EP2252081A2 - Appareil auditif binaural et procédé de fonctionnement d'un tel dispositif auditif binaural avec ajustement fréquentiel non linéaire - Google Patents

Appareil auditif binaural et procédé de fonctionnement d'un tel dispositif auditif binaural avec ajustement fréquentiel non linéaire Download PDF

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Publication number
EP2252081A2
EP2252081A2 EP10157539A EP10157539A EP2252081A2 EP 2252081 A2 EP2252081 A2 EP 2252081A2 EP 10157539 A EP10157539 A EP 10157539A EP 10157539 A EP10157539 A EP 10157539A EP 2252081 A2 EP2252081 A2 EP 2252081A2
Authority
EP
European Patent Office
Prior art keywords
frequency
hearing aid
signal
acoustic signal
hearing
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Granted
Application number
EP10157539A
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German (de)
English (en)
Other versions
EP2252081B1 (fr
EP2252081A3 (fr
Inventor
Stefan Dr. Petrausch
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Sivantos Pte Ltd
Original Assignee
Siemens Medical Instruments Pte Ltd
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Publication date
Application filed by Siemens Medical Instruments Pte Ltd filed Critical Siemens Medical Instruments Pte Ltd
Publication of EP2252081A2 publication Critical patent/EP2252081A2/fr
Publication of EP2252081A3 publication Critical patent/EP2252081A3/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
    • H04R25/35—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception using translation techniques
    • H04R25/353—Frequency, e.g. frequency shift or compression
    • 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
    • H04R25/552—Binaural

