EP1850634A2 - Procédé de réglage d'une prothèse auditive avec amplification des hautes fréquences - Google Patents

Procédé de réglage d'une prothèse auditive avec amplification des hautes fréquences Download PDF

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Publication number
EP1850634A2
EP1850634A2 EP07103023A EP07103023A EP1850634A2 EP 1850634 A2 EP1850634 A2 EP 1850634A2 EP 07103023 A EP07103023 A EP 07103023A EP 07103023 A EP07103023 A EP 07103023A EP 1850634 A2 EP1850634 A2 EP 1850634A2
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EP
European Patent Office
Prior art keywords
frequency range
gain
curve
hearing aid
amplification
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Withdrawn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
EP07103023A
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German (de)
English (en)
Inventor
Volkmar Hamacher
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
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 Audioligische Technik GmbH filed Critical Siemens Audioligische Technik GmbH
Publication of EP1850634A2 publication Critical patent/EP1850634A2/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Withdrawn legal-status Critical Current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
    • H04R25/35—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception using translation techniques
    • H04R25/356—Amplitude, e.g. amplitude shift or compression

Definitions

  • the present invention relates to a method for adjusting the amplification of a hearing aid by means of a loudness-based or prescriptive setting of the amplification of the hearing device in a lower frequency range and another setting in the upper frequency range.
  • the optimal gain of a hearing aid to compensate for a hearing loss is usually determined by loudness scaling or auditory threshold based prescriptive fitting formulas. These formulas describe the target gain as a function of the frequency and the sound level.
  • the common formulas such as NAL-NL1 or DSL-I / O, are defined for the frequency range 0 to 8 kHz. About the target gain in the range above 8 kHz, they make no statement. This is mainly because common hearing aids can only transmit frequencies below 8 kHz, so a fitting formula for high frequencies is not necessary.
  • special audiometer are required and the realization of a defined gain in this frequency range is very difficult (wavelength in the same order of magnitude as Ohrkanalgeometrien).
  • hearing aids Due to special broadband amplifiers and electroacoustic transducers, however, hearing aids can nowadays be realized which can transmit frequencies above 8 kHz up to 15 kHz.
  • a problem now is the adaptation of the gain in this frequency range to the hearing loss, which is the subject of the present invention.
  • acoustic feedback can greatly affect the gain setting. This is generally true for the entire frequency range but especially for the frequency range above 6 kHz.
  • loudness scaling narrowband stimuli
  • comparison with reference scaling in normal hearing listeners sets the gain over the entire frequency range so that the loudness impression normalizes, i. H.
  • a hearing aid stimulus is perceived as loud by the hearing impaired as by a normal hearing subject without a hearing aid.
  • the disadvantages here are the very long measurement times for the loudness scaling and the relatively frequently occurring acoustic feedback.
  • the publication DE 41 25 378 C1 discloses a hearing aid having a signal path for a lower frequency range and another signal path for an upper frequency range.
  • a method for regulating a hearing aid is known from the document DE 35 42 566 A1 known.
  • the user can change the steepness of the frequency response above a cutoff frequency.
  • EP 0 917 397 A1 a method for determining a parameter set of a hearing aid.
  • the volume and feedback are also taken into account.
  • the object of the present invention is therefore to provide a method with which an adaptation of the hearing aid gain in the higher frequency range, in particular above 8 kHz, is effectively possible with little effort.
  • this object is achieved by a method for adjusting the amplification of a hearing device by setting the amplification of the hearing device in a lower frequency range by loudness-based or prescriptive, performing an open-loop gain measurement in an upper frequency range following the lower frequency range and setting a maximum Gain or a frequency-dependent maximum gain curve at least in the upper frequency range based on the open-loop gain measurement.
  • a hybrid fitting procedure in which a loudness-based or prescriptive adjustment in the lower frequency range and a different type of adaptation in the higher frequency range is performed.
  • a fast adaptation in the high frequency range is possible because no audiometric measurements are required.
  • the adjustment of the gain in the high frequency range is characterized by their robustness, as a feedback whistling through the OLG restriction (open-loop gain) is excluded in principle.
  • a further advantage to be emphasized is that a good basic adaptation and a high spontaneous acceptance are achieved by proven matching formulas in the basic frequency range.
  • the susceptibility to feedback is reduced by at least one narrow band filter and / or by a feedback reduction algorithm, so that a higher maximum gain or a higher maximum gain curve can be achieved. This can also be used to provide more serious hearing damage to people without feedback whistling.
  • At least one underlying gain curve is obtained from the maximum gain curve and the hearing aid wearer may select one of the plurality of gain curves for the gain.
