EP1290914B1 - Verfahren zur anpassung eines hörgerätes an ein individuum - Google Patents

Verfahren zur anpassung eines hörgerätes an ein individuum Download PDF

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Publication number
EP1290914B1
EP1290914B1 EP01916843A EP01916843A EP1290914B1 EP 1290914 B1 EP1290914 B1 EP 1290914B1 EP 01916843 A EP01916843 A EP 01916843A EP 01916843 A EP01916843 A EP 01916843A EP 1290914 B1 EP1290914 B1 EP 1290914B1
Authority
EP
European Patent Office
Prior art keywords
loudness
function
individual
hearing
determined
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
EP01916843A
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German (de)
English (en)
French (fr)
Other versions
EP1290914A2 (de
Inventor
Volker KÜHNEL
Andreas Von Buol
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.)
Sonova Holding AG
Original Assignee
Phonak AG
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Filing date
Publication date
Application filed by Phonak AG filed Critical Phonak AG
Publication of EP1290914A2 publication Critical patent/EP1290914A2/de
Application granted granted Critical
Publication of EP1290914B1 publication Critical patent/EP1290914B1/de
Anticipated expiration legal-status Critical
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    • 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
    • H04R25/35—Electric hearing aids using translation techniques
    • H04R25/356—Amplitude, e.g. amplitude shift or compression
    • 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
    • H04R25/70—Adaptation of deaf aid to hearing loss, e.g. initial electronic fitting

