EP1841281B1 - System und Verfahren zur Erzeugung von richtungsbestimmenden Merkmalen im Hörbereich - Google Patents

System und Verfahren zur Erzeugung von richtungsbestimmenden Merkmalen im Hörbereich Download PDF

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Publication number
EP1841281B1
EP1841281B1 EP06111808.9A EP06111808A EP1841281B1 EP 1841281 B1 EP1841281 B1 EP 1841281B1 EP 06111808 A EP06111808 A EP 06111808A EP 1841281 B1 EP1841281 B1 EP 1841281B1
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European Patent Office
Prior art keywords
unit
hearing aid
microphone
electric signal
signal
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EP06111808.9A
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English (en)
French (fr)
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EP1841281A1 (de
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Graham Naylor
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Oticon AS
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Oticon AS
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Priority to EP06111808.9A priority Critical patent/EP1841281B1/de
Priority to DK06111808.9T priority patent/DK1841281T3/en
Priority to CN 200710086965 priority patent/CN101064972B/zh
Priority to AU2007201362A priority patent/AU2007201362B2/en
Publication of EP1841281A1 publication Critical patent/EP1841281A1/de
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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
    • H04R25/407—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
    • H04R25/55—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception using an external connection, either wireless or wired
    • H04R25/554—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception using an external connection, either wireless or wired using a wireless connection, e.g. between microphone and amplifier or using Tcoils
    • 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

  • This invention relates a system and method for generating auditory spatial cues.
  • this invention relates to a hearing aid such as a behind-the-ear (BTE), in-the-ear (ITE), completely-in-canal (CIC), receiver-in-the-ear (RITE), middle-ear-implant (MEI) or cochlear implant (CI), wherein the hearing aid compensates for a hearing-impaired user's lost sense of the spatial locations of sounds.
  • BTE behind-the-ear
  • ITE in-the-ear
  • CIC completely-in-canal
  • RITE receiver-in-the-ear
  • MEI middle-ear-implant
  • CI cochlear implant
  • a normal-hearing person has an inherent sense of the location of sounds in his spatial surroundings. This inherent sense is achieved by the fact that sound emitted somewhere in the spatial surroundings of the person is transmitted both directly and indirectly to the ear canal.
  • sound reflections from the body of the person i.e. torso, shoulders, head, neck and external part of ears, provide a head-related transfer function (HRTF).
  • HRTF head-related transfer function
  • the HRTF consists of a plurality of dips and peaks, which are caused by the constructive and destructive summing of reflected and thus time delayed sounds and direct sound before arrival in the ear canal. These dips and/or peaks are generally referred to as auditory spatial cues.
  • the pattern of auditory spatial cues in a HRTF is dependent on the spatial location of the source emitting the sound, relative to the ear and body structures causing the reflections. Hence the auditory spatial cues may assist the normal-hearing person to locate where sounds originate from in the spatial surroundings.
  • the normal-hearing person has an inherent means for selecting, concentrating, or parsing his hearing for particular sounds in the spatial surroundings by using the auditory spatial cues.
  • the auditory spatial cues occur in a frequency range where the person has a hearing impairment this affects the person's ability to determine the location of sound sources.
  • the auditory spatial cues be inaudible due to having insufficient intensity to overcome the listener's hearing threshold, but the reduced perceptual frequency resolution which often accompanies hearing impairment may also cause the cues to lose distinctness and thus utility.
  • WO 03/009639 discloses a directional acoustic receiver such as a microphone array or a human external ear that has a varying acoustic impulse response with the direction in space of the sound source relative to the acoustic receiver.
  • the international patent further discloses a method for recording and reproducing a three dimensional auditory scene for listeners by recording a three dimensional auditory scene using the microphone array, modifying the sound recorded by the microphone array using information derived from differences between directional acoustic transfer function of the microphones in the microphone array and the directional acoustic transfer functions of the external ears of the listener, and collecting, arranging and combining the signals intended for the left and right external ear of the listener into an output format identifying these signals as a representation of a three dimensional auditory scene that enables a perceptually valid acoustic reproduction of the sound that would have been present at the ears of the listener, were the listener to have been present at the position of the microphone array in the original sound environment.
  • the international patent application relates to a system for recreation of a sound for a listener in a spatial position as if the listener was in the position of the microphone array in the originally recorded sound.
