WO2004021740A1 - Method for counteracting the occlusion effects - Google Patents

Method for counteracting the occlusion effects Download PDF

Info

Publication number
WO2004021740A1
WO2004021740A1 PCT/DK2003/000528 DK0300528W WO2004021740A1 WO 2004021740 A1 WO2004021740 A1 WO 2004021740A1 DK 0300528 W DK0300528 W DK 0300528W WO 2004021740 A1 WO2004021740 A1 WO 2004021740A1
Authority
WO
WIPO (PCT)
Prior art keywords
signal
ear
cavity
sound
occlusion
Prior art date
Application number
PCT/DK2003/000528
Other languages
French (fr)
Inventor
Karsten Bo Rasmussen
Søren Laugesen
Original Assignee
Oticon A/S
Priority date (The priority date 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 date listed.)
Filing date
Publication date
Family has litigation
First worldwide family litigation filed litigation Critical https://patents.darts-ip.com/?family=31970214&utm_source=google_patent&utm_medium=platform_link&utm_campaign=public_patent_search&patent=WO2004021740(A1) "Global patent litigation dataset” by Darts-ip is licensed under a Creative Commons Attribution 4.0 International License.
Application filed by Oticon A/S filed Critical Oticon A/S
Priority to US10/526,229 priority Critical patent/US7477754B2/en
Priority to DK03790755.7T priority patent/DK1537759T3/en
Priority to EP03790755.7A priority patent/EP1537759B1/en
Priority to AU2003247271A priority patent/AU2003247271A1/en
Publication of WO2004021740A1 publication Critical patent/WO2004021740A1/en

Links

Classifications

    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R25/00—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception
    • H04R25/50—Customised settings for obtaining desired overall acoustical characteristics
    • H04R25/505—Customised settings for obtaining desired overall acoustical characteristics using digital signal processing
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F11/00—Methods or devices for treatment of the ears or hearing sense; Non-electric hearing aids; Methods or devices for enabling ear patients to achieve auditory perception through physiological senses other than hearing sense; Protective devices for the ears, carried on the body or in the hand
    • A61F11/06—Protective devices for the ears
    • A61F11/14—Protective devices for the ears external, e.g. earcaps or earmuffs
    • A61F11/145—Protective devices for the ears external, e.g. earcaps or earmuffs electric, e.g. for active noise reduction
    • 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

