EP2750410B1 - Prothèse auditive avec une meilleure localisation - Google Patents

Prothèse auditive avec une meilleure localisation Download PDF

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Publication number
EP2750410B1
EP2750410B1 EP12199720.9A EP12199720A EP2750410B1 EP 2750410 B1 EP2750410 B1 EP 2750410B1 EP 12199720 A EP12199720 A EP 12199720A EP 2750410 B1 EP2750410 B1 EP 2750410B1
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EP
European Patent Office
Prior art keywords
btec
iec
hearing aid
microphone
bte
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EP12199720.9A
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German (de)
English (en)
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EP2750410A1 (fr
Inventor
Karl-Fredrik Johan Gran
Guilin Ma
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GN Hearing AS
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GN Hearing AS
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Priority to DK12199720.9T priority Critical patent/DK2750410T3/en
Priority to EP12199720.9A priority patent/EP2750410B1/fr
Priority to US13/872,720 priority patent/US9338561B2/en
Priority to JP2013266879A priority patent/JP5723962B2/ja
Priority to CN201810895006.8A priority patent/CN109089200B/zh
Priority to CN201310744341.5A priority patent/CN103916806A/zh
Publication of EP2750410A1 publication Critical patent/EP2750410A1/fr
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Publication of EP2750410B1 publication Critical patent/EP2750410B1/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
    • H04R25/70—Adaptation of deaf aid to hearing loss, e.g. initial electronic fitting
    • 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
    • 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
    • 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
    • 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 l 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 2004/136541 discloses a hearing aid device, and operating and adjustment methods therefor, with microphone disposed outside of the auditory canal.
  • the localization capability with regard to a signal source is lost.
  • the transfer function of the head or of the external ear is taken into account between the position at which the microphone is located and a position in the auditory canal of the hearing device user.
  • EP 2 088 802 discloses a method of estimating weighting function of audio signals in a hearing aid.
  • a method of generating an audible signal in a hearing aid by estimating a weighting function of received audio signals is disclosed, the hearing aid is adapted to be worn by a user; the method comprises the steps of: estimating a directional signal by estimating a weighted sum of two or more microphone signals from two or more microphones, where a first microphone of the two or more microphones is a front microphone, and where a second microphone of the two or more microphones is a rear microphone; estimating a direction-dependent time-frequency gain, and synthesizing an output signal.
  • a microphone of the hearing aid at a position 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 a microphone positioned behind the ear.
  • a microphone positioned in front of the pinna 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. 3 . 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 may provide 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) of the 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 new 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 acoustic 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 cue filter, each of which having an input that is provided with an output signal from a respective one of the at least one BTE sound input transducer and at least one ITE microphone, a processor configured to generate a hearing loss compensated output signal based on a combination of the BTE sound input
  • the hearing aid may further have a sound signal transmission member for transmission of a signal representing sound 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, 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 new 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.
  • Possible 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 "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 earpiece 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.
  • 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.
  • a method may be performed in the new hearing aid, comprising the steps of:
  • Feedback may be taken into account by performing the solution of the minimization problem above subject to the condition that the gain of the feedback loops must be less than one, i.e. subject to the condition that: 1
  • frequency weights W(f) may optimize the solution in certain one or more frequency ranges
  • angular weights W(l) may optimize the solution for certain directions of arrival of sound.
  • L (I) is the angular direction towards a sound source with respect to the looking direction of a user wearing the hearing aid.
  • ⁇ MSG f or min G i IEC f , G j BTEC f ( ⁇ l 0 L ⁇ 1 W l ⁇ W f HRT F l f ⁇ ⁇ i G i IEC f H l , i IEC f ⁇ ⁇ j G j BTEC f H l , j BTEC f
  • 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 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.
  • the output signal of each of the at least one ITE microphone may be pre-processed.
  • the output signal of each of the at least one BTE sound input transducer 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.
  • the at least one ITE microphone may operate as monitor microphone(s) for generation of an electronic sound signal with the desired spatial information of the current sound environment.