Definitions

  • the present invention relates to a method for Adaptation of a hearing aid to an individual.
  • a successful fitting of a hearing aid to one Individual with hearing loss and Correcting is a crucial under another factor forming the acceptance of the hearing aid. It is not just the type and extent of hearing loss important, but a number of others Circumstances, such as personal, i.e. individual feeling of loudness.
  • a method of fitting a hearing aid to a Individual is from the European disclosure Patent application number EP-A2-0 661 905 known.
  • the known method relates to the correction of a individual, damaged psycho-acoustic perception by setting parameters in a hearing aid. there becomes the statistical objective function for the correction determined average perception of people with normal hearing used.
  • the standard loudness function used as the target function becomes determined on a collective of people with normal hearing, whereby this standard loudness function if possible with the same Procedure is determined like the actual individual Measurement.
  • the present invention is therefore the object based on specifying a procedure in which recruitment on Hearing aids are made that have an improved fit of hearing aids to the loudness perception of the individual enable.
  • the invention has the following advantages: individual perception as well as statistical norm perception of hearing impaired in Dependence of hearing loss and the norm perception of Normal hearing people in determining the attitudes of a Hearing aid are taken into account, weighted according to Data reliability will be optimal for the individual Get target function for setting the hearing aid, with what also improves the individual's hearing ability is. In other words, it is through the invention managed to get an optimal target loudness, which the individual perception of loudness is taken into account.
  • An offset can be determined from the individual HVL0 function, in comparison to the hearing impaired standard HVL0 function. which describes the mean difference in the abscissa section of the loudness functions of the individual in comparison to the norm.
  • an audiogram is created. This happens in that in the case of a potential hearing aid wearer Hearing thresholds for pure tones of different frequencies be measured. The measured increases in hearing thresholds are considered as hearing loss in dB at each frequency or in expressed and represented at certain frequency intervals. With the help of the audiogram, it can be determined in what hearing range there is hearing loss. Furthermore Support points - d. H. separate Frequencies - determined in which in the sequence Loudness scales in the manner described below be made.
  • the loudness "L” is a psycho-acoustic quantity, which indicates how “loud” an individual is at presented acoustic Signal senses.
  • FIG. 1 One way to experience the individually felt loudness selected acoustic signals as usable To detect the size at all is the schematic in FIG. 1 shown, for example from O. Heller, "Hörfeldaudiometrie with the process of category division ", Psychological contributions 26, 1985, or V. Hohmann, "Dynamic compression for hearing aids, psychoacoustic Fundamentals and Algorithms ", thesis UNI Göttingen, VDI-Verlag, Row 17, No. 93, or Thomas Brand, Analysis and optimization of psychophysical procedures in audiology oldenburg: library and information system der Univ., 2000. - 148 S. Oldenburg, Diss., Univ., 1999. ISBN 3-8142-0721-1, known method.
  • the levels are given numerical weights, assigned from 0 to 10, for example.
  • FIG. 2 shows the loudness L, recorded with a category scaling according to FIG. 1, as a function of the mean sound pressure level in dB-SPL for a sinusoidal signal of the frequency f k .
  • the loudness L kN of the standard increases non-linearly with the signal level in the chosen representation, the slope course becomes in a first approximation for normal hearing people for all critical bands with the regression line entered as N in FIG. 2 reproduced with the slope ⁇ N in [categories per dB-SPL]:
  • model parameter ⁇ N corresponds to a non-linear amplification, approximately the same for normal hearing persons in every critical frequency band, but to be determined for hearing-impaired individuals with ⁇ kI at every frequency or in every frequency band.
  • the straight line with the slope ⁇ kI approximates the non-linear loudness function at the frequency f k by a regression line.
  • L kI typically denotes the course of the loudness L I of a hearing impaired person at a frequency f k .
  • the curve of a hearing impaired person has a larger offset (L 0 ) to the zero point and is steeper than the curve of the norm.
  • the larger offset corresponds to an increased hearing threshold
  • the phenomenon of the fundamentally steeper temper curve is referred to as loudness recruitment and corresponds to an increased ⁇ parameter
  • such loudness scales are carried out at at least one, preferably at three support points - ie at one or more different frequencies.
  • a so-called HVLS function is determined by plotting the slopes of the loudness function ⁇ 1 , ⁇ 2 , ⁇ 3 , ... as a function of the hearing loss HV in dB.
  • Fig. 3 shows an HVLS function for a hearing impaired Individual, with the individual HVLS function, dashed line, through three support points using a suitable modeling described below is determined.
  • a preferred possibility for taking the standard loudness function into account is that an average is formed between the individual slope ⁇ determined by measurement and extrapolation at 0 dB hearing loss and the standard loudness slope, with a weighting corresponding to an expected spread of the values, namely both with the individual gradient ⁇ at 0 dB hearing loss and with the standard loudness increase. Weighting the individual scaling data depending on both the quality of the individual scaling data and the number of measuring points for the individual scalings and the number of scalings carried out has proven to be advantageous.
  • an extremely good adjustment of the hearing aid can be achieved with a weighting of the individual slope ⁇ at 0 dB hearing loss with a factor 2/3 and a weighting of the standard loudness gradient ⁇ N with a factor 1/3.
  • an optimal band-specific amplification can be derived from the abscissa sections L 0 of the loudness function in conjunction with the hearing loss determined in the audiogram.
  • loudness scales are carried out at at least one, preferably at three support points, ie at one or more different frequencies.
  • the HVL0 function is determined by plotting the abscissa sections of the loudness function L 01 , L 02 , L 03 , ... as a function of the hearing loss HV in dB.
  • Fig. 4 shows an HVLO function for a hearing impaired Individual, whereby the individual HVLO function, dashed line, through three support points using a suitable modeling described below. is determined.
  • the HVLO function shown in FIG. 4 due to its calculation from several support points, has less measurement-related scatter than the individual support points, and thus better reflects changes in individual perception.
  • the target function for setting the hearing aid could already be obtained based on this individual HVL0 function, the level L 0 at 0 dB hearing loss determined by extrapolation (dotted curve in FIG. 3) and the hearing aid set accordingly. It has been shown that the hearing aid setting can be significantly improved if information about healthy hearing is also taken into account analogously to the gradient ⁇ of the loudness function. It is proposed according to the invention that the standard loudness perception is used to determine the individually required amplification with 0 dB hearing loss. According to the invention, the fact is taken into account that the loudness perception of people with normal hearing themselves is not negligible.
  • a preferred possibility for taking the standard loudness function into account is that a weighted mean value is formed between the individual level L 0 determined by measurement and extrapolation at 0 dB hearing loss and the level Norm-L 0 , with a weighting corresponding to an expected spread of the Values, both at the individual level L 0 at 0 dB hearing loss and at the level Norm-L 0 .
  • a weighting of the individual scaling data as a function of both the quality of the individual scaling data and the number of measuring points for the individual scalings and the number of scalings carried out has also proven advantageous for the level L 0 .
  • an extremely good adjustment of the hearing aid can be achieved with a weighting of the individual level L 0 at 0 dB hearing loss with a factor 1/3 and a weighting of the level Norm-L 0 with a factor 2/3 ,

