EP2224752B1 - Device and method for reducing subsonic effects in hearing devices with active occlusion reduction - Google Patents

Device and method for reducing subsonic effects in hearing devices with active occlusion reduction Download PDF

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Publication number
EP2224752B1
EP2224752B1 EP09179426.3A EP09179426A EP2224752B1 EP 2224752 B1 EP2224752 B1 EP 2224752B1 EP 09179426 A EP09179426 A EP 09179426A EP 2224752 B1 EP2224752 B1 EP 2224752B1
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EP
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Prior art keywords
impact noise
occlusion reduction
hearing device
hearing
wearer
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German (de)
French (fr)
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EP2224752A1 (en
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Georg-Erwin Arndt
Dr. Volker Gebhardt
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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
    • H04R25/30—Monitoring or testing of hearing aids, e.g. functioning, settings, battery power
    • H04R25/305—Self-monitoring or self-testing
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R2460/00—Details of hearing devices, i.e. of ear- or headphones covered by H04R1/10 or H04R5/033 but not provided for in any of their subgroups, or of hearing aids covered by H04R25/00 but not provided for in any of its subgroups
    • H04R2460/05—Electronic compensation of the occlusion effect

Definitions

  • the invention relates to a specified in claim 1 hearing with an occlusion reduction unit and a specified in claim 10 method for operating a hearing.
  • An occlusion is a closure of the auditory canal which occurs when a hearing device, for example a hearing aid, is worn.
  • a hearing aid placed in the ear or an earmold piece of the hearing aid seals the auditory canal from the outside environment.
  • the hearing aid wearer perceives his own voice much louder and more distorted than usual.
  • the occlusion is perceived as very uncomfortable and complicates the perception of complex ambient sounds such as e.g. Language.
  • the occlusion effect is caused by vibrations of the wall of the ear canal. These vibrations are transmitted when speaking or chewing from the vocal cords or other sound sources via the so-called bone conduction. They vibrate the walls of the soft part of the ear canal, similar to a sound membrane. If the external auditory canal is e.g. is clogged by an earmold, these vibrations produce a relatively high sound pressure level, since the sound can not escape to the outside as in an open ear.
  • the sound pressure on the eardrum can be up to 30 dB higher than usual. The sound pressure increase depends on the frequency.
  • the occlusion effect is particularly noticeable at low frequencies below 1 kHz. At these frequencies, your own voice can be amplified by up to 20 dB.
  • occlusion reduction circuits are also provided known.
  • This loop filters are used, which are arranged in a feedback loop of the hearing aid. The output signal of the loop filter is thereby subtracted from the actual audio signal in order to achieve a damping of the frequencies that are increased by the occlusion.
  • compensation filters arranged in the transmission path of the audio signal are also used. Both the loop filter and the compensation filter are designed as static or adaptive filters.
  • the principle of antinoise is applied.
  • the counter sound is determined in a loop. All signals that are introduced into the loop from the outside are subject to filtering. Since, to extinguish an occlusion sound, the corresponding counter-sound must be output by the system phase-inverted, sufficient filtering of the occlusion sound is technically possible only over a limited frequency range.
  • Characteristic of the loop principle used in hearing aids is that signals in the frequency range of typical speech occlusion (100-1000 Hz) are reduced.
  • the stated object is achieved with the hearing device of independent claim 1 and the method for operating a hearing device of independent claim 10.
  • the invention claims a hearing device with an active occlusion reduction unit and with at least one first means by which an impact sound formed by steps of a wearer of the hearing device in the auditory canal of the wearer and / or effects on the occlusion reduction unit caused by the impact sound can be reduced. This offers the advantage that the impact sound artifacts audible to a wearer of the hearing device can be avoided.
  • the hearing device may be an in-the-ear hearing device or a behind-the-ear hearing device.
  • the effects may include harmonics generated in a listener and / or in an ear canal microphone. It is advantageous that these disturbances originating from nonlinearities can be avoided.
  • the first means may include an ear canal microphone and / or a handset with a harmonic distortion of less than 10% in the frequency range 20 to 50 Hz.
  • the first means may comprise two or more listeners, wherein a listener has a harmonic distortion of less than 10% in the frequency range 20 to 50 Hz.
  • the first means may comprise a footfall sound detection unit, the footfall sound level in the ear canal above a predefinable limit value and / or impact sound frequency pattern recognizes. As a result, impact sound can be reliably detected.
  • the impact sound recognition unit may preferably include an acceleration and / or vibration sensor.
  • the amplification of the active occlusion reduction unit can be adaptively reduced or the active occlusion reduction unit can be switched off.
  • the first means may comprise a control element with which the gain of the occlusion reduction unit is variable.
  • the invention also claims a method for operating a hearing device with an active occlusion reduction, wherein a footfall sound formed by steps of a wearer of the hearing device in the auditory canal of the wearer and / or effects on the occlusion reduction caused by the impact sound are reduced.
  • FIG. 1 schematically shows the structure of a hearing aid 1 with an occlusion reduction.
  • the hearing aid 1 has a transmission path for an audio signal S on. Along the transmission path several signal processing components are arranged, with the aid of which the audio signal S is processed.
  • the audio signal S is processed inter alia by means of filter and amplifier circuits in order to compensate for an individual hearing loss. Since signal processing in modern hearing aids generally takes place digitally, this is preferably a digital signal processing processor.
  • the audio signal S is emitted via a receiver R, usually an electroacoustic output transducer, as a sound signal in the ear canal.
  • the output transducer R is preferably designed as a speaker.
  • an analog signal coupled into the acoustic device must first be digitized.
  • an A / D (analog / digital) converter is provided at the beginning of the transmission path.
