EP1208723B8 - Hearing aid and external unit for communication therewith - Google Patents

Hearing aid and external unit for communication therewith Download PDF

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Publication number
EP1208723B8
EP1208723B8 EP00957131A EP00957131A EP1208723B8 EP 1208723 B8 EP1208723 B8 EP 1208723B8 EP 00957131 A EP00957131 A EP 00957131A EP 00957131 A EP00957131 A EP 00957131A EP 1208723 B8 EP1208723 B8 EP 1208723B8
Authority
EP
European Patent Office
Prior art keywords
hearing aid
setting
trigger signals
parameters
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
Other languages
German (de)
French (fr)
Other versions
EP1208723B1 (en
EP1208723A1 (en
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
GN Resound AS
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 GN Resound AS filed Critical GN Resound AS
Priority to EP00957131A priority Critical patent/EP1208723B8/en
Publication of EP1208723A1 publication Critical patent/EP1208723A1/en
Publication of EP1208723B1 publication Critical patent/EP1208723B1/en
Application granted granted Critical
Publication of EP1208723B8 publication Critical patent/EP1208723B8/en
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; 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
    • H04R25/50—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; 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
    • H04R25/50—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; 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

  • Hearing aid and external unit for communication therewith.
  • 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.
  • 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
  • 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. As a matter of fact, a person of average skill in the art will be able to think of a great many other means for realising the desired successive trigger signals.
  • 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 1 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)

Abstract

A hearing aid comprising memory means for storing preset signal processing parameters, and adjusting means for the stepwise adjustment of one or more of the stored signal processing parameters from a starting point of a predetermined range to an end point of said range. Examples of signal processing parameters to be adjusted are high tone amplification, maximum output level and noise suppression threshold value. Examples of providing the trigger signals include: a time clock, repeated turning on of the hearing aid, repeated placing of a battery and repeated operation of a knob. The hearing aid may be arranged for mutual communication with an external unit. The external unit may include selection means for the setting in the adjusting means of the one or more parameters to be adjusted, range setting means for the setting in the adjusting means of the range of the one or more parameters to be adjusted, step magnitude setting means for the setting in the adjusting means of a step magnitude to be used in said setpwise adjustment, and interval setting means for the setting of the repeat interval of the successive trigger signals in the time clock. The hearing aid carries out the adjustment autonomously in inaudible steps.

Description

Hearing aid and external unit for communication therewith.
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.
In practice it has become apparent, among other things, that people who are hard of hearing have a hearing aid fitted after having been unable for years to hear for example high tones and/or soft sounds and/or have not experienced high sound pressures. The setting to be made by the adjuster of the hearing aid (an audiologist, for example), is aimed at maximum audibility as regards speech, which implies amplification of high tones, among other things. Apart from that, the manner in which the ambient sound caught by the transducer is processed, for example amplified, filtered, etc., is adapted to the loss of hearing of the person in question. When a person who is hard of hearing hears high tones again after several years, he or she may experience this as highly unpleasant, partly because of the shrill sound, certainly upon first fitting of a first hearing aid. Consequently, the adjuster will probably opt for a setting with fewer high tones and thus a reduced audibility as regards speech, in order to satisfy the person who is hard of hearing upon his first visit. Otherwise there is a good chance that in the end the person who is hard of hearing will not use his hearing aid. On the other hand this risk also exists when the audibility as regards speech is not improved to a sufficient degree. The setting may be enhanced upon repeat visits towards more high tones and thus improved audibility as regards speech. Normally, the number of repeat visits will be relatively small, and consequently the adjustment steps will be relatively large. When 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.
In the above, the problem of high tones has been discussed. Problems with regard to soft sounds and high sound pressures are analogous thereto, however. Generally one adjustment parameter or a combination of adjustment parameters is concerned. Returning to the problems associated with high sound pressures, 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. As regards 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. In this case 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 clock. 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.
Preferably, 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, and 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 .
It is noted that 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. Technically, all this could be realised in a great many different ways, for example by: incorporating in the hearing aid a clock that adjusts the setting by one step after a predetermined period of time; adjusting the setting by one step after the hearing aid has been turned off and on again one or more times; adjusting the setting by one step after the battery has been placed anew one or more times or a new battery has been placed into service; adjusting the setting by one step after a knob on the hearing aid has been operated one or more times; etc. More in particular, 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.
Preferably, 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.
The advantages that can be gained include the following.
At the first fitting, 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.
At the least, the chance of an optimally adjusted hearing aid, that is, having an optimum, shrill sound, being put away for good by a person who is hard of hearing because the sound is not acceptable in the beginning will be smaller.
The invention will now be explained in more detail with reference to a drawing consisting of one figure, which drawing shows the hearing aid and the external unit.
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.
In an embodiment of the hearing aid 1 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, and 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 .
Alternative or additional parameters can be used, if desired; wherein each parameter has a range which is defined by a predetermined initial setting and a "predetermined final setting.
In the introduction, the maximum output level and the noise suppression threshold value have already been mentioned as possible examples of such alternative or additional parameters. Further possibilities will be apparent to those skilled in the art.
In an embodiment of the hearing aid 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.
Although 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.
It will be appreciated by a person of average skill in the art how 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. As a matter of fact, a person of average skill in the art will be able to think of a great many other means for realising the desired successive trigger signals.
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 1 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.
It is more practical, however, to incorporate said fourth to seventh means in an external unit 20, whereby the third means 6, and also the second means 5, and the external unit 20 are arranged for communication with each other. To that end, 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.