  • the hearing aid wearer may select one of the plurality of gain curves for the gain.
  • it is favorable to present sound examples to the hearing aid wearer, so that he can interactively select one of the several amplification curves. The selection can make the hearing aid wearer on the basis of everyday sounds.
  • a subjectively optimal solution for the amplification in the high frequency range can be found quickly.
  • the gain curve in the upper frequency range is adapted to a gain curve in the lower frequency range or vice versa or both. This avoids points of discontinuity at the interface between the upper and lower frequency ranges.
  • a conventional gain adaptation first takes place in the lower frequency range or in the base frequency range [0-fb] according to the steps S1 and S2.
  • loudness impressions are recorded by a hearing device wearer in step S1, so that a gain adjustment based on the subjectively perceived loudness can be performed.
  • an audiogram of the patient is recorded, so that its hearing threshold is known.
  • step S2 From the loudness scaling or the audiogram, according to step S2, those amplifications or amplification curves are calculated which are to be implemented in the hearing device. For this one uses prescriptive fitting formulas, which are known for example under the name NAL-NL1, DSL-I / O. In addition, firm-specific formulas but also a loudness normalization can be used for the gain calculation. Finally, one obtains a gain curve or a gain curve set for the lower frequency range [0-fb Hz]. The base limit frequency fb is for example 6 kHz.
  • This OLG measurement can also be extended to the lower frequency range.
  • the signal path of the hearing device is separated, test tones of different frequencies are generated digitally in the hearing device, emitted via the hearing device handset, and the digital level of the signal picked up again via the hearing device microphone (s) is determined before the separation point.
  • the difference to the original digital level of the test stimulus represents the open-loop gain (OLG), which can be used to quantify the maximum possible gain (feedback threshold) without feedback whistles.
  • This determination of the maximum gain in accordance with step S4 takes place for each frequency or each desired frequency band in the high-frequency range [fb-fg].
  • a certain distance [feedback reserve, preferably 6-12 dB] is kept to the feedback threshold in order to avoid feedback whistling even with slight changes in the feedback path in everyday life.
  • the reduction in the susceptibility to feedback by notch filters or other narrowband filters is reduced.
  • feedback reduction algorithms such as oscillation detection and adaptive notch filters or feedback compensators may be used. In any case, this can expand the gain range.
  • the amplification curves consist of the maximum possible amplification in the upper frequency range Gmax (f) and reduced amplifications derived therefrom in the desired number.
  • percentage reduced curves such as 75% Gmax (f), 50% Gmax (f), etc. can be provided.
  • the exact adjustment of the amplification in the high-frequency range can be done with the aid of several bands, in particular using a filter bank. In the high-frequency domain, therefore, no prescriptive or loudness-based fitting method is explicitly used.
  • fb 6 kHz
  • f1 4 kHz
  • f2 8 kHz.
  • the hearing device wearer selects a variant suitable for him in step S7. For this he will be given sound examples or he will make the selection based on the everyday sound environment. In both cases, listening situations such as music, speech or the like can be used (see step S8).
  • step S5 the gain in the high-frequency range is varied in accordance with step S5. Subsequently, the smoothing of the amplification curves of the high-frequency and low-frequency ranges takes place again in step S6 and the hearing aid wearer can then re-evaluate the newly obtained amplification curve in step S7.
  • a gain curve for the hearing aid wearer is in order, this gain curve is firmly implemented in the hearing aid.
  • an automatic boost can also take place over time. In this way, the hearing aid wearer can gradually adjust to the new hearing impression, d. H. acclimatize.
  • the gain is determined according to another fitting method.
  • the high-frequency components should be constantly amplified in accordance with the curve 5. Since the maximum gain curve 4 intersects the target curve 1 at approximately 4 kHz and the gain curve 5 at approximately 8 kHz, the loudness gain in the range between 4 and 8 kHz is limited to the maximum gain.
  • interpolations are performed in the range between 4 and 6 kHz, which connect the gain curve 5 and the maximum gain curve 4 at about 6 kHz to the target gain curve 2 or the target gain curve 3 at 4 kHz. This results in the interpolation sections 6 and 7. In this way, a smooth transition from the respective gain curve 1, 2, 3 in the low-frequency range to the gain curve 5 in the high-frequency range can be ensured.
  • the gain in the high-frequency range can be varied according to the arrow 8.
  • a gain curve 9 in the high-frequency range can also be selected.
  • this curve 9 is not obtained here by dividing the maximum gain curve 4 by a constant factor according to the above-mentioned example. Rather, it should be shown by the example of FIG 2, that the gain curves in the high-frequency range can be obtained by other methods than by constant division. Also for the gain curve 9 will be in the frequency domain between 4 kHz and 6 kHz interpolation transitions to the target gain curves 1 to 3 used.
EP07103023A 2006-04-27 2007-02-26 Procédé de réglage d'une prothèse auditive avec amplification des hautes fréquences Withdrawn EP1850634A2 (fr)