  • the international patent application fails to disclose an acoustic receiver compensating for the perceptual degradation of spatial hearing suffered by a listener with a hearing impairment.
  • WO 2005/015952 discloses a hearing device for enhancing sound heard by a hearing-impaired listener by monitoring sound in an environment in which the listener is located, and manipulating the frequency placement of high-frequency components of the sound in a high-frequency band (e.g. above 4 kHz) so as to make the spectral features corresponding to auditory spatial cues audible to the hearing-impaired listener, thus aiding in the listener's sound externalisation and spatialisation.
  • the hearing aid comprises a processor for transposing the spectral features from a high-frequency band to a lower-frequency band.
  • the processor transposes the high-frequency spectral features by performing a Fast Fourier Transform (FFT) and modifying the frequency representation of the signal, or by performing a re-sampling technique on the received signal in the time domain and shifting and/or compressing the high-frequency spectral features to a lower frequency band.
  • FFT Fast Fourier Transform
  • the hearing device according to the international patent application utilises a complicated algorithmic manipulation of the signal, which introduces domain shifts generally requiring great processing time and importantly takes up physical space on a signal processing chip, which for a hearing device already faces tremendous restrictions as to availability of space.
  • International patent application WO 99/14986 discloses a system for transposing high-frequency band auditory cues to a lower frequency band by proportionally compressing the audio signal.
  • the system achieves this objective by maintaining the spectral shape of the audio signal, while scaling its spectrum in the frequency domain, via frequency compression, and transposing its spectrum in the frequency domain, via frequency shifting.
  • the system comprises a Fast Fourier Transform (FFT) unit for transforming the audio signal from time domain to frequency domain, a processor for performing scaling and transposing functions on the frequency signal, and finally an inverse FFT unit for transforming the scaled and transposed frequency signal back into the time domain.
  • FFT Fast Fourier Transform
  • WO 2005/015952 the system according to the international patent application no: WO 99/14986 also utilises a similar complicated algorithmic manipulation of the signal, which obviously requires processing time and space.
  • UK Patent Application GB 2 370 176 A also refers to a microphone unit that aims to enhance the capabilities and performance of existing live recording equipment by generating and incorporating artificial vertical localisation cues into the signal output.
  • An object of the present invention is to provide an improved hearing aid generating new auditory spatial cues.
  • a particular advantage of the present invention is the provision of a hearing aid wherein the introduction of new auditory spatial cues require very little processing time and thus require very little physical space on a signal processing chip.
  • auditory spatial cue is in this context to be construed as a dip, notch or peak in the frequency response of a signal presented to a user.
  • spatial dimension is in this context to be construed as a part of a spherical orientation as, for example may be represented by the r, ⁇ , and ⁇ spherical coordinate system.
  • the spatial dimension thus may comprise a semicircular part of the polar angle ⁇ , whereas the polar axis is construed as the axis through the first and second microphones.
  • first is in this context to be construed as entirely a means for distinguishing or differentiating between a plurality of elements, i.e. a first, second, and third element is not to be construed as a sequential series starting with the first element.
  • speaker is in this context to be construed as a receiver or miniature loudspeaker.
  • the sound originating from a sound source at one spatial location may, when converted at each of the microphones, differ since the distance from each of the microphones to the sound source may be different causing the sound reaching the first microphone to be time-delayed or time-advanced relative to the sound reaching the second microphone. Therefore summing of the first and second electric signal, advantageously, generates a first auditory spatial cue in the frequency spectrum of the summed signal. By moving the sound source in the first spatial dimension the first auditory spatial cue is shifted in the frequency domain thus enabling the user to experience a sense of sound location in the first spatial dimension.
  • the frequency of the first auditory spatial cue may, advantageously, be placed in an optimum frequency range for the user of the hearing aid system. Consequently, the hearing aid system according to the present invention provides a new auditory cue for a first spatial dimension, which may be used by the user of the hearing aid system to improve the user's sense of sound location thereby enabling the user to select, concentrate, or parse hearing for particular sounds in the spatial surroundings.
  • the microphone unit according to the present invention further comprises a third microphone for converting sound to a third electric signal on a third output, and wherein the third microphone is separated perpendicularly relative to an axis between the first and second microphones by a second predetermined distance. By introducing the third microphone a second spatial dimension may be accomplished.
