB , n BTEC f
    Figure imgb0048
     sont les fonctions de transfert du trajet de rétroaction associés au n-ième microphone BTE de l'au moins un microphone BTE,
    p est le facteur de norme,
    W(f) est un facteur de pondération dépendant de la fréquence, et
    α est un facteur de pondération équilibrant la précision de repérage spatial et la performance de rétroaction.
  3. Prothèse auditive selon la revendication 1, dans laquelle les coefficients de filtre de l'au moins un filtre de repérage adaptatif (42, 44, 42-1, ..., 42-M) sont adaptés vers une solution de: min G 1 BTEC f t … G n BTEC f t ‖ W f S IEC f t − G 1 BTEC f t S 1 BTEC f t − … − G n f t S n BTEC f t ‖ p
    Figure imgb0049
     à la condition que 1 ‖ G 1 BTEC f t H FB , 1 BTEC f + … + G n BTEC f t H FB , n BTEC ‖ 2 ≥ MSG f
    Figure imgb0050
     dans laquelle
    SIEC (f,t) est le spectre de courte durée à un temps t du signal de sortie de l'au moins un microphone ITE, et
    S 1 BTEC f t t ) , S 2 BTEC f t , … , S n BTEC f t
    Figure imgb0051
     sont les spectres de courte durée à un temps t des signaux de sortie de l'au moins un transducteur d'entrée acoustique BTE, et
    G 1 BTEC f t , G 2 BTEC f t , … , G n BTEC f t
    Figure imgb0052
     sont les fonctions de transfert des filtres de prétraitelmlent connectés aux sorties respectives de l'au moins un transducteur d'entrée acoustique BTE et
    H FB , 1 BTEC f , H FB , 2 BTEC f , … , H FB , n BTEC f
    Figure imgb0053
     sont les fonctions de transfert du trajet de rétroaction associés au n-ième microphone BTE de l'au moins un microphone BTE,
    p est le facteur de norme, et
    MSG(f) est le gain maximal stable,
  4. Prothèse auditive selon l'une quelconque des revendications précédentes, comprenant en outre une mémoire pour le logement d'ensembles de coefficients de filtre de l'au moins un filtre de repérage adaptatif (42, 44, 42-1, ..., 42-M), chaque ensemble de coefficients de filtre ayant été déterminé pour une direction spécifique d'arrivée par rapport à la prothèse auditive par l'adaptation de l'au moins un filtre de repérage adaptatif pour la direction d'arrivée en question.
  5. Prothèse auditive selon la revendication 4, dans laquelle l'au moins un filtre de repérage adaptatif est chargé avec l'ensemble de coefficients de filtre qui fournit la différence minimale entre une sortie de l'au moins un microphone ITE (26, 26-1, ..., 26-N) et une sortie combinée (52) de l'au moins un filtre de repérage adaptatif (42, 44, 42-1, ..., 42-M).
  6. Prothèse auditive selon la revendication 5, dans laquelle l'au moins un filtre adaptatif de repérage (42, 44, 42-1, ..., 42-M) est autorisé à s'adapter davantage après chargement.
  7. Prothèse auditive selon l'une quelconque des revendications précédentes, dans laquelle l'au moins un filtre de repérage adaptif (42, 44, 42-1, ..., 42-M) est empêché de s'adapter davantage, lorsque les valeurs de coefficient de filtre ont cessé de changer de manière significative.
  8. Prothèse auditive selon l'une quelconque des revendications précédentes, dans laquelle les signaux audio sont divisés en une pluralité de canaux de fréquence, et dans laquelle l'au moins un filtre de repérage adaptatif (42, 44, 42-1, ..., 42-M) est configuré pour traiter individuellement les signaux audio dans des canaux de fréquence sélectionnés.
  9. Prothèse auditive selon la revendication 8, dans laquelle l'au moins un microphone BTE est déconnecté du processeur dans un canal de fréquence sélectionné si bien que la compensation de la perte auditive est basée uniquement sur la sortie de l'au moins un microphone ITE.
  10. Prothèse auditive selon l'une quelconque des revendications précédentes, dans laquelle
    l'au moins un transducteur d'entrée acoustique BTE est constitué d'un premier et un deuxième transducteur d'entrée acoustique BTE (14, 16), et
    l'au moins un filtre de repérage adaptif est constitué d'un premier et un deuxième filtre de repérage adaptif (42, 44), dans lequel
    le premier filtre de repérage adaptif présente une entrée qui est pourvue d'un signal de sortie du premier transducteur d'entrée acoustique BTE, et
    les coefficients de filtre du premier filtre de repérage adaptif sont adaptés si bien que la différence entre une sortie de l'au moins un microphone ITE et une sortie combinée du premier et deuxième filtre de repérage adaptatif est réduite.
    le deuxième filtre de repérage adaptif a une entrée qui est pourvue d'un signal de sortie du deuxième transducteur d'entrée acoustique BTE, et
    les coefficients de filtre du deuxième filtre de repérage adaptif sont adaptés si bien que la différence entre une sortie de l'au moins un microphone ITE et une sortie combinée du premier et deuxième filtre de repérage adaptatif est réduite.
  11. Prothèse auditive selon l'une quelconque des revendications précédentes, dans laquelle α dépend de la fréquence.
  12. Prothèse auditive selon l'une quelconque des revendications précédentes, dans laquelle W (f) = 1.
  13. Prothèse auditive selon l'une quelconque des revendications précédentes, dans laquelle p = 2.
  14. Prothèse auditive selon l'une quelconque des revendications précédentes, comprenant
    un élément de transmission de signal sonore (20) pour la transmission d'un signal sonore d'une sortie sonore dans le boîtier de prothèse auditive BTE à une première extrémité de l'élément de transmission de signal sonore au conduit auditif de l'utilisateur à une deuxième extrémité de l'élément de transmission de signal sonore,
    un écouteur (24) conçu pour être inséré dans le conduit auditif de l'utilisateur pour fixer et retenir l'élément de transmission de signal sonore (20) dans sa position prévue dans le conduit auditif de l'utilisateur.
EP12199761.3A 2012-12-28 2012-12-28 Localisation améliorée avec rétroaction Active EP2750412B1 (fr)

