EP2234411A1 - Procédé de fonctionnement d'un dispositif auditif doté d'une compensation de contre-réaction renforcée et dispositif auditif - Google Patents

Procédé de fonctionnement d'un dispositif auditif doté d'une compensation de contre-réaction renforcée et dispositif auditif Download PDF

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Publication number
EP2234411A1
EP2234411A1 EP10153770A EP10153770A EP2234411A1 EP 2234411 A1 EP2234411 A1 EP 2234411A1 EP 10153770 A EP10153770 A EP 10153770A EP 10153770 A EP10153770 A EP 10153770A EP 2234411 A1 EP2234411 A1 EP 2234411A1
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EP
European Patent Office
Prior art keywords
hearing
feedback
offset
hearing aid
compensation
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.)
Withdrawn
Application number
EP10153770A
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German (de)
English (en)
Inventor
Ulrich Kornagel
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
Priority date (The priority date 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 date listed.)
Filing date
Publication date
Application filed by Siemens Medical Instruments Pte Ltd filed Critical Siemens Medical Instruments Pte Ltd
Publication of EP2234411A1 publication Critical patent/EP2234411A1/fr
Withdrawn legal-status Critical Current

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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
    • H04R25/45—Prevention of acoustic reaction, i.e. acoustic oscillatory feedback
    • H04R25/453—Prevention of acoustic reaction, i.e. acoustic oscillatory feedback electronically
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R2410/00—Microphones
    • H04R2410/07—Mechanical or electrical reduction of wind noise generated by wind passing a microphone

