EP2506602B1 - Hearing aid and method for operating the same - Google Patents

Hearing aid and method for operating the same Download PDF

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Publication number
EP2506602B1
EP2506602B1 EP12159057.4A EP12159057A EP2506602B1 EP 2506602 B1 EP2506602 B1 EP 2506602B1 EP 12159057 A EP12159057 A EP 12159057A EP 2506602 B1 EP2506602 B1 EP 2506602B1
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EP
European Patent Office
Prior art keywords
gain
signal
hearing aid
frequency
input signal
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EP12159057.4A
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German (de)
French (fr)
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EP2506602A3 (en
EP2506602A2 (en
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Sebastian Pape
Maja Dr. Serman
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Sivantos Pte Ltd
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Sivantos Pte Ltd
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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
    • H04R25/45—Prevention of acoustic reaction, i.e. acoustic oscillatory feedback
    • H04R25/453—Prevention of acoustic reaction, i.e. acoustic oscillatory feedback electronically
    • G—PHYSICS
    • G10—MUSICAL INSTRUMENTS; ACOUSTICS
    • G10L—SPEECH ANALYSIS TECHNIQUES OR SPEECH SYNTHESIS; SPEECH RECOGNITION; SPEECH OR VOICE PROCESSING TECHNIQUES; SPEECH OR AUDIO CODING OR DECODING
    • G10L25/00—Speech or voice analysis techniques not restricted to a single one of groups G10L15/00 - G10L21/00
    • G10L25/78—Detection of presence or absence of voice signals
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R2225/00—Details of deaf aids covered by H04R25/00, not provided for in any of its subgroups
    • H04R2225/43—Signal processing in hearing aids to enhance the speech intelligibility

Definitions

  • the invention relates to a hearing aid according to the preamble of claim 1 and to a method for operating a hearing aid according to the preamble of claim 5.
  • the US 2011/004 468 A1 discloses a hearing aid according to the preamble of claim 1 and a method for operating a hearing aid according to the preamble of claim 5.
  • the EP 1 175 125 A2 relates to an adaptive gain and filter circuit and discloses an adaptive filter circuit for use in a hearing aid by a person having a hearing impairment comprising a predetermined frequency range.
  • the filter circuit comprises a variable filter and an amplifier having a bandwidth corresponding to the predetermined frequency range of the hearing impairment.
  • the DE 10 2009 032 238 A1 discloses a method of controlling the fitting of a hearing aid having a filter bank for spectrally selective amplification and dynamic compression of audio signals to a hearing deficit of a hearing aid wearer.
  • This document describes a maximum possible by means of the hearing aid amplification in the upper frequency bands and a feedback whistle that uses in unfavorable constructions or leaks in the earmold even at low gains, which are too low for a sufficient amplification of frikativischen energies.
  • the maximum achievable with a hearing aid gain are usually by the required, small size of the devices and the small distance between the input transducer (especially microphone) and output transducer (especially listener) set narrow limits. If the gain is too high, especially the extremely annoying feedback whistling occurs.
  • the feedback tendency of a hearing aid is frequency-dependent and usually affects the upper range of the transferable from a hearing aid frequency range.
  • a method for frequency transposition in a hearing aid device and a hearing aid device for carrying out a frequency transposition are disclosed in the document EP 1 441 562 A2 known.
  • the frequency transposition has two major disadvantages: on the one hand spectrally the destruction of the original spectral
  • a method for automatic gain adjustment in a hearing aid in which a speech signal level and a noise level is determined in several frequency bands of an input signal during operation. There is an automatic adjustment of the gain as a function of the detected signal level and the signal frequency.
  • gain parameters are determined by including a loudness model and a speech intelligibility model.
  • WO 00/05923 From the WO 00/05923 is a hearing aid with improved speech intelligibility by frequency-selective signal processing and a method for operating such a hearing aid known.
  • Object of the present invention is to understand the language of hearing loss, in which certain frequency ranges are no longer perceived even at high volume can improve.
  • This object is achieved by a hearing aid according to claim 1 and by a method for operating a hearing aid according to claim 5.
  • a hearing aid device is understood to mean any device which provides or helps to provide an output signal perceptible by a user as an audible signal, and which has means which help or compensate for an individual hearing loss of the user.
  • acts this is a hearing aid which can be worn on the body or on the head, in particular on or in the ear, and which can be implanted in whole or in part.
  • such devices are also included, whose primary purpose is not to compensate for hearing loss, such as consumer electronics (TVs, hi-fi systems, MP3 players, etc.), or communication devices (mobile phones, PDAs, headsets etc), but over Have means to compensate for an individual hearing loss.
  • a hearing aid generally includes an input transducer for receiving an input signal.
  • the input transducer is designed, for example, as a microphone which picks up an acoustic signal and converts it into an electrical input signal.
  • input transducers are also units into consideration, which have a coil or an antenna and receive an electromagnetic signal and convert it into an electrical input signal.
  • a hearing aid usually includes a signal processing unit for processing and frequency-dependent amplification of the electrical input signal.
  • a preferably digital signal processor (DSP) is used, whose operation can be influenced by means of programs or parameters which can be transmitted to the hearing aid.
  • the mode of operation of the signal processing unit can be adapted both to the individual hearing loss of a hearing aid wearer and to the current hearing situation in which the hearing aid is currently being operated.
  • the thus changed electrical input signal is finally fed to an output transducer.
  • This is usually designed as a handset, which converts the electrical output signal into an acoustic signal.
  • other embodiments are also possible here, e.g. an implantable output transducer that connects directly to an auditory ossicle and causes it to vibrate.
  • the gain is adjusted to compensate for a user's individual hearing loss becomes.
  • the gain required for this is usually dependent on the signal frequency.
  • the maximum adjustable gain physical limits are set, on the one hand result from the technical possibilities of the hearing aid used and on the other hand serve to avoid feedback. Feedbacks usually occur in the upper frequency range that can be transmitted by a hearing aid.
  • many hearing aid wearers have a large amount of hearing loss in this frequency range, which would require a high gain to compensate.
  • the gain in a respective frequency range is set so that the hearing aid in question can still be operated stably, even if it can no longer be achieved to compensate for the individual hearing loss gain.
  • the gain is set up by the mechanical stability of the devices limits.
  • the hearing aid has, in addition to the usual components (input transducer, signal processing unit, output transducer) via a sound detector device for detecting sounds, in particular consonants, in a speech signal incoming to the hearing aid.
  • a sound is generally a sound or sound produced by the human or animal voice.
  • a sound in the narrower sense is a defined sound wave produced by the flow of the breath (phonation current) at a certain position of the speech tools.
  • the generation and perception of sounds is the subject of phonetics.
  • a phoneme or phon is understood as the smallest phonetic unit of the spoken language.
  • consonant in the context of the invention is general understood a sound whose articulation includes a narrowing of the vocal tract, so that the respiratory air flow is completely or partially blocked and it comes to audible turbulence (air turbulence). Consonants are inhibitor overcoming sounds. In particular, consonants within the meaning of the invention are not limited to the consonant letters (B, C, D, F, etc.).
  • the invention now provides, in a recognized sound, in particular a consonant or fricative, the signal components in a frequency range in which the necessary to compensate for the individual hearing loss gain can not be achieved permanently, briefly, especially for the duration of the sound, to increase the gain beyond the permanently possible gain. This makes it possible for the hearing aid wearer to better perceive the sound and thus better understand the overall language.
  • a splitting of the electrical input signal into a plurality of parallel frequency bands (channels) is provided and the signal processing in the hearing aid in the signal processing unit is at least partially parallel in the individual frequency bands.
  • the gain is then raised beyond the normal gain for at least one particular frequency band if the desired gain is not permanently achievable for the reasons already stated and the detected sound has signal components in the respective frequency band.
  • the invention offers the advantage that, unlike frequency compression, the clarity of speech is not compromised to any extent.
  • FIG. 1 shows in a simplified block diagram the structure of a hearing aid according to the prior art.
  • Hearing aids have in principle as essential components one or more input transducers, an amplifier and an output transducer.
  • the input transducer is usually a sound receiver, z. As a microphone, or an electromagnetic receiver, for. B. an induction coil.
  • the output transducer is usually used as an electroacoustic transducer, z. As miniature speaker or handset, or as an electromechanical transducer, z. B. bone conduction, realized.
  • the amplifier is usually integrated in a signal processing unit. This basic structure is in FIG. 2 Exemplary a behind-the-ear hearing aid 1 shown.
  • a hearing aid housing 2 for carrying behind the ear two microphones 3 and 4 are installed for receiving the sound from the environment.
  • a signal processing unit 5 which is also integrated into the hearing aid housing 2, processes the microphone signals and amplifies them.
  • the output signal of the signal processing unit 5 is transmitted to a loudspeaker or earpiece 6, which outputs an acoustic signal. If necessary, the sound is transmitted to the eardrum of the hearing aid wearer via a sound tube, which is fixed in the auditory canal with an earmold.
  • the power supply of the hearing device and in particular of the signal processing unit 5 is effected by a likewise integrated into the hearing aid housing 2 battery. 7
  • FIG. 2 shows in a simplified block diagram how an electrical output signal AS is generated from an electrical input signal ES, which optionally contains a speech signal.
  • the acoustic input signal recorded by a microphone 12 is first converted into an electrical input signal ES and fed to a filter bank 13.
  • the filter bank 13 effects a splitting of the electrical input signal ES into a plurality of (in the exemplary embodiment three) parallel channels.
  • the further signal processing to compensate for the individual hearing loss of a user is then carried out in parallel in the three channels, in particular in the signal processing units 14, 15 and 16, before the processed signals are combined in a summer 17 again.
  • a receiver 18 finally converts the resulting electrical output signal AS into an acoustic output signal.
  • an appropriate setting of parameters sets a gain that compensates for the user's individual hearing loss.
  • the gain may need to a maximum amount can be reduced in order to prevent overloading of the amplifier included in the signal processing unit concerned or to avoid the occurrence of feedback. It is therefore set for each channel 14, 15 and 16 as a normal gain permanently possible, maximum gain, which does not overload the relevant amplifier and in which a stable operation is ensured.
  • the hearing aid according to the invention comprises as a special feature a per se known sound detector device 19 for detecting sounds, in particular consonants, in a speech signal contained in the input signal. If a specific sound, for example a consonant, has been detected, a signal in this regard is forwarded to a gain control unit 20.
  • the gain control unit 20 By means of the gain control unit 20, the amplification exerted by the signal processing units 14, 15 and 16 in the individual channels is adapted to the detected sound. It is possible that the gain briefly, in particular for the duration of the detected sound, exceeds the "normal" and in particular the permanently maximum possible gain.
  • FIG. 3 explains the procedure described again with reference to the indicated gain V as a function of the signal frequency f.
  • FIG. 3 is based on a hearing aid with 8 frequency bands (channels) K1 to K8. It is a technically conditional, partly dependent on individual factors of the hearing aid wearer dependent characteristic of a maximum gain V max on the frequency f visible.
  • the amplifications V1 to V8 are set in the exemplary embodiment, which form the characteristic of the "normal" gain V N over the frequency f. It is always V N ⁇ V Max , so that a stable operation is always guaranteed and the amplifier of the hearing aid is not overloaded.
  • the gains V6 to V8 set in the channels K6 to K8 are no longer intended to compensate completely of the user's individual hearing loss.
  • the gain briefly exceeds, in particular for the duration of the sound, the normal gain V N or the maximum gain V Max . This is indicated in FIG. 6 for the channel K6, for which a short-term gain (for a short time) assumes the value V6 '.
  • the amount at which the short-term gain V6 'exceeds the normal gain V N may be dependent on various factors. In particular, it depends on the signal strength of the detected sound in the input signal. On the other hand, it is limited to a maximum value due to technical restrictions.
  • the maximum value of the short-time gain is a certain amount, eg 5 dB, above the permanently achievable, maximum gain V Max . This measure is advantageous, in particular channel-dependent, adjustable by programming the hearing aid in question.
  • the duration of the short-term gain is adapted to the duration of the detected sound.
  • the duration of the short-term gain essentially corresponds to the duration of the detected sound.
  • the speech intelligibility especially for large hearing loss, increased without increasing the feedback tendency. It can help to avoid a frequency transposition which is often undesirable because of its serious disadvantages in the case of large hearing losses.

