EP2224752B1 - Vorrichtung und Verfahren zur Reduzierung von Trittschallwirkungen bei Hörvorrichtungen mit aktiver Okklusionsreduktion - Google Patents

Vorrichtung und Verfahren zur Reduzierung von Trittschallwirkungen bei Hörvorrichtungen mit aktiver Okklusionsreduktion 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
European Patent Office
Prior art keywords
impact noise
occlusion reduction
hearing device
hearing
wearer
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Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
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Application number
EP09179426.3A
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German (de)
English (en)
French (fr)
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EP2224752A1 (de
Inventor
Georg-Erwin Arndt
Dr. Volker Gebhardt
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Sivantos 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.

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  • Health & Medical Sciences (AREA)
  • General Health & Medical Sciences (AREA)
  • Otolaryngology (AREA)
  • Neurosurgery (AREA)
  • Physics & Mathematics (AREA)
  • Engineering & Computer Science (AREA)
  • Acoustics & Sound (AREA)
  • Signal Processing (AREA)
  • Soundproofing, Sound Blocking, And Sound Damping (AREA)
  • Circuit For Audible Band Transducer (AREA)
  • Headphones And Earphones (AREA)
EP09179426.3A 2009-02-27 2009-12-16 Vorrichtung und Verfahren zur Reduzierung von Trittschallwirkungen bei Hörvorrichtungen mit aktiver Okklusionsreduktion Active EP2224752B1 (de)

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
US15595909P 2009-02-27 2009-02-27
DE102009010892A DE102009010892B4 (de) 2009-02-27 2009-02-27 Vorrichtung und Verfahren zur Reduzierung von Trittschallwirkungen bei Hörvorrichtungen mit aktiver Okklusionsreduktion

Publications (2)

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EP2224752A1 EP2224752A1 (de) 2010-09-01
EP2224752B1 true EP2224752B1 (de) 2015-12-02

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Country Status (4)

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US (1) US20100220881A1 (da)
EP (1) EP2224752B1 (da)
DE (1) DE102009010892B4 (da)
DK (1) DK2224752T3 (da)

Families Citing this family (10)

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Publication number Priority date Publication date Assignee Title
EP2378788A3 (en) 2010-04-13 2012-01-25 Sony Corporation Device and method for in-ear sound generation
US8594353B2 (en) 2010-09-22 2013-11-26 Gn Resound A/S Hearing aid with occlusion suppression and subsonic energy control
US8494201B2 (en) 2010-09-22 2013-07-23 Gn Resound A/S Hearing aid with occlusion suppression
EP2434780B1 (en) * 2010-09-22 2016-04-13 GN ReSound A/S Hearing aid with occlusion suppression and subsonic energy control
DE102011075006B3 (de) * 2011-04-29 2012-10-31 Siemens Medical Instruments Pte. Ltd. Verfahren zum Betrieb eines Hörgerätes mit verringerter Kammfilterwahrnehmung und Hörgerät mit verringerter Kammfilterwahrnehmung
US9729977B2 (en) 2013-06-12 2017-08-08 Sonova Ag Method for operating a hearing device capable of active occlusion control and a hearing device with user adjustable active occlusion control
US20170195811A1 (en) * 2015-12-30 2017-07-06 Knowles Electronics Llc Audio Monitoring and Adaptation Using Headset Microphones Inside User's Ear Canal
US10951996B2 (en) 2018-06-28 2021-03-16 Gn Hearing A/S Binaural hearing device system with binaural active occlusion cancellation
DE102020209906A1 (de) 2020-08-05 2022-02-10 Sivantos Pte. Ltd. Verfahren zum Betrieb eines Hörgeräts und Hörgerät
DE102020209907A1 (de) 2020-08-05 2022-02-10 Sivantos Pte. Ltd. Verfahren zum Betrieb eines Hörgeräts und Hörgerät

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DE19946467A1 (de) * 1999-09-28 2001-04-26 Siemens Ag Elektrostatischer Wandler und Verfahren zu seiner Herstellung
DE10114838A1 (de) * 2001-03-26 2002-10-10 Implex Ag Hearing Technology I Vollständig implantierbares Hörsystem
US6937738B2 (en) * 2001-04-12 2005-08-30 Gennum Corporation Digital hearing aid system
US6714654B2 (en) * 2002-02-06 2004-03-30 George Jay Lichtblau Hearing aid operative to cancel sounds propagating through the hearing aid case
EP1537759B1 (en) * 2002-09-02 2014-07-23 Oticon A/S Method for counteracting the occlusion effects
DE10344032A1 (de) * 2003-09-23 2005-06-23 Schlegel, Udo D. Hörsystem verwendbar für schwerhörige Personen
US7043037B2 (en) * 2004-01-16 2006-05-09 George Jay Lichtblau Hearing aid having acoustical feedback protection
US20070053522A1 (en) * 2005-09-08 2007-03-08 Murray Daniel J Method and apparatus for directional enhancement of speech elements in noisy environments
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US20100027823A1 (en) * 2006-10-10 2010-02-04 Georg-Erwin Arndt Hearing aid having an occlusion reduction unit and method for occlusion reduction
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US9191740B2 (en) * 2007-05-04 2015-11-17 Personics Holdings, Llc Method and apparatus for in-ear canal sound suppression
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WO2009143898A1 (en) * 2008-05-30 2009-12-03 Phonak Ag Method for adapting sound in a hearing aid device by frequency modification and such a device

Also Published As

Publication number Publication date
DK2224752T3 (da) 2016-02-29
DE102009010892B4 (de) 2012-06-21
US20100220881A1 (en) 2010-09-02
DE102009010892A1 (de) 2010-09-02
EP2224752A1 (de) 2010-09-01

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