EP1208723B1 - Appareil de correction auditive et unite externe pouvant communiquer mutuellement - Google Patents

Appareil de correction auditive et unite externe pouvant communiquer mutuellement Download PDF

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Publication number
EP1208723B1
EP1208723B1 EP00957131A EP00957131A EP1208723B1 EP 1208723 B1 EP1208723 B1 EP 1208723B1 EP 00957131 A EP00957131 A EP 00957131A EP 00957131 A EP00957131 A EP 00957131A EP 1208723 B1 EP1208723 B1 EP 1208723B1
Authority
EP
European Patent Office
Prior art keywords
hearing aid
setting
parameters
trigger signals
range
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.)
Expired - Lifetime
Application number
EP00957131A
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German (de)
English (en)
Other versions
EP1208723B8 (fr
EP1208723A1 (fr
Inventor
Franciscus Hubertus Janssen
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.)
GN Hearing AS
Original Assignee
Beltone Netherlands BV
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 Beltone Netherlands BV filed Critical Beltone Netherlands BV
Priority to EP00957131A priority Critical patent/EP1208723B8/fr
Publication of EP1208723A1 publication Critical patent/EP1208723A1/fr
Application granted granted Critical
Publication of EP1208723B1 publication Critical patent/EP1208723B1/fr
Publication of EP1208723B8 publication Critical patent/EP1208723B8/fr
Anticipated expiration legal-status Critical
Expired - Lifetime legal-status Critical Current

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Classifications

    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; ELECTRIC HEARING AIDS; PUBLIC ADDRESS SYSTEMS
    • H04R25/00—Electric hearing aids
    • H04R25/50—Customised settings for obtaining desired overall acoustical characteristics
    • H04R25/502—Customised settings for obtaining desired overall acoustical characteristics using analog signal processing
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; ELECTRIC HEARING AIDS; PUBLIC ADDRESS SYSTEMS
    • H04R25/00—Electric hearing aids
    • H04R25/50—Customised settings for obtaining desired overall acoustical characteristics
    • H04R25/505—Customised settings for obtaining desired overall acoustical characteristics using digital signal processing
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; ELECTRIC HEARING AIDS; PUBLIC ADDRESS SYSTEMS
    • H04R25/00—Electric hearing aids
    • H04R25/55—Electric hearing aids using an external connection, either wireless or wired
    • H04R25/558—Remote control, e.g. of amplification, frequency