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  • Engineering & Computer Science (AREA)
  • Physics & Mathematics (AREA)
  • Signal Processing (AREA)
  • Health & Medical Sciences (AREA)
  • Acoustics & Sound (AREA)
  • Audiology, Speech & Language Pathology (AREA)
  • Human Computer Interaction (AREA)
  • Computational Linguistics (AREA)
  • Multimedia (AREA)
  • General Health & Medical Sciences (AREA)
  • Neurosurgery (AREA)
  • Otolaryngology (AREA)
  • Circuit For Audible Band Transducer (AREA)
  • Tone Control, Compression And Expansion, Limiting Amplitude (AREA)

Description

Die Erfindung betrifft ein Hörhilfegerät gemäß dem Oberbegriff des Anspruchs 1 sowie ein Verfahren zum Betrieb eines Hörhilfegerätes gemäß dem Oberbegriff des Anspruchs 5.The invention relates to a hearing aid according to the preamble of claim 1 and to a method for operating a hearing aid according to the preamble of claim 5.

Die US 2011/004 468 A1 offenbart ein Hörhilfegerät gemäß dem Oberbegriff des Anspruchs 1 sowie ein Verfahren zum Betrieb eines Hörhilfegerätes gemäß dem Oberbegriff des Anspruchs 5.The US 2011/004 468 A1 discloses a hearing aid according to the preamble of claim 1 and a method for operating a hearing aid according to the preamble of claim 5.

Die EP 1 175 125 A2 betrifft eine adaptive Verstärkungsgrad- und Filterschaltung und offenbart eine adaptive Filterschaltung für die Verwendung in einem Hörgerät durch eine Person mit einer einen vorbestimmten Frequenzbereich umfassenden Hörbeeinträchtigung. Die Filterschaltung umfasst ein variables Filter und einen Verstärker, die eine Bandbreite haben, die dem vorbestimmten Frequenzbereich der Hörbeeinträchtigung entspricht.The EP 1 175 125 A2 relates to an adaptive gain and filter circuit and discloses an adaptive filter circuit for use in a hearing aid by a person having a hearing impairment comprising a predetermined frequency range. The filter circuit comprises a variable filter and an amplifier having a bandwidth corresponding to the predetermined frequency range of the hearing impairment.

Die DE 10 2009 032 238 A1 offenbart ein Verfahren zur Kontrolle der Anpassung eines Hörgerätes, das eine Filterbank zur spektral selektiven Verstärkung und Dynamikkompression von Audiosignalen aufweist, an ein Hördefizit eines Hörgeräteträgers. Diese Druckschrift beschreibt eine mittels des Hörgerätes maximal mögliche Verstärkung in den oberen Frequenzbändern sowie ein Rückkopplungspfeifen, das bei ungünstigen Konstruktionen oder bei Undichtigkeiten der Otoplastik schon bei geringen Verstärkungen einsetzt, die für eine ausreichende Verstärkung der frikativischen Energien zu gering sind.The DE 10 2009 032 238 A1 discloses a method of controlling the fitting of a hearing aid having a filter bank for spectrally selective amplification and dynamic compression of audio signals to a hearing deficit of a hearing aid wearer. This document describes a maximum possible by means of the hearing aid amplification in the upper frequency bands and a feedback whistle that uses in unfavorable constructions or leaks in the earmold even at low gains, which are too low for a sufficient amplification of frikativischen energies.

