EP0793897B1 - Prothese auditive - Google Patents

Prothese auditive Download PDF

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Publication number
EP0793897B1
EP0793897B1 EP95921771A EP95921771A EP0793897B1 EP 0793897 B1 EP0793897 B1 EP 0793897B1 EP 95921771 A EP95921771 A EP 95921771A EP 95921771 A EP95921771 A EP 95921771A EP 0793897 B1 EP0793897 B1 EP 0793897B1
Authority
EP
European Patent Office
Prior art keywords
signal
hearing aid
low
clock
output
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
EP95921771A
Other languages
German (de)
English (en)
Other versions
EP0793897A1 (fr
Inventor
Henning Haugaard Andersen
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.)
Topholm and Westermann ApS
Original Assignee
Topholm and Westermann ApS
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Filing date
Publication date
Application filed by Topholm and Westermann ApS filed Critical Topholm and Westermann ApS
Publication of EP0793897A1 publication Critical patent/EP0793897A1/fr
Application granted granted Critical
Publication of EP0793897B1 publication Critical patent/EP0793897B1/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; 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

Definitions

  • the invention relates to a hearing aid with a microphone, a transmission part for signal processing and an output amplifier with connected Listener.
  • Output amplifiers for hearing aids should have low distortion have a low energy requirement, even with high output power.
  • Class B amplifiers are more efficient than A amplifiers.
  • Amplifiers of this type have also hitherto been customary in hearing aids.
  • D-amplifiers are e.g. in the European patent application o 590 903 Al from Exar Corporation and in US-A 5,247,581 from Exar Corporation and US-A 4,689,819 and US-A 4,592,087 to Industrial Research Products Inc. discloses and describes in detail.
  • the rectangular pulse sequence of an oscillator lying in the ultrasound range is an integrator supplied, which also the output voltage of a low frequency signal is supplied by a microphone via an amplifier train arrives and serves as a preload.
  • the output signal of the integrator is then a triangular pulse train, the zero crossings through the Bias voltage supplied to the integrator varies in the hearing frequency range will. That is, this low-frequency bias makes the zero crossings of the triangular signal from one symmetrical to the axis of symmetry Course without bias signal variable to asymmetrical conditions shifted, the asymmetry in terms of sign and size a continuously changing function of the amplitude of the low frequency Input signal is.
  • Such D-amplifiers working with pulse width modulation have a very good efficiency and have almost no cross modulation.
  • a disadvantage of the D-amplifier with pulse width modulation is that the pulse width changes either continuously or in very small steps should be achieved when a high signal to noise ratio is reached shall be.
  • the known class D output amplifiers use a continuous one Modulation, i.e. a continuous variation in pulse width and need hence a continuous microphone output signal as an input signal. If the signal processing preceding the output amplifier is time-discrete and / or amplitude discretely, then this digital signal must first e.g. converted into a holding network or a digital / analog converter will. This represents an additional effort that can hardly be sold.
  • EP-A 0495328 e.g. known as a sigma-delta converter particularly suitable as an A / D converter with discrete components.
  • circuits are for use in hearing aids with highly integrated ones digital circuits less suitable.
  • EP-A0597523 discloses a fast D / A converter which is made of a sigma-delta converter and a downstream asynchronous Sigma-delta modulator consists of the output signal of the sigma-delta converter generates an ambivalent, asynchronously modulated signal, which is then fed to a low pass filter.
  • the effort for the output amplifier is a fully digitized one Hearing aid too high. In addition, it does not allow a high signal / noise ratio achieve.
  • a hearing aid which consists of an ear part to be carried and a part connected by a cable to the body supporting signal processing part, in which over an A / D converter a digital signal processing and a subsequent D / A converter Adaptation of the transfer function of the hearing aid to the auditory deficit Carrier should be reached.
  • EP-A 0578021 discloses a hearing aid, but not one Signa-Delta converter contains a normal A / D converter, one Signal processing and a D / A converter.
  • the invention therefore goes a completely different way, the use of D / A converters of the usual type in the output amplifier of a fully digital Avoids hearing aid.
  • the invention is therefore intended to provide a hearing aid device with a novel, essential simpler output amplifiers are proposed, in which a relative high signal / noise ratio can be achieved with extremely low power requirements and high output power with minimal distortion and anything Lack of cross-modulation and control of the output amplifier with a digital input signal.