  • This invention relates to a method for counteracting the occlusion effect of a sound protector and/or communication device like a hearing aid, whereby an ear piece is inserted into the ear canal and totally or partially blocks the canal.
  • the earmold (or ITE hearing aid) may be equipped with a vent, through which the body-conducted part of own voice can dissipate.
  • CIC instruments that are fitted with a seal in the bony part of the ear canal can solve or at least reduce the occlusion problem in many cases.
  • bony sealed CICs have earned a bad reputation for introducing physical discomfort and are hence rarely dispensed.
  • occlusion problems may be dealt with by counseling - along the lines of "You'll get used to it!.
  • the invention seeks to provide a real solution to the occlusion problem by making use of active hearing aid components.
  • the electronic device comprises a transmission path with an external microphone or input line which receives a signal from the environment and a signal processor and a receiver which receives a signal from the signal processor and delivers sound signals to the ear, whereby an ear piece is inserted into the ear canal and totally or partially blocks the canal.
  • the sound conditions in the cavity between the ear piece and the tympanic membrane are directly or indirectly determined, and whenever conditions leading to occlusion problems are present, the transmission characteristic of the transmission path to the receiver counteracts the occlusion effect.
  • Keeping track of the sound conditions in the cavity of the occluded ear canal can be done in a number of different ways and the chosen way is not crucial to the invention. Also counteracting the occlusion can be done in a number of different ways by appropriate choice of transmission characteristic of the transmission path from the input to the receiver.
  • the conditions leading to occlusion problems are determined by monitoring the activity of the users own voice, and when own voice activity is detected the amplification through the signal processor in the frequency region below 1 kHz is reduced. It is the sound transmission through the tissue of the sound from own voice, which often leads to the sound pressure build up in the cavity. This can be compensated for by reducing the amplification through the hearing aid in the relevant frequency region below 1 kHz. Hereby the total sound pressure level in the cavity becomes comfortable.
  • own voice activity can be monitored.
  • One way is to analyze the input signal from the usual microphone and to determine when characteristics which are special to the users voice are present in the signal.
  • a vibration monitor which monitors the level of vibration in the tissue adjacent to the ear piece. Possibly the vibration monitor is built into the ear piece.
  • the sound conditions in the cavity are monitored by an additional microphone, which is acoustically coupled to the cavity.
  • the signal from the additional microphone is used in a feed back loop to the receiver in order to attenuate the low frequency part of the sound in the cavity.
  • the feed back loop attenuates all low frequency sounds regardless of whether they stem from body functions such as chewing or from own voice or from another source.
  • the feed back loop from the additional microphone is activated by own voice activity of the user. It is not a simple task to determine when to activate the feed back loop, but one safe clue is the activity from the users own voice. As mentioned earlier this can be done in many different ways and it is not crucial to the invention which way is chosen here.
  • the sound entering the cavity from the tissue and causing the problematic sound levels in the cavity is captured by a vibration pick-up device.
  • the vibration signal is filtered in a filter and combined with the signal which is captured by the external microphone or input line of the device.
  • the cause of the occlusion problem namely the sound conducted into the ear canal from the surrounding tissue is used in a direct feed forward manner to eliminate or reduce the low frequency sound built up in the cavity.
  • an inward pointing microphone monitors the sound pressure in the cavity. This signal is compared with the signal from the external microphone or input line, and where the comparison result is used to control the shape of the filter. In this way it is assured that the sound inside the ear canal is not allowed to become elevated due to sounds transmission through the tissue of the user and into the ear canal.
  • FIG. 1 is a sketch of the feed back approach to anti-occlusion with an internal microphone according to the invention.
  • Fig. 2 shows a sketch of the feed forward control approach to anti-occlusion using a vibration pick-up.
  • Fig. 3 is a schematic representation of the vibration pick-up.