Der mit einem Hörhilfegerät maximal erreichbaren Verstärkung sind in der Regel durch die geforderte, geringe Größe der Geräte sowie den geringen Abstand zwischen Eingangswandler (insbesondere Mikrofon) und Ausgangswandler (insbesondere Hörer) enge Grenzen gesetzt. Bei einer zu hohen Verstärkung tritt insbesondere das extrem störende Feedback-Pfeifen auf. Die Feedback-Neigung eines Hörhilfegerätes ist frequenzabhängig und betrifft zumeist den oberen Bereich des von einem Hörhilfegerät übertragbaren Frequenzbereiches.The maximum achievable with a hearing aid gain are usually by the required, small size of the devices and the small distance between the input transducer (especially microphone) and output transducer (especially listener) set narrow limits. If the gain is too high, especially the extremely annoying feedback whistling occurs. The feedback tendency of a hearing aid is frequency-dependent and usually affects the upper range of the transferable from a hearing aid frequency range.

Bei vielen Hörgeschädigten stellt sich daher das Problem, dass bestimmte Frequenzbereiche selbst bei einer Versorgung mit einem Hörhilfegerät nicht mehr ausreichend wahrgenommen werden können. Bei der Wahrnehmung von Sprache führt dies dazu, dass bestimmte Laute, insbesondere Konsonanten, die in Bezug auf Sprache Signalanteile im hochfrequenten Signalspektrum aufweisen, nicht richtig verstanden werden. Davon sind insbesondere sogenannte Frikative, die nach ihrer Artikulationsart benannten sind, betroffen, beispielsweise "s", "sch", "v" oder "z".For many hearing-impaired persons, therefore, the problem arises that certain frequency ranges can no longer be adequately perceived even when supplied with a hearing aid. In the perception of speech, this means that certain sounds, especially consonants that have signal components in the high-frequency signal spectrum with respect to speech, are not understood correctly. Of these, in particular so-called fricatives, which are named according to their type of articulation, are affected, for example "s", "sch", "v" or "z".

Zum Ausgleich der genannten Hörverluste ist es bekannt, die betroffenen Frequenzbereiche in andere Frequenzbereiche zu transponieren, die besser wahrgenommen werden können. Bei der Durchführung einer derartigen Frequenztransposition unterscheidet man hauptsächlich zwei Verfahren: bei der Frequenzverschiebung wird ein Frequenzbereich (z.B. 4 kHz - 6 kHz) in einen anderen Frequenzbereich (z.B. 2 KHz - 4 kHz) verschoben. Im Unterschied hierzu ergibt sich bei der Kompression die Frequenz des Ausgangssignals durch Multiplikation der Frequenz des Eingangssignals mit einem Faktor (z.B. 0,75). Häufig erfolgt eine Frequenzkompression jedoch nicht bei 0 Hz beginnend, sondern erst oberhalb einer bestimmten (Kniepunkt) Frequenz, z.B. 2 kHz.To compensate for the said hearing losses, it is known to transpose the affected frequency ranges in other frequency ranges that can be better perceived. In performing such a frequency transposition, there are mainly two methods: in frequency shifting, one frequency range (e.g., 4 kHz - 6 kHz) is shifted to another frequency range (e.g., 2 KHz - 4 kHz). In contrast, in compression, the frequency of the output signal is multiplied by the frequency of the input signal by a factor (e.g., 0.75). Frequently, however, frequency compression does not begin at 0 Hz, but only above a certain (knee-point) frequency, e.g. 2 kHz.

Ein Verfahren zur Frequenztransposition in einem Hörhilfegerät sowie ein Hörhilfegerät zur Durchführung einer Frequenztransposition sind aus der Druckschrift EP 1 441 562 A2 bekannt.A method for frequency transposition in a hearing aid device and a hearing aid device for carrying out a frequency transposition are disclosed in the document EP 1 441 562 A2 known.

Die Frequenztransposition hat zwei wesentliche Nachteile: einerseits spektral die Zerstörung der ursprünglichen spektralen Zusammensetzung bestimmter Konsonanten und anderer Laute und andererseits - die Wahrnehmung betreffend - wird die Fähigkeit, zwischen unterschiedlichen Frikativen zu unterscheiden, wesentlich verschlechtert.The frequency transposition has two major disadvantages: on the one hand spectrally the destruction of the original spectral The composition of certain consonants and other sounds, and on the other hand, regarding perception, significantly worsens the ability to differentiate between different sounds.

Aus dem Stand der Technik sind Verfahren zur Sprachsignalverarbeitung bekannt, durch die Vokale oder Konsonanten in einem Sprachsignal erkannt werden können. Beispielsweise offenbart die Druckschrift DE 691 05 154 T2 ein derartiges Verfahren, bei dem ein Sprachsignalspektrum analysiert wird zur Bestimmung von Spitzen- und Mittelwerten, die zum Erkennen von Vokalen und Konsonanten mit bestimmten Schwellenwerten verglichen werden.Methods for speech signal processing are known from the prior art, by which vowels or consonants can be recognized in a speech signal. For example, the document discloses DE 691 05 154 T2 such a method in which a speech signal spectrum is analyzed to determine peak and mean values that are compared to certain thresholds to detect vowels and consonants.

Auch aus der Druckschrift US 2009/0 112 594 A1 ist ein Verfahren bekannt, bei dem auf Grundlage akustischer Modelle zwischen vor- und nachvokalischen Konsonanten unterschieden wird.Also from the publication US 2009/0 112 594 A1 For example, a method is known in which a distinction is made between pre- and post-vocal consonants on the basis of acoustic models.

Aus der Offenlegungsschrift DE 103 08 483 A1 ist ein Verfahren zur automatischen Verstärkungseinstellung bei einem Hörhilfegerät bekannt, bei dem während des Betriebes ein Sprachsignalpegel sowie ein Störsignalpegel in mehreren Frequenzbändern eines Eingangssignals ermittelt wird. Es erfolgt eine automatische Einstellung der Verstärkung in Abhängigkeit von der ermittelten Signalpegel und der Signalfrequenz. Dabei werden Verstärkungsparameter unter Einbeziehung eines Lautheitsmodells sowie eines Sprachverständlichkeitsmodells ermittelt.From the publication DE 103 08 483 A1 a method for automatic gain adjustment in a hearing aid is known in which a speech signal level and a noise level is determined in several frequency bands of an input signal during operation. There is an automatic adjustment of the gain as a function of the detected signal level and the signal frequency. In this case, gain parameters are determined by including a loudness model and a speech intelligibility model.

Aus der WO 00/05923 ist eine Hörhilfe mit verbesserter Sprachverständlichkeit durch frequenzselektive Signalverarbeitung sowie ein Verfahren zum Betrieb einer derartigen Hörhilfe bekannt.From the WO 00/05923 is a hearing aid with improved speech intelligibility by frequency-selective signal processing and a method for operating such a hearing aid known.

Aufgabe der vorliegenden Erfindung ist es, das Verstehen von Sprache bei Hörverlusten, bei denen bestimmte Frequenzbereiche selbst bei hoher Lautstärke nicht mehr wahrgenommen werden können, zu verbessern.Object of the present invention is to understand the language of hearing loss, in which certain frequency ranges are no longer perceived even at high volume can improve.