Definitions

  • the invention relates to a hearing aid comprising at least one first transducer for converting sound into an electric signal, a second transducer for converting an electric signal into sound, first means for processing and amplifying an electric signal from the first transducer and supplying the processed and amplified electric signal to the second transducer, and second means linked to said first means for storing signal processing parameters, as well as to an external unit arranged for communication with a hearing aid.
  • a hearing aid of this kind and an external unit of this kind are generally known.
  • the prior art external unit is used for storing signal processing parameters that have been set by an adjuster of hearing aids in the prior art hearing aid.
  • the number of repeat visits will be relatively small, and consequently the adjustment steps will be relatively large.
  • the adjustment steps are too large, there is a possibility that the person who is hard of hearing will prefer the previous, actually less optimum setting and ask the adjuster to use the previous setting and subsequently leave it at that, or that he or she will refrain from further use of the hearing aid yet, with all its negative consequences.
  • a lower than optimum maximum output will be set when the hearing aid is first being fitted, because the person who is hard of hearing may not be accustomed to high sounds pressures any more.
  • soft sounds said person may not have heard the sound of ticking clocks, for example, or ambient noise produced by traffic or electric equipment for a prolonged period of time, and initially these sounds may be experienced as objectionable, in spite of the fact that soft sounds often contain valuable information.
  • the adjuster will set a relatively high noise suppression threshold value at a first fitting.
  • Said noise suppression threshold value is a switching point in a noise suppression circuit which will reduce its amplification factor when only soft sounds below the noise suppression threshold value are presented.
  • the object of the invention is to provide a hearing aid and an external unit which enable an essential improvement as regards the above-described practice, and in order to accomplish that objective the invention provides a hearing aid of the kind referred to in the introduction, which is characterised in that the hearing aid comprises third means linked to said second means for the stepwise adjustment from a starting point of a predetermined range to an end point of said range of one or more signal processing parameters from the second means in response to successive trigger signals, as well as an external unit of the kind referred to in the introduction, which is characterised in that it is arranged for communication with the third means of a hearing aid according to the invention, and which comprises fourth means for the selecting and setting in said third means of one or more parameters to be adjusted, fifth means for the setting in the third means of the range of said one or more parameters to be adjusted, and sixth means for the setting in said third means of the magnitude of the steps to be used in said stepwise adjustment, and, if the hearing aid includes a time clock, seventh means for the setting of the repeat interval of the successive trigger signals in the time
  • the hearing aid automatically adjusts itself in time, irrespective of the fact whether the trigger signals are generated manually or automatically.
  • the adjustment of the setting can take place gradually, in small steps thereby.
  • the difference between two steps hardly needs to be audible, if at all; the difference between the first step and the last step of a succession of steps must be audible, however.
  • the starting point of a parameter range is defined by an initial setting that is acceptable to an intended user of the hearing aid, wherein the amplification of high tones is less than optimal and consequently the audibility as regards speech is less than optimal
  • the end point of a parameter range is defined by a final setting that is optimal for the intended user, wherein the amplification of high tones is optimal and consequently the audibility as regards speech is optimal.
  • the hearing aid is not limited to adjustment of the amplification parameter, but that instead thereof or in addition thereto other parameters can be used, such as filter function parameters, noise suppression parameters, etc.
  • the time that is required for going from the initial setting to the final setting is the habituation period, it may last a number of weeks, for example.
  • Both the initial setting and the final setting are pre-set, or in other words, pre-programmed by the adjuster.
  • the hearing aid subsequently arranges the gradual shift from the initial setting to the final setting in sufficiently small steps.