  • Each output signal of the at least one BTE sound input transducer and of the at least one ITE microphone is filtered with a respective cue filter, the transfer function of which are configured to provide a combined output signal of the cue filters with a transfer function that approximates the HRTFs of the user as closely as possible.
  • the combined output signal of the cue filters is passed on for further hearing loss compensation processing, e.g. with a compressor.
  • signals from the at least one BTE sound input transducer and the at least one ITE microphone are appropriately processed before hearing loss compensation whereby risk of feedback from the output transducer to the at least one ITE microphone and the at least one BTE sound input transducer is minimized and a large maximum stable gain can be provided.
  • the at least one cue filter G i IEC f of the respective at least one ITE microphone and the at least one cue filter G j BTEC f of the respective at least one BTE sound transducer may be determined by the following steps: With the hearing aid worn by the individual user:
  • measurements above need not be performed with the individual user; rather measurements may be performed that constitute good approximations to individual measurements for a number of humans with certain characteristics in common, e.g. humans within a certain age group, population, etc.: For a number of user's with certain characteristics in common:
  • the audio signals may be divided into a plurality of frequency channels, and be individually processed in individual frequency channels, and the transfer functions of
  • the at least one BTE microphone may be disconnected from the processor in one or more selected frequency channels so that hearing loss compensation is performed solely on the output of the at least one ITE microphone in the one or more selected frequency channels.
  • 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.
  • Fig. 4 schematically illustrates an example of the new 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 108, 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 BTE hearing aid 10 has an array of microphones 14-1, 14-2, ... , 14-M, 26-1, 26-2, ... , 26-N, for example constituted by a front microphone 14 and a rear microphone 16 and an ITE microphone 26 that resides in an earpiece 24 to be positioned in the outer ear of the user as illustrated in Figs. 4 - 6 .
  • the microphone output audio signals are digitized (A/D-converters not shown) and pre-processed, such as pre-filtered, in respective pre-processors 32-1, 32-2, ... , 32-N, 34-1, 34-2, ... , 34-M.
  • the digitized and possibly pre-processed microphone output audio signals 38-1, 38-2, ... , 38-N, 40-1, 40-2, ... , 40-M are filtered in cue filters 42-1, 42-2, ... , 42-N, 44-1, 44-2, ... , 44-M and the filtered signals 46-1, 46-2, ... , 46-N, 48-1, 48-2, ...
  • the hearing loss compensated signal 54 is output to a receiver 22 that converts the signal to an acoustic signal for transmission towards the ear drum of the user.
  • the new hearing aid circuitry shown in Fig. 7 may operate in the entire frequency range of the BTE hearing aid 10.
  • the hearing aid 10 shown in Fig. 7 may be a multi-channel hearing aid in which microphone output audio signals are divided into a plurality of frequency channels, and wherein divided 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 10 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.
  • one or more of 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.
  • one or more or all of the at least one ITE microphone provide the input to the processor 18 at frequencies where the hearing aid is capable of supplying the desired gain based on the input from the one or more of the at least one ITE microphone.
  • 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 as provided by the array of microphones.
  • the minimization problem may be solved subject to the condition that: 1
  • weights W(f) may optimize the solution in certain one or more frequency ranges
  • angular weights W(l) may optimize the solution for certain directions of arrival of sound.
  • ⁇ MSG f or min G i IEC f , G j BTEC f ( ⁇ l 0 L ⁇ 1 W l ⁇ W f HRT F l f ⁇ ⁇ i G i IEC f H l , i IEC f ⁇ ⁇ j G j BTEC f H l , j BTEC
  • 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 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.
  • 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 an adaptive feedback canceller 70 has been added with an input 72 connected to the output of the processor 18 and outputs 74-1, 74-2, ... , 74-N, 76-1, 76-2, ... , 76-M connected to respective subtractors 78-1, 78-2, ... , 78-N. 80-1, 80-2, ... , 80-M for subtraction of the outputs from each respective microphone output audio signal to provide feedback compensated signals fed to the corresponding pre-processors 32-1, 32-2, ... , 32-N, 34-1, 34-2, ...