Definitions

  • the present invention relates to a method for operating a hearing device by amplifying an input sound to an output sound and compensating a caused by the output sound feedback to a predetermined extent. Moreover, the present invention relates to a hearing device with an amplifying device for amplifying an input sound to an output sound and a feedback compensation device for compensating a caused by the output sound feedback in a predetermined amount.
  • the term hearing device is understood here to mean any sound-emitting device which can be worn in or on the ear or on the head, in particular a hearing device, a headset, headphones and the like.
  • Hearing aids are portable hearing aids that are used to care for the hearing impaired.
  • different types of hearing aids such as behind-the-ear hearing aids (BTE), hearing aid with external receiver (RIC: receiver in the canal) and in-the-ear hearing aids (IDO), e.g. Concha hearing aids or canal hearing aids (ITE, CIC).
  • BTE behind-the-ear hearing aids
  • RIC hearing aid with external receiver
  • IDO in-the-ear hearing aids
  • ITE canal hearing aids
  • the hearing aids listed by way of example are worn on the outer ear or in the ear canal.
  • bone conduction hearing aids, implantable or vibrotactile hearing aids are also available on the market. The stimulation of the damaged hearing takes place either mechanically or electrically.
  • Hearing aids have in principle as essential components an input transducer, an amplifier and an output transducer.
  • the input transducer is usually a sound receiver, z. As a microphone, and / or an electromagnetic receiver, for. B. an induction coil.
  • the output transducer is usually used as an electroacoustic transducer, z. B. miniature speakers, or as an electromechanical transducer, z. B. bone conduction, realized.
  • the amplifier is usually integrated in a signal processing unit.
  • FIG. 1 shown using the example of a behind-the-ear hearing aid.
  • a hearing aid housing 1 for carrying behind the ear one or more microphones 2 for receiving the sound from the environment are installed.
  • a signal processing unit 3 which is also integrated in the hearing aid housing 1, processes the microphone signals and amplifies them.
  • the output signal of the signal processing unit 3 is transmitted to a loudspeaker or earpiece 4, which outputs an acoustic signal.
  • the sound is optionally transmitted via a sound tube, which is fixed with an earmold in the ear canal, to the eardrum of the device carrier.
  • the power supply of the hearing device and in particular the signal processing unit 3 is effected by a likewise integrated into the hearing aid housing 1 battery. 5
  • a hearing aid When a hearing aid is to be used, it is usually turned on first and then inserted into the ear. Due to the hands on the hearing aid or on the ear, the feedback conditions of the hearing aid change. Usually the degree of feedback is increased by the hands. Depending on the set or selected amplification of the hearing aid, therefore, it often comes in the process of inserting the hearing aid to feedback whistles.
  • a signal generated in the hearing device (eg melody) is output during the muting time. This is a sure sign to the hearing aid wearer that the hearing aid has been activated. However, such a playback of an artificial signal is often rejected by the hearing aid wearers.
  • the object of the present invention is thus to make the operation of attaching a hearing device to an ear more comfortable with respect to feedback artifacts.
  • the feedback corresponding to the offset is thus additionally reduced or compensated (completely or partially) when the hearing device is switched on.
  • this additional reduction of feedback artifacts for example, it can be avoided that feedback whistling occurs for a predicted insertion time of a hearing device into an ear.
  • the predetermined amount of compensating for the feedback is a maximum value set for the normal operation of the hearing device. This means that for the usual operation of the hearing device, a maximum value of the feedback compensation is set at which the disturbing artifacts are barely acceptable. For the insertion phase, this maximum value can then be exceeded by the offset, because in this phase the artefacts caused by the compensation algorithm will be less disturbing than the feedback whistling.
  • the offset may be constant for a predetermined period of time. This is advantageous if the hand during the entire phase of attaching the hearing in or on the ear consistently high feedback provoked.
  • the offset may also decrease from an initial value to zero for the predetermined period of time. This results in the end of the phase of attaching the hearing no sudden transitions to normal operation.
  • the predetermined period of time in which the compensation is additionally increased after switching on can be adjustable for a user individually in the hearing device.
  • the time required for a single user to Attaching the hearing device or the hearing aid has to be taken into account individually.
  • the temporal profile of the offset in the hearing device can also be selectable from a plurality of profiles. This also allows the user or hearing aid wearer to independently decide how long and in which way he wants to use the additional compensation for feedback after switching on.
  • the embodiments described in more detail below represent preferred embodiments of the present invention. They relate to the insertion of a hearing device into an ear or the attachment of a hearing device to an ear.
  • the amplification of the hearing aid may be set so high that the system is close to the stability limit beyond which the hearing aid begins to whistle.
  • the hand on the hearing aid then suffices, for example, to increase the intensity of the feedback so that the stability limit is exceeded.
  • a feedback compensator which reduces the feedback effects (completely or partially compensated) during the predicted Insertion of the hearing aid in the ear is switched to a particularly high strength.
  • FIG. 2 A concrete example shows FIG. 2 , There, the increase in the effective strength of a feedback compensator or a feedback compensation device is shown in its time profile.
  • the feedback compensation algorithm operates at a predetermined power level. This means that the feedback effect is reduced to a certain extent, ie in whole or in part.
  • This predetermined strength of the feedback compensation algorithm may be an initial onset power level or, for example, a maximum power level.
  • the maximum strength is - as already mentioned - set by the fact that it represents a limit below which the artifacts of the feedback compensation for the hearing aid wearer are just acceptable.
  • This initial or maximum value of the strength of the feedback compensation is in FIG. 2 shown in the right part.
  • the increase in potency in this normal operation is by definition zero. In the examples of FIG. 2 Normal operation starts after about 15 seconds. Previously, in the switch-on phase, ie from zero to 15 seconds, the strength is increased by an offset.
  • a maximum increase in the strength of effect takes place by the measure one.
  • the increase, d. H. the offset of the effect strength remains the same throughout the switch-on time.
  • the increase in the effective strength is abruptly or very quickly reduced to zero. This means that the effectiveness of the feedback compensation algorithm is no longer increased compared to the normal operating phase: The normal operating phase begins.
  • the height of the offset during the switch-on phase can be predetermined or selected by the hearing device wearer within a certain range.
  • the switch-on phase can be predetermined or variable for the hearing aid wearer. Usually, the hearing aid wearer the switch-on as short as possible so that it is annoyed as quickly as possible by artifacts that increase the strength of the feedback compensation algorithm.
  • the rapid or abrupt reduction of the strength increase of the back-compensation algorithm after the switch-on phase can itself lead to problems or artifacts. Therefore, it may be favorable if, according to the example of FIG. 3 the increase in the power of the compensation algorithm is gradually reduced during the switch-on phase.
  • the potency starts at 100% increase and is then lowered linearly to zero percent increase. The time for this lowering also depends on the expected duration for the insertion of the hearing aid.
  • other functions can be chosen to reduce the increase, ie to reduce the offset of the strength of the feedback compensation algorithm to zero. For this purpose, continuous functions without jumps are preferred.
  • Particularly advantageous in terms of the increase in potency of the feedback compensation device during the switch-on phase is that the feedback whistling is effectively suppressed even with highly pronounced feedback paths, as occur when the hearing device is inserted.
  • the hearing aid wearer immediately perceives whether he has activated the hearing aid correctly, because he receives already at inserting output sound signals from his hearing aid.
  • immediately after insertion of the hearing device ie even in the switch-on phase of the hearing device, it can acoustically perceive its surroundings, even if the particularly high intensity of the feedback compensator possibly causes new artifacts, but this is limited in time.