  • the output amplifier can completely be constructed as a digital highly integrated CMOS circuit.
  • FIG. 1 shows, for example, a hearing aid with a novel output amplifier, however, its use is not limited to use in hearing aids is limited, but is generally applicable to digital amplifiers where it comes down to a high ratio of useful signal to interference signal.
  • the acoustic Signal recorded by a microphone 1 and in a low-pass filter Antialiasing filter is limited to a frequency range that is common in hearing aids.
  • This low-frequency signal is now in a signal processor 3rd subjected to signal processing. Among them is e.g. to understand that the analog input signal is either further processed analogously in the manner that the amplifier characteristic of the signal processor to that for the respective Hearing damage or hearing loss of its wearer regarding all necessary variables is adjusted.
  • Such variable which are dependent on the frequency, are e.g. the Amplification of the individual stages, the limit level, the compression threshold, the automatic gain control with its response and Fall times, a combination of compression and expansion, or whatever a non-linear course of the amplification of individual stages or overall all levels, as well as the output sound pressure level.
  • the signal processor would have to have a digital-to-analog converter on the input side included, for which a separate clock generator for the clock would be required.
  • a separate clock generator for the clock would be required.
  • a new output amplifier then follows the signal processor 3.
  • This consists essentially of a signal converter 4, which is essentially a ⁇ - ⁇ converter.
  • This signal converter first contains a subtraction stage 5 with two inputs, namely a positive input and a negative Input, with the positive input at the output of the signal processor 3 connected.
  • a low-pass filter 6 follows this subtraction stage 5
  • the low-pass filter 6 could be an integrator.
  • On a comparator 7 with holding network is connected to this integrator 6.
  • the output of this comparison stage is via a feedback connection connected to the negative input of subtracting stage 5.
  • a High-frequency clock generator 8 is provided, which is a high-frequency clock pulse signal with a frequency in the range of about 1 MHz to the comparison stage 7 issues.
  • the output of the signal converter 4 is via a low-pass function connected to the handset 10.
  • a clock generator required for the signal processor 3 is essential lower frequency is preferably by the high frequency clock generator 8 synchronized. This can be done simply by frequency division, for example can be achieved with a factor M.
  • a typical clock frequency for the signal processor 3 could be about 32 kHz.
  • the mode of operation of the signal converter 4 should be based on FIGS. 2 and 3 are explained.
  • the high-frequency clock signal 11 of the clock pulse generator 8 is, as already mentioned, forwarded to comparison level 7.
  • the digital input signal 12 in FIG. 3 (an extremely simplified representation) is the subtracting level at their positive input fed.
  • the output signal 14 of the signal converter 4 reaches the negative input of the via a feedback connection Subtracting stage and is subtracted there from the input signal 12.
  • the resulting output signal is the integrator 6 (which here Represents low-pass filter) and integrated there to the output signal 13.
  • This signal 13 is synchronized in the comparison stage 7 with holding network with the edges of the high-frequency clock signal into the output signal 14 converted, which has only two possible values, here the simplicity are shown as +1 and -1 for the sake of convenience.
  • the input signal 12 should initially have the value -0.5.
  • the integrated Signal 13 then rises from -1.5 to zero, resulting in a first output pulse transition from -1 to +1.
  • the integrated signal then drops again to -1.5, after which the output signal 14 again assumes the value -1.
  • the output signal 14 of the signal converter 4 in addition the desired increased low-frequency component a strong high-frequency component Contains signal portion, which of course is an unwanted interference signal represents e.g. must be removed by a passive low-pass filter.
  • This new output amplifier especially suitable for hearing aids has a number of advantages. All pulse edges are with a known one Clock frequency synchronized, which can also be used to the essential for the upstream signal processor, at essential synchronize lower clock frequency working clock pulse generator.
  • the input signal of the output amplifier can be a digital signal be, and the output amplifier can be designed as a pure digital circuit will. I.e. but that the entire circuit is constructed as a digital circuit can be, only at the input of the signal processor 3 Analog / digital Vandler would have to be provided. This results in the further one Possibility of using the entire circuit in C-MOS technology as a highly integrated Build circuit.