Diese Aufgabe wird durch ein Hörhilfegerät gemäß Patentanspruch 1 und durch ein Verfahren zum Betrieb eines Hörhilfegerätes gemäß Patentanspruch 5 gelöst.This object is achieved by a hearing aid according to claim 1 and by a method for operating a hearing aid according to claim 5.

Die Erfindung schlägt gemäß einem ersten Aspekt ein Hörhilfegerät vor mit wenigstens

  • einem Eingangswandler zur Aufnahme eines Eingangssignals und Wandlung in ein elektrisches Eingangssignal;
  • einer Signalverarbeitungseinheit zur Verarbeitung und frequenzabhängigen Verstärkung des elektrischen Eingangssignals und zur Erzeugung eines elektrischen Ausgangssignals;
  • einem Ausgangswandler zur Wandlung des elektrischen Ausgangssignals in ein von einem Benutzer als akustisches Ausgangssignal wahrnehmbares Ausgangssignal;
  • eine Laut-Detektor-Einrichtung zum Erkennen von Lauten in einem in das Hörhilfegerät eingehenden Sprachsignal;
  • Mittel zur kurzzeitigen Anhebung der Verstärkung über eine normale Verstärkung hinaus für wenigstens einen Frequenzbereich, in dem ein erkannter Laut Signalanteile aufweist;
  • Mittel zur Einstellung der normalen Verstärkung eines elektrischen Eingangssignals in Abhängigkeit von der Signalfrequenz;
wobei
  • die Verstärkung wenigstens in einem bestimmten Frequenzbereich auf eine dauerhaft mögliche, maximale Verstärkung begrenzt ist;
  • die Verstärkung derart einstellbar ist, dass diese wenigstens im Wesentlichen für die Dauer des erkannten Lautes die normale Verstärkung oder die dauerhaft mögliche, maximale Verstärkung übersteigt;
  • die Verstärkung derart einstellbar ist, dass diese höchstens für eine Dauer, die unter einer Einschwingzeit eines Feedback-Pfeifens liegt, die normale Verstärkung oder die dauerhaft mögliche, maximale Verstärkung übersteigt.
The invention proposes according to a first aspect of a hearing aid before at least
  • an input transducer for receiving an input signal and converting it to an electrical input signal;
  • a signal processing unit for processing and frequency-dependent amplification of the electrical input signal and for generating an electrical output signal;
  • an output transducer for converting the electrical output signal into an output signal perceivable by a user as an acoustic output signal;
  • a sound detector means for detecting sounds in a voice signal input to the hearing aid;
  • Means for momentarily increasing the gain beyond a normal gain for at least one frequency range in which a detected sound has signal portions;
  • Means for adjusting the normal gain of an input electrical signal in response to the signal frequency;
in which
  • the gain is limited at least in a certain frequency range to a permanently possible maximum gain;
  • the gain is adjustable to exceed, for at least substantially the duration of the detected sound, the normal gain or the permanently possible maximum gain;
  • the gain is adjustable so that it exceeds the normal gain or the permanently possible, maximum gain at most for a duration that is less than a settling time of a feedback whistle.

Die Erfindung schlägt gemäß einem zweiten Aspekt ein Verfahren zum Betrieb eines Hörhilfegerätes vor mit wenigstens

  • einem Eingangswandler zur Aufnahme eines Eingangssignals und Wandlung in ein elektrisches Eingangssignal;
  • einer Signalverarbeitungseinheit zur Verarbeitung und frequenzabhängigen Verstärkung des elektrischen Eingangssignals und zur Erzeugung eines elektrischen Ausgangssignals;
  • einem Ausgangswandler zur Wandlung des elektrischen Ausgangssignals in ein von einem Benutzer als akustisches Ausgangssignal wahrnehmbares Ausgangssignal;
wobei
  • Laute in einem in das Hörhilfegerät eingehenden Sprachsignal erkannt werden;
  • die Verstärkung kurzzeitig über eine normale Verstärkung hinaus angehoben wird für wenigstens einen Frequenzbereich, in dem ein erkannter Laut Signalanteile aufweist;
  • die normalen Verstärkung eines elektrischen Eingangssignals in Abhängigkeit von der Signalfrequenz eingestellt wird;
  • die Verstärkung wenigstens in einem bestimmten Frequenzbereich auf eine dauerhaft mögliche, maximale Verstärkung begrenzt wird;
  • die Verstärkung wenigstens im Wesentlichen für die Dauer des erkannten Lautes die normale Verstärkung oder die dauerhaft mögliche, maximale Verstärkung übersteigt;
  • die Verstärkung höchstens für eine Dauer, die unter einer Einschwingzeit eines Feedback-Pfeifens liegt, die normale Verstärkung oder die dauerhaft mögliche, maximale Verstärkung übersteigt.
The invention proposes according to a second aspect, a method for operating a hearing aid before at least
  • an input transducer for receiving an input signal and converting it to an electrical input signal;
  • a signal processing unit for processing and frequency-dependent amplification of the electrical input signal and for generating an electrical output signal;
  • an output transducer for converting the electrical output signal into an output signal perceivable by a user as an acoustic output signal;
in which
  • Sounds are detected in a voice signal entering the hearing aid;
  • the gain is briefly raised above a normal gain for at least one frequency range in which a detected sound has signal components;
  • the normal gain of an electrical input signal is adjusted in dependence on the signal frequency;
  • the gain is limited to a permanently possible, maximum gain at least in a certain frequency range;
  • the gain exceeds, for at least substantially the duration of the detected sound, the normal gain or the permanently possible maximum gain;
  • the gain is at most for a duration that is less than a settling time of a feedback whistle that exceeds normal gain or permanently possible maximum gain.

Unter einem Hörhilfegerät gemäß der Erfindung wird jedes Gerät verstanden, welches ein von einem Benutzer als akustisches Signal wahrnehmbares Ausgangssignal liefert oder dazu beiträgt, ein solches Ausgangssignal zu liefern, und das über Mittel verfügt, die zum Ausgleich eines individuellen Hörverlustes des Benutzers dienen oder beitragen. Insbesondere handelt es sich dabei um ein am Körper oder am Kopf, insbesondere am oder im Ohr, tragbares sowie ganz oder teilweise implantierbares Hörgerät. Es sind jedoch auch solche Geräte mit umfasst, deren vorwiegender Zweck nicht im Ausgleich eines Hörverlustes liegt, beispielsweise Geräte der Unterhaltungselektronik (Fernsehgeräte, Hifi-Anlagen, MP3-Player etc), oder Kommunikationsgeräte (Mobiltelefone, PDAs, Headsets etc), die jedoch über Mittel zum Ausgleich eines individuellen Hörverlustes verfügen.A hearing aid device according to the invention is understood to mean any device which provides or helps to provide an output signal perceptible by a user as an audible signal, and which has means which help or compensate for an individual hearing loss of the user. In particular, acts this is a hearing aid which can be worn on the body or on the head, in particular on or in the ear, and which can be implanted in whole or in part. However, such devices are also included, whose primary purpose is not to compensate for hearing loss, such as consumer electronics (TVs, hi-fi systems, MP3 players, etc.), or communication devices (mobile phones, PDAs, headsets etc), but over Have means to compensate for an individual hearing loss.