Definitions

  • the invention relates to a specified in claim 1 method for operating a binaural hearing with frequency distortion and a specified in claim 8 binaural hearing with frequency distortion.
  • frequency-distorting algorithms are used for different purposes and at different points of signal processing.
  • frequency-distorting algorithms are used for different purposes and at different points of signal processing.
  • FIG. 1 shows a block diagram of an exemplary implementation of a frequency distortion in a hearing aid.
  • An input signal 100 is divided by a crossover filter 1 ("split-band filter") with a predefinable limit frequency GF ("split frequency”) into a low-frequency and a high-frequency signal component 101, 102.
  • the high-frequency signal component 102 is then distorted in a frequency equalizer 2.
  • the distorted output signal 103 is supplied to an input of an adder 3.
  • the low-frequency signal component 101 passes through an all-pass filter 4, which rotates the phase of the signal component 101 in such a way that signal deletion in the region of the limit frequency GF does not occur during a subsequent signal addition in the adder 3.
  • the phase-rotated low-frequency signal component 104 is supplied to a further input of the adder 3. At the output of the adder 3, the sum of the two signal components 103, 104 is available as an output signal 105.
  • Crossovers are not ideal and have a finite frequency overlap at their cutoff frequency GF.
  • FIG. 2 is shown as an example of the frequency response of a crossover in a hearing aid with the limit frequency GF 1800 Hz.
  • the curves K1, K2 show the damping D in dB as a function of the frequency F in Hz in the range 0 to 4000 Hz.
  • the curve K1 shows a low-pass characteristic and the curve K2 a high-pass characteristic.
  • the EP 1 333 700 A2 discloses a method and a hearing aid for frequency shifting.
  • a shifted spectrum is obtained from the spectrum of a microphone signal of the hearing aid by means of a non-linear frequency shift function.
  • the stated object is achieved with the method for operating a binaural hearing device of the independent patent claim 1 and the binaural hearing device of the independent patent claim 8.
  • the acoustic signal received by the left hearing aid or the signal component of the recorded acoustic signal and the acoustic signal picked up by the right hearing aid or the signal component of the recorded acoustic signal can be distorted relative to each other antisymmetrically.
  • the advantage of this is that overlay artifacts are less noticeable to a hearing aid wearer due to a decentralized localization.
  • the acoustic signal picked up by the left hearing aid or the signal component of the recorded acoustic signal and the acoustic signal picked up by the right hearing aid or the signal component of the recorded acoustic signal can be asymmetrically distorted relative to each other. This has the advantage that a tonal detuning of an input signal for a hearing aid wearer is laminated.
  • the frequency distortions of the left and right hearing aids may include a frequency shift and / or a frequency compression.
  • the frequency distortions can be changed over time.
  • the overlay artifacts vary, making them less noticeable to a hearing aid wearer and avoiding a perceived tonal imbalance.
  • the frequency distortions of the left and right hearing aids can be coupled binaurally to one another. This ensures synchronization.
  • the frequencies in one or more frequency subbands can be distorted.
  • the first and the second frequency distortion unit can distort each other antisymmetrically.
  • the first and the second frequency distortion units may distort each other asymmetrically.
  • the frequency distortions of the first and the second frequency distortion unit may include a frequency shift and / or a frequency compression.
  • the frequency distortions of the first and the second frequency distortion unit can be changed over time.
  • the first and the second frequency distortion unit can be binaurally coupled to each other.
  • the frequencies in one or more frequency subbands may be distorted.
  • the hearing device a first crossover in the left hearing aid, which divides the recorded acoustic signal into a low-frequency and a high-frequency signal component whose frequencies are distorted and / or a second crossover in the right hearing aid, the recorded acoustic signal in a low-frequency and high-frequency Signal component divides whose frequencies are distorted include.
  • FIG. 3 exemplifies the principle and operations of the invention.
  • the illustration shows the head 10 of a hearing aid wearer with a left hearing aid 11 and a right hearing aid 12 for a binaural care.
  • the left hearing aid 11 comprises a microphone 13 and a listener 14.
  • the right hearing aid 12 comprises a microphone 15 and a listener 16. From a sound source 17, a sinusoidal sound signal 18 with the frequency 1000 Hz is emitted.
  • the sound signal 18 is received by the two microphones 13 and 15, each converted into electrical signals, including amplified and distorted in frequency, before the signals are emitted by the handset 14 and 16.
  • the frequency distortion is antisymmetric with 10 Hz frequency shift, ie the listener signal of the left hearing aid 11 is 1010 Hz and the listener signal of the right hearing aid 12 is 990 Hz.
  • the hearing aid wearer takes the original 1000 Hz sound despite the frequency shift between the two shifts, so again on the original frequency 1000 Hz true.
  • a frequency distortion is set antisymmetrically according to the invention, originally pure tones are perceived at a frequency between the two distortions, ie again at the original frequency.
  • a tonal detuning of the sound signal 18 is laminated.
  • a pure sine tone appears broader to the hearing aid wearer but not detuned from the original frequency. It is important that a distortion or a shift is not too large, so that the brain of the hearing aid wearer suspected the same origin of the sound signal 18 for the right and left ear.