  • the hearing aid system according to the present invention further comprises a filter unit connecting to the third output and adapted to filter the third electric signal thereby generating a filtered third electric signal. The filter unit removes unnecessary auditory spatial cues so that the user is presented with a single auditory spatial cue for a second spatial dimension.
  • the hearing aid system generates a first auditory spatial cue based on the sound received at the first and second microphones and a second auditory spatial cue based on the sound received at the third microphone relative to the summed signal from the first and second microphones.
  • the hearing aid system further comprises a second delay unit connecting to the first calculation unit and adapted to delay the first summed signal.
  • the hearing aid system may comprise a second delay unit connecting to the filter unit and adapted to delay the filtered third electric signal.
  • the hearing aid system may comprise a second delay unit connecting to the third microphone and adapted to delay the third electric signal.
  • the hearing aid system may comprise a plurality of second delay unit connecting to the third microphone, the filter unit, and/or first calculation unit, and adapted to delay the third electric signal, the filtered third electric signal and/or the first summed signal.
  • the hearing aid system further comprises a second calculation unit connecting to the second delay unit and the filter unit and adapted to sum the delayed filtered first summed signal and the filtered third electric signal. Hence the first and second auditory cues are thereby introduced into the signal presented to the user of the hearing aid system.
  • the first calculation unit may further be adapted to weight the delayed first electric signal and the second electric signal.
  • the second calculation unit may further be adapted to weight the delayed filtered first summed signal and the filtered third electric signal. This advantageously enables a more general solution since the signals may be multiplied by weighting factors before summing. In practice weigthing enables adjusting the depth/height of the spectral dips/peaks.
  • the hearing aid system may further comprise a transceiver unit connecting to the first microphone unit and adapted to transmit the first, second and/or third electric signal of a first hearing aid to a transceiver unit of a second hearing aid, which may comprise a second microphone unit separated from the first microphone unit by a third predetermined distance being perpendicular to the axis between the first and second microphone.
  • the transceiver unit may further be adapted to receive electric signals from said second microphone unit.
  • the transceiver unit may comprise a third delay unit adapted to delay the first, second, and/or third electric signal by a third predetermined delay.
  • the third predetermined delay unit may as well as the third predetermined separation advantageously be used for positioning of a third auditory spatial cue in an optimal frequency range for the user.
  • the hearing aid system may further comprise a calculation device adapted to be carried elsewhere on the user's body and communicating with the transceivers of the first and second hearing aids and adapted to generate a first, second and/or third auditory spatial cues associated with spatial orientation of sound received at the first and second microphone unit.
  • the calculation device may comprise a third microphone unit adapted to provide a further electric signal for generating a further auditory spatial cue.
  • the hearing aid system advantageously does not require a microphone to be exposed to the pinna's natural reflection patterns, does not require any algorithmic manipulation of the digitised signal, and it creates no non-linear distortions of the true acoustic signal.
  • the hearing aid system may further comprise a first filterbank connecting to the first microphone and adapted to generate a first series of frequency channel signals from the first electric signal and second filterbank connected to the second microphone and adapted to generate a second series of frequency channel signals from the second electric signal, and wherein the first delay unit is adapted to independently delay each of said first series of frequency channel signals and the first calculation unit is adapted to independently sum each of said delayed first series of frequency channel signals and said second series of frequency channel signals.
  • the filterbank enables that each microphone signal may be filtered into a plurality frequency channels and that each channel may be processed by its own set of further filter, calculation and delay units before being recombined in a processing unit to be presented to the user. Thus a multiplicity of auditory spatial cues may be optimally placed in a multiplicity of frequency ranges.
  • the hearing aid system may further comprise A/D, D/A conversion units adapted to convert the microphone signals from analogue to digital domain and to convert the processed signal from digital to analogue domain. This obviously provides improved capability in performing detailed calculations on the signals.
  • a method for generating auditory spatial cues comprising generating a first electric signal defining a sound received at a first position, generating a second electric signal defining said sound received at a second position, delaying said first electric signal a predetermined first time delay thereby generating a delayed first electric signal, summing said delayed first electric signal and said second electric signal thereby generating a first summed signal having a first auditory cue representing a first spatial dimension, processing said first summed signal, and converting said processed signal to a processed sound.