  • the magnitude of the steps can be programmable. Furthermore it is possible to preset the desired habituation period.
  • the hearing aid may include a time clock for supplying the successive trigger signals: a knob for supplying the successive trigger signals in response to repeated operation of the knob; eighth means for supplying the successive trigger signals in response to repeated turning on of the hearing aid; or ninth means for detecting the placing of a battery in the hearing aid and supplying the successive trigger signals in response to the repeated placing of a battery.
  • the third means of the hearing aid and the external unit are arranged for communication with each other, in which case the second means of the hearing aid and the external unit will be arranged for communication with each other, exactly as may the case in the prior art hearing aid.
  • a person who is hard of hearing will receive a hearing aid which sounds acceptable and pleasant. After the habituation period, the hearing aid will automatically have been adjusted optimally without the person having had to go through a period of unpleasant sound and repeated visits to an adjuster.
  • An adjuster supplies a hearing aid which sounds pleasant from the outset, whilst nevertheless an optimum setting will be achieved after the habituation period without any interim adjustments.
  • Hearing aid 1 comprises at least one transducer (microphone) 2 for converting sound into an electric signal, a second transducer (loudspeaker) 3 for converting an electric signal into sound, first means 4 for processing and amplifying an electric signal from the first transducer 2 and supplying the processed and amplified electric signal to the second transducer 3, second means (memory) 5 linked to said first means 4 for storing signal processing parameters, and third means 6 linked to said second means 5 for the stepwise adjustment of one or more signal processing parameters from second means 5 from a starting point of a predetermined range to an end point of said range in response to successive trigger signals 7.
  • the starting point of said range is defined by an initial setting that is acceptable to an intended user of the hearing aid, wherein the amplification of high tones is less than optimal and consequently the audibility as regards speech is less than optimal
  • the end point of said range is defined by a final setting that is optimal for the intended user, wherein the amplification of high tones is optimal and consequently the audibility as regards speech is optimal.
  • each parameter has a range which is defined by a predetermined initial setting and a predetermined final setting.
  • the first, second and third means 4 - 6 form part of one or more integrated circuits.
  • An embodiment of the hearing aid 1 includes a time clock 8 for supplying the successive trigger signals 7.
  • Another embodiment of the hearing aid includes eighth means 9 for supplying the successive trigger signals 7 in response to repeated turning on of the hearing aid 1.
  • Yet another embodiment of the hearing aid 1 includes ninth means 10 for detecting the placing of a battery in the hearing aid 1 and supplying the successive trigger signals 7 in response to the repeated placing of a battery.
  • Yet another embodiment of the hearing aid 1 includes a knob 11 for supplying the successive trigger signals 7 in response to repeated operation of said knob 11.
  • the hearing aid 1 as shown in the drawing includes the time clock 8, eighth means 9, ninth means 10 as well as knob 11, the hearing aid 1 will generally include either the time clock 8, or the eighth means 9, or the ninth means 10 or the knob 11.
  • time clock 8, eighth and ninth mans 9, 10 and knob 11 can be arranged or be provided with electronics that may form part of the aforesaid one or more integrated circuits, such that the successive trigger signals 7 will be supplied, so that this will not be discussed in more detail herein. Manuals can be consulted for this purpose, if desired.
  • Hearing aid 1 could include fourth means (not shown) for the selecting and setting in the third means 6 of one or more parameters to be adjusted, fifth means (not shown) for the setting in the third means 6 of the range of said one or more parameters to be adjusted, sixth means (not shown) for the setting in the third means 6 of a step magnitude to be used in the stepwise adjustment, and, in the case that the hearing aid I includes the clock 8, seventh means (not shown) for the setting of the repeat interval of the successive trigger signals 7 in the time clock 8.
  • the external unit 20 comprises communication means 21 and the aforesaid fourth to seventh means 22 - 25, which in an embodiment comprise software which runs on a PC.