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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)
  • Amplifiers (AREA)
EP10153770A 2009-03-24 2010-02-17 Procédé de fonctionnement d'un dispositif auditif doté d'une compensation de contre-réaction renforcée et dispositif auditif Withdrawn EP2234411A1 (fr)

Applications Claiming Priority (1)

Application Number Priority Date Filing Date Title
DE102009014540A DE102009014540A1 (de) 2009-03-24 2009-03-24 Verfahren zum Betreiben einer Hörvorrichtung mit verstärkter Rückkopplungskompensation und Hörvorrichtung

Publications (1)

Publication Number Publication Date
EP2234411A1 true EP2234411A1 (fr) 2010-09-29

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Application Number Title Priority Date Filing Date
EP10153770A Withdrawn EP2234411A1 (fr) 2009-03-24 2010-02-17 Procédé de fonctionnement d'un dispositif auditif doté d'une compensation de contre-réaction renforcée et dispositif auditif

Country Status (3)

Country Link
US (1) US20100246868A1 (fr)
EP (1) EP2234411A1 (fr)
DE (1) DE102009014540A1 (fr)

Families Citing this family (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO2014179489A1 (fr) * 2013-05-01 2014-11-06 Starkey Laboratories, Inc. Coefficients d'annulation de retour adaptative basés sur la tension

Citations (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO2002013576A1 (fr) * 2000-08-10 2002-02-14 Gn Resound A/S Prothese auditive dotee d'une activation retardee
EP1655997A2 (fr) * 2004-11-08 2006-05-10 Siemens Audiologische Technik GmbH Procédé pour amplifier un signal acoustique et système acoustique correspondant
EP1788843A1 (fr) * 2004-04-06 2007-05-23 Phonak AG Dispositif auditif et procédé d'activation d'un dispositif auditif

Family Cites Families (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US6434246B1 (en) * 1995-10-10 2002-08-13 Gn Resound As Apparatus and methods for combining audio compression and feedback cancellation in a hearing aid
DE19904538C1 (de) * 1999-02-04 2000-07-13 Siemens Audiologische Technik Verfahren zur Rückkopplungserkennung in einem Hörgerät und Hörgerät
US7489790B2 (en) * 2000-12-05 2009-02-10 Ami Semiconductor, Inc. Digital automatic gain control
DE10242700B4 (de) * 2002-09-13 2006-08-03 Siemens Audiologische Technik Gmbh Rückkopplungskompensator in einem akustischen Verstärkungssystem, Hörhilfsgerät, Verfahren zur Rückkopplungskompensation und Anwendung des Verfahrens in einem Hörhilfsgerät
ATE460053T1 (de) * 2004-12-16 2010-03-15 Widex As Hörgerät mit modellierter rückkopplungsverstärkungsschätzung
WO2007113282A1 (fr) * 2006-04-01 2007-10-11 Widex A/S Appareil auditif et procédé permettant de commander la vitesse d'adaptation dans des systèmes anti-rétroaction pour appareils auditifs

Patent Citations (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO2002013576A1 (fr) * 2000-08-10 2002-02-14 Gn Resound A/S Prothese auditive dotee d'une activation retardee
EP1788843A1 (fr) * 2004-04-06 2007-05-23 Phonak AG Dispositif auditif et procédé d'activation d'un dispositif auditif
EP1655997A2 (fr) * 2004-11-08 2006-05-10 Siemens Audiologische Technik GmbH Procédé pour amplifier un signal acoustique et système acoustique correspondant

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US20100246868A1 (en) 2010-09-30
DE102009014540A1 (de) 2010-10-07

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