  • the method may comprise any features of the hearing aid system according to the first aspect of the present invention.
  • the method is particularly advantageous since it enables the adaptation of the auditory cues to a user of a hearing aid system to be performed by simulating sounds originating from various positions in a three-dimensional space without actually having to move a loudspeaker around in said space.
  • the simulation may be performed by phase-shifting the first electric signal relative to the second electric signal.
  • Figure 1 shows a hearing aid system and designated in entirety by reference numeral 100.
  • the hearing aid system 100 comprises a first and second microphone 102 and 104 for converting the sound into a first and second electric signal, respectively.
  • the first and second microphones 102 and 104 are separated by a distance d 1 between the centers of the membranes of the first and second microphones 102 and 104.
  • the first electric signal is time delayed by a delay unit 106 before being communicated to a first calculation unit 108, which weights and sums the delayed first electric signal and the second electric signal.
  • a first calculation unit 108 By positioning of the first and second microphones 102, 104 relative to one another by the distance d 1 and by adjusting the time delay of the first electric signal the output of the first calculation unit 108 provides a first auditory spatial cue, which in case of movement of the sound source shifts up and down in the frequency spectrum of the summed signal.
  • the change in frequency of the auditory spatial cue represents a change in elevation of the sound source.
  • the summed signal is communicated from the first calculation unit 108 to a signal processing unit 110, which performs any signal processing required in accordance with the user's hearing impairment. That is, the processor performs the general frequency shaping, compression and amplification required to obtain an audible signal to the user through a speaker 112.
  • the hearing aid system 100 may be advantageous decouple the first and second microphones 102 and 104 and generate the first and second electric signal by means of a signal generator so as to simulate a sound environment.
  • the simulated sound established by the signal generator may be established by phase-shifting the first electric signal relative to the second electric signal.
  • Figure 2 shows a graph of the summed signal as a function of frequency at a first and second elevation angle ⁇ 1 and ⁇ 2 when the first and second microphones 102 and 104 are positioned vertically relative to one another and relative to a user standing upright.
  • the auditory spatial cue (notch) changes as the elevation angle ⁇ changes thus helping the hearing-impaired user, who otherwise has limited sense of sound directionality due to the fact that the normal auditory cues caused by HRTF are in a frequency range where the user has a hearing impairment.
  • FIG. 3 shows a hearing aid system according to the present invention and designated in entirety by reference numeral 200.
  • the hearing aid system 200 comprises some of the elements of the hearing aid system 100, which elements are referenced using the same reference numerals.
  • the hearing aid system 200 comprises a third microphone 114 separated perpendicularly relative to the axis of the first and second microphones 102, 104 by a distance d 2 .
  • the third microphone 114 converts the sound to a third electric signal, which is forwarded to a filter 116 with for example a low-pass cut-off frequency lying for example between 2 kHz and 4 kHz thereby avoiding the occurrence of auditory cues above the cut-off frequency to ensure that the first elevation auditory cue provided by microphones 102 and 104 is not disturbed.
  • the first and second microphones 102 and 102 may be placed on a behind-the-ear component of a hearing aid, while the third microphone 114 may be placed on a receiver-in-the-ear, ear-mould or ear-plug part of the hearing aid having its membrane facing outward.
  • the filtered third electric signal is communicated to a second calculation unit 120, which connects to the filter unit 116 and to a second delay unit 118 delaying the first summed signal and which weights and sums the filtered third electric signal and the first summed signal.
  • the second calculation unit 120 generates a second summed signal within which is encoded for example an elevation auditory cue and a front/back auditory cue based on the filtered third electric signal and the first summed signal. Subsequently, the second summed signal is forwarded to the processing unit 110 and the speaker 112.
  • Figure 4 shows a hearing aid system according to an embodiment of the present invention and designated in entirety by reference numeral 300. It should be understood that the hearing aid system 300 may incorporate features of the hearing aid systems designated 100 and 200.
  • the hearing aid system 300 comprises a first and second hearing aid 302 and 304.
  • the first hearing aid 302 comprises elements of hearing aid systems 100 and 200, that is, comprises a first microphone unit 306 generating a first, second and/or third electric signal from a sound. These signals are communicated to a first auditory cue generator 308 generating an elevation auditory cue and/or a front/back auditory cue in a first summed signal communicated to a first processing unit 310 performing the, normally, required processing operations in accordance with sound and hearing impairment of the user before communicating a processed signal to a speaker 312.