Landscapes

  • 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)
  • Telephone Function (AREA)
  • Telephone Set Structure (AREA)
  • Circuit For Audible Band Transducer (AREA)
  • Control Of Amplification And Gain Control (AREA)

Claims (10)

  1. Prothèse auditive (1) comprenant au moins un premier transducteur (2) pour convertir un son en signal électrique, un second transducteur (3) pour convertir un signal électrique en son, des premiers moyens (4) pour traiter et amplifier un signal électrique provenant du premier transducteur (2) et fournir le signal électrique traité et amplifié au second transducteur (3) et des seconds moyens (5) reliés aux dits premiers moyens (4) pour stocker des paramètres de traitement du signal, caractérisée en ce que la prothèse auditive comprend des troisièmes moyens (6) reliés aux dits seconds moyens (5) pour le réglage par étapes allant d'un point de départ d'une plage prédéterminée à un point d'arrivée de ladite plage d'un ou de plusieurs paramètres de traitement du signal issu des seconds moyens (5) en réponse à des signaux de déclenchement successifs (7).
  2. Prothèse auditive (1) selon la revendication 1, caractérisée en ce que ledit ou lesdits paramètres de traitement du signal à régler sont sélectionnés à partir d'une amplification des tonalités aiguës, d'un niveau de sortie maximal et d'une valeur de seuil de suppression de bruit.
  3. Prothèse auditive (1) selon la revendication 1 ou 2, caractérisée en ce que le point de départ de ladite plage est défini par un réglage initial qui est acceptable pour un utilisateur donné de la prothèse auditive, dans laquelle l'amplification des tonalités aiguës est inférieure à l'amplification optimale et, en conséquence, l'audibilité par rapport à la parole est inférieure à l'optimale, et le point d'extrémité de ladite plage est défini par un réglage final qui est optimal pour l'utilisateur donné, dans laquelle l'amplification des tonalités aiguës est optimale et, par conséquent, l'audibilité par rapport à la parole, est optimale.
  4. Prothèse auditive (1) selon l'une quelconque des revendications 1 à 3, caractérisée en ce que lesdits troisièmes moyens (6) sont disposés pour une communication avec une unité externe (20) qui comprend des quatrièmes moyens pour sélectionner et régler dans lesdits troisièmes moyens (6) l'un ou plusieurs des paramètres à régler, des cinquièmes moyens pour régler dans les troisièmes moyens (6) la plage dudit ou desdits paramètres à régler, et des sixièmes moyens pour régler dans lesdits troisièmes moyens (6) l'amplitude des étapes à utiliser dans ledit réglage par étapes.
  5. Prothèse auditive (1) selon l'une quelconque des revendications 1 à 4, caractérisée en ce que ladite prothèse (1) comporte une horloge (8) pour fournir les signaux de déclenchement successifs (7).
  6. Prothèse auditive (1) selon la revendication 5, caractérisée en ce que lesdits troisièmes moyens (6) sont disposés pour une communication avec une unité externe (20) qui comporte des septièmes moyens pour régler l'intervalle de répétition des signaux de déclenchement successifs (7) dans l'horloge (8).
  7. Prothèse auditive (1) selon l'une quelconque des revendications 1 à 4, caractérisée en ce que ladite prothèse auditive (1) comporte des huitièmes moyens (9) pour fournir les signaux de déclenchement successifs (7) en réponse à la mise en route répétée de la prothèse auditive (1).
  8. Prothèse auditive (1) selon l'une quelconque des revendications 1 à 4, caractérisée en ce que ladite prothèse auditive (1) comprend des neuvièmes moyens (10) pour détecter la mise en service d'une batterie dans la prothèse auditive (1) et fournir les signaux de déclenchement successifs (7) en réponse à la mise en service répétée d'une batterie.
  9. Prothèse auditive (1) selon l'une quelconque des revendications 1 à 4, caractérisée en ce que ladite prothèse (1) comporte un bouton (11) pour fournir les signaux de déclenchement successifs (7) en réponse à une opération répétée dudit bouton (11).
  10. Unité externe (20) disposée pour une communication avec une prothèse auditive, caractérisée en ce que ladite unité externe (20) est agencée pour être en communication avec les troisièmes moyens (6) d'une prothèse auditive (1) selon l'une quelconque des revendications précédentes, et qui comporte des quatrième moyens pour sélectionner et régler dans lesdits troisièmes moyens (6) un ou plusieurs paramètres à régler, des cinquièmes moyens pour régler dans les troisièmes moyens (6) la plage dudit ou desdits paramètre(s) à régler, et des sixièmes moyens pour régler dans lesdits troisièmes moyens (6) l'amplitude des étapes à utiliser dans ledit réglage par étapes, et, si la prothèse (1) comporte une horloge (8) des septièmes moyens pour régler l'intervalle de répétition des signaux de déclenchement successifs (7) dans l'horloge (8).
EP00957131A 1999-09-02 2000-08-14 Appareil de correction auditive et unite externe pouvant communiquer mutuellement Expired - Lifetime EP1208723B8 (fr)

Priority Applications (1)

Application Number Priority Date Filing Date Title
EP00957131A EP1208723B8 (fr) 1999-09-02 2000-08-14 Appareil de correction auditive et unite externe pouvant communiquer mutuellement

Applications Claiming Priority (4)

Application Number Priority Date Filing Date Title
EP99202848 1999-09-02
EP99202848 1999-09-02
PCT/NL2000/000571 WO2001026419A1 (fr) 1999-09-02 2000-08-14 Appareil de correction auditive et unite externe pouvant communiquer mutuellement
EP00957131A EP1208723B8 (fr) 1999-09-02 2000-08-14 Appareil de correction auditive et unite externe pouvant communiquer mutuellement

Publications (3)

Publication Number Publication Date
EP1208723A1 EP1208723A1 (fr) 2002-05-29
EP1208723B1 true EP1208723B1 (fr) 2003-10-29
EP1208723B8 EP1208723B8 (fr) 2004-01-21

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Application Number Title Priority Date Filing Date
EP00957131A Expired - Lifetime EP1208723B8 (fr) 1999-09-02 2000-08-14 Appareil de correction auditive et unite externe pouvant communiquer mutuellement

Country Status (6)

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EP (1) EP1208723B8 (fr)
AT (1) ATE253288T1 (fr)
AU (1) AU6878800A (fr)
DE (1) DE60006255T2 (fr)
DK (1) DK1208723T3 (fr)
WO (1) WO2001026419A1 (fr)

