EP1696700B1 - Prothèse auditive avec un système de calibration automatique commandé par l'utilisateur - Google Patents

Prothèse auditive avec un système de calibration automatique commandé par l'utilisateur Download PDF

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Publication number
EP1696700B1
EP1696700B1 EP06101565.7A EP06101565A EP1696700B1 EP 1696700 B1 EP1696700 B1 EP 1696700B1 EP 06101565 A EP06101565 A EP 06101565A EP 1696700 B1 EP1696700 B1 EP 1696700B1
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EP
European Patent Office
Prior art keywords
hearing apparatus
measuring
hearing
measuring cycle
feedback
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.)
Active
Application number
EP06101565.7A
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German (de)
English (en)
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EP1696700A3 (fr
EP1696700A2 (fr
EP1696700B2 (fr
Inventor
Tom Weidner
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 GmbH
Original Assignee
Siemens Audioligische Technik GmbH
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Application filed by Siemens Audioligische Technik GmbH filed Critical Siemens Audioligische Technik GmbH
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Publication of EP1696700A3 publication Critical patent/EP1696700A3/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
    • H04R25/45—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
    • H04R25/00—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception
    • H04R25/30—Monitoring or testing of hearing aids, e.g. functioning, settings, battery power
    • H04R25/305—Self-monitoring or self-testing
    • 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
    • H04R25/558—Remote control, e.g. of amplification, frequency