  • the digital audio signal must be converted back to an analog signal at the end of the transmission path by means of a D / A (digital / analog) converter before it can be output to the ear canal as an audible signal via the output transducer.
  • the D / A converter is already integrated in the output converter so that the electroacoustic output converter can be controlled directly digitally.
  • the electronic occlusion reduction unit 10 is typically implemented by a feedback loop that includes an ear canal microphone M and a filter element B.
  • the auditory canal microphone M detects the sound field currently prevailing in the ear canal, which comprises an occlusion signal OS, and generates an electrical output signal Z.
  • This signal passes through the loop filter B, in which it corresponds to the Filter settings is shaped.
  • the output signal T of the loop filter B is then subtracted from a signal X in the transmission path of the audio signal S.
  • the optionally present analog output signal Z of the auditory canal microphone M is still converted into a digital signal before it can be further processed digitally in the feedback loop.
  • the audio signal S usually undergoes a linear distortion.
  • a compensation filter C is used.
  • the filter C also called a predistortion filter, is typically arranged in the transmission path of the audio signal S between a signal processing device and the output transducer R.
  • an arbitrary acoustic input transducer arranged in the auditory canal can also be provided.
  • the output transducer R and the ear canal microphone M can be combined with each other.
  • the handset speaker R as a sound receiver, so that it can be dispensed with a separate ear canal microphone M with appropriate design of the circuit.
  • the impact sound TS When walking, a brief impulse arises at each occurrence of the foot, which is delivered to the human body. The body responds to this impulse with an impulse response, creating a damped vibration.
  • the so-called impact sound TS generated in this way passes via bone conduction into the ear canal and can be measured here.
  • FIG. 2 a measurement of footfall sound in the ear canal is shown for a single step.
  • the impact sound TS may vary in frequency and level. Typically, 2 to 5 wave trains per step were measured at a frequency of 20 to 40 Hz.
  • the impact sound level in the ear canal also depends on how tightly the ear canal is closed to the outside, for example by an in-the-ear hearing device or by the earmold of a behind-the-ear hearing device. When the ear canal is completely closed, extremely high levels of up to 130 dB signal power can result.
  • the low-frequency impact sound signal TS is from the microphone M of the occlusion reduction unit 10 in FIG. 1 recorded, filtered in the loop and delivered by the handset R.
  • a high input level leads to a distortion of the signal when using conventional microphones, which are currently used in hearing aids.
  • the listener R is forced by the occlusion reduction unit 10 to deliver such high levels, which in conventional hearing device listeners lead to a strong distortion of the listener R.
  • the transducer non-linearities thus lead to the formation of harmonics ("clinking"), which are perceived by a wearer of the hearing aid 1 extremely disturbing.
  • the unwanted effects (distortions, harmonics) of the impact sound can be reduced according to the invention to such an extent that they are no longer perceived as disturbing by a hearing aid wearer.
  • the first means may comprise various embodiments, a selection being described below.
  • a special microphone is used as the first means which, in contrast to microphones M typically used in hearing aids 1, has a significantly lower harmonic distortion in the range of the frequencies of 20 to 50 Hz with impact sound volume levels typically occurring in the ear canal having.
  • the harmonic distortion is well below 10%, as a total harmonic distortion greater than 10% is distracting to a hearing aid wearer.
  • the handset R is replaced by a special handset and thus forms the first means.
  • the particular handset has a significantly lower harmonic distortion in the range of the frequencies of 20 to 50 Hz with impact sound volume levels typically occurring in the ear canal.
  • the first means comprises two or more listeners. At least one listener serves as a bass handset, i. the listener can deliver low frequencies in the range of impact sound with low harmonic distortion.
  • the other handset (s) are for the remaining frequency range, i. the normal hearing aid frequency range designed.
  • FIG. 3 is a hearing aid 1 with an occlusion reduction unit 10 according to FIG. 1 equipped with a footfall sound detection unit 20 as the first means.
  • the detection unit detects whether a critically high impact sound level TS occurs in the ear canal.
  • the detection of impact sound TS can take place via a mechanical, an electrical or electromechanical system.
  • An acceleration or vibration sensor installed in the footfall sound detection unit 20 detects the forces occurring during walking.
  • the occlusion reduction unit 10 adaptively reduces the gain of the active occlusion reduction, thereby limiting the non-linearities created by the handset driver.
  • the microphone input signal is used to detect the impact sound level and the impact sound frequency pattern typical during walking in conjunction with typical step frequencies of 0.5 - 2 Hz.
  • the hearing aid adaptively reduces the gain of the active occlusion reduction at critically high impact sound levels or even deactivates the active occlusion reduction.
  • the impact sound frequencies of hearing aid wearers are measured by a hearing care professional. Since the impact sound level and the impact sound frequency differ significantly from person to person, this approach can be used to optimally set an active occlusion reduction individually with regard to impact sound and occlusion reduction.
  • the measurement of the impact sound frequency can e.g. done with universal earplugs with built-in microphones. Both impact sound frequency and level are recorded. This pre-measurement also determines whether a device with acceptable occlusion reduction effect can be built for the subject.
  • individualized settings of the loop setting of the occlusion reduction unit 10 can be made by individual feedback of the hearing aid wearer.
  • the prerequisite is that algorithmically positioning options are available with which the strength of the impact sound effect can be changed.
  • the bandwidth of the adjustment options can be provided via a control element 30 continuously or via a selection of fixed settings to the hearing aid wearer via the fitting software available.
  • the value of the control element 30 is individually determined by feedback from the hearing aid wearer with respect to footfall sound artifacts during a fitting session.