Ein Hörhilfegerät umfasst in der Regel einen Eingangswandler zur Aufnahme eines Eingangssignals. Der Eingangswandler ist beispielsweise als Mikrofon ausgebildet, das ein akustisches Signal aufnimmt und in ein elektrisches Eingangssignal wandelt. Als Eingangswandler kommen jedoch auch Einheiten in Betracht, die eine Spule oder eine Antenne aufweisen und die ein elektromagnetisches Signal aufnehmen und in ein elektrisches Eingangssignal wandeln. Ferner umfasst ein Hörhilfegerät üblicherweise eine Signalverarbeitungseinheit zur Verarbeitung und frequenzabhängigen Verstärkung des elektrischen Eingangssignals. Zur Signalverarbeitung im Hörhilfegerät dient ein vorzugsweise digitaler Signalprozessor (DSP), dessen Arbeitsweise mittels auf das Hörhilfegerät übertragbarer Programme oder Parameter beeinflussbar ist. Dadurch lässt sich die Arbeitsweise der Signalverarbeitungseinheit sowohl an den individuellen Hörverlust eines Hörhilfegeräteträgers als auch an die aktuelle Hörsituation anpassen, in der das Hörhilfegerät gerade betrieben wird. Das so veränderte elektrische Eingangssignal ist schließlich einem Ausgangswandler zugeführt. Dieser ist in der Regel als Hörer ausgebildet, der das elektrische Ausgangssignal in ein akustisches Signal wandelt. Jedoch sind auch hier andere Ausführungsformen möglich, z.B. ein implantierbarer Ausgangswandler, der direkt mit einem Gehörknöchelchen verbunden ist und dieses zu Schwingungen anregt.A hearing aid generally includes an input transducer for receiving an input signal. The input transducer is designed, for example, as a microphone which picks up an acoustic signal and converts it into an electrical input signal. However, as input transducers are also units into consideration, which have a coil or an antenna and receive an electromagnetic signal and convert it into an electrical input signal. Furthermore, a hearing aid usually includes a signal processing unit for processing and frequency-dependent amplification of the electrical input signal. For signal processing in the hearing aid, a preferably digital signal processor (DSP) is used, whose operation can be influenced by means of programs or parameters which can be transmitted to the hearing aid. As a result, the mode of operation of the signal processing unit can be adapted both to the individual hearing loss of a hearing aid wearer and to the current hearing situation in which the hearing aid is currently being operated. The thus changed electrical input signal is finally fed to an output transducer. This is usually designed as a handset, which converts the electrical output signal into an acoustic signal. However, other embodiments are also possible here, e.g. an implantable output transducer that connects directly to an auditory ossicle and causes it to vibrate.

Bei einem Hörhilfegerät wird die Verstärkung so eingestellt, dass dadurch der individuelle Hörverlust eines Benutzers ausgeglichen wird. Die hierzu erforderliche Verstärkung ist gewöhnlich abhängig von der Signalfrequenz. Der maximal einstellbaren Verstärkung sind jedoch physikalische Grenzen gesetzt, die einerseits aus den technischen Möglichkeiten des verwendeten Hörhilfegerätes resultieren und andererseits der Vermeidung von Rückkopplungen dienen. Rückkopplungen treten zumeist im oberen, von einem Hörhilfegerät übertragbaren Frequenzbereich auf. Unglücklicherweise haben viele Hörhilfegeräteträger gerade in diesem Frequenzbereich jedoch einen großen Hörverlust, zu dessen Ausgleich eine hohe Verstärkung erforderlich wäre. Um Rückkopplungen zu vermeiden, wird daher die Verstärkung in einem betreffenden Frequenzbereich so eingestellt, dass das betreffende Hörhilfegerät noch stabil betrieben werden kann, auch wenn damit die zum Ausgleich des individuellen Hörverlustes erforderliche Verstärkung nicht mehr erreicht werden kann. Weiterhin sind bei den sogenannten Power-Geräten, die eine sehr hohe Verstärkung unter Vermeidung akustischer Rückkopplungen ermöglichen, der Verstärkung nach oben durch die mechanische Stabilität der Geräte Grenzen gesetzt.In a hearing aid, the gain is adjusted to compensate for a user's individual hearing loss becomes. The gain required for this is usually dependent on the signal frequency. However, the maximum adjustable gain physical limits are set, on the one hand result from the technical possibilities of the hearing aid used and on the other hand serve to avoid feedback. Feedbacks usually occur in the upper frequency range that can be transmitted by a hearing aid. Unfortunately, many hearing aid wearers have a large amount of hearing loss in this frequency range, which would require a high gain to compensate. In order to avoid feedback, therefore, the gain in a respective frequency range is set so that the hearing aid in question can still be operated stably, even if it can no longer be achieved to compensate for the individual hearing loss gain. Furthermore, in the so-called power devices that allow a very high gain while avoiding acoustic feedback, the gain is set up by the mechanical stability of the devices limits.

Gemäß der Erfindung verfügt das Hörhilfegerät neben den üblichen Komponenten (Eingangswandler, Signalverarbeitungseinheit, Ausgangswandler) über eine Laut-Detektor-Einrichtung zum Erkennen von Lauten, insbesondere von Konsonanten, in einem in das Hörhilfegerät eingehenden Sprachsignal.According to the invention, the hearing aid has, in addition to the usual components (input transducer, signal processing unit, output transducer) via a sound detector device for detecting sounds, in particular consonants, in a speech signal incoming to the hearing aid.

Ein Laut ist allgemein ein Geräusch oder ein Klang, hervorgerufen durch die menschliche oder tierische Stimme. In der allgemeinen Sprachwissenschaft ist ein Laut im engeren Sinn eine definierte, mit dem Strom des Atems (Phonationsstrom) bei bestimmter Stellung der Sprechwerkzeuge hervorgebrachte Schallwelle. Die Erzeugung und Wahrnehmung von Lauten ist Gegenstand der Phonetik. Ein Sprachlaut bzw. Phon wird dort als kleinste phonetische Einheit der gesprochenen Sprache verstanden.A sound is generally a sound or sound produced by the human or animal voice. In general linguistics, a sound in the narrower sense is a defined sound wave produced by the flow of the breath (phonation current) at a certain position of the speech tools. The generation and perception of sounds is the subject of phonetics. A phoneme or phon is understood as the smallest phonetic unit of the spoken language.

Unter einem Konsonant im Sinne der Erfindung wird allgemein ein Laut verstanden, dessen Artikulation eine Verengung des Stimmtraktes beinhaltet, so dass der Atemluftstrom ganz oder teilweise blockiert wird und es zu hörbaren Turbulenzen (Luftwirbelungen) kommt. Konsonanten sind Hemmnis überwindende Laute. Insbesondere sind Konsonanten im Sinne der Erfindung nicht auf die Konsonantenbuchstaben (B, C, D, F etc) beschränkt.Under a consonant in the context of the invention is general understood a sound whose articulation includes a narrowing of the vocal tract, so that the respiratory air flow is completely or partially blocked and it comes to audible turbulence (air turbulence). Consonants are inhibitor overcoming sounds. In particular, consonants within the meaning of the invention are not limited to the consonant letters (B, C, D, F, etc.).

Die Erfindung sieht nun vor, bei einem erkannten Laut, insbesondere einem Konsonant oder Frikativ, der Signalanteile in einem Frequenzbereich aufweist, in dem die zum Ausgleich des individuellen Hörverlustes erforderliche Verstärkung nicht mehr dauerhaft erreicht werden kann, kurzzeitig, insbesondere für die Dauer des Lautes, die Verstärkung über die dauerhaft mögliche Verstärkung hinaus zu erhöhen. Dadurch ist es dem Hörhilfegeräteträger möglich, den Laut besser wahrzunehmen und damit insgesamt Sprache besser zu verstehen.The invention now provides, in a recognized sound, in particular a consonant or fricative, the signal components in a frequency range in which the necessary to compensate for the individual hearing loss gain can not be achieved permanently, briefly, especially for the duration of the sound, to increase the gain beyond the permanently possible gain. This makes it possible for the hearing aid wearer to better perceive the sound and thus better understand the overall language.