  • An internal microphone 8 is used in a conventional feed back control system as sketched in fig. 1. Note that the control loop 9 is assumed to be formed in the analog domain. This is reflected in symbols for the receiver H Ta and internal microphone H Ma transfer functions, where the subscript a denotes a transfer function between two analog signals. Furthermore, the transfer function of the analog feed back controller is denoted by D a and finally an additional digital block H c has been added after the hearing aid block
  • H HA as a means of correcting the changes to the amplification characteristic of the hearing aid introduced by the feed back control system.
  • H c also includes the conversion from discrete time signal to analogue signal.
  • H TMa will vary considerably between individual subjects and over time on each individual user, the design of D a will have to be adaptive.
  • the system sketched in fig. 1 will have to be extended with an adaptive model of H TMa , which obviously will have to be digital.
  • the anti-occlusion system will comprise an adaptive discrete time observer from which the transfer function of the analogue controller will be designed. The resulting adjustments to the controller structure will then be implemented as a digitally controllable analogue filter.
  • the filter D a is designed according to the requested attenuation at low frequencies due to occlusion, but stability considerations must also be taken into account. Stability is ensured through analysis of the appropriate Nyquist curve for the open loop case and subsequent gain and filtering adjustment.
  • the combination of signals from the feed back path and from the hearing aid block can be done by means of a receiver equipped with two seperate coils in the electromagnetic system. Hence, as shown in EP patent 1 154 673 the magnetic fields are added within the transducer.
  • vent If a vent is present in the hearing aid, the signal coming into the cavity through the vent will also be attenuated by the feed back system. If the vent has a large diameter it will in general decrease the occlusion effect and the anti-occlusion system will be adjusted accordingly or in some cases removed entirely.
  • an additional electroacoustic transducer 10 is used, which can pick up the vibrations of the soft tissue in the ear canal 5, without picking up either the external sound pressure or the sound pressure generated in the volume 6 between the earmould 4 and the eardrum 7.
  • An idealised block digram of the control system using such a transducer is seen in fig. 2.
  • H HA includes the conversion from discrete time to continuous time.
  • Z F ' C and Z A ' the relations between the own voice volume velocity, q ov , and the volume velocity of other internal sources, q A , and the signal picked up by the additional transducer 10 has been denoted by Z F ' C and Z A ' , respectively, the (analogue) transfer function of the alternative transducer has been denoted by H M ' a , and the controller by D a ' .
  • the relation between the source signals and the sound pressure at the eardrum is
  • the above described feed forward approach may be supplemented by a microphone 8 measuring the sound pressure in the cavity 6 as in the feed back approach (se fig. 1).
  • the transducer provides an error signal used for dynamic adjustment of the controller D a ' for minimum deviation between sound pressure in the cavity and the desired signal at the eardrum which will probably be,
  • the additional internal microphone makes it possible to use an adaptive filter approach taking changes in transfer functions through human tissue into account. These changes could stem from facial expressions, jaw movements, temperature changes etc.
  • the feed forward embodiment of the anti-occlusion system has a transducer which provides a measure of the tissue vibrations and since this vibration contribution is known, an equivalent signal can be emitted in opposite phase from the receiver in order to cancel the influence of this signal in the cavity.
  • the feed forward embodiment above may also be implemented using digital signal processing, such that the signal from the vibration pick-up is converted with its own AD converter and the DA converter in fig. 2 instead becomes part of H Ta .
  • the above mentioned adaptive adjustment is not included and the internal microphone is not included.
  • a transducer 10 for picking up body conducted sound is outlined.
  • the transducer 10 is constructed on the basis of a cylindrically shaped Knowles FG microphone 11.
  • a Knowles FG3453-C with a cut-off frequency of 125Hz is used.
  • the transducer 10 consists of a microphone 11 equipped with an airtight cap 12 or bell of fluoride rubber.
  • the rubber bell is 1.5 mm high measured from the top of the microphone and 0.15 mm thick at the top.
  • the design provides good vibration sensitivity when suitable physical contact exists between the rubber and the surrounding tissue. This choice represents a very compact and yet simple transducer, and it ensures good sensitivity and a high degree of attenuation of air-borne sound.
  • the transducer is mounted so that good contact to the skin is provided while leaving sufficient air in the cavity 13 in front of the microphone in order to avoid rectifying the signal.