Claims

1. 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, 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.
2. A hearing aid according to claim 1, characterised in that said one or more signal processing parameters to be adjusted are selected from high tones amplification, maximum output level and noise suppression threshold value.
3. A hearing aid according to claim 1 or 2, characterised in that 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, and 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.
4. A hearing aid according to any one of the claims 1- 3, characterised in that said third means are arranged for communication with an external unit 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.
5. A hearing aid according to any one of the claims 1- 4, characterised in that said hearing aid includes a time clock for supplying the successive trigger signals.
6. A hearing aid according to claim 5, characterised in that said third means are arranged for communication with an external unit which comprises seventh means for the setting of the repeat interval of the successive trigger signals in the time clock.
7. A hearing aid according to any one of the claims 1 - 4, characterised in that said hearing aid comprises eighth means for supplying the successive trigger signals in response to repeated turning on of the hearing aid.
8. A hearing aid according to any one of the claims 1- 4, characterised in that said hearing aid comprises 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.
9. A hearing aid according to any one of the claims 1- 4, characterised in that said hearing aid includes a knob for supplying the successive trigger signals in response to repeated operation of said knob.
10. An external unit arranged for communication with a hearing aid, characterised in that said external unit is arranged for communication with the third means of a hearing aid according to any one of the preceding claims, 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 clock.
EP00957131A 1999-09-02 2000-08-14 Hearing aid and external unit for communication therewith Expired - Lifetime EP1208723B8 (en)

Priority Applications (1)

Application Number Priority Date Filing Date Title
EP00957131A EP1208723B8 (en) 1999-09-02 2000-08-14 Hearing aid and external unit for communication therewith

Applications Claiming Priority (4)

Application Number Priority Date Filing Date Title
EP99202848 1999-09-02
EP99202848 1999-09-02
PCT/NL2000/000571 WO2001026419A1 (en) 1999-09-02 2000-08-14 Hearing aid and external unit for communication therewith
EP00957131A EP1208723B8 (en) 1999-09-02 2000-08-14 Hearing aid and external unit for communication therewith

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EP1208723A1 EP1208723A1 (en) 2002-05-29
EP1208723B1 EP1208723B1 (en) 2003-10-29
EP1208723B8 true EP1208723B8 (en) 2004-01-21

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

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EP1414271B1 (en) * 2003-03-25 2013-06-26 Phonak Ag Method for recording of information in a hearing aid and such a hearing aid
DE102005043348A1 (en) * 2005-09-12 2006-12-28 Siemens Audiologische Technik Gmbh Switching device for hearing aid, has control circuit with timing unit by which parameter of right microphone circuit is changed independent of time, where microphone circuit is provided for obtaining right microphone signal
EP1841286B1 (en) 2006-03-31 2014-06-25 Siemens Audiologische Technik GmbH Hearing aid with adaptive starting values of parameters
DE602007013121D1 (en) † 2007-10-16 2011-04-21 Phonak Ag HEARING SYSTEM AND METHOD FOR OPERATING A HEARING SYSTEM
DE102009021855A1 (en) * 2009-05-19 2010-11-25 Siemens Medical Instruments Pte. Ltd. A method for acclimating a programmable hearing device and associated hearing device
US8787603B2 (en) 2009-12-22 2014-07-22 Phonak Ag Method for operating a hearing device as well as a hearing device
US8965016B1 (en) 2013-08-02 2015-02-24 Starkey Laboratories, Inc. Automatic hearing aid adaptation over time via mobile application
WO2016004970A1 (en) 2014-07-07 2016-01-14 Advanced Bionics Ag System for combined neural and acoustic hearing stimulation
US10376698B2 (en) 2014-08-14 2019-08-13 Advanced Bionics Ag Systems and methods for gradually adjusting a control parameter associated with a cochlear implant system
US10382872B2 (en) 2017-08-31 2019-08-13 Starkey Laboratories, Inc. Hearing device with user driven settings adjustment
DE102020214329A1 (en) * 2020-11-13 2022-05-19 Sivantos Pte. Ltd. Methods to support the use of a hearing aid and hearing aid

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Publication number Priority date Publication date Assignee Title
AU610705B2 (en) * 1988-03-30 1991-05-23 Diaphon Development A.B. Auditory prosthesis with datalogging capability
US4901353A (en) * 1988-05-10 1990-02-13 Minnesota Mining And Manufacturing Company Auditory prosthesis fitting using vectors
DE59008091D1 (en) * 1990-10-12 1995-02-02 Siemens Ag Hearing aid with a data storage device.
JP2904272B2 (en) * 1996-12-10 1999-06-14 日本電気株式会社 Digital hearing aid and hearing aid processing method thereof

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Publication number Publication date
EP1208723B1 (en) 2003-10-29
DK1208723T3 (en) 2004-03-08
DE60006255T2 (en) 2004-08-12
AU6878800A (en) 2001-05-10
DE60006255D1 (en) 2003-12-04
WO2001026419A1 (en) 2001-04-12
ATE253288T1 (en) 2003-11-15
EP1208723A1 (en) 2002-05-29

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