  • the feedback canceller 70 provide signals 74-1, 74-2, ... , 74-N, 76-1, 76-2, ... , 76-M that constitute approximations of corresponding feedback signals travelling from the output transducer 22 to the respective microphones 14-1, 14-2, ... , 14-M, 26-1, 26-2, ... , 26-N.
  • the hearing aid 10 shown in Fig. 8 may be a multi-channel hearing aid in which microphone output audio signals are divided into a plurality of frequency channels, and wherein divided signals are processed individually in each of the frequency channels.
  • Fig. 8 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 adaptive feedback cancelling circuitry may also be divided into the plurality of frequency channels; or, 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 other circuitry is divided into.
  • the signal processing illustrated in Fig. 8 may be performed in a selected frequency band, e.g. selected during fitting of the hearing aid 10 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.
  • one or more of 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 one or more of the at least one ITE microphone provide the input to the processor 18 at frequencies where the hearing aid is capable of supplying the desired gain based on the input from the one or more of the at least one ITE microphone.
  • 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 as provided by the array of microphones.
  • Fig. 9 is a schematic block diagram illustrating one method of determining the cue filters 42-1, 42-2, ... , 42-N, 44-1, 44-2, ... , 44-M of the hearing aids shown in Figs. 7 and 8 , e.g. during fitting of the hearing aid.
  • the cue filters 42-1, 42-2, ... , 42-N, 44-1, 44-2, ... , 44-M are adaptive filters that are allowed to adapt during fitting of the hearing aid. After determination of the cue filters, , the filter coefficients are kept constant at the respective determined values.
  • the microphone ITE REF 25 may be a single microphone located in a position with relation to an artificial head or a user with good preservation of spatial cues of incoming sound; or, the microphone ITE REF 25 may represent an array of microphones connected to pre-processor 31 and located in a position with relation to an artificial head or a user in which a combined signal output from the array of microphones, e.g. in cooperation with pre-processor 31, has good preservation of spatial cues of incoming sound.
  • the output signal of microphone (array) ITE REF 25 has a transfer function that constitutes a good approximation to the HRTFs of the user for one or more directions towards a sound source.
  • various sound sources emit sound from respective various directions with relation to the artificial head or user of the hearing aid
  • the cue filters 42-1, 42-2, ... , 42-N, 44-1, 44-2, ... , 44-M are allowed to adapt to the output signal 51 of the delay 41 and at the end of adaptation, e.g. when the filter coefficients of the cue filters 42-1, 42-2, ... , 42-N, 44-1, 44-2, ... , 44-M have stabilized, i.e. the changes of the filter coefficients have become less than a certain threshold, the filter coefficients are no longer allowed to change.
  • the signal 51 is disconnected from subtractor 54 so that signal 56 constitutes a combined output signal of the cue filters 42-1, 42-2, ... , 42-N, 44-1, 44-2, ... , 44-M that has substantially the same spatial cues as the output signal 51.
  • the delay 41 delays the output signal of the pre-processor 31 with a delay that is substantially equal to the delay of the cue filters 42-1, 42-2, ,..., 42-N, 44-1, ... , 44-M.
  • adaptation of the filter coefficients of the cue filters 42-1, 42-2, ,..., 42-N, 44-1, ... , 44-M are controlled by adaptive cue controller 48 that controls the adaptation of the filter coefficients to minimize the output signal 52 of the subtractor 54 equal to the difference between sum of output signals 50-1, 50-2, ... , 50-N, 46-1, 46-2, ... , 46-M and the ITE REF microphone audio signal 51.
  • W(f) may be equal to one for all frequencies and/or W(l) may be equal to one for all directions.