Cited By (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
DE102005043348A1 (de) * 2005-09-12 2006-12-28 Siemens Audiologische Technik Gmbh Schaltungsvorrichtung zum Betrieb eines Hörgeräts mit zeitadaptivem Verhalten und entsprechendes Verfahren
US8787603B2 (en) 2009-12-22 2014-07-22 Phonak Ag Method for operating a hearing device as well as a hearing device
US20200045484A1 (en) * 2017-08-31 2020-02-06 Starkey Laboratories, Inc. Hearing device with user driven settings adjustment

Families Citing this family (8)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
EP1414271B1 (fr) * 2003-03-25 2013-06-26 Phonak Ag Procédé d'enregistrement d'information dans une prothèse auditive et une telle prothèse auditive
DK1841286T3 (da) 2006-03-31 2014-10-06 Siemens Audiologische Technik Høreapparat med adaptive startværdier af parametre
ATE501604T1 (de) † 2007-10-16 2011-03-15 Phonak Ag Hörsystem und verfahren zum betrieb eines hörsystems
DE102009021855A1 (de) * 2009-05-19 2010-11-25 Siemens Medical Instruments Pte. Ltd. Verfahren zur Akklimatisierung einer programmierbaren Hörvorrichtung und zugehörige Hörvorrichtung
US8965016B1 (en) 2013-08-02 2015-02-24 Starkey Laboratories, Inc. Automatic hearing aid adaptation over time via mobile application
EP3166683B1 (fr) 2014-07-07 2020-10-07 Advanced Bionics AG Système pour une stimulation auditive neuronale et acoustique combinée
EP3180076B1 (fr) 2014-08-14 2019-08-07 Advanced Bionics AG Systèmes d'ajustement progressif d'un paramètre de contrôle associé à un système d'implant cochléaire
DE102020214329A1 (de) * 2020-11-13 2022-05-19 Sivantos Pte. Ltd. Verfahren zur Unterstützung bei der Nutzung eines Hörgerätes und Hörgerät

Family Cites Families (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
DE68920060T2 (de) * 1988-03-30 1995-09-14 3M Hearing Health Ab Hörprothese mit Datenerfassungsmöglichkeiten.
US4901353A (en) * 1988-05-10 1990-02-13 Minnesota Mining And Manufacturing Company Auditory prosthesis fitting using vectors
EP0480097B1 (fr) * 1990-10-12 1994-12-21 Siemens Audiologische Technik GmbH Prothèse auditive avec mémoire pour données
JP2904272B2 (ja) * 1996-12-10 1999-06-14 日本電気株式会社 ディジタル補聴器、及びその補聴処理方法

Cited By (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
DE102005043348A1 (de) * 2005-09-12 2006-12-28 Siemens Audiologische Technik Gmbh Schaltungsvorrichtung zum Betrieb eines Hörgeräts mit zeitadaptivem Verhalten und entsprechendes Verfahren
US8787603B2 (en) 2009-12-22 2014-07-22 Phonak Ag Method for operating a hearing device as well as a hearing device
US20200045484A1 (en) * 2017-08-31 2020-02-06 Starkey Laboratories, Inc. Hearing device with user driven settings adjustment
US10945086B2 (en) * 2017-08-31 2021-03-09 Starkey Laboratories, Inc. Hearing device with user driven settings adjustment
US11641556B2 (en) 2017-08-31 2023-05-02 Starkey Laboratories, Inc. Hearing device with user driven settings adjustment
US12047750B2 (en) 2017-08-31 2024-07-23 Starkey Laboratories, Inc. Hearing device with user driven settings adjustment

Also Published As

Publication number Publication date
EP1208723B8 (fr) 2004-01-21
EP1208723A1 (fr) 2002-05-29
DE60006255D1 (de) 2003-12-04
DK1208723T3 (da) 2004-03-08
DE60006255T2 (de) 2004-08-12
ATE253288T1 (de) 2003-11-15
AU6878800A (en) 2001-05-10
WO2001026419A1 (fr) 2001-04-12

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