  • the second hearing aid 304 similarly comprises elements of hearing aid systems 100 and 200, that is, comprises a second microphone unit 314 generating a first, second and/or third electric signal from a sound. These signals are communicated to a first auditory cue generator 316 generating an elevation auditory cue and/or a front/back auditory cue in a second summed signal communicated to a second processing unit 318 performing the required audio-logical operations in accordance with sound and hearing impairment of the user before communicating a processed signal to a speaker 320.
  • the first hearing aid further comprises a first transceiver unit 322 for transmitting and receiving first, second, and/or third electric signals from the first and second microphone units 306 and 314.
  • the first transceiver 322 includes a time delay unit for time delaying the first, second and/or third electric signal prior to summing, and the time delaying of the first, second and/or third electric signal together with the distance d 3 between the microphone units 306 and 314 determine the position of a rotation auditory cue in addition to the elevation auditory cue and the front/back auditory cue.
  • the second hearing aid similarly further comprises a second transceiver unit 324 for transmitting and receiving first, second, and/or third electric signals from the first and second microphone units 306 and 314.
  • the second transceiver 322 also includes a time delay unit for time delaying the first, second and/or third electric signal prior to summing, and the time delaying of the first, second and/or third electric signal together with the distance d 3 between the microphone units 306 and 314 determine the position of a rotation auditory cue in addition to the elevation auditory cue and the front/back auditory cue.
  • the first and second transceiver units 322 and 324 may be communicating through a connecting wire or by wireless transmission.
  • the hearing aid system 300 may comprise a body worn calculation device 326 communicating with the first and second transceiver units 322 and 324.
  • the body worn calculation device 326 may be carried elsewhere on the user's body and comprises a time delay unit for appropriately delay the first, second and/or third electric signals from the first and second microphone unit 306 and 314 and being encoded with the predetermined distances d 1 , d 2 and d 3 .
  • the body worn calculation device 326 may perform the required delay and summing functions and return appropriate auditory cues to the first and second transceiver 322 and 324. Further, the body worn calculation device 326 may comprise a third microphone unit to be used for further specifying the auditory cues in all spatial dimensions.
  • the adaptation of the hearing aid system 300 to the user may advantageously be accomplished by decoupling the first and second microphone units 306 and 314 and generating the first, second, and third electric signal by means of a signal generator so as to simulate a sound environment.
  • the first and second tranceiver units 322 and 324 may receive the first, second, and third electric signal simulating a specific sound from the signal generator transmitting directly to each of the hearing aids 302 and 304.

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  • Health & Medical Sciences (AREA)
  • General Health & Medical Sciences (AREA)
  • Neurosurgery (AREA)
  • Otolaryngology (AREA)
  • Physics & Mathematics (AREA)
  • Engineering & Computer Science (AREA)
  • Acoustics & Sound (AREA)
  • Signal Processing (AREA)
  • Circuit For Audible Band Transducer (AREA)

Claims (10)