  • Possible feedback may be taken into account by solving the minimization problem above subject to the condition that 1
  • ⁇ MSG f or min G i IEC f , G j BTEC f ( ⁇ l 0 L ⁇ 1 W l ⁇ W f HRT F l f ⁇ ⁇ i G i IEC f H l , i IEC f ⁇ j G j BTEC f H l , j BTEC f ⁇ p + ⁇ ⁇ ⁇ i G i IEC f H FB , i IEC f + ⁇ j G j BTEC f H FB , j BTEC f ⁇ p )
  • the feedback compensation circuitry 72, 70, 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, shown in Fig. 8 may be added to the circuit of Fig. 9 and in addition connecting the outputs 74-1, 74-2, ... , 74-N, 76-1, 76-2, ...
  • 76-M of the adaptive feedback filter 70 to respective inputs of the adaptive cue control 48 each of the outputs 74-1, 74-2, ... , 74-N, 76-1, 76-2, ... , 76-M providing an estimate of the hearing aid related transfer function of the respective at least one ITE microphone H l , i ITEC f , and the hearing aid related transfer functions of the respective at least one BTE microphone H l , j BTEC f so that the adaptive cue control 48 can check the condition: 1
  • ⁇ MSG f or solve the minimization problem: min G i IEC f , G j BTEC f ( ⁇ l 0 L ⁇ 1 W l ⁇ W f HRT F l f ⁇ ⁇ i G i IEC f H l

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Claims (14)

  1. Procédé de détermination de paramètres d'une prothèse auditive (10) pour préserver des repères spatiaux de sons arrivant à un utilisateur de la prothèse auditive, la prothèse auditive (10) comprenant
    un boîtier de prothèse auditive BTE (12) configuré pour être porté derrière la pinna d'un utilisateur,
    au moins un transducteur d'entrée acoustique BTE logé dans le boîtier de prothèse auditive BTE et comprenant au moins un microphone BTE (14-1, ..., 14-M), dont chacun est configuré pour la conversion de son acoustique en un signal audio respectif,
    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 (26-1, ..., 26-N) logé dans le boîtier du microphone ITE, dont chacun est configuré pour la conversion du son acoustique en un signal audio respectif,
    au moins un filtre de repérage (44-1, ..., 44-M) ayant une entrée qui est pourvue d'un signal de sortie de l'un respectif de l'au moins un transducteur d'entrée acoustique BTE (14-1, ..., 14-M), et au moins un filtre de repérage (42-1, ..., 42-N) ayant une entrée qui est pourvue d'un signal de sortie de l'un respectif de l'au moins un microphone ITE (26-1, ..., 26-N),
    un processeur (18) configuré pour générer un signal de sortie compensé en perte auditive (54) basé sur une combinaison (52) des signaux audio filtrés sortis par les filtres de repérage,
    un transducteur de sortie (22) pour la conversion du signal de sortie compensé en perte auditive en un signal de sortie acoustique qui peut être reçu par le système auditif humain,
    le procédé comprenant les étapes consistant à :
    pour un ensemble de directions (l) lié à a prothèse auditive BTE, déterminer les fonctions de transfert liées à la têteHRTFl (f),
    les fonctions de transfert liées à la prothèse auditive H l , i ITEC f
    Figure imgb0146
     du i-ième microphone de l'au moins un microphone ITE (26-1, ..., 26-N) pour la direction (I),
    les fonctions de transfert liées à la prothèse auditive H l , j BTEC f
    Figure imgb0147
     du j-ième microphone de l'au moins un microphone BTE (14-1, ..., 14-M),
    déterminer les fonctions de transfert G FB , i IEC f
    Figure imgb0148
     d'un trajet de rétroaction associé au i-ième microphone de l'au moins un microphone ITE,
    déterminer les fonctions de transfert H FB , j BTEC f
    Figure imgb0149
     d'un trajet de rétroaction associé au j-ième microphone de l'au moins un transducteur d'entrée acoustique BTE, et
    déterminer des fonctions de transfert G i IEC f
    Figure imgb0150
     du i-ième filtre de repérage de l'au moins un filtre de repérage filtrant des signaux audio de l'au moins un microphone ITE (26-1, ..., 26-N),
    déterminer des fonctions de transfert G j BTEC f
    Figure imgb0151
     du j-ième filtre de repérage de l'au moins un filtre de repérage filtrant des signaux audio de l'au moins un microphone BTE (14-1, ..., 14-M) en résolvant : min G i IEC f , G i BTEC f ∑ l = 0 L − 1 W l ‖ W f ( HRT F l f − ∑ i G i IEC f H l , i IEC f − ∑ j G j BTEC f H l , j BTEC f ) ‖ p
    Figure imgb0152
    dans lequel
    W(l) est un facteur de pondération angulaire,
    W(f) est un facteur de pondération dépendant de la fréquence, et
    p est un nombre entier positif.