Description

Die Erfindung betrifft eine im Patentanspruch 1 angegebene Hörvorrichtung mit einer Okklusionsreduktionseinheit und ein im Patentanspruch 10 angegebenes Verfahren zum Betrieb einer Hörvorrichtung.The invention relates to a specified in claim 1 hearing with an occlusion reduction unit and a specified in claim 10 method for operating a hearing.

Als Okklusion wird ein Verschluss des Gehörganges bezeichnet, der beim Tragen einer Hörvorrichtung, beispielsweise einem Hörgerät, auftritt. Ein im Ohr platziertes Hörgerät bzw. ein Ohrpassstück des Hörgeräts dichtet den Gehörgang von der äußeren Umgebung ab. Infolgedessen nimmt der Hörgeräte-Träger die eigene Stimme viel lauter und verzerrter wahr als üblich. Die Okklusion wird als sehr unangenehm empfunden und erschwert die Wahrnehmung komplexer Umgebungsgeräusche, wie z.B. Sprache.An occlusion is a closure of the auditory canal which occurs when a hearing device, for example a hearing aid, is worn. A hearing aid placed in the ear or an earmold piece of the hearing aid seals the auditory canal from the outside environment. As a result, the hearing aid wearer perceives his own voice much louder and more distorted than usual. The occlusion is perceived as very uncomfortable and complicates the perception of complex ambient sounds such as e.g. Language.

Der Okklusionseffekt entsteht durch Schwingungen der Wand des Gehörgangs. Diese Schwingungen werden beim Sprechen oder Kauen von den Stimmbändern oder anderen Schallquellen über die sogenannte Knochenleitung übertragen. Sie versetzen die Wände des weichen Teils des Gehörgangs in Schwingung, ähnlich einer Schallmembran. Wenn der äußere Gehörgang z.B. durch ein Ohrpassstück verstopft ist, erzeugen diese Schwingungen einen relativ hohen Schalldruckpegel, da der Schall nicht wie in einem offenen Ohr nach außen entweichen kann. Der Schalldruck kann dabei am Trommelfell um bis zu 30 dB höher sein als üblich. Die Schalldruckerhöhung hängt von der Frequenz ab. Der Okklusionseffekt zeigt sich insbesondere bei den niedrigen Frequenzen unter 1 kHz. Bei diesen Frequenzen kann die eigene Stimme um bis zu 20 dB verstärkt werden.The occlusion effect is caused by vibrations of the wall of the ear canal. These vibrations are transmitted when speaking or chewing from the vocal cords or other sound sources via the so-called bone conduction. They vibrate the walls of the soft part of the ear canal, similar to a sound membrane. If the external auditory canal is e.g. is clogged by an earmold, these vibrations produce a relatively high sound pressure level, since the sound can not escape to the outside as in an open ear. The sound pressure on the eardrum can be up to 30 dB higher than usual. The sound pressure increase depends on the frequency. The occlusion effect is particularly noticeable at low frequencies below 1 kHz. At these frequencies, your own voice can be amplified by up to 20 dB.

Um die in einem verschlossenen Gehörgang auftretenden Okklusionseffekte zu reduzieren, sind neben mechanischen Lösungen, z.B. sogenannten Vent-Öffnungen, auch Okklusionsreduktionsschaltungen bekannt. Hierbei kommen Schleifenfilter zum Einsatz, die in einer Rückkopplungsschleife des Hörgeräts angeordnet sind. Das Ausgangssignal des Schleifenfilters wird dabei vom eigentlichen Audiosignal subtrahiert, um eine Dämpfung der durch die Okklusion überhöhten Frequenzen zu erreichen. Um auch die durch die Okklusionsreduktionsschaltung selbst verursachte Verzerrung zu kompensieren, werden ferner sogenannte Ausgleichsfilter verwendet, die im Übertragungspfad des Audiosignals angeordnet sind. Sowohl das Schleifenfilter als auch das Ausgleichsfilter sind als statische oder adaptive Filter ausgebildet.In order to reduce the occlusion effects occurring in a closed auditory canal, in addition to mechanical solutions, eg so-called vent openings, occlusion reduction circuits are also provided known. This loop filters are used, which are arranged in a feedback loop of the hearing aid. The output signal of the loop filter is thereby subtracted from the actual audio signal in order to achieve a damping of the frequencies that are increased by the occlusion. In order to compensate also for the distortion caused by the occlusion reduction circuit itself, so-called compensation filters arranged in the transmission path of the audio signal are also used. Both the loop filter and the compensation filter are designed as static or adaptive filters.

In der DE 10 2006 047 965 A1 wird eine Vorrichtung und ein Verfahren zur Okklusionsreduktion bei Hörhilfegeräten beschrieben.In the DE 10 2006 047 965 A1 An apparatus and a method for occlusion reduction in hearing aids is described.

Zusammenfassend gilt, dass bei einer aktiven Okklusionsreduktion das Prinzip des Gegenschalls angewandt wird. Der Gegenschall wird in einer Schleife ermittelt. Alle Signale, die von außen in die Schleife eingebracht werden, unterliegen dabei einer Filterung. Da zur Auslöschung eines Okklusionsschalls der entsprechende Gegenschall phaseninvertiert vom System abgegeben werden muss, ist eine ausreichende Filterung des Okklusionsschalls technisch bedingt nur über einen begrenzten Frequenzbereich möglich. Charakteristisch für das in Hörgeräten verwendete Schleifen-Prinzip ist, dass Signale im Frequenzbereich typischer Sprach-Okklusion (100 - 1000 Hz) vermindert werden.In summary, with active occlusion reduction, the principle of antinoise is applied. The counter sound is determined in a loop. All signals that are introduced into the loop from the outside are subject to filtering. Since, to extinguish an occlusion sound, the corresponding counter-sound must be output by the system phase-inverted, sufficient filtering of the occlusion sound is technically possible only over a limited frequency range. Characteristic of the loop principle used in hearing aids is that signals in the frequency range of typical speech occlusion (100-1000 Hz) are reduced.