  1. Hörhilfesystem (100, 200) zum Erzeugen von Raumrichtungsmerkmalen im Hörbereich und aufweisend eine erste Mikrofoneinheit, die ausgebildet ist, Töne die an einem ersten Mikrofon (102) empfangen werden zu einem ersten elektrischen Signal an einem ersten Ausgang zu wandeln und Töne die an einem zweiten Mikrofon (104) empfangen werden zu einem zweiten elektrischen Signal an einem zweiten Ausgang zu wandeln, eine erste Verzögerungseinheit (106), die mit dem ersten Ausgang verbunden ist und die ausgebildet ist, das erste elektrische Signal zu verzögern, eine erste Berechnungseinheit (108), die mit der ersten Verzögerungseinheit (106) und dem zweiten Ausgang verbunden ist und die ausgebildet ist, das verzögerte erste elektrische Signal und das zweite elektrische Signal zu summieren und ein erstes summiertes Signal zu erzeugen, eine Verarbeitungseinheit (110), die mit der ersten Berechnungseinheit (108) verbunden ist und die ausgebildet ist, das erste summierte Signal zu verarbeiten und ein verarbeitetes Signal zu erzeugen, und ein Lautsprecher (112), der ausgebildet ist, das verarbeitete Signal in einen verarbeiteten Ton umzuwandeln, wobei das erste Mikrofon (102) und das zweite Mikrofon (104) durch eine vorbestimmte erste Distanz (d1) voneinander beabstandet sind und die erste Verzögerungseinheit (106) ausgebildet ist, eine vorbestimmte erste Zeitverzögerung des ersten elektrischen Signals auszugeben und dadurch ein Erzeugen eines ersten Raumrichtungsmerkmals im Hörbereich, welches eine erste räumliche Dimension in dem ersten summierten Signal für den Nutzer repräsentiert, durch die erste Berechnungseinheit (108) zu verursachen,
    dadurch gekennzeichnet, dass die Mikrofoneinheit weiterhin ein drittes Mikrofon (114) zum Wandeln von Tönen in ein drittes elektrisches Signal an einem dritten Ausgang aufweist, wobei das dritte Mikrofon (114) rechtwinklig bezüglich einer Achse zwischen dem ersten und dem zweiten Mikrofon durch eine zweite vorbestimmte Distanz (d2) beabstandet ist, wobei das Hörhilfesystem (100, 200) weiterhin eine Filtereinheit (116) aufweist, die mit dem dritten Ausgang verbunden ist und die ausgebildet ist, das dritte elektrische Signal zu filtern und dadurch ein gefiltertes drittes elektrisches Signal zu erzeugen, wobei das Hörhilfesystem (100, 200) weiterhin eine zweite Verzögerungseinheit (118) aufweist, die mit der ersten Berechnungseinheit (108) verbunden ist und die ausgebildet ist, das erste summierte Signal zu verzögern, und wobei das Hörhilfesystem (100, 200) weiterhin eine zweite Berechnungseinheit (120) aufweist, die mit der zweiten Verzögerungseinheit (118), der Filtereinheit (116) und mit der Verarbeitungseinheit (110) verbunden ist, wobei die zweite Berechnungseinheit (120) ausgebildet ist, das verzögerte erste summierte Signal und das gefilterte dritte elektrische Signal zu summieren, und dass die zweite vorbestimmte Distanz (d2) und die Zeitverzögerung der zweiten Verzögerungseinheit (118) ein Erzeugen eines zweiten Raumrichtungsmerkmals im Hörbereich, welches eine zweite räumliche Dimension in einem zweiten summierten Signal für den Nutzer repräsentiert, durch die zweite Berechnungseinheit (120) verursachen.
  2. Hörhilfesystem (100, 200) gemäß Anspruch 1, bei dem die erste Berechnungseinheit (108) weiterhin ausgebildet ist, das verzögerte erste elektrische Signal und das zweite elektrische Signal zu gewichten.
  3. Hörhilfesystem (100, 200) gemäß Anspruch 1 oder 2, bei dem die zweite Berechnungseinheit (120) weiterhin ausgebildet ist, das verzögerte erste summierte Signal und das gefilterte dritte elektrische Signal zu gewichten.
  4. Hörhilfesystem (100, 200, 300) gemäß einem der Ansprüche 1 bis 3, weiterhin aufweisend eine Sendeempfängereinheit (322), die mit der ersten Mikrofoneinheit (306) in Verbindung steht und die ausgebildet ist, das erste, das zweite und/oder das dritte elektrische Signal eines ersten Hörgeräts (302) an eine Sendeempfängereinheit (324) eines zweiten Hörgeräts (304) zu senden, welches eine zweite Mikrofoneinheit (314) aufweist, die von der ersten Mikrofoneinheit (306) rechtwinklig bezüglich der Achse zwischen dem ersten und dem zweiten Mikrofon (102, 104) durch eine dritte vorbestimmte Distanz (d3) beabstandet ist.
  5. Hörhilfesystem (100, 200, 300) gemäß Anspruch 4, bei dem die Sendeempfängereinheit (322) weiterhin ausgebildet ist, elektrische Signale von der zweiten Mikrofoneinheit (314) zu empfangen.
  6. Hörhilfesystem (100, 200, 300) gemäß einem der Ansprüche 4 oder 5, bei dem die Sendeempfängereinhiet (322) eine dritte Zeitverzögerungseinheit aufweist, die ausgebildet ist, das erste, das zweite und/oder das dritte elektrische Signal durch eine dritte vorbestimmte Zeitverzögerung zu verzögern.