  2. Procédé selon la revendication 1, comprenant en outre les étapes consistant à :
    déterminer les fonctions de transfert H FB , i IEC f
    Figure imgb0153
     du trajet de rétroaction associé à l'au moins un microphone ITE respectif,
    déterminer les fonctions de transfert H FB , i BTEC f
    Figure imgb0154
     du trajet de rétroaction associé à l'au moins un transducteur d'entrée acoustique BTE respectif, et
    déterminer les coefficients de filtre de
    l'au moins un filtre de repérage G i IEC f
    Figure imgb0155
     de l'au moins un microphone ITE respectif,
    l'au moins un filtre de repérage G j BTEC f
    Figure imgb0156
     de l'au moins un transducteur acoustique BTE respectif, en résolvant min G i IEC f , G i BTEC f ∑ l = 0 L − 1 W l ‖ W f ( HRT F l f − ∑ i G i IEC f H l , i IEC f − ∑ j G j BTEC f H l , j BTEC f ) ‖ p
    Figure imgb0157
     soumis à 1 | ∑ i G i IEC f H FB , i IEC f + ∑ j G j BTEC f H FB , j BTEC f | ≥ MSG f
    Figure imgb0158
     dans lequel MSG(f) est le gain stable maximal en fonction de la fréquence f.
  3. Procédé selon la revendication 1, comprenant en outre les étapes consistant à :
    déterminer les fonctions de transfert H FB , i IEC f
    Figure imgb0159
     du trajet de rétroaction associé à l'au moins un microphone ITE respectif,
    déterminer les fonctions de transfert H FB , i BTEC f
    Figure imgb0160
     du trajet de rétroaction associé à l'au moins un transducteur d'entrée acoustique BTE respectif, et
    déterminer les coefficients de filtre de
    l'au moins un filtre de repérage G i IEC f
    Figure imgb0161
     de l'au moins un microphone ITE respectif,
    l'au moins un filtre de repérage G j BTEC f
    Figure imgb0162
     de l'au moins un transducteur acoustique BTE respectif, en résolvant min G i IEC f , G i BTEC f ( ∑ l = 0 L − 1 W l ‖ W f ( HRT F l f − ∑ i G i IEC f H l , i IEC f − ∑ j G j BTEC f H l , j BTEC f ) ‖ p + α ‖ ∑ i G i IEC f H FB , i IEC f + ∑ j G j BTEC f H FB , j BTEC f ‖ p )
    Figure imgb0163
     dans lequel α est un facteur de pondération équilibrant la précision de repérage spatial et la performance de rétroaction.
  4. Procédé selon la revendication 1, dans lequel les fonctions de transfert liées à la tête HRTFl (f) sont approximées avec les fonctions de transfert associées à la prothèse auditive d'une combinaison de l'au moins un microphone ITE :
    H l , ref ITEC f ,
    Figure imgb0164
     comprenant les étapes consistant à:
    déterminer les fonctions de transfert H FB , i IEC f
    Figure imgb0165
     du trajet de rétroaction associé à l'au moins un microphone ITE respectif,
    déterminer les fonctions de transfert H FB , i BTEC f
    Figure imgb0166
     du trajet de rétroaction associé à l'au moins un transducteur d'entrée acoustique BTE respectif, et
    déterminer les coefficients de filtre de
    l'au moins un filtre de repérage G i IEC f
    Figure imgb0167
     de l'au moins un microphone ITE respectif non inclus dans la combinaison de l'au moins un microphone ITE, l'au moins un filtre de repérage G j BTEC f
    Figure imgb0168
     de l'au moins un transducteur acoustique BTE respectif, en résolvant min G i IEC f , G i BTEC f ∑ l = 0 L − 1 W l ‖ W f ( H l , ref ITEC f − ∑ i ≠ ref G i IEC f H l , i IEC f − ∑ j G j BTEC f H l , j BTEC f ) ‖ p
    Figure imgb0169
     soumis à 1 | ∑ i ≠ ref G i IEC f H FB , i IEC f + ∑ j G j BTEC f H FB , j BTEC f | ≥ MSG f
    Figure imgb0170
     dans lequel MSG(f) est le gain stable maximal en fonction de la fréquence f.