Sowohl bei tieferen (bis etwa 100 Hz) als auch bei höheren Frequenzen (ab etwa 1000 Hz) findet keine Verminderung des Okklusionssignals statt, da hier die Phaseninvertierung nicht mehr gilt. Insbesondere bei einem durch Trittschall im Gehörgang eines gehenden Hörgeräteträgers induzierten Schallpegel kann es bei einer aktiven Okklusionsreduktion zu unerwünschten Signalverzerrungen kommen.Both at lower (up to about 100 Hz) and at higher frequencies (from about 1000 Hz) there is no reduction of the occlusion signal, since here the phase inversion no longer applies. In particular, in the case of a sound level induced by impact sound in the auditory canal of a walking hearing aid wearer, undesired signal distortions may occur with an active occlusion reduction.

Es ist Aufgabe der Erfindung eine Hörvorrichtung anzugeben, die den Einfluss von Trittschall auf eine aktive Okklusionsreduktion verringert.It is an object of the invention to specify a hearing device which reduces the influence of impact sound on an active occlusion reduction.

Gemäß der Erfindung wird die gestellte Aufgabe mit der Hörvorrichtung des unabhängigen Patentanspruchs 1 und dem Verfahren zum Betrieb einer Hörvorrichtung des unabhängigen Patentanspruchs 10 gelöst.According to the invention, the stated object is achieved with the hearing device of independent claim 1 and the method for operating a hearing device of independent claim 10.

Die Erfindung beansprucht eine Hörvorrichtung mit einer aktiven Okklusionsreduktionseinheit und mit mindestens einem erstes Mittel, durch das ein durch Schritte eines Trägers der Hörvorrichtung im Gehörgang des Trägers gebildeter Trittschall und/oder durch den Trittschall verursachte Wirkungen auf die Okklusionsreduktionseinheit verringerbar sind. Dies bietet den Vorteil, dass die für einen Träger der Hörvorrichtung hörbaren Trittschall-Artefakte vermieden werden können.The invention claims a hearing device with an active occlusion reduction unit and with at least one first means by which an impact sound formed by steps of a wearer of the hearing device in the auditory canal of the wearer and / or effects on the occlusion reduction unit caused by the impact sound can be reduced. This offers the advantage that the impact sound artifacts audible to a wearer of the hearing device can be avoided.

In einer Weiterbildung kann die Hörvorrichtung ein In-dem-Ohr-Hörgerät oder ein Hinter-dem-Ohr-Hörgerät sein.In a development, the hearing device may be an in-the-ear hearing device or a behind-the-ear hearing device.

In einer weiteren Ausführungsform können die Wirkungen in einem Hörer und/oder in einem Gehörgangsmikrofon erzeugte Oberwellen umfassen. Vorteilhaft ist, dass diese von Nichtlinearitäten stammenden Störungen vermieden werden können.In a further embodiment, the effects may include harmonics generated in a listener and / or in an ear canal microphone. It is advantageous that these disturbances originating from nonlinearities can be avoided.

Bevorzugt kann das erste Mittel ein Gehörgangmikrofon und/oder einen Hörer mit einem Klirrfaktor kleiner 10 % im Frequenzbereich 20 bis 50 Hz umfassen.Preferably, the first means may include an ear canal microphone and / or a handset with a harmonic distortion of less than 10% in the frequency range 20 to 50 Hz.

Des Weiteren kann das erste Mittel zwei oder mehrere Hörer umfassen, wobei ein Hörer einen Klirrfaktor kleiner 10 % im Frequenzbereich 20 bis 50 Hz aufweist.Furthermore, the first means may comprise two or more listeners, wherein a listener has a harmonic distortion of less than 10% in the frequency range 20 to 50 Hz.

In einer Weiterbildung der Erfindung kann das erste Mittel eine Trittschallerkennungseinheit umfassen, die Trittschallpegel im Ohrkanal oberhalb eines vorgebbaren Grenzwerts und/oder Trittschall-Frequenzmuster erkennt. Dadurch Trittschall sicher erkannt werden.In one development of the invention, the first means may comprise a footfall sound detection unit, the footfall sound level in the ear canal above a predefinable limit value and / or impact sound frequency pattern recognizes. As a result, impact sound can be reliably detected.

Bevorzugt kann die Trittschallerkennungseinheit einen Beschleunigungs- und/oder Erschütterungssensor umfassen.The impact sound recognition unit may preferably include an acceleration and / or vibration sensor.

In einer weiteren Ausführungsform kann bei Vorliegen von Trittschall die Verstärkung der aktiven Okklusionsreduktionseinheit adaptiv verringert oder die aktive Okklusionsreduktionseinheit ausgeschaltet werden.In a further embodiment, in the presence of impact sound, the amplification of the active occlusion reduction unit can be adaptively reduced or the active occlusion reduction unit can be switched off.

Außerdem kann das erste Mittel ein Regelelement umfassen, mit dem die Verstärkung der Okklusionsreduktionseinheit veränderbar ist.In addition, the first means may comprise a control element with which the gain of the occlusion reduction unit is variable.

Die Erfindung beansprucht auch ein Verfahren zum Betrieb einer Hörvorrichtung mit einer aktiven Okklusionsreduktion, wobei ein durch Schritte eines Trägers der Hörvorrichtung im Gehörgang des Trägers gebildeter Trittschall und/oder durch den Trittschall verursachte Wirkungen auf die Okklusionsreduktion verringert werden.The invention also claims a method for operating a hearing device with an active occlusion reduction, wherein a footfall sound formed by steps of a wearer of the hearing device in the auditory canal of the wearer and / or effects on the occlusion reduction caused by the impact sound are reduced.