  • FIG. 4 shows the head 10 of a hearing aid wearer with a left hearing aid 11 and a right hearing aid 12 for a binaural care.
  • the left hearing aid 11 comprises a microphone 13 and a listener 14.
  • the right hearing aid 12 comprises a microphone 15 and a listener 16. From a sound source 17, a sinusoidal sound signal 18 with the frequency 1000 Hz is emitted.
  • the sound signal 18 is recorded on the paths 19 of the two microphones 13 and 15, respectively converted into electrical signals, including amplified and shifted in frequency by 20 Hz, before the signals are emitted by the handset 14 and 16.
  • a hearing device user perceives the sound signal 18 also on direct paths 20, as so-called direct sound.
  • direct sound By superimposing the direct sound at 1000 Hz and the sound emitted by the listeners 14 and 16 at 1020 Hz, a beat with a frequency of 20 Hz, centered by the hearing device user, is perceived directly in the user's head 10. This enhances the perception of amplitude modulation due to frequency distortion.
  • FIG. 5 shows the head 10 of a hearing aid wearer with a left hearing aid 11 and a right hearing aid 12 for a binaural care.
  • the left hearing aid 11 comprises a microphone 13 and a listener 14.
  • the right hearing aid 12 comprises a microphone 15 and a listener 16. From a sound source 17, a sinusoidal sound signal 18 with the frequency 1000 Hz is emitted.
  • the sound signal 18 is recorded on the paths 19 of the two microphones 13 and 15, respectively converted into electrical signals, including amplified and shifted in frequency by 25 Hz or 15 Hz, before the signals are emitted by the handset 14 and 16.
  • a hearing device user takes that Sound signal 18 on direct paths 20, as a so-called direct sound true.
  • the direct sound at 1000 Hz and the emitted by the handset 14 of the left hearing aid 11 sound at 1025 Hz creates a beating at a frequency of 25 Hz, the hearing aid user outside of the head 10 - indicated by the cloud "25 Hz modulation" - is perceived.
  • Due to the superimposition of the direct sound at 1000 Hz and the sound emitted by the handset 16 of the right hearing aid 12 with 1015 Hz, a beating at a frequency of 15 Hz, the hearing aid user also outside of the head 10 - indicated by the cloud "15 Hz modulation" - is perceived.
  • a hearing aid user locates the source (s) of beat outside of the head 10 and therefore associates it with background noise because there is no correlation between the right and left ears. Setting asymmetric frequency distortion is thus a very efficient and simple way to minimize artifacts of frequency distortion.
  • the inventive solutions described can also be the frequency distortion, or the strength of the frequency distortion, eg. The frequency offset over time slowly and / or randomly changed.
  • the degree of distortion can then be chosen more from an audiological point of view, usually in such a way that overlay artifacts are no longer perceived as mere modulation or beating, but rather as roughness, and that the detuning is minimal.
  • a frequency offset can be varied and should also be dynamic over time. On the one hand, it can be avoided that the same sounds are repeated over and over again Artifacts occur. If a hearing aid wearer knows the critical tones after some wearing time, then he only waits for it and is annoyed when he actually has to perceive the artifacts again. In addition, hearing tests have shown that in the asymmetric frequency distortion according to the invention, a hearing device user can get a feeling of "imbalance". For example, if the sounds in the left ear are always deeper than those in the right, the hearing device user may feel that the hearing aids are sitting asymmetrically. This is avoided by varying the frequency distortion over time and once the right and once the left ear is the one with the higher frequency.
  • FIG. 6 shows a block diagram of a portion of a binaural hearing device according to the invention with a left and a right hearing aid 11, 12.
  • An input signal 100L of the left hearing aid 11 is divided by a crossover 1L into a low-frequency and a high-frequency signal component 101L, 102L.
  • the high frequency signal portion 102L is then distorted in a first frequency distortion unit 2L.
  • the distorted output signal 103L is supplied to an input of an adder 3L.
  • the low-frequency signal component 101L is supplied to a further input of the adder 3L.
  • the sum of the two signal components 103L, 101L is available as output signal 105L.
  • a frequency distortion control unit 5L of the left hearing aid 11 the degree and the type and frequency distortion of the first frequency distortion unit 2L are controlled by means of a control signal 106L.
  • An input signal 100R of the right hearing aid 12 is divided by a crossover network 1R into a low-frequency and a high-frequency signal component 101R, 102R.
  • the high-frequency signal portion 102R is then distorted in a second frequency distortion unit 2R.
  • the distorted output signal 103R is supplied to an input of an adder 3R.
  • the low-frequency signal component 101R is supplied to a further input of the adder 3R.
  • the sum of the two signal components 103R, 101R is available as an output signal 105R.
  • a frequency distortion control unit 5R of the right hearing aid 12 the degree or the type and the type of frequency distortion of the second frequency distortion unit 2R is controlled by means of a control signal 106R.
  • the two frequency distortion control units 5L and 5R of the two hearing aids 11 and 12 are wirelessly coupled to each other and can be synchronized via a coupling signal 107, for example, despite time variation still remain strictly asymmetric and / or strictly antisymmetric in the frequency distortion.
  • a temporal change can be advantageously equal to right and left, for example, equally fast or with the same expectation, take place.
  • the change of the frequency distortion can be done continuously or in steps. It can be changed to broadband, or only in subbands.