  5. Procédé selon la revendication 1, dans lequel les fonctions de transfert liées à la tête HRTFl (f) sont approximées avec la fonction de transfert associée à la prothèse auditive d'une combinaison de l'au moins un microphone ITE :
    H l , ref ITEC f ,
    Figure imgb0171
     comprenant les étapes consistant à:
    déterminer les fonctions de transfert H FB , i IEC f
    Figure imgb0172
     du trajet de rétroaction associé à l'au moins un microphone ITE respectif,
    déterminer les fonctions de transfert H FB , i BTEC f
    Figure imgb0173
     du trajet de rétroaction associé à l'au moins un transducteur d'entrée acoustique BTE respectif, et
    déterminer les coefficients de filtre de
    l'au moins un filtre de repérage G i IEC f
    Figure imgb0174
     de l'au moins un microphone ITE respectif non inclus dans la combinaison de l'au moins un microphone ITE,
    l'au moins un filtre de repérage G j BTEC f
    Figure imgb0175
     de l'au moins un transducteur acoustique BTE respectif, en résolvant min G i IEC f , G i BTEC f ( ∑ l = 0 L − 1 W l ‖ W f ( H l , ref ITEC f − ∑ i ≠ ref G i IEC f H l , i IEC f − ∑ j G j BTEC f H l , j BTEC f ) ‖ p + α ‖ ∑ i ≠ ref G i IEC f H FB , i IEC f + ∑ j G j BTEC f H FB , j BTEC f ‖ p )
    Figure imgb0176
     dans lequel α est un facteur de pondération équilibrant la précision de repérage spatial et la performance de rétroaction.
  6. Procédé selon l'une quelconque des revendications précédentes, dans lequel les déterminations, pour un ensemble de directions I par rapport à la prothèse auditive BTE,
    des fonctions de transfert liées à la têteHRTFl (f),
    des fonctions de transfert liées à la prothèse auditive de l'au moins un microphone ITE respectif H l , i ITEC f ,
    Figure imgb0177
     et
    des fonctions de transfert liées à la prothèse auditive de l'au moins un microphone BTE respectif H l , i BTEC f
    Figure imgb0178
    sont effectuées avec la prothèse auditive montée sur une tête artificielle.
  7. Procédé selon l'une quelconque des revendications précédentes 1 à 5, dans lequel les déterminations individuelles, pour un ensemble de directions (l) par rapport à la prothèse auditive BTE,
    des fonctions de transfert liées à la tête HRTFl (f),
    des fonctions de transfert liées à la prothèse auditive de l'au moins un microphone ITE respectif H l , i ITEC f ,
    Figure imgb0179
     et
    des fonctions de transfert liées à la prothèse auditive de l'au moins un microphone BTE respectif H l , i BTEC f
    Figure imgb0180
    sont effectuées pour un certain nombre d'utilisateurs représentant un groupe sélectionné d'utilisateurs, et dans lequel les coefficients de filtre de l'au moins un filtre de repérage G j BTEC f
    Figure imgb0181
     de l'au moins un transducteur acoustique BTE respectif sont déterminés en fonction de valeurs moyennées des fonctions de transfert liées à la têteHRTFl (f),
    des fonctions de transfert liées à la prothèse auditive de l'au moins un microphone ITE respectif H l , i ITEC f ,
    Figure imgb0182
     et
    des fonctions de transfert liées à la prothèse auditive de l'au moins un microphone BTE respectif H l , i BTEC f
    Figure imgb0183
    du nombre d'utilisateurs représentant le groupe d'utilisateurs sélectionné.