Abstract

The invention concerns a method for counteracting the occlusion effect of an electronic device delivering an audio signal to the ear, like a hearing aid or and active ear protector, where the electronic device comprises a transmission path with an external microphone or input line which receives a signal from the environment and a signal processor and a receiver which receives processes signal from the signal from the signal processor and delivers sound signals to the ear, whereby an ear piece is inserted into the ear canal and totally or partially blocks the canal. According to the invention the sound conditions in the cavity between the ear piece and the tympanic membrane are directly or indirectly determined, and whenever conditions leading to occlusion problems are determined, the transmission characteristic of the transmission path to the receiver changes in order to counteract the occlusion effect.

Description

TITLE Method for counteracting the occlusion effects.
AREA OF THE INVENTION This invention relates to a method for counteracting the occlusion effect of a sound protector and/or communication device like a hearing aid, whereby an ear piece is inserted into the ear canal and totally or partially blocks the canal.
BACKGROUND OF THE INVENTION
One of the most common complaints of hearing aid users is that their own voice sounds unnatural: boomy, hollow or echoing. Poor sound quality of own voice is also one of the top ten reasons why some hearing aids end up in the drawer. This problem with own voice is very often due to the so-called occlusion effect, which occurs because the body- conducted contribution to a person's perception of own voice is trapped in the cavity between the occluding earmold of the hearing instrument and the tympanic membrane. The result is a build-up of sound pressure at low frequencies that maybe as much as 30 dB relative to the open-ear. Typically, the occlusion effect has a flat maximum between 80-500 Hz and vanishes above 1 kHz. In the open-ear condition and at the low frequencies considered here, the body-conducted contribution is insignificant compared to the air-conducted contribution.
In today's hearing aid dispensing there are basically three ways to address the client's eventual occlusion problem with own voice. First, the earmold (or ITE hearing aid) may be equipped with a vent, through which the body-conducted part of own voice can dissipate. Secondly, it has been shown that CIC instruments that are fitted with a seal in the bony part of the ear canal can solve or at least reduce the occlusion problem in many cases. Unfortunately, bony sealed CICs have earned a bad reputation for introducing physical discomfort and are hence rarely dispensed. Thirdly, occlusion problems may be dealt with by counseling - along the lines of "You'll get used to it!". A number of hearing aid users do not manage to get used to it, and they prefer to live with their hearing disorder un-aided. hi US patent No 4 985 925 an active noise reduction based on a negative feed back electro-acoustical system is shown. The system consists of an electronic earplug seated in the concha fossa combining active and passive noise reduction in the quiet zone at the ear, a bilateral transducer circuit which drives a speaker as an acoustical velocity source, a shunt feed back control filter network which improves stability and increases noise redution, and a combined input noise-filter/feed back system. A typical application is in a noisy environment for hearing protection and for improved communication capability.
SUMMARY OF THE INVENTION
The invention seeks to provide a real solution to the occlusion problem by making use of active hearing aid components.
This is achieved in a method for counteracting the occlusion effect of an electronic device delivering an audio signal to the ear, like a hearing aid or an active ear protector according to claim 1. The electronic device comprises a transmission path with an external microphone or input line which receives a signal from the environment and a signal processor and a receiver which receives a signal from the signal processor and delivers sound signals to the ear, whereby an ear piece is inserted into the ear canal and totally or partially blocks the canal. The sound conditions in the cavity between the ear piece and the tympanic membrane are directly or indirectly determined, and whenever conditions leading to occlusion problems are present, the transmission characteristic of the transmission path to the receiver counteracts the occlusion effect.
Keeping track of the sound conditions in the cavity of the occluded ear canal can be done in a number of different ways and the chosen way is not crucial to the invention. Also counteracting the occlusion can be done in a number of different ways by appropriate choice of transmission characteristic of the transmission path from the input to the receiver.
In an embodiment of the invention according to claim 2 the conditions leading to occlusion problems are determined by monitoring the activity of the users own voice, and when own voice activity is detected the amplification through the signal processor in the frequency region below 1 kHz is reduced. It is the sound transmission through the tissue of the sound from own voice, which often leads to the sound pressure build up in the cavity. This can be compensated for by reducing the amplification through the hearing aid in the relevant frequency region below 1 kHz. Hereby the total sound pressure level in the cavity becomes comfortable. There are a number of ways in which own voice activity can be monitored. One way is to analyze the input signal from the usual microphone and to determine when characteristics which are special to the users voice are present in the signal. Also it is possible to use a vibration monitor which monitors the level of vibration in the tissue adjacent to the ear piece. Possibly the vibration monitor is built into the ear piece.
According to claim 3 the sound conditions in the cavity are monitored by an additional microphone, which is acoustically coupled to the cavity. The signal from the additional microphone is used in a feed back loop to the receiver in order to attenuate the low frequency part of the sound in the cavity. The feed back loop attenuates all low frequency sounds regardless of whether they stem from body functions such as chewing or from own voice or from another source.
When the occlusion problem is solved as described above the attenuation of the low frequency parts of the sound also is applied to the sound, which is received from the surroundings, and this is not desirable. According to claim 4 this is overcome by having the signal processor amplifying the low frequency part of the signal from the external microphone in order to compensate for the attenuation of the useful part of the signal from the external microphone or input line. In this way the useful low frequency parts of the signal, which are attenuated by the feed back loop, may be restored in the signal processor. Thus the user gets the sound from the surroundings with the usual amplification while the occlusion effect is removed or reduced.