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)
  • Amplifiers (AREA)
  • Adornments (AREA)
  • Finger-Pressure Massage (AREA)
  • Compression, Expansion, Code Conversion, And Decoders (AREA)

Claims (5)

  1. Prothèse auditive avec un microphone (1), un transmetteur (2, 3) pour le traitement du signal et un amplificateur de sortie (4) auquel est relié un écouteur (10), amplificateur composé essentiellement d'un convertisseur du type Σ-Δ auquel est relié un générateur d'impulsions d'horloge (8) produisant un signal d'horloge haute fréquence et suivi d'une fonction passe-bas (15), ainsi qu'avec une pile pour l'alimentation électrique, caractérisée en ce que le signal d'entrée du convertisseur est une représentation numérique composée de plusieurs bits / octets du signal d'entrée de la prothèse auditive, en ce que ce signal d'entrée peut être converti par le convertisseur en un signal de sortie (14) qui ne peut prendre que deux valeurs et en ce que ce signal de sortie (14) représente essentiellement, après être passé par la fonction passe-bas, une image amplifiée du signal d'entrée basse fréquence de la prothèse auditive.
  2. Prothèse auditive selon la revendication 1,
    caractérisée en ce que le convertisseur (4) relié en entrée au transmetteur (2, 3) se compose essentiellement d'un étage soustracteur (5) possédant une entrée positive et une entrée négative, d'un filtre passe-bas (6) et d'un circuit comparateur (7) attaqué par des impulsions haute fréquence (11) du générateur d'impulsions d'horloge (8) avec un réseau de maintien, l'entrée positive de l'étage soustracteur (5) étant reliée au transmetteur (2, 3) et l'entrée négative de l'étage soustracteur à la sortie de l'étage comparateur (7) par une ligne de contre-réaction.
  3. Prothèse auditive selon la revendication 1,
    caractérisée en ce que la fréquence d'horloge des impulsions produites par le générateur d'impulsions d'horloge (8) est de 1 MHz.
  4. Prothèse auditive selon la revendication 1,
    caractérisée en ce que le signal d'horloge fourni par une horloge (9) au processeur (3) peut être synchronisé par le signal d'horloge haute fréquence (11) du générateur d'impulsions d'horloge (8).
  5. Prothèse auditive selon la revendication 1,
    caractérisée en ce que la fonction passe-bas est formée par les caractéristiques électriques, acoustiques et mécaniques de l'écouteur (10) et de l'oreille humaine.
EP95921771A 1994-11-26 1995-05-29 Prothese auditive Expired - Lifetime EP0793897B1 (fr)

Applications Claiming Priority (3)

Application Number Priority Date Filing Date Title
DE4441996 1994-11-26
DE4441996A DE4441996A1 (de) 1994-11-26 1994-11-26 Hörhilfsgerät
PCT/EP1995/002033 WO1996017493A1 (fr) 1994-11-26 1995-05-29 Prothese auditive

Publications (2)

Publication Number Publication Date
EP0793897A1 EP0793897A1 (fr) 1997-09-10
EP0793897B1 true EP0793897B1 (fr) 1998-05-13

Family

ID=6534142

Family Applications (1)

Application Number Title Priority Date Filing Date
EP95921771A Expired - Lifetime EP0793897B1 (fr) 1994-11-26 1995-05-29 Prothese auditive

Country Status (9)