Weitere Besonderheiten und Vorteile der Erfindung werden aus den nachfolgenden Erläuterungen mehrerer Ausführungsbeispiele anhand von schematischen Zeichnungen ersichtlich.Other features and advantages of the invention will become apparent from the following explanations of several embodiments with reference to schematic drawings.

Es zeigen:

Figur 1:
ein Blockschaltbild einer Okklusionsreduktionsvorrichtung gemäß Stand der Technik,
Figur 2:
einen zeitlichen Verlauf eines einzelnen Trittschalls im Ohr und
Figur 3:
ein Blockschaltbild einer aktiven Okklusionsreduktion mit Trittschallerkennung.
Show it:
FIG. 1:
a block diagram of a Okklusionsreduktionsvorrichtung according to the prior art,
FIG. 2:
a temporal course of a single impact sound in the ear and
FIG. 3:
a block diagram of an active occlusion reduction with impact sound detection.

Figur 1 zeigt schematisch den Aufbau eines Hörgeräts 1 mit einer Okklusionsreduktion. Das Hörgerät 1 weist einen Übertragungspfad für ein Audiosignal S auf. Entlang des Übertragungspfads sind mehrere Signalverarbeitungskomponenten angeordnet, mit deren Hilfe das Audiosignal S verarbeitet wird. Das Audiosignal S wird unter anderem mithilfe von Filter- und Verstärkerschaltungen verarbeitet, um einen individuellen Hörverlust zu kompensieren. Da in modernen Hörgeräten die Signalverarbeitung in der Regel digital erfolgt, handelt es sich hierbei vorzugsweise um einen digitalen Signalverarbeitungsprozessor. Am Ende des Übertragungspfads wird das Audiosignal S über einen Hörer R, in der Regel ein elektroakustischer Ausgangswandler, als Schallsignal in den Gehörgang abgegeben. Der Ausgangswandler R ist vorzugsweise als Lautsprecher ausgebildet. Um akustische Signale der Umgebung in das Hörgerät 1 als elektrische Signale einzukoppeln, ist vorzugsweise ein in der Figur 1 nicht gezeigter Eingangswandler vorgesehen, beispielsweise ein Eingangsmikrofon. Für die Einkopplung elektrischer Signale oder elektromagnetischer Funksignale können ferner auch entsprechende Signaleingänge vorgesehen sein. Sofern das Hörgerät 1 eine digitale Signalverarbeitung aufweist, muss ein in das akustische Gerät eingekoppeltes analoges Signal zunächst digitalisiert werden. Hierzu ist üblicherweise ein A/D-(Analog/Digital) Wandler am Anfang des Übertragungspfads vorgesehen. Entsprechend muss das digitale Audiosignal mithilfe eines D/A- (digital/analog) Wandlers am Ende des Übertragungspfads wieder in ein analoges Signal umgewandelt werden, bevor es als akustisches Signal über den Ausgangswandler in den Gehörgang ausgegeben werden kann. Häufig ist der D/A-Wandler bereits im Ausgangswandler integriert, so dass der elektroakustische Ausgangswandler direkt digital angesteuert werden kann. FIG. 1 schematically shows the structure of a hearing aid 1 with an occlusion reduction. The hearing aid 1 has a transmission path for an audio signal S on. Along the transmission path several signal processing components are arranged, with the aid of which the audio signal S is processed. The audio signal S is processed inter alia by means of filter and amplifier circuits in order to compensate for an individual hearing loss. Since signal processing in modern hearing aids generally takes place digitally, this is preferably a digital signal processing processor. At the end of the transmission path, the audio signal S is emitted via a receiver R, usually an electroacoustic output transducer, as a sound signal in the ear canal. The output transducer R is preferably designed as a speaker. To couple acoustic signals of the environment in the hearing aid 1 as electrical signals, is preferably in the FIG. 1 not shown input transducer provided, for example, an input microphone. Furthermore, corresponding signal inputs can also be provided for the coupling of electrical signals or electromagnetic radio signals. If the hearing device 1 has digital signal processing, an analog signal coupled into the acoustic device must first be digitized. For this purpose, usually an A / D (analog / digital) converter is provided at the beginning of the transmission path. Similarly, the digital audio signal must be converted back to an analog signal at the end of the transmission path by means of a D / A (digital / analog) converter before it can be output to the ear canal as an audible signal via the output transducer. Frequently, the D / A converter is already integrated in the output converter so that the electroacoustic output converter can be controlled directly digitally.

Die elektronische Okklusionsreduktionseinheit 10 wird typischerweise durch eine Rückkopplungsschleife realisiert, die ein Gehörgangsmikrofon M und ein Filterelement B umfasst. Das Gehörgangsmikrofon M erfasst das aktuell im Gehörgang herrschende Schallfeld, das ein Okklusionssignal OS umfasst, und erzeugt ein elektrisches Ausgangssignal Z. Dieses Signal durchläuft das Schleifenfilter B, in dem es entsprechend den Filtereinstellungen geformt wird. Das Ausgangsignal T des Schleifenfilters B wird anschließend von einem Signal X im Übertragungspfad des Audiosignals S subtrahiert. Bei einer optimalen Einstellung des Schleifenfilters B werden vor allem diejenigen Frequenzen, etwa 100 bis 1000 Hz, des Audiosignal S gedämpft, welche im Gehörgang durch die Okklusionseffekte überhöht auftreten. Das gegebenenfalls analog vorliegende Ausgangssignal Z des Gehörgangsmikrofons M wird noch in ein digitales Signal umgewandelt, bevor es in der Rückkopplungsschleife digital weiterverarbeitet werden kann.The electronic occlusion reduction unit 10 is typically implemented by a feedback loop that includes an ear canal microphone M and a filter element B. The auditory canal microphone M detects the sound field currently prevailing in the ear canal, which comprises an occlusion signal OS, and generates an electrical output signal Z. This signal passes through the loop filter B, in which it corresponds to the Filter settings is shaped. The output signal T of the loop filter B is then subtracted from a signal X in the transmission path of the audio signal S. With an optimum setting of the loop filter B, especially those frequencies, approximately 100 to 1000 Hz, of the audio signal S are attenuated, which occur in the auditory canal excessively due to the occlusion effects. The optionally present analog output signal Z of the auditory canal microphone M is still converted into a digital signal before it can be further processed digitally in the feedback loop.