  7. Hörhilfesystem (100, 200, 300) gemäß einem der Ansprüche 1 bis 6, weiterhin aufweisend ein körpergetragenes Berechnungsgerät (326), das mit den Sendeempfängern des ersten und zweiten Hörgeräts (302, 304) kommuniziert und das ausgebildet ist, ein erstes, zweites und/oder drittes Raumrichtungsmerkmal im Hörbereich zu erzeugen, welche in Verbindung stehen mit einer räumlichen Ausrichtung von Tönen, die an der ersten und zweiten Mikrofoneinheit (306, 314) empfangen wurden.
  8. Hörhilfesystem (100, 200, 300) gemäß Anspruch 7, bei dem das körpergetragene Berechnungsgerät (326) eine dritte Mikrofoneinheit aufweist, die ausgebildet ist, ein weiteres elektrisches Signal zum Erzeugen eines weiteren Raumrichtungsmerkmals im Hörbereich bereitzustellen.
  9. Hörhilfesystem (100, 200, 300) gemäß einem der Ansprüche 1 bis 8, weiterhin aufweisend eine erste Filterbank, die mit dem ersten Mikrofon (102) verbunden ist und die ausgebildet ist, eine erste Reihe von Frequenzkanal-Signalen des ersten elektrischen Signals zu erzeugen, und eine zweite Filterbank, die mit dem zweiten Mikrofon (104) verbunden ist und die ausgebildet ist, eine zweite Reihe von Frequenzkanal-Signalen des zweiten elektrischen Signals zu erzeugen, und wobei die erste Verzögerungseinheit (106) ausgebildet ist, jedes Signal aus der ersten Reihe von Frequenzkanal-Signalen unabhängig zu verzögen, und wobei die erste Berechnungseinheit (108) ausgebildet ist, die verzögerte erste Reihe von Frequenzkanal-Signalen und die zweite Reihe von Frequenzkanal-Signalen jeweils zu summieren.
  10. Hörhilfesystem (100, 200, 300) gemäß einem der Ansprüche 1 bis 9, weiterhin aufweisend A/D, D/A Übertragungseinheiten, die ausgebildet sind, die Mikrofonsignale aus dem analogen in den digitalen Bereich zu übertragen und das verarbeitete Signal aus dem digitalen in den analogen Bereich zu übertragen.
EP06111808.9A 2006-03-28 2006-03-28 System und Verfahren zur Erzeugung von richtungsbestimmenden Merkmalen im Hörbereich Not-in-force EP1841281B1 (de)

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EP06111808.9A EP1841281B1 (de) 2006-03-28 2006-03-28 System und Verfahren zur Erzeugung von richtungsbestimmenden Merkmalen im Hörbereich
DK06111808.9T DK1841281T3 (en) 2006-03-28 2006-03-28 System and method for generating auditory spatial information
CN 200710086965 CN101064972B (zh) 2006-03-28 2007-03-27 用于产生听觉空间提示的方法和***
AU2007201362A AU2007201362B2 (en) 2006-03-28 2007-03-28 System and method for generating auditory spatial cues

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FI20135125L (fi) * 2013-02-12 2014-08-13 Hannu Hätinen Laitteisto ja menetelmä auditiivisen viiveen korjaamiseksi
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EP3160157B1 (de) * 2015-10-21 2018-09-26 Sonion Nederland B.V. Vibrationskompensierte vibroakustische anordnung
DE102018210053A1 (de) * 2018-06-20 2019-12-24 Sivantos Pte. Ltd. Verfahren zur Audio-Wiedergabe in einem Hörgerät
CN109806498B (zh) * 2019-02-14 2022-11-04 深圳信息职业技术学院 一种电子耳蜗信号处理的方法及装置
CN113347544A (zh) * 2021-06-03 2021-09-03 中国科学院声学研究所 助听器的信号处理方法、装置及助听器

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CN101064972B (zh) 2012-12-12
DK1841281T3 (en) 2015-10-26
AU2007201362A1 (en) 2007-10-18
AU2007201362B2 (en) 2010-12-16
EP1841281A1 (de) 2007-10-03

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