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)
  • Measurement Of The Respiration, Hearing Ability, Form, And Blood Characteristics Of Living Organisms (AREA)
  • Tone Control, Compression And Expansion, Limiting Amplitude (AREA)
EP01916843A 2001-04-10 2001-04-10 Verfahren zur anpassung eines hörgerätes an ein individuum Expired - Lifetime EP1290914B1 (de)

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
US09/829,700 US7194100B2 (en) 2001-04-10 2001-04-10 Method for individualizing a hearing aid
PCT/CH2001/000232 WO2001049068A2 (de) 2001-04-10 2001-04-10 Verfahren zur anpassung eines hörgerätes an ein individuum

Publications (2)

Publication Number Publication Date
EP1290914A2 EP1290914A2 (de) 2003-03-12
EP1290914B1 true EP1290914B1 (de) 2004-05-26

Family

ID=25705677

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Application Number Title Priority Date Filing Date
EP01916843A Expired - Lifetime EP1290914B1 (de) 2001-04-10 2001-04-10 Verfahren zur anpassung eines hörgerätes an ein individuum

Country Status (7)

Country Link
US (1) US7194100B2 (da)
EP (1) EP1290914B1 (da)
AU (1) AU2001244029A1 (da)
CA (1) CA2409838A1 (da)
DE (1) DE50102419D1 (da)
DK (1) DK1290914T3 (da)
WO (1) WO2001049068A2 (da)

Cited By (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
DE102008019374A1 (de) * 2008-04-17 2009-10-22 Siemens Medical Instruments Pte. Ltd. Verfahren zur Bestimmung einer Zeitkonstante des Gehörs und Verfahren zum Einstellen einer Hörvorrichtung