Country Link
US (1) US5878146A (fr)
EP (1) EP0793897B1 (fr)
JP (1) JP3274469B2 (fr)
AT (1) ATE166199T1 (fr)
AU (1) AU691001B2 (fr)
CA (1) CA2204757C (fr)
DE (2) DE4441996A1 (fr)
DK (1) DK0793897T3 (fr)
WO (1) WO1996017493A1 (fr)

Cited By (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
EP1694095A2 (fr) 2005-02-15 2006-08-23 Siemens Audiologische Technik GmbH Prothèse auditive avec un amplificateur de sortie comportant un modulateur du type Sigma-Delta
WO2022200436A1 (fr) 2021-03-24 2022-09-29 Widex A/S Dispositif audio à niveau d'oreille et procédé de fonctionnement d'un dispositif audio à niveau d'oreille

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US5754131A (en) * 1996-07-01 1998-05-19 General Electric Company Low power delta sigma converter
US6044162A (en) * 1996-12-20 2000-03-28 Sonic Innovations, Inc. Digital hearing aid using differential signal representations
US6144748A (en) * 1997-03-31 2000-11-07 Resound Corporation Standard-compatible, power efficient digital audio interface
DE19736406B4 (de) * 1997-08-21 2007-05-16 Siemens Ag Einrichtung zum Steuern eines automatischen Getriebes für ein Kraftfahrzeug
US5995036A (en) * 1998-03-17 1999-11-30 Sonic Innovations, Inc. Passive switched capacitor delta analog-to-digital converter with programmable gain control
WO2000044198A1 (fr) * 1999-01-25 2000-07-27 Tøpholm & Westermann APS Systeme de correction auditive et appareil de correction auditive destine a etre assemble in situ
AU753295B2 (en) * 1999-02-05 2002-10-17 Widex A/S Hearing aid with beam forming properties
US6163287A (en) 1999-04-05 2000-12-19 Sonic Innovations, Inc. Hybrid low-pass sigma-delta modulator
US6408318B1 (en) 1999-04-05 2002-06-18 Xiaoling Fang Multiple stage decimation filter
US6445321B2 (en) 1999-04-05 2002-09-03 Sonic Innovations, Inc. Hybrid low-pass sigma-delta modulator
US6313773B1 (en) 2000-01-26 2001-11-06 Sonic Innovations, Inc. Multiplierless interpolator for a delta-sigma digital to analog converter
DE60105819T2 (de) 2000-07-05 2005-10-06 Koninklijke Philips Electronics N.V. A/d umwandler mit integrierter vorspannung für mikrofon
EP1251714B2 (fr) 2001-04-12 2015-06-03 Sound Design Technologies Ltd. Système digital de prothèse auditive
US6633202B2 (en) 2001-04-12 2003-10-14 Gennum Corporation Precision low jitter oscillator circuit
CA2382358C (fr) * 2001-04-18 2007-01-09 Gennum Corporation Detecteur numerique quasi quadratique
ATE318062T1 (de) * 2001-04-18 2006-03-15 Gennum Corp Mehrkanal hörgerät mit übertragungsmöglichkeiten zwischen den kanälen
US20020191800A1 (en) * 2001-04-19 2002-12-19 Armstrong Stephen W. In-situ transducer modeling in a digital hearing instrument
EP1284587B1 (fr) 2001-08-15 2011-09-28 Sound Design Technologies Ltd. Appareil auditif reconfigurable à faible consommation d'énergie
US7315626B2 (en) * 2001-09-21 2008-01-01 Microsound A/S Hearing aid with performance-optimized power consumption for variable clock, supply voltage and DSP processing parameters
CN1608393B (zh) 2001-11-30 2011-08-24 桑尼昂公司 一种小型扬声器的高效率驱动器
WO2007106399A2 (fr) 2006-03-10 2007-09-20 Mh Acoustics, Llc Reseau de microphones directionnels reducteur de bruit
US8098844B2 (en) * 2002-02-05 2012-01-17 Mh Acoustics, Llc Dual-microphone spatial noise suppression
US7171008B2 (en) * 2002-02-05 2007-01-30 Mh Acoustics, Llc Reducing noise in audio systems
GB2386280B (en) * 2002-03-07 2005-09-14 Zarlink Semiconductor Inc Digital microphone
EP1429455A1 (fr) * 2002-12-11 2004-06-16 Dialog Semiconductor GmbH Linéarisation d'un amplificateur PDM de classe D
CA2619028A1 (fr) 2005-08-23 2007-03-01 Widex A/S Prothese auditive avec bande passante acoustique accrue
EP2417778B1 (fr) 2009-04-06 2015-06-17 Widex A/S Prothèse auditive en deux parties à connexion par bus de données
US8553897B2 (en) 2009-06-09 2013-10-08 Dean Robert Gary Anderson Method and apparatus for directional acoustic fitting of hearing aids
US8879745B2 (en) * 2009-07-23 2014-11-04 Dean Robert Gary Anderson As Trustee Of The D/L Anderson Family Trust Method of deriving individualized gain compensation curves for hearing aid fitting
US9101299B2 (en) * 2009-07-23 2015-08-11 Dean Robert Gary Anderson As Trustee Of The D/L Anderson Family Trust Hearing aids configured for directional acoustic fitting
EP2544587B1 (fr) 2010-03-09 2023-05-10 T&W Engineering A/S Dispositif de surveillance d'eeg en deux parties comprenant un bus de données et procédé de communication entre les parties
WO2011110218A1 (fr) 2010-03-09 2011-09-15 Widex A/S Prothèse auditive en deux parties comprenant un bus de données et procédé de communication entre les parties
US8942397B2 (en) 2011-11-16 2015-01-27 Dean Robert Gary Anderson Method and apparatus for adding audible noise with time varying volume to audio devices
US9582452B2 (en) * 2013-06-05 2017-02-28 The Boeing Company Sensor network using pulse width modulated signals
US10142742B2 (en) 2016-01-01 2018-11-27 Dean Robert Gary Anderson Audio systems, devices, and methods
DK180177B1 (en) 2018-04-30 2020-07-16 Widex As Method of operating a hearing aid system and a hearing aid system
US11696083B2 (en) 2020-10-21 2023-07-04 Mh Acoustics, Llc In-situ calibration of microphone arrays