Definitions

  • the present invention relates to a hearing aid device having a measuring device for measuring a feedback path and an operating device for operating the hearing device by the hearing device wearer.
  • the actual feedback path and its properties are not known and there is always a so-called adaptation, whereby the risk of artifacts is very high.
  • the actual feedback path is first measured by an adapter computer or a programmer. From this measurement, basic values for the feedback reduction result and only a minimal continuous adaptation by the hearing aid has to be carried out on the basis of these basic values or this fine adaptation is completely dispensed with. Since a special matching computer is necessary for measuring the feedback path, the measurement is performed only by an acoustician, but never by a hearing aid user himself.
  • a digital hearing aid in which an acoustic sensor detects an otoacoustic reaction of the inner ear of the hearing aid wearer to the measurement sounds emitted by an electroacoustic transducer.
  • a microcomputer makes a comparison and a correction of the transfer function based on the respective sensor voltage. The measurement and correction process is initiated, for example, by actuating a button connected to the microcomputer which has the function of a switch.
  • the feedback signal is defined as the part of the output signal that is fed back to the microphone.
  • the return is either through a ventilation groove or a leak between the earmold and ear canal. If the attenuation on the path of the feedback signal is less than the amplification of the hearing aid, vibrations with a very high sound pressure level occur in the system.
  • the digital feedback cancellation system continuously measures the frequency response of the feedback path and generates a correction signal that is superimposed on the input signal to suppress the feedback.
  • this system also has the above-mentioned disadvantages of a constantly adapting system.
  • the patent DE 199 04 538 C1 discloses a method for feedback detection in a hearing aid. After the hearing aid is switched on or after a user-initiated initialization command, a signal transmission path is monitored for feedback. A control unit gradually increases the gain of the hearing aid as long as no feedback occurs and a predetermined maximum gain has not yet been reached.
  • EP 0 581 261 A1 a hearing aid with user-controlled sound feedback.
  • the hearing aid has an adaptable feedback compensator.
  • the user can activate the adaptation by means of a control.
  • the object of the present invention is to make the feedback reduction for the user of a hearing device as comfortable as possible.
  • a hearing device according to claim 1 is provided for this purpose.
  • the invention is based on the idea of creating a hearing device and in particular a hearing aid with a feedback compensator, which automatically initialises after deliberate activation by the wearer or hearing device wearer.
  • a type of adaptive filtering can be used for feedback compensation, which, however, does not adapt permanently, but only during a calibration phase. Thereafter, the parameters thus determined are permanently recorded.
  • a hearing aid device autonomously measure the current feedback path at the instigation of the hearing aid wearer and, after successful measurement, permanently store it in the hearing aid depending on the program without having to connect a programming device to the hearing aid device or make any connection to an external computer.
  • the operating device of the hearing device is realized as a remote control. This can be dispensed with a separate switching mechanism for triggering the measurement phase.
  • the operating device may have a plurality of keys, wherein the measuring cycle can be triggered by a key combination.
  • the measuring cycle can also be triggered by a predetermined chronological sequence of actuation of a key. In this way, keys can be used to trigger the measuring cycle, which are also used for other functionalities.
  • the operating device is arranged invisibly from the outside in the shell of the hearing aid device or the hearing device.
  • the operating device may comprise, for example, a reed relay as a magnetic field detector or a high-frequency detector. Both allow the hearing aid to be operated through the hearing device shell.
  • the hearing device according to the invention has a signal generator for outputting a control tone upon activation and / or at the end of the measurement cycle.
  • a control tone can be output even if the measurement cycle is successful / unsuccessful.
  • optical or tactile signals are also suitable for controlling the measuring cycle.
  • the operating device has a sound receiver, so that the measuring cycle can be triggered or influenced by a tone or a sequence of tones.
  • the measuring cycle can be triggered for example by means of a mobile phone that outputs corresponding key tones.
  • a special control is implemented, which is activated by a predetermined operation of the hearing aid for performing a calibration process.
  • the measured coefficients are written to a non-volatile memory of the hearing aid. From this time on, even after switching off and changing the battery, the feedback algorithm in the hearing aid remains preset with the measured parameters. This is immediately one given effective feedback reduction. Since the feedback algorithm no longer needs to adapt, there are no adaptation artifacts.
  • the advantage of the calibration method according to the invention is that even in the case of non-programmable devices (eg headsets) or in devices in which the adaptation does not take place via an acoustician, complex algorithms such as a feedback compensator can be individually calibrated and preset. This makes calibration operations more user-friendly.
  • the calibration process takes place according to the steps of the figure.
  • the step S1 symbolically indicates that the hearing device or especially the hearing device is ready to perform a calibration procedure.
  • the user triggers the calibration process by conscious operation.
  • an operating manual or other information provides the hearing aid wearer with the necessary information and explanations about the system. For example, a particular key combination or control must be actuated in a particular time sequence. This can be done either directly on the hearing aid or on any existing remote control.
  • Another alternative, as already mentioned, is a non-visible operating element, for. B. to provide a reed relay or an RFID detector on the hearing aid and to start the Einmessvorgang about it.
  • the hearing aid conveniently outputs a control signal (step S3), which indicates to the hearing device wearer the start of the calibration system.
  • This control signal can be a sound, but also an optical signal.
  • the hearing device is set in the measuring state. This may be done special device settings.
  • the measuring process is thus started according to step S5 and a measurement signal is output.
  • a measurement signal is output.
  • a defined noise is emitted via the handset.
  • the returning portion of the measured noise is recorded in step S6 and fed to an analysis unit.
  • a step S7 it is checked whether the measurement has been successfully completed. It is monitored whether a measurement time has expired and / or an error parameter has fallen below a certain limit. After successful measurement, the measured parameters for the current program are stored permanently in a non-volatile memory of the hearing aid according to step S8. Subsequently, the hearing aid returns to the original operating state according to step S9.
  • the feedback system now works with the newly measured parameters.
  • the hearing device then outputs a control signal to the hearing device wearer via the successful measurement in accordance with step S10. This control signal can be optical, acoustic or even tactile nature.
  • the feedback algorithm is now available with the updated presets and can work without artifacts, as an additional adaptation is not or only to a very limited extent necessary.
  • step S7 If the measurement has not yet ended after step S7, one or more termination criteria are checked in accordance with step S11. This includes, for example, the timeout or the presence of a specific error condition. If the abort criteria are not met, the measurement continues with step S5. If, on the other hand, fulfillment of a termination criterion is given, then the hearing aid returns in accordance with step S12 returns to the original operating state, but no parameters are stored. This means that the feedback system continues to work with the old parameters.
  • step S13 Even in the case of unsuccessful measurement, a control signal of an optical, acoustic or tactile nature is output according to step S13, thereby indicating to the user that the calibration, that is to say measuring, is not required. h., the measurement of the feedback path has failed. The end of the entire measuring process is symbolized in the graph by step S14.
  • the described method for measuring a hearing aid with respect to a feedback path can be used for any hearing aid, but also for non-programmable headsets and the like.
  • a static currently optimized compensation of the feedback can be achieved. In many cases, this eliminates the need for dynamic compensation, or the dynamic compensation can be performed on a very small scale.

Landscapes

  • Health & Medical Sciences (AREA)
  • General Health & Medical Sciences (AREA)
  • Otolaryngology (AREA)
  • Neurosurgery (AREA)
  • Physics & Mathematics (AREA)
  • Engineering & Computer Science (AREA)
  • Acoustics & Sound (AREA)
  • Signal Processing (AREA)
  • Measurement Of The Respiration, Hearing Ability, Form, And Blood Characteristics Of Living Organisms (AREA)
  • Circuit For Audible Band Transducer (AREA)

Claims (11)