Durch die der Signalverarbeitung nachgeschaltete Okklusionsreduktionseinheit 10 erfährt das Audiosignal S in der Regel eine lineare Verzerrung. Um diese Verzerrung zu kompensieren, wird ein Ausgleichsfilter C verwendet. Das auch Vorverzerrungsfilter genannte Filter C ist typischerweise im Übertragungspfad des Audiosignals S zwischen einer Signalverarbeitungseinrichtung und dem Ausgangswandler R angeordnet.As a result of the signal processing downstream occlusion reduction unit 10, the audio signal S usually undergoes a linear distortion. To compensate for this distortion, a compensation filter C is used. The filter C, also called a predistortion filter, is typically arranged in the transmission path of the audio signal S between a signal processing device and the output transducer R.

An Stelle eines Gehörgangsmikrofons M kann grundsätzlich auch ein beliebiger im Gehörgang angeordneter akustischer Eingangswandler vorgesehen werden. Ferner können unter Ausnutzung des Superpositionsprinzips von Signalen auch der Ausgangswandler R und das Gehörgangsmikrofon M miteinander kombiniert werden. In diesem Fall wirkt z.B. der Hörerlautsprecher R auch als Schallempfänger, so dass bei entsprechender Auslegung der Schaltung auf ein separates Gehörgangsmikrofon M verzichtet werden kann.In principle, instead of an auditory canal microphone M, an arbitrary acoustic input transducer arranged in the auditory canal can also be provided. Further, taking advantage of the superposition principle of signals, the output transducer R and the ear canal microphone M can be combined with each other. In this case, e.g. the handset speaker R as a sound receiver, so that it can be dispensed with a separate ear canal microphone M with appropriate design of the circuit.

Beim Gehen entsteht bei jedem Auftreten des Fußes ein kurzer Impuls, der an den menschlichen Körper abgegeben wird. Der Körper reagiert auf diesen Impuls mit einer Impulsantwort, es entsteht eine gedämpfte Schwingung. Der so erzeugte sogenannte Trittschall TS gelangt über Knochenleitung in den Ohrkanal und kann hier gemessen werden. In Figur 2 ist eine Messung eines Trittschalls im Ohrkanal für einen einzelnen Schritt dargestellt. Je nach Person, Schuhwerk, Bodenbeschaffenheit etc. kann der Trittschall TS in Frequenz und Pegel variieren. Typischerweise wurden 2 bis 5 Wellenzüge je Schritt mit einer Frequenz von 20 bis 40 Hz gemessen. Der Trittschallpegel im Ohrkanal hängt auch davon ab, wie dicht der Ohrkanal nach außen, beispielsweise durch ein In-dem-Ohr-Hörgerät oder durch die Otoplastik eines Hinter-dem-Ohr-Hörgeräts verschlossen ist. Bei völligem Verschließen des Ohrkanals können extrem hohe Pegel von bis zu 130 dB Signalleistung entstehen.When walking, a brief impulse arises at each occurrence of the foot, which is delivered to the human body. The body responds to this impulse with an impulse response, creating a damped vibration. The so-called impact sound TS generated in this way passes via bone conduction into the ear canal and can be measured here. In FIG. 2 a measurement of footfall sound in the ear canal is shown for a single step. Depending on the person, footwear, floor conditions, etc., the impact sound TS may vary in frequency and level. Typically, 2 to 5 wave trains per step were measured at a frequency of 20 to 40 Hz. The impact sound level in the ear canal also depends on how tightly the ear canal is closed to the outside, for example by an in-the-ear hearing device or by the earmold of a behind-the-ear hearing device. When the ear canal is completely closed, extremely high levels of up to 130 dB signal power can result.

Das tieffrequente Trittschallsignal TS wird vom Mikrofon M der Okklusionsreduktionseinheit 10 in Figur 1 aufgenommen, in der Schleife gefiltert und vom Hörer R abgegeben. Durch einen hohen Eingangspegel kommt es bei Verwendung von konventionellen Mikrofonen, wie sie derzeit in Hörgeräten Verwendung finden, zu einer Verzerrung des Signals. Ebenso wird der Hörer R durch die Okklusionsreduktionseinheit 10 zur Abgabe derart hoher Pegel gezwungen, die bei konventionellen Hörgeräte-Hörern zu einer starken Verzerrung des Hörers R führen. Die Wandler-Nichtlinearitäten führen so zur Entstehung von Oberwellen ("Klirren"), die von einem Träger des Hörgeräts 1 extrem störend wahrgenommen werden.The low-frequency impact sound signal TS is from the microphone M of the occlusion reduction unit 10 in FIG. 1 recorded, filtered in the loop and delivered by the handset R. A high input level leads to a distortion of the signal when using conventional microphones, which are currently used in hearing aids. Likewise, the listener R is forced by the occlusion reduction unit 10 to deliver such high levels, which in conventional hearing device listeners lead to a strong distortion of the listener R. The transducer non-linearities thus lead to the formation of harmonics ("clinking"), which are perceived by a wearer of the hearing aid 1 extremely disturbing.