Priority Applications (5)

Application Number Priority Date Filing Date Title
DK12199761.3T DK2750412T3 (en) 2012-12-28 2012-12-28 Improved localization with feedback
EP12199761.3A EP2750412B1 (fr) 2012-12-28 2012-12-28 Localisation améliorée avec rétroaction
US13/872,459 US9148733B2 (en) 2012-12-28 2013-04-29 Hearing aid with improved localization
JP2013263656A JP5624202B2 (ja) 2012-12-28 2013-12-20 空間的キューおよびフィードバック
CN201310744757.7A CN103916807B (zh) 2012-12-28 2013-12-30 空间线索和反馈

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EP12199761.3A EP2750412B1 (fr) 2012-12-28 2012-12-28 Localisation améliorée avec rétroaction

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DK3038381T3 (da) 2014-12-22 2017-11-20 Gn Resound As Lytning i diffus støj
US9774960B2 (en) 2014-12-22 2017-09-26 Gn Hearing A/S Diffuse noise listening
DK3116240T4 (da) 2015-07-09 2023-03-27 Oticon As Høreanordning med aftagelig højttalerenhed

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WO2009049320A1 (fr) * 2007-10-12 2009-04-16 Earlens Corporation Système et procédé multifonction pour une audition et une communication intégrées avec gestion de l'annulation du bruit et de la contre-réaction
US8107654B2 (en) * 2008-05-21 2012-01-31 Starkey Laboratories, Inc Mixing of in-the-ear microphone and outside-the-ear microphone signals to enhance spatial perception
JP4355359B1 (ja) * 2008-05-27 2009-10-28 パナソニック株式会社 マイクを外耳道開口部に設置する耳掛型補聴器
EP2262285B1 (fr) * 2009-06-02 2016-11-30 Oticon A/S Dispositif d'écoute fournissant des repères de localisation améliorés, son utilisation et procédé

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DK2750412T3 (en) 2016-09-05

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