  1. Prothèse auditive comprenant
    - un dispositif de mesure d'un trajet de réaction de la prothèse auditive et
    - un dispositif de commande de la prothèse auditive par un porteur, dans laquelle
    - par le dispositif de commande, un cycle de mesure pour la détermination d'au moins une propriété du trajet de réaction peut être déclenché ( S2 ) et
    - un compensateur de feedback, qui a plusieurs paramètres variables, dont la valeur est déterminée sur la base du cycle de mesure,
    caractérisée en ce que
    - la prothèse auditive est conçue pour contrôler si la mesure est achevée avec succès ( S7 ) et pour contrôler, à cet effet, si une durée de mesure s'est écoulée et/ou si un paramètre d'erreur s'est abaissé en dessous d'une limite déterminée et
    - les valeurs déterminées des paramètres ne sont inscrites, d'une manière permanente dans une mémoire rémanente de la prothèse auditive, qu'après une mesure réussie pour un programme présent ( S8 ),
    dans lequel, après une mesure réussie, le compensateur de feedback travaille avec les valeurs déterminées des paramètres.
  2. Prothèse auditive suivant la revendication 1,
    dans laquelle le dispositif de commande est une télécommande.
  3. Prothèse auditive suivant l'une des revendications 1 ou 2,
    dans laquelle le dispositif de commande a plusieurs touches et le cycle de mesure peut être déclenché par une combinaison de touches ( S2 ).
  4. Prothèse auditive suivant l'une des revendications précédentes,
    dans laquelle le cycle de mesure peut être déclenché par une succession prescrite dans le temps d'un actionnement d'une touche.
  5. Prothèse auditive suivant l'une des revendications précédentes,
    dans laquelle le dispositif de commande est disposé invisible de l'extérieur dans la coquille de la prothèse auditive.
  6. Prothèse auditive suivant la revendication 5,
    dans laquelle le dispositif de commande comprend un détecteur de champs magnétique, notamment un relais reed ou un détecteur RFID ou un détecteur de haute fréquence.
  7. Prothèse auditive suivant l'une des revendications précédentes, qui a un générateur de signal pour l'émission ( S3, S10, S13 ) d'une tonalité de contrôle à l'activation et/ou à l'achèvement du cycle de mesure.
  8. Prothèse auditive suivant l'une des revendications précédentes, qui a un générateur de signal pour l'émission ( S3, S10, S13 ) d'une tonalité de contrôle lorsque le cycle de mesure est réussi et d'une autre tonalité de contrôle lorsque le cycle de mesure n'est pas réussi ( S7 ).
  9. Prothèse auditive suivant l'une des revendications précédentes, qui a un dispositif optique de signalisation et/ou un indicateur de mouvement pour l'émission ( S3, S10, S13 ) d'un signal de commande se rapportant au fait qu'un cycle de mesure est effectué.
  10. Prothèse auditive suivant la revendication 1,
    dans laquelle le dispositif de commande a un récepteur de sons de sorte que le cycle de commande peut être déclenché ou influencé par une tonalité ou par une succession de tonalités.
  11. Prothèse auditive suivant la revendication 10,
    dans laquelle le dispositif de commande est conçu pour déclencher le cycle de mesure en fonction de tonalités de touche d'un téléphone portable.
EP06101565.7A 2005-02-23 2006-02-13 Prothèse auditive avec un système de calibration automatique commandé par l'utilisateur Active EP1696700B2 (fr)

Applications Claiming Priority (1)

Application Number Priority Date Filing Date Title
DE102005008318A DE102005008318B4 (de) 2005-02-23 2005-02-23 Hörhilfegerät mit benutzergesteuerter Einmessautomatik

Publications (4)

Publication Number Publication Date
EP1696700A2 EP1696700A2 (fr) 2006-08-30
EP1696700A3 EP1696700A3 (fr) 2009-07-01
EP1696700B1 true EP1696700B1 (fr) 2013-08-07
EP1696700B2 EP1696700B2 (fr) 2021-07-28

Family

ID=36676594

Family Applications (1)

Application Number Title Priority Date Filing Date
EP06101565.7A Active EP1696700B2 (fr) 2005-02-23 2006-02-13 Prothèse auditive avec un système de calibration automatique commandé par l'utilisateur

Country Status (4)

Country Link
US (1) US8842862B2 (fr)
EP (1) EP1696700B2 (fr)
DE (1) DE102005008318B4 (fr)
DK (1) DK1696700T4 (fr)

Families Citing this family (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
DE102009052575A1 (de) 2009-11-10 2011-05-12 Siemens Medical Instruments Pte. Ltd. Verfahren, Hörgerät und Anordnung zur Kalibrierung eines akustischen Anpasssystems
US9332358B2 (en) * 2012-01-16 2016-05-03 Sonova Ag Method for monitoring usage of a hearing device
DK3016407T3 (da) * 2014-10-28 2020-02-10 Oticon As Høresystem til estimering af en tilbagekoblingsvej for et høreapparat