  8. Procédé selon l'une quelconque des revendications précédentes, comprenant l'étape de division des signaux audio représentant le son en une pluralité de canaux fréquentiels, et du traitement individuel des signaux audio dans des canaux fréquentiels individuels, les coefficients de filtrage
    l'au moins un filtre de repérage G i IEC f
    Figure imgb0184
     de l'au moins un microphone ITE respectif,
    de l'au moins un filtre de repérage G j BTEC f
    Figure imgb0185
     de l'au moins un transducteur acoustique BTE respectif
    sont déterminés individuellement dans des canaux de fréquence sélectionnés.
  9. Procédé selon la revendication 8, comprenant l'étape consistant à déconnecter l'au moins un microphone BTE 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. Procédé selon l'une quelconque des revendications précédentes, dans lequel W(l) = 1.
  11. Procédé selon l'une quelconque des revendications précédentes, dans lequel W(f) = 1.
  12. Procédé selon l'une quelconque des revendications précédentes, dans lequel p = 2.
  13. Prothèse auditive avec un processeur configuré pour exécuter un procédé selon l'une quelconque des revendications précédentes.
  14. Prothèse auditive selon la revendication 13, comprenant un élément de transmission de signal sonore pour la transmission d'un signal représentant un son provenant d'une sortie du son dans le boîtier de la prothèse auditive BTE à une première extrémité de l'élément de transmission de signal sonore dans le conduit auditif de l'utilisateur à une deuxième extrémité de l'élément de transmission de signal sonore,
    un écouteur conçu pour être inséré dans le conduit auditif de l'utilisateur pour fixer et retenir l'élément de transmission de signal sonore dans sa position prévue dans le conduit auditif de l'utilisateur.
EP12199720.9A 2012-12-28 2012-12-28 Prothèse auditive avec une meilleure localisation Active EP2750410B1 (fr)

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DK12199720.9T DK2750410T3 (en) 2012-12-28 2012-12-28 Hearing aid with improved location
EP12199720.9A EP2750410B1 (fr) 2012-12-28 2012-12-28 Prothèse auditive avec une meilleure localisation
US13/872,720 US9338561B2 (en) 2012-12-28 2013-04-29 Hearing aid with improved localization
JP2013266879A JP5723962B2 (ja) 2012-12-28 2013-12-25 定位が向上された補聴器
CN201810895006.8A CN109089200B (zh) 2012-12-28 2013-12-30 确定助听器的参数的方法以及助听器
CN201310744341.5A CN103916806A (zh) 2012-12-28 2013-12-30 具有改进定位的助听器

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EP3038381B1 (fr) 2014-12-22 2017-08-09 GN Resound A/S Écoute de bruit diffus
US9774960B2 (en) 2014-12-22 2017-09-26 Gn Hearing A/S Diffuse noise listening
EP3185589B1 (fr) 2015-12-22 2024-02-07 Oticon A/s Dispositif auditif comprenant un système de commande de microphone

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DE10249416B4 (de) * 2002-10-23 2009-07-30 Siemens Audiologische Technik Gmbh Verfahren zum Einstellen und zum Betrieb eines Hörhilfegerätes sowie Hörhilfegerät
US8401212B2 (en) * 2007-10-12 2013-03-19 Earlens Corporation Multifunction system and method for integrated hearing and communication with noise cancellation and feedback management
EP1594344A3 (fr) * 2005-08-03 2006-03-15 Phonak Ag Méthode pour obtenir des charactéristiques acoustiques, prothèse auditive et son procédé de fabrication
EP2088802B1 (fr) * 2008-02-07 2013-07-10 Oticon A/S Procédé d'évaluation de la fonction de poids des signaux audio dans un appareil d'aide auditive

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