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US5448644A (en) * 1992-06-29 1995-09-05 Siemens Audiologische Technik Gmbh Hearing aid
EP0597523B1 (fr) * 1992-11-09 1997-07-23 Koninklijke Philips Electronics N.V. Convertisseur numérique-analogique

Cited By (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
EP1694095A2 (fr) 2005-02-15 2006-08-23 Siemens Audiologische Technik GmbH Prothèse auditive avec un amplificateur de sortie comportant un modulateur du type Sigma-Delta
DE102005006858A1 (de) * 2005-02-15 2006-09-07 Siemens Audiologische Technik Gmbh Hörhilfegerät mit einem Ausgangsverstärker, der einen Sigma-Delta-Modulator umfasst
WO2022200436A1 (fr) 2021-03-24 2022-09-29 Widex A/S Dispositif audio à niveau d'oreille et procédé de fonctionnement d'un dispositif audio à niveau d'oreille

Also Published As

Publication number Publication date
AU691001B2 (en) 1998-05-07
CA2204757A1 (fr) 1996-06-06
CA2204757C (fr) 1999-08-03
DK0793897T3 (da) 1999-02-15
EP0793897A1 (fr) 1997-09-10
ATE166199T1 (de) 1998-05-15
DE4441996A1 (de) 1996-05-30
WO1996017493A1 (fr) 1996-06-06
JP3274469B2 (ja) 2002-04-15
DE59502189D1 (de) 1998-06-18
US5878146A (en) 1999-03-02
JPH10504155A (ja) 1998-04-14
AU2671495A (en) 1996-06-19

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