Family Cites Families (25)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
DE3109049A1 (de) * 1981-03-10 1982-09-30 Siemens AG, 1000 Berlin und 8000 München Hoergeraet
DE3205685A1 (de) * 1982-02-17 1983-08-25 Robert Bosch Gmbh, 7000 Stuttgart Hoergeraet
US4783818A (en) * 1985-10-17 1988-11-08 Intellitech Inc. Method of and means for adaptively filtering screeching noise caused by acoustic feedback
US4731850A (en) † 1986-06-26 1988-03-15 Audimax, Inc. Programmable digital hearing aid system
US4955729A (en) * 1987-03-31 1990-09-11 Marx Guenter Hearing aid which cuts on/off during removal and attachment to the user
US5091952A (en) * 1988-11-10 1992-02-25 Wisconsin Alumni Research Foundation Feedback suppression in digital signal processing hearing aids
GB8919591D0 (en) * 1989-08-30 1989-10-11 Gn Davavox As Hearing aid having compensation for acoustic feedback
DE4128172C2 (de) * 1991-08-24 2000-07-13 Ascom Audiosys Ag Flamatt Digitales Hörgerät
DK170600B1 (da) * 1992-03-31 1995-11-06 Gn Danavox As Høreapparat med kompensation for akustisk tilbagekobling
CA2100015A1 (fr) * 1992-07-29 1994-01-30 Resound Corporation Prothese auditive permettant l'elimination de la reaction acoustique commandee par l'utilisateur
DK169958B1 (da) * 1992-10-20 1995-04-10 Gn Danavox As Høreapparat med kompensation for akustisk tilbagekobling
DK0824845T3 (da) † 1995-05-02 1999-06-21 Toepholm & Westermann Fremgangsmåde til styring af et programmerbart eller programstyret høreapparat til dettes in situ tilpasningsjustering
DK0814634T3 (da) * 1996-06-21 2003-02-03 Siemens Audiologische Technik Programmerbart høreapparatsystem og fremgangsmåde til fastsættelse af optimale parametersæt i et høreapparat
US6236731B1 (en) * 1997-04-16 2001-05-22 Dspfactory Ltd. Filterbank structure and method for filtering and separating an information signal into different bands, particularly for audio signal in hearing aids
US6211861B1 (en) * 1998-06-23 2001-04-03 Immersion Corporation Tactile mouse device
DE19802568C2 (de) * 1998-01-23 2003-05-28 Cochlear Ltd Hörhilfe mit Kompensation von akustischer und/oder mechanischer Rückkopplung
DE19904538C1 (de) * 1999-02-04 2000-07-13 Siemens Audiologische Technik Verfahren zur Rückkopplungserkennung in einem Hörgerät und Hörgerät
US20020015506A1 (en) * 2000-03-13 2002-02-07 Songbird Hearing, Inc. Remote programming and control means for a hearing aid
DE10041726C1 (de) * 2000-08-25 2002-05-23 Implex Ag Hearing Technology I Implantierbares Hörsystem mit Mitteln zur Messung der Ankopplungsqualität
EP1191813A1 (fr) * 2000-09-25 2002-03-27 TOPHOLM & WESTERMANN APS Prothèse auditive avec un filtre adaptatif pour la suppression de la réaction acoustique
US6842647B1 (en) * 2000-10-20 2005-01-11 Advanced Bionics Corporation Implantable neural stimulator system including remote control unit for use therewith
DE10110258C1 (de) * 2001-03-02 2002-08-29 Siemens Audiologische Technik Verfahren zum Betrieb eines Hörhilfegerätes oder Hörgerätesystems sowie Hörhilfegerät oder Hörgerätesystem
DE10345173B3 (de) * 2003-09-29 2005-01-13 Siemens Audiologische Technik Gmbh Modulare Fernbedieneinheit für Hörhilfegeräte
US6912289B2 (en) * 2003-10-09 2005-06-28 Unitron Hearing Ltd. Hearing aid and processes for adaptively processing signals therein
US7463745B2 (en) * 2004-04-09 2008-12-09 Otologic, Llc Phase based feedback oscillation prevention in hearing aids

Also Published As

Publication number Publication date
US8842862B2 (en) 2014-09-23
EP1696700A3 (fr) 2009-07-01
DK1696700T4 (da) 2021-10-18
EP1696700A2 (fr) 2006-08-30
DE102005008318A1 (de) 2006-08-31
DE102005008318B4 (de) 2013-07-04
DK1696700T3 (da) 2013-11-04
EP1696700B2 (fr) 2021-07-28
US20060188106A1 (en) 2006-08-24

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