Im Zusammenhang mit der Erfindung ist es unerheblich, ob die gewünschte Verstärkung nicht dauerhaft erreicht werden kann, weil dies die dauerhaft mögliche, maximale Ausgangsleistung des Endverstärkers in dem betreffenden Frequenzbereich überschreiten würde, oder ob die Verstärkung zur Vermeidung von Feedback zur Wahrung der mechanischen Stabilität des betreffenden Gerätes begrenzt wurde. Bezüglich des Endverstärkers ist es nämlich möglich, die Ausgangsleistung kurzzeitig über die dauerhaft mögliche maximale Ausgangsleistung zu erhöhen, ohne dass hierdurch ein Schaden verursacht wird. Auch bezüglich der Feedback-Problematik oder der mechanischen Stabilität ist eine kurzzeitige Überschreitung der dauerhaft maximal zulässigen Verstärkung unproblematisch, da z.B. das unerwünschte Feedback-Pfeifen eine gewisse Einschwingzeit benötigt, ehe es sich störend bemerkbar macht. Die Dauer eines Lautes liegt jedoch unter dieser Einschwingzeit.In the context of the invention, it is irrelevant whether the desired gain can not be achieved permanently, because this would exceed the permanently possible, maximum output power of the power amplifier in the relevant frequency range, or if the gain to avoid feedback to maintain the mechanical stability of the was limited. With respect to the power amplifier, it is possible to increase the output power for a short time over the permanently possible maximum output power, without this causing any damage. Also with regard to the feedback problem or the mechanical stability, a short-term exceeding of the permanently maximum permissible amplification is unproblematic, since e.g. the unwanted feedback whistling needs a certain settling time before it makes itself disturbing. The duration of a sound, however, is below this settling time.

Bei einer bevorzugten Ausführungsform der Erfindung ist eine Aufspaltung des elektrischen Eingangssignals in mehrere parallele Frequenzbänder (Kanäle) vorgesehen und die Signalverarbeitung im Hörhilfegerät in der Signalverarbeitungseinheit erfolgt zumindest teilweise parallel in den einzelnen Frequenzbändern. Vorteilhaft wird dann in Abhängigkeit von einem erkannten Laut die Verstärkung wenigstens für ein bestimmtes Frequenzband über die normale Verstärkung hinaus angehoben, wenn die gewünschte Verstärkung aus den bereits genannten Gründen nicht dauerhaft erreichbar ist und der erkannte Laut Signalanteile in dem betreffenden Frequenzband aufweist.In a preferred embodiment of the invention, a splitting of the electrical input signal into a plurality of parallel frequency bands (channels) is provided and the signal processing in the hearing aid in the signal processing unit is at least partially parallel in the individual frequency bands. Advantageously, in response to a detected sound, the gain is then raised beyond the normal gain for at least one particular frequency band if the desired gain is not permanently achievable for the reasons already stated and the detected sound has signal components in the respective frequency band.

Die Erfindung bietet den Vorteil, dass - anders als bei einer Frequenzkompression - die Klarheit von Sprache nicht in dem Maße beeinträchtigt wird.The invention offers the advantage that, unlike frequency compression, the clarity of speech is not compromised to any extent.

Die Erfindung wird nachfolgend anhand von Ausführungsbeispielen näher erläutert. Dabei zeigen:

Figur 1
ein Hörhilfegerät gemäß dem Stand der Technik im stark vereinfachten Blockschaltbild,
Figur 2
ein Blockschaltbild zur Einstellung der Verstärkung in Abhängigkeit von einem erkannten Laut und
Figur 3
ein Diagramm bezüglich einer gemäß der Erfindung eingestellten Verstärkung in Abhängigkeit von der Signalfrequenz.
The invention will be explained in more detail with reference to embodiments. Showing:
FIG. 1
a hearing aid according to the prior art in a highly simplified block diagram,
FIG. 2
a block diagram for adjusting the gain in response to a detected sound and
FIG. 3
a diagram relating to a gain set according to the invention as a function of the signal frequency.

Figur 1 zeigt im stark vereinfachten Blockschaltbild den Aufbau eines Hörhilfegerätes nach dem Stand der Technik. Hörhilfegeräte besitzen prinzipiell als wesentliche Komponenten einen oder mehrere Eingangswandler, einen Verstärker und einen Ausgangswandler. Der Eingangswandler ist in der Regel ein Schallempfänger, z. B. ein Mikrofon, oder ein elektromagnetischer Empfänger, z. B. eine Induktionsspule. Der Ausgangswandler ist meist als elektroakustischer Wandler, z. B. Miniaturlautsprecher bzw. Hörer, oder als elektromechanischer Wandler, z. B. Knochenleitungshörer, realisiert. Der Verstärker ist üblicherweise in eine Signalverarbeitungseinheit integriert. Dieser prinzipielle Aufbau ist in Figur 2 am Beispiel eines Hinter-dem-Ohr-Hörgerätes 1 dargestellt. In ein Hörgerätegehäuse 2 zum Tragen hinter dem Ohr sind zwei Mikrofone 3 und 4 zur Aufnahme des Schalls aus der Umgebung eingebaut. Eine Signalverarbeitungseinheit 5, die ebenfalls in das Hörgerätegehäuse 2 integriert ist, verarbeitet die Mikrofonsignale und verstärkt sie. Das Ausgangssignal der Signalverarbeitungseinheit 5 wird an einen Lautsprecher bzw. Hörer 6 übertragen, der ein akustisches Signal ausgibt. Der Schall wird gegebenenfalls über einen Schallschlauch, der mit einer Otoplastik im Gehörgang fixiert ist, zum Trommelfell des Hörgeräteträgers übertragen. Die Energieversorgung des Hörgerätes und insbesondere die der Signalverarbeitungseinheit 5 erfolgt durch eine ebenfalls ins Hörgerätegehäuse 2 integrierte Batterie 7. FIG. 1 shows in a simplified block diagram the structure of a hearing aid according to the prior art. Hearing aids have in principle as essential components one or more input transducers, an amplifier and an output transducer. The input transducer is usually a sound receiver, z. As a microphone, or an electromagnetic receiver, for. B. an induction coil. The output transducer is usually used as an electroacoustic transducer, z. As miniature speaker or handset, or as an electromechanical transducer, z. B. bone conduction, realized. The amplifier is usually integrated in a signal processing unit. This basic structure is in FIG. 2 Exemplary a behind-the-ear hearing aid 1 shown. In a hearing aid housing 2 for carrying behind the ear two microphones 3 and 4 are installed for receiving the sound from the environment. A signal processing unit 5, which is also integrated into the hearing aid housing 2, processes the microphone signals and amplifies them. The output signal of the signal processing unit 5 is transmitted to a loudspeaker or earpiece 6, which outputs an acoustic signal. If necessary, the sound is transmitted to the eardrum of the hearing aid wearer via a sound tube, which is fixed in the auditory canal with an earmold. The power supply of the hearing device and in particular of the signal processing unit 5 is effected by a likewise integrated into the hearing aid housing 2 battery. 7