Applications Claiming Priority (1)

Application Number Priority Date Filing Date Title
DE102006019694A DE102006019694B3 (de) 2006-04-27 2006-04-27 Verfahren zum Einstellen eines Hörgeräts mit Hochfrequenzverstärkung

Publications (1)

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EP1850634A2 true EP1850634A2 (fr) 2007-10-31

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EP07103023A Withdrawn EP1850634A2 (fr) 2006-04-27 2007-02-26 Procédé de réglage d'une prothèse auditive avec amplification des hautes fréquences

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US (1) US8311250B2 (fr)
EP (1) EP1850634A2 (fr)
DE (1) DE102006019694B3 (fr)

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* Cited by examiner, † Cited by third party
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DE102009051200B4 (de) * 2009-10-29 2014-06-18 Siemens Medical Instruments Pte. Ltd. Hörgerät und Verfahren zur Rückkopplungsunterdrückung mit einem Richtmikrofon
EP2360944B1 (fr) 2010-02-01 2017-12-13 Oticon A/S Procédé de suppression de réponse acoustique dans un dispositif auditif et dispositif auditif correspondant
EP2566193A1 (fr) * 2011-08-30 2013-03-06 TWO PI Signal Processing Application GmbH Système et procédé d'adaptation d'un appareil auditif
US10124168B2 (en) 2014-07-07 2018-11-13 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
US11184713B2 (en) * 2019-11-19 2021-11-23 Sonova Ag Systems and methods for adjusting a gain limit of a hearing device

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DE3542566A1 (de) * 1984-12-21 1986-07-03 Danavox A/S, Kopenhagen/Koebenhavn Verfahren zum einregulieren eines hoergeraets, ein hoergeraet und dessen verwendung
US4630305A (en) 1985-07-01 1986-12-16 Motorola, Inc. Automatic gain selector for a noise suppression system
CH678692A5 (en) * 1989-06-08 1991-10-31 Phonak Ag Measuring individual acoustic performance in human ear - using microphone adjacent ear drum with loudspeaker with ear canal sealed by insert
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DE4125378C1 (en) * 1991-07-31 1992-10-08 Siemens Ag, 8000 Muenchen, De Hearing aid device with improved speech discrimination characteristics - has amplification setting control fitted between preamplifier and amplifier
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DE4441755C1 (de) * 1994-11-23 1996-01-18 Siemens Audiologische Technik Elektrische Hörhilfeschaltung
EP0824845B1 (fr) * 1995-05-02 1998-09-30 TOPHOLM & WESTERMANN APS Procede permettant de commander une prothese auditive programmable ou geree par programme pour le reglage de ladite prothese in situ
EP0845921A1 (fr) 1996-10-23 1998-06-03 Siemens Audiologische Technik GmbH Procédé et circuit pour réguler le volume dans des prothèses auditives numériques
US6134329A (en) * 1997-09-05 2000-10-17 House Ear Institute Method of measuring and preventing unstable feedback in hearing aids
EP0917397A1 (fr) * 1997-10-14 1999-05-19 Siemens Audiologische Technik GmbH Procédé de déterminer une série de paramètres d'une prothèse acoustique
US20040151332A1 (en) * 1998-10-07 2004-08-05 Finn Danielsen Feedback management for hearing aid
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Publication number Publication date
DE102006019694B3 (de) 2007-10-18
US20070280494A1 (en) 2007-12-06
US8311250B2 (en) 2012-11-13

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