According to an embodiment of the invention as claimed in claim 5 the feed back loop from the additional microphone is activated by own voice activity of the user. It is not a simple task to determine when to activate the feed back loop, but one safe clue is the activity from the users own voice. As mentioned earlier this can be done in many different ways and it is not crucial to the invention which way is chosen here.
In an embodiment of the invention as claimed in claim 6 the sound entering the cavity from the tissue and causing the problematic sound levels in the cavity is captured by a vibration pick-up device. The vibration signal is filtered in a filter and combined with the signal which is captured by the external microphone or input line of the device. In this way the cause of the occlusion problem, namely the sound conducted into the ear canal from the surrounding tissue is used in a direct feed forward manner to eliminate or reduce the low frequency sound built up in the cavity.
In a further embodiment of the invention as claimed in claim 7 an inward pointing microphone monitors the sound pressure in the cavity. This signal is compared with the signal from the external microphone or input line, and where the comparison result is used to control the shape of the filter. In this way it is assured that the sound inside the ear canal is not allowed to become elevated due to sounds transmission through the tissue of the user and into the ear canal.
BRIEF DESCRIPTION OF THE DRAWINGS Fig. 1 is a sketch of the feed back approach to anti-occlusion with an internal microphone according to the invention.
Fig. 2 shows a sketch of the feed forward control approach to anti-occlusion using a vibration pick-up. Fig. 3 is a schematic representation of the vibration pick-up.
DESCRIPTION OF A PREFERRED EMBODIMENT
An internal microphone 8 is used in a conventional feed back control system as sketched in fig. 1. Note that the control loop 9 is assumed to be formed in the analog domain. This is reflected in symbols for the receiver HTa and internal microphone HMa transfer functions, where the subscript a denotes a transfer function between two analog signals. Furthermore, the transfer function of the analog feed back controller is denoted by Da and finally an additional digital block Hc has been added after the hearing aid block
HHA , as a means of correcting the changes to the amplification characteristic of the hearing aid introduced by the feed back control system. In this set-up Hc also includes the conversion from discrete time signal to analogue signal.
The relation between the source variables and the pressure at the eardrum PED is
,. -. _ P 'ES- EM- HA™ C " Ta + <lθV \^FC + ^ AC* EM™ HA™ C™ Ta /"*" Q A^1 A l + DaIITaHMa
From this equation it is seen that the amount of attenuation, which the body-conducted terms will be subject to is determined by the denominator 1 + DaHTaHMa . Thus, the design of the controller Da will depend on the desired performance, but is otherwise only dependent on the combined physical transfer function HTaHMa — in the following shortened to Hma . It is also seen that desired sound pES will be subjected to the same attenuation as the body-conducted terms. However, this can be counteracted by setting Hc = 1 + DaHTMa , which in turn will mean that the second term in the parantheses following qov also will assume its original un-controlled value.
Since HTMa will vary considerably between individual subjects and over time on each individual user, the design of Da will have to be adaptive. Thus, the system sketched in fig. 1 will have to be extended with an adaptive model of HTMa , which obviously will have to be digital. Thus the anti-occlusion system will comprise an adaptive discrete time observer from which the transfer function of the analogue controller will be designed. The resulting adjustments to the controller structure will then be implemented as a digitally controllable analogue filter.
In the feed back realization (Fig. 1), the filter Da is designed according to the requested attenuation at low frequencies due to occlusion, but stability considerations must also be taken into account. Stability is ensured through analysis of the appropriate Nyquist curve for the open loop case and subsequent gain and filtering adjustment. The combination of signals from the feed back path and from the hearing aid block can be done by means of a receiver equipped with two seperate coils in the electromagnetic system. Hence, as shown in EP patent 1 154 673 the magnetic fields are added within the transducer.
If a vent is present in the hearing aid, the signal coming into the cavity through the vent will also be attenuated by the feed back system. If the vent has a large diameter it will in general decrease the occlusion effect and the anti-occlusion system will be adjusted accordingly or in some cases removed entirely.
In another approach as seen in fig. 2 an additional electroacoustic transducer 10 is used, which can pick up the vibrations of the soft tissue in the ear canal 5, without picking up either the external sound pressure or the sound pressure generated in the volume 6 between the earmould 4 and the eardrum 7. An idealised block digram of the control system using such a transducer is seen in fig. 2.
As in the previous section the control is realised in the analogue domain, which means that in this case HHA includes the conversion from discrete time to continuous time. Further, the relations between the own voice volume velocity, qov , and the volume velocity of other internal sources, qA , and the signal picked up by the additional transducer 10 has been denoted by ZF'C and ZA' , respectively, the (analogue) transfer function of the alternative transducer has been denoted by HM' a , and the controller by Da' . The relation between the source signals and the sound pressure at the eardrum is
Figure imgf000007_0001
+ qA(ZA - ZA' HM' aDa'HTa) .
It is seen that occlusion can be reduced by adjustment of the controller Da' so that the qov term is made sufficiently small. In this idealised description it is clear that a couple of potential signal paths have been left out of the picture. The most important one is the path from the sound pressure at the eardrum to the signal picked up by the vibration pick-up. If this path is significant the system will be a hybrid feed forward/feed back system, which will be more difficult to design. A probably much less important contribution is