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US7922671B2 (en) * 2002-01-30 2011-04-12 Natus Medical Incorporated Method and apparatus for automatic non-cooperative frequency specific assessment of hearing impairment and fitting of hearing aids
US7020581B2 (en) * 2002-10-18 2006-03-28 Medacoustics Research & Technology Medical hearing aid analysis system
MXPA05012785A (es) * 2003-05-28 2006-02-22 Dolby Lab Licensing Corp Metodo, aparato y programa de computadora para el calculo y ajuste de la sonoridad percibida de una senal de audio.
US7435228B2 (en) * 2003-07-18 2008-10-14 Harris Corporation High fidelity hearing restoration
US7756276B2 (en) * 2003-08-20 2010-07-13 Phonak Ag Audio amplification apparatus
AU2004201374B2 (en) * 2004-04-01 2010-12-23 Phonak Ag Audio amplification apparatus
MX2007005027A (es) 2004-10-26 2007-06-19 Dolby Lab Licensing Corp Calculo y ajuste de la sonoridad percibida y/o el balance espectral percibido de una senal de audio.
US8199933B2 (en) 2004-10-26 2012-06-12 Dolby Laboratories Licensing Corporation Calculating and adjusting the perceived loudness and/or the perceived spectral balance of an audio signal
EP2363421B1 (de) * 2005-04-18 2013-09-18 Basf Se Copolymere CP für die Herstellung von Zubereitungen, enthaltend wenigstens ein Conazolfungizid
US7890377B2 (en) * 2005-10-31 2011-02-15 Phonak Ag Method for producing an order and ordering apparatus
KR100842618B1 (ko) * 2005-11-01 2008-06-30 삼성전자주식회사 음악 파일 재생 방법 및 장치
TWI517562B (zh) 2006-04-04 2016-01-11 杜比實驗室特許公司 用於將多聲道音訊信號之全面感知響度縮放一期望量的方法、裝置及電腦程式
EP2002426B1 (en) * 2006-04-04 2009-09-02 Dolby Laboratories Licensing Corporation Audio signal loudness measurement and modification in the mdct domain
RU2417514C2 (ru) 2006-04-27 2011-04-27 Долби Лэборетериз Лайсенсинг Корпорейшн Регулировка усиления звука с использованием основанного на конкретной громкости обнаружения акустических событий
CN101529721B (zh) 2006-10-20 2012-05-23 杜比实验室特许公司 使用复位的音频动态处理
US8521314B2 (en) * 2006-11-01 2013-08-27 Dolby Laboratories Licensing Corporation Hierarchical control path with constraints for audio dynamics processing
JP5192544B2 (ja) * 2007-07-13 2013-05-08 ドルビー ラボラトリーズ ライセンシング コーポレイション 聴覚情景分析とスペクトルの歪みを用いた音響処理
DE102007035174B4 (de) 2007-07-27 2014-12-04 Siemens Medical Instruments Pte. Ltd. Hörvorrichtung gesteuert durch ein perzeptives Modell und entsprechendes Verfahren
DE102007035172A1 (de) 2007-07-27 2009-02-05 Siemens Medical Instruments Pte. Ltd. Hörsystem mit visualisierter psychoakustischer Größe und entsprechendes Verfahren
KR101597375B1 (ko) * 2007-12-21 2016-02-24 디티에스 엘엘씨 오디오 신호의 인지된 음량을 조절하기 위한 시스템
US8144909B2 (en) 2008-08-12 2012-03-27 Cochlear Limited Customization of bone conduction hearing devices
US8538042B2 (en) 2009-08-11 2013-09-17 Dts Llc System for increasing perceived loudness of speakers
US9172345B2 (en) * 2010-07-27 2015-10-27 Bitwave Pte Ltd Personalized adjustment of an audio device
US9479879B2 (en) 2011-03-23 2016-10-25 Cochlear Limited Fitting of hearing devices
US9312829B2 (en) 2012-04-12 2016-04-12 Dts Llc System for adjusting loudness of audio signals in real time

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US4953112A (en) * 1988-05-10 1990-08-28 Minnesota Mining And Manufacturing Company Method and apparatus for determining acoustic parameters of an auditory prosthesis using software model
US5729658A (en) * 1994-06-17 1998-03-17 Massachusetts Eye And Ear Infirmary Evaluating intelligibility of speech reproduction and transmission across multiple listening conditions
EP1207718A3 (de) 1995-03-13 2003-02-05 Phonak Ag Verfahren zur Anpassung eines Hörgerätes, Vorrichtung hierzu und Hörgerät
US6327366B1 (en) * 1996-05-01 2001-12-04 Phonak Ag Method for the adjustment of a hearing device, apparatus to do it and a hearing device
JP2953397B2 (ja) * 1996-09-13 1999-09-27 日本電気株式会社 ディジタル補聴器の聴覚補償処理方法及びディジタル補聴器

Cited By (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
DE102008019374A1 (de) * 2008-04-17 2009-10-22 Siemens Medical Instruments Pte. Ltd. Verfahren zur Bestimmung einer Zeitkonstante des Gehörs und Verfahren zum Einstellen einer Hörvorrichtung
US8238591B2 (en) 2008-04-17 2012-08-07 Siemens Medical Instruments Pte. Ltd. Method for determining a time constant of the hearing and method for adjusting a hearing apparatus

Also Published As

Publication number Publication date
US7194100B2 (en) 2007-03-20
DE50102419D1 (de) 2004-07-01
CA2409838A1 (en) 2002-11-19
AU2001244029A1 (en) 2001-07-09
DK1290914T3 (da) 2004-09-27
WO2001049068A3 (de) 2002-09-12
US20020146137A1 (en) 2002-10-10
EP1290914A2 (de) 2003-03-12
WO2001049068A2 (de) 2001-07-05

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