Figur 2 zeigt im stark vereinfachten Blockschaltbild, wie aus einem elektrischen Eingangssignal ES, welches ggf. ein Sprachsignal enthält, ein elektrisches Ausgangssignal AS erzeugt wird. Hierzu wird das von einem Mikrofon 12 aufgenommene akustische Eingangssignal zunächst in ein elektrisches Eingangssignal ES gewandelt und einer Filterbank 13 zugeführt. Die Filterbank 13 bewirkt eine Aufspaltung des elektrischen Eingangssignals ES in mehrere (im Ausführungsbeispiel drei) parallele Kanäle. Die weitere Signalverarbeitung zum Ausgleich des individuellen Hörverlustes eines Benutzers erfolgt anschließend parallel in den drei Kanälen, insbesondere in den Signalverarbeitungseinheiten 14, 15 und 16, bevor die verarbeiteten Signale in einem Summierer 17 wieder zusammengeführt werden. Ein Hörer 18 wandelt schließlich das resultierende elektrische Ausgangssignal AS in ein akustisches Ausgangssignal. FIG. 2 shows in a simplified block diagram how an electrical output signal AS is generated from an electrical input signal ES, which optionally contains a speech signal. For this purpose, the acoustic input signal recorded by a microphone 12 is first converted into an electrical input signal ES and fed to a filter bank 13. The filter bank 13 effects a splitting of the electrical input signal ES into a plurality of (in the exemplary embodiment three) parallel channels. The further signal processing to compensate for the individual hearing loss of a user is then carried out in parallel in the three channels, in particular in the signal processing units 14, 15 and 16, before the processed signals are combined in a summer 17 again. A receiver 18 finally converts the resulting electrical output signal AS into an acoustic output signal.

Für jeden Kanal ist durch eine entsprechende Einstellung von Parametern eine Verstärkung eingestellt, durch die der individuelle Hörverlust des Benutzers ausgeglichen wird. In Abhängigkeit von dem individuellen Grad des Hörverlustes ist jedoch häufig kein vollständiger Ausgleich des Hörverlustes möglich. Vielmehr muss die Verstärkung unter Umständen auf ein Maximalmaß reduziert werden, um eine Überlastung des von der betreffenden Signalverarbeitungseinheit umfassten Verstärkers zu verhindern oder das Auftreten von Feedback zu vermeiden. Es wird daher für jeden Kanal 14, 15 bzw. 16 als normale Verstärkung eine dauerhaft mögliche, maximale Verstärkung eingestellt, die den betreffenden Verstärker nicht überlastet und bei der ein stabiler Betrieb gewährleistet ist.For each channel, an appropriate setting of parameters sets a gain that compensates for the user's individual hearing loss. However, depending on the individual degree of hearing loss, complete compensation of the hearing loss is often impossible. Rather, the gain may need to a maximum amount can be reduced in order to prevent overloading of the amplifier included in the signal processing unit concerned or to avoid the occurrence of feedback. It is therefore set for each channel 14, 15 and 16 as a normal gain permanently possible, maximum gain, which does not overload the relevant amplifier and in which a stable operation is ensured.

Das Hörhilfegerät gemäß der Erfindung umfasst als Besonderheit eine an sich bekannte Laut-Detektor-Einrichtung 19 zum Erkennen von Lauten, insbesondere Konsonanten, in einem in dem Eingangssignal enthaltenen Sprachsignal. Wurde ein bestimmter Laut, beispielsweise ein Konsonant, erkannt, so wird ein diesbezügliches Signal an eine Verstärkungssteuereinheit 20 weitergeleitet. Mittels der Verstärkungssteuereinheit 20 wird nun die von den Signalverarbeitungseinheiten 14, 15 und 16 in den einzelnen Kanälen ausgeübte Verstärkung an den erkannten Laut angepasst. Dabei ist es möglich, dass die Verstärkung kurzzeitig, insbesondere für die Dauer des erkannten Lautes, die "normale" und insbesondere auch die dauerhaft maximal mögliche Verstärkung übersteigt.The hearing aid according to the invention comprises as a special feature a per se known sound detector device 19 for detecting sounds, in particular consonants, in a speech signal contained in the input signal. If a specific sound, for example a consonant, has been detected, a signal in this regard is forwarded to a gain control unit 20. By means of the gain control unit 20, the amplification exerted by the signal processing units 14, 15 and 16 in the individual channels is adapted to the detected sound. It is possible that the gain briefly, in particular for the duration of the detected sound, exceeds the "normal" and in particular the permanently maximum possible gain.

Figur 3 erläutert die beschriebene Vorgehensweise nochmals anhand der aufgezeigten Verstärkung V in Abhängigkeit von der Signalfrequenz f. Dem Ausführungsbeispiel gemäß Figur 3 liegt ein Hörhilfegerät mit 8 Frequenzbändern (Kanälen) K1 bis K8 zugrunde. Es ist eine zum Teil technisch bedingte, zum Teil auch von individuellen Faktoren des betreffenden Hörhilfegeräteträgers abhängige Kennlinie einer maximalen Verstärkung VMax über der Frequenz f ersichtlich. Für die einzelnen Kanäle sind im Ausführungsbeispiel die Verstärkungen V1 bis V8 eingestellt, die die Kennlinie der "normalen" Verstärkung VN über der Frequenz f bilden. Es gilt stets VN ≤ VMax, so dass stets ein stabiler Betrieb gewährleistet ist und der Verstärker des Hörhilfegerätes nicht überlastet wird. Im Ausführungsbeispiel sollen die in den Kanälen K6 bis K8 eingestellten Verstärkungen V6 bis V8 nicht mehr zum vollständigen Ausgleich des individuellen Hörverlustes des Benutzers reichen. FIG. 3 explains the procedure described again with reference to the indicated gain V as a function of the signal frequency f. According to the embodiment FIG. 3 is based on a hearing aid with 8 frequency bands (channels) K1 to K8. It is a technically conditional, partly dependent on individual factors of the hearing aid wearer dependent characteristic of a maximum gain V max on the frequency f visible. For the individual channels, the amplifications V1 to V8 are set in the exemplary embodiment, which form the characteristic of the "normal" gain V N over the frequency f. It is always V N ≤ V Max , so that a stable operation is always guaranteed and the amplifier of the hearing aid is not overloaded. In the exemplary embodiment, the gains V6 to V8 set in the channels K6 to K8 are no longer intended to compensate completely of the user's individual hearing loss.

Gemäß der Erfindung ist nun vorgesehen, dass infolge eines erkannten Lautes die Verstärkung kurzzeitig, insbesondere für die Dauer des Lautes, die normale Verstärkung VN bzw. die maximale Verstärkung VMax übersteigt. Dies ist in Figur 6 für den Kanal K6 angedeutet, für den eine Kurzzeitverstärkung (kurzzeitig) den Wert V6' annimmt.According to the invention, it is now provided that, as a result of a detected sound, the gain briefly exceeds, in particular for the duration of the sound, the normal gain V N or the maximum gain V Max . This is indicated in FIG. 6 for the channel K6, for which a short-term gain (for a short time) assumes the value V6 '.

Die Höhe, mit der die Kurzzeitverstärkung V6' die normale Verstärkung VN übersteigt, kann von verschiedenen Faktoren abhängig sein. Insbesondere hängt sie ab von der Signalstärke des erkannten Lautes in dem Eingangssignal. Andererseits ist auch sie aufgrund technischer Restriktionen auf einen Maximalwert beschränkt. Vorteilhaft liegt der Maximalwert der Kurzzeitverstärkung um ein bestimmtes Maß, z.B. 5 dB, über der dauerhaft erreichbaren, maximalen Verstärkung VMax. Dieses Maß ist vorteilhaft, insbesondere auch kanalabhängig, durch Programmierung des betreffenden Hörhilfegerätes einstellbar.The amount at which the short-term gain V6 'exceeds the normal gain V N may be dependent on various factors. In particular, it depends on the signal strength of the detected sound in the input signal. On the other hand, it is limited to a maximum value due to technical restrictions. Advantageously, the maximum value of the short-time gain is a certain amount, eg 5 dB, above the permanently achievable, maximum gain V Max . This measure is advantageous, in particular channel-dependent, adjustable by programming the hearing aid in question.