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  • Engineering & Computer Science (AREA)
  • Health & Medical Sciences (AREA)
  • General Health & Medical Sciences (AREA)
  • Neurosurgery (AREA)
  • Otolaryngology (AREA)
  • Physics & Mathematics (AREA)
  • Acoustics & Sound (AREA)
  • Signal Processing (AREA)
  • Computer Networks & Wireless Communication (AREA)
  • Stereophonic System (AREA)
  • Circuit For Audible Band Transducer (AREA)
EP10157539.7A 2009-05-14 2010-03-24 Appareil auditif binaural et procédé de fonctionnement d'un tel dispositif auditif binaural avec ajustement fréquentiel non linéaire Active EP2252081B1 (fr)

Applications Claiming Priority (1)

Application Number Priority Date Filing Date Title
DE102009021310A DE102009021310B4 (de) 2009-05-14 2009-05-14 Binaurale Hörvorrichtung und Verfahren zum Betrieb einer binauralen Hörvorrichtung mit Frequenzverzerrung

Publications (3)

Publication Number Publication Date
EP2252081A2 true EP2252081A2 (fr) 2010-11-17
EP2252081A3 EP2252081A3 (fr) 2013-11-13
EP2252081B1 EP2252081B1 (fr) 2015-06-17

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US (1) US8611571B2 (fr)
EP (1) EP2252081B1 (fr)
DE (1) DE102009021310B4 (fr)
DK (1) DK2252081T3 (fr)

Cited By (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
EP3373599A1 (fr) * 2017-03-06 2018-09-12 Sivantos Pte. Ltd. Procédé de restriction de fréquence d'un signal audio et dispositif auditif fonctionnant selon ledit procédé

Families Citing this family (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20130010967A1 (en) * 2011-07-06 2013-01-10 The Monroe Institute Spatial angle modulation binaural sound system
US9046974B2 (en) * 2012-02-28 2015-06-02 Eastman Kodak Company Transparent touch-screen capacitor with micro-wire electrode
EP2988529B1 (fr) * 2014-08-20 2019-12-04 Sivantos Pte. Ltd. Frequence de division adaptative dans appareils d'aide auditive
DE102017200320A1 (de) * 2017-01-11 2018-07-12 Sivantos Pte. Ltd. Verfahren zur Frequenzverzerrung eines Audiosignals
DE102017201195A1 (de) * 2017-01-25 2018-07-26 Sivantos Pte. Ltd. Verfahren zum Betrieb eines binauralen Hörgerätesystems

Citations (2)

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Publication number Priority date Publication date Assignee Title
EP1333700A2 (fr) 2003-03-06 2003-08-06 Phonak Ag Procédé de transposition de fréquence dans une prothèse auditive et une telle prothèse auditive
DE69922940T2 (de) 1998-04-01 2005-12-29 Gn Resound As Vorrichtung und verfahren zur kombinierung von audiokompression und rückkopplungsunterdrückung in einem hörgerät

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US6831986B2 (en) 2000-12-21 2004-12-14 Gn Resound A/S Feedback cancellation in a hearing aid with reduced sensitivity to low-frequency tonal inputs
US20040175010A1 (en) * 2003-03-06 2004-09-09 Silvia Allegro Method for frequency transposition in a hearing device and a hearing device
AU2003904207A0 (en) * 2003-08-11 2003-08-21 Vast Audio Pty Ltd Enhancement of sound externalization and separation for hearing-impaired listeners: a spatial hearing-aid
US7769439B2 (en) 2004-11-30 2010-08-03 Infinite Z, Inc. Brain balancing by binaural beat
DK1742509T3 (da) * 2005-07-08 2013-11-04 Oticon As Et system og en fremgangsmåde til eliminering af feedback og støj i et høreapparat
AU2008203351B2 (en) * 2007-08-08 2011-01-27 Oticon A/S Frequency transposition applications for improving spatial hearing abilities of subjects with high frequency hearing loss
DE102007037659B4 (de) * 2007-08-09 2013-06-13 Siemens Audiologische Technik Gmbh Verfahren zum Betrieb eines Hörgerätesystems und Hörgerätesystem

Patent Citations (2)

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Publication number Priority date Publication date Assignee Title
DE69922940T2 (de) 1998-04-01 2005-12-29 Gn Resound As Vorrichtung und verfahren zur kombinierung von audiokompression und rückkopplungsunterdrückung in einem hörgerät
EP1333700A2 (fr) 2003-03-06 2003-08-06 Phonak Ag Procédé de transposition de fréquence dans une prothèse auditive et une telle prothèse auditive

Cited By (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
EP3373599A1 (fr) * 2017-03-06 2018-09-12 Sivantos Pte. Ltd. Procédé de restriction de fréquence d'un signal audio et dispositif auditif fonctionnant selon ledit procédé
US10674283B2 (en) 2017-03-06 2020-06-02 Sivantos Pte. Ltd. Method for distorting the frequency of an audio signal and hearing apparatus operating according to this method

Also Published As

Publication number Publication date
DK2252081T3 (da) 2015-09-28
EP2252081B1 (fr) 2015-06-17
US8611571B2 (en) 2013-12-17
DE102009021310B4 (de) 2011-02-24
DE102009021310A1 (de) 2010-12-30
EP2252081A3 (fr) 2013-11-13
US20100290631A1 (en) 2010-11-18

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