Mithilfe eines ersten Mittels im Hörgerät 1 können die unerwünschten Wirkungen (Verzerrungen, Oberwellen) des Trittschalls erfindungsgemäß soweit reduziert werden, dass sie von einem Hörgeräteträger nicht mehr störend wahrgenommen werden. Das erste Mittel kann verschiedene Ausführungsformen umfassen, wobei im Folgenden eine Auswahl beschrieben wird.With the aid of a first means in the hearing aid 1, the unwanted effects (distortions, harmonics) of the impact sound can be reduced according to the invention to such an extent that they are no longer perceived as disturbing by a hearing aid wearer. The first means may comprise various embodiments, a selection being described below.

In einer ersten Ausführungsform wird anstelle eines konventionellen Gehörgangmikrofons M ein spezielles Mikrofon als erstes Mittel verwendet, das im Gegensatz zu typischerweise in Hörgeräten 1 verwendeten Mikrofonen M einen wesentlich niedrigeren Klirrfaktor im Bereich der Frequenzen von 20 bis 50 Hz bei typischerweise im Ohrkanal auftretenden Trittschall-Lautstärkepegeln aufweist. Typischerweise liegt der Klirrfaktor deutlich unter 10 %, da ein Klirrfaktor größer 10 % von einem Hörgeräteträger störend empfunden wird.In a first embodiment, instead of a conventional auditory canal microphone M, a special microphone is used as the first means which, in contrast to microphones M typically used in hearing aids 1, has a significantly lower harmonic distortion in the range of the frequencies of 20 to 50 Hz with impact sound volume levels typically occurring in the ear canal having. Typically, the harmonic distortion is well below 10%, as a total harmonic distortion greater than 10% is distracting to a hearing aid wearer.

In einer weiteren erfindungsgemäßen Ausführungsform wird der Hörer R durch einen speziellen Hörer ersetzt und bildet somit das erste Mittel. Im Gegensatz zu typischerweise in Hörgeräten 1 verwendeten Hören R weist der spezielle Hörer einen deutlich niedrigeren Klirrfaktor im Bereich der Frequenzen von 20 bis 50 Hz bei typischerweise im Ohrkanal auftretenden Trittschall-Lautstärkepegeln auf.In a further embodiment of the invention, the handset R is replaced by a special handset and thus forms the first means. In contrast to the hearing R typically used in hearing aids 1, the particular handset has a significantly lower harmonic distortion in the range of the frequencies of 20 to 50 Hz with impact sound volume levels typically occurring in the ear canal.

In einer weiteren erfindungsgemäßen Ausführungsform umfasst das erste Mittel zwei oder mehreren Hörer. Mindestens ein Hörer dient als Bass-Hörer, d.h. der Hörer kann tiefe Frequenzen im Bereich des Trittschalls mit niedrigem Klirrfaktor abgeben. Der oder die weiteren Hörer sind für den restlichen Frequenzbereich, d.h. den normalen Hörgerätefrequenzbereich, ausgelegt.In a further embodiment according to the invention, the first means comprises two or more listeners. At least one listener serves as a bass handset, i. the listener can deliver low frequencies in the range of impact sound with low harmonic distortion. The other handset (s) are for the remaining frequency range, i. the normal hearing aid frequency range designed.

In Figur 3 ist ein Hörgerät 1 mit einer Okklusionsreduktionseinheit 10 gemäß Figur 1 mit einer Trittschallerkennungseinheit 20 als erstes Mittel ausgestattet. Die Erkennungseinheit erfasst, ob ein kritisch hoher Trittschall-Pegel TS im Ohrkanal auftritt. Die Erkennung von Trittschall TS kann über ein mechanisches, ein elektrisches oder elektromechanisches System erfolgen. Ein in der Trittschallerkennungseinheit 20 eingebauter Beschleunigungs- oder Erschütterungs-Sensor erkennt die beim Gehen auftretenden Kräfte. Bei einem kritisch hohen Trittschall-Pegel TS reduziert die Okklusionsreduktionseinheit 10 adaptiv die Verstärkung der aktiven Okklusionsreduktion, so dass dadurch die durch die Höreransteuerung entstehenden Nichtlinearitäten begrenzt werden. Über das Mikrofon-Eingangssignal werden die beim Gehen typischerweise entstehenden Trittschall-Pegel und Trittschall-Frequenz-Muster in Verbindung mit typischen Schrittfrequenzen von 0.5 - 2 Hz erkannt. Liegt ein Muster für "Person geht" vor, reduziert das Hörgerät adaptiv die Verstärkung der aktiven Okklusionsreduktion bei kritisch hohen Trittschall-Pegeln oder deaktiviert sogar die aktive Okklusionsreduktion.In FIG. 3 is a hearing aid 1 with an occlusion reduction unit 10 according to FIG. 1 equipped with a footfall sound detection unit 20 as the first means. The detection unit detects whether a critically high impact sound level TS occurs in the ear canal. The detection of impact sound TS can take place via a mechanical, an electrical or electromechanical system. An acceleration or vibration sensor installed in the footfall sound detection unit 20 detects the forces occurring during walking. At a critically high impact sound level TS, the occlusion reduction unit 10 adaptively reduces the gain of the active occlusion reduction, thereby limiting the non-linearities created by the handset driver. The microphone input signal is used to detect the impact sound level and the impact sound frequency pattern typical during walking in conjunction with typical step frequencies of 0.5 - 2 Hz. When a pattern for "person goes", the hearing aid adaptively reduces the gain of the active occlusion reduction at critically high impact sound levels or even deactivates the active occlusion reduction.

In einer weiteren Variante werden die Trittschall-Frequenzen von Hörgeräte-Trägern bei einem Hörgeräteakustiker gemessen. Da sich Trittschall-Pegel und Trittschall-Frequenz von Person zu Person signifikant unterscheiden, kann durch diese Vorgehensweise eine aktive Okklusionsreduktion individuell bzgl. Trittschall und Okklusionsreduktion optimal eingestellt werden. Die Messung der Trittschall-Frequenz kann z.B. mit Universal-Ohrenstöpseln mit eingebauten Mikrofonen erfolgen. Sowohl Trittschall-Frequenz als auch Pegel werden aufgenommen. Durch diese Vorabmessung wird auch entschieden, ob für die betreffende Person ein Gerät mit akzeptabler Okklusionsreduktionswirkung gebaut werden kann.In a further variant, the impact sound frequencies of hearing aid wearers are measured by a hearing care professional. Since the impact sound level and the impact sound frequency differ significantly from person to person, this approach can be used to optimally set an active occlusion reduction individually with regard to impact sound and occlusion reduction. The measurement of the impact sound frequency can e.g. done with universal earplugs with built-in microphones. Both impact sound frequency and level are recorded. This pre-measurement also determines whether a device with acceptable occlusion reduction effect can be built for the subject.

In einer weiteren Ausbildung der Erfindung können individualisierte Einstellungen der Schleifeneinstellung der Okklusionsreduktionseinheit 10 durch individuelle Rückmeldung der Hörgeräteträger vorgenommen werden. Vorraussetzung ist, dass algorithmisch Stellmöglichkeiten vorhanden sind, mit denen sich die Stärke des Trittschalleffektes verändern lässt. Die Bandbreite der Einstellmöglichkeiten kann über ein Regelelement 30 kontinuierlich oder über eine Auswahl von festen Einstellungen dem Hörgeräteträger über die Anpasssoftware zur Verfügung gestellt werden. Der Wert des Regelelements 30 wird durch Rückmeldung des Hörgeräteträgers bzgl. Trittschallartefakte bei einer Anpasssitzung individuell festgelegt.In a further embodiment of the invention, individualized settings of the loop setting of the occlusion reduction unit 10 can be made by individual feedback of the hearing aid wearer. The prerequisite is that algorithmically positioning options are available with which the strength of the impact sound effect can be changed. The bandwidth of the adjustment options can be provided via a control element 30 continuously or via a selection of fixed settings to the hearing aid wearer via the fitting software available. The value of the control element 30 is individually determined by feedback from the hearing aid wearer with respect to footfall sound artifacts during a fitting session.

BezugszeichenlisteLIST OF REFERENCE NUMBERS

11
Hörgeräthearing Aid
1010
OkklusionsreduktionseinheitOkklusionsreduktionseinheit
2020
TrittschallerkennungseinheitImpact sound recognition unit
3030
Regelelementcontrol element
BB
Filterelementfilter element
CC
Ausgleichsfiltercompensating filter
MM
GehörgangsmikrofonEar canal microphone
OSOS
Okklusionssignalocclusion
SS
Audiosignalaudio signal
TT
Ausgangssignal des Filterelements BOutput signal of the filter element B
TSTS
Trittschallfootfall
RR
Hörerreceiver
XX
Signal nach dem AusgleichsfilterSignal after the equalization filter
ZZ
Ausgangssignal des Gehörgangmikrofons MOutput signal of the auditory canal microphone M

Claims (7)

  1. Hearing device (1), comprising
    - an active occlusion reduction unit (10), characterized by:
    - at least one first means (R, M, 20, 30) which identifies an impact noise (TS), formed in the auditory canal of the wearer by steps of the wearer of the hearing device (1), on the basis of the impact noise level and impact noise frequency pattern or on the basis of the impact noise frequency pattern and which reduces an amplification of the occlusion reduction unit (10) when impact noise is present or which switches the occlusion reduction unit (10) off when impact noise is present.
  2. Hearing device (1) according to Claim 1, characterized in that the hearing device (1) is an in-the-ear hearing aid or a behind-the-ear hearing aid.
  3. Hearing device (1) according to Claim 1 or 2, characterized
    in that the first means comprises an auditory canal microphone (M) and/or a receiver (R) with a total harmonic distortion of less than 10% in the case of occurring impact noise volume levels in the frequency range from 20 to 50 Hz.
  4. Hearing device (1) according to one of the preceding claims, characterized
    in that the first means comprises two or more receivers (R), wherein one receiver (R) has a total harmonic distortion of less than 10% in the case of occurring impact noise volume levels in the frequency range from 20 to 50 Hz.
  5. Hearing device (1) according to one of the preceding claims, characterized
    in that the first means (20) comprises an acceleration and/or tremor sensor.
  6. Hearing device (1) according to one of the preceding claims, characterized
    in that the first means comprises a closed-loop control element (30), by means of which the amplification of the occlusion reduction unit (10) is modifiable by a wearer of the hearing device (1) or an audiologist.
  7. Method for operating a hearing device (1) comprising an active occlusion reduction,
    characterized by:
    - identifying an impact noise (TS), formed in the auditory canal of the wearer by steps of the wearer of the hearing device (1), on the basis of the impact noise level and impact noise frequency pattern or on the basis of the impact noise frequency pattern and
    - reducing an amplification of the occlusion reduction unit (10) when impact noise (TS) is present or
    - switching the occlusion reduction unit (10) off when impact noise (TS) is present.
EP09179426.3A 2009-02-27 2009-12-16 Device and method for reducing subsonic effects in hearing devices with active occlusion reduction Active EP2224752B1 (en)

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