Vorteilhaft ist die Dauer der Kurzzeitverstärkung an die Dauer des erkannten Lautes angepasst. Insbesondere entspricht die Dauer der Kurzzeitverstärkung im Wesentlichen der Dauer des erkannten Lautes.Advantageously, the duration of the short-term gain is adapted to the duration of the detected sound. In particular, the duration of the short-term gain essentially corresponds to the duration of the detected sound.

Durch die Erfindung wird die Sprachverständlichkeit, insbesondere bei großen Hörverlusten, erhöht, ohne dabei die Feedback-Neigung zu vergrößern. Sie kann dazu beitragen, eine wegen ihrer gravierenden Nachteile häufig nicht gewünschte Frequenztransposition bei großen Hörverlusten zu vermeiden.By the invention, the speech intelligibility, especially for large hearing loss, increased without increasing the feedback tendency. It can help to avoid a frequency transposition which is often undesirable because of its serious disadvantages in the case of large hearing losses.

Claims (8)

  1. Hearing aid (1; 11) having at least
    - an input converter (3, 4; 12) for acquiring an input signal and converting it into an electrical input signal (ES);
    - a signal processing unit (5; 14, 15, 16) for processing and amplifying (V, V1, V2, V3, V4, V5, V6, V7, V8) the electrical input signal (ES) on the basis of the frequency and for generating an electrical output signal (AS);
    - an output converter (6; 18) for converting the electrical output signal (AS) into an output signal which can be perceived by a user as an acoustic output signal;
    - a sound detector device (19) for detecting sounds in a voice signal entering the hearing aid (1; 11) ;
    - means (20) for briefly increasing (V6') the gain (V6) beyond a normal gain (VN) for at least one frequency range (K6) in which a detected sound has signal components;
    characterized by
    - means for setting the normal gain (VN) of an electrical input signal (ES) on the basis of the signal frequency (f);
    wherein
    - the gain (V, V1, ..., V8) is limited to a permanently possible maximum gain (VMax) at least in a particular frequency range (K1, ..., K8);
    - the gain (V, V1, ..., V8) can be set in such a manner that it exceeds the normal gain (VN) or the permanently possible maximum gain (VMax) at least substantially for the duration of the detected sound;
    - the gain (V, V1, ..., V8) can be set in such a manner that it exceeds the normal gain (VN) or the permanently possible maximum gain (VMax) at most for a duration which is shorter than a settling time of feedback whistling.
  2. Hearing aid (1; 11) according to Claim 1, wherein fricatives can be detected using the sound detector device (19).
  3. Hearing aid (1; 11) according to Claim 1 or 2, wherein the gain (V, V1, ..., V8) can be increased (V6') at least substantially for the duration of the detected sound.
  4. Hearing aid (1; 11) according to one of the preceding claims, wherein the electrical input signal (ES) is divided into a plurality of parallel frequency bands (K1, ..., K8) and the signal processing in the hearing aid (1; 11) is carried out in the signal processing unit (5; 14, 15, 16) at least partially in a parallel manner in the individual frequency bands (K1, ..., K8), and wherein the gain (V6) can be increased (V6') beyond the normal gain (VN) at least for one frequency band (K6) on the basis of the detected sound.
  5. Method for operating a hearing aid (1; 11) having at least
    - an input converter (3, 4; 12) for acquiring an input signal and converting it into an electrical input signal (ES);
    - a signal processing unit (5; 14, 15, 16) for processing and amplifying (V, V1, V2, V3, V4, V5, V6, V7, V8) the electrical input signal (ES) on the basis of the frequency and for generating an electrical output signal (AS);
    - an output converter (6; 18) for converting the electrical output signal (AS) into an output signal which can be perceived by a user as an acoustic output signal;
    wherein
    - sounds in a voice signal entering the hearing aid (1; 11) are detected;
    - the gain (V6) is briefly increased (V6') beyond a normal gain (VN) for at least one frequency range (K6) in which a detected sound has signal components;
    characterized in that
    - the normal gain (VN) of an electrical input signal (ES) is set on the basis of the signal frequency (f);
    - the gain (V1, ..., V8) is limited to a permanently possible maximum gain (VMax) at least in a particular frequency range (K1, ..., K8) ;
    - the gain (V1, ..., V8) exceeds the normal gain (VN) or the permanently possible maximum gain (VMax) at least substantially for the duration of the detected sound;
    - the gain (V1, ..., V8) exceeds the normal gain (VN) or the permanently possible maximum gain at most for a duration which is shorter than a settling time of feedback whistling.
  6. Method according to Claim 5, wherein fricatives are detected using the sound detector device (19).
  7. Method according to Claim 5 or 6, wherein the gain (V, V1, ..., V8) is increased (V6') at least substantially for the duration of the detected sound.
  8. Method according to one of Claims 5 to 7, wherein the electrical input signal (ES) is divided into a plurality of parallel frequency bands (K1, ..., K8) and the signal processing in the hearing aid (1; 11) is carried out in the signal processing unit (5; 14, 15, 16) at least partially in a parallel manner in the individual frequency bands (K1, ..., K8), and wherein the gain (V6) is increased (V6') beyond the normal gain (VN) at least for one frequency band (K6) on the basis of the detected sound.
EP12159057.4A 2011-03-31 2012-03-12 Hearing aid and method for operating the same Active EP2506602B1 (en)

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EP2506602A3 EP2506602A3 (en) 2015-06-10
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Family Cites Families (11)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5204906A (en) 1990-02-13 1993-04-20 Matsushita Electric Industrial Co., Ltd. Voice signal processing device
US5706352A (en) * 1993-04-07 1998-01-06 K/S Himpp Adaptive gain and filtering circuit for a sound reproduction system
US6434246B1 (en) * 1995-10-10 2002-08-13 Gn Resound As Apparatus and methods for combining audio compression and feedback cancellation in a hearing aid
US6768801B1 (en) 1998-07-24 2004-07-27 Siemens Aktiengesellschaft Hearing aid having improved speech intelligibility due to frequency-selective signal processing, and method for operating same
CA2492091C (en) * 2002-07-12 2009-04-28 Widex A/S Hearing aid and a method for enhancing speech intelligibility
DE10308483A1 (en) 2003-02-26 2004-09-09 Siemens Audiologische Technik Gmbh Method for automatic gain adjustment in a hearing aid and hearing aid
EP1333700A3 (en) 2003-03-06 2003-09-17 Phonak Ag Method for frequency transposition in a hearing device and such a hearing device
US7457741B2 (en) * 2004-03-30 2008-11-25 National Institute of Advnaced Industrial Science and Technology Device for transmitting speech information
US8015008B2 (en) 2007-10-31 2011-09-06 At&T Intellectual Property I, L.P. System and method of using acoustic models for automatic speech recognition which distinguish pre- and post-vocalic consonants
DE102009032238A1 (en) * 2008-12-30 2010-07-08 Forschungsgesellschaft für Arbeitsphysiologie und Arbeitsschutz e.V. Method for controlling adjustment of behind-the-ear hearing aid, involves spectrally filtering or selecting natural language element of test signal, where spectrum of test signal corresponds to spectral range of filter of filter bank
US8374877B2 (en) * 2009-01-29 2013-02-12 Panasonic Corporation Hearing aid and hearing-aid processing method

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DE102011006511A1 (en) 2012-10-04
EP2506602A3 (en) 2015-06-10
US20120250919A1 (en) 2012-10-04
DE102011006511B4 (en) 2016-07-14
DK2506602T3 (en) 2017-01-16
EP2506602A2 (en) 2012-10-03
US8811641B2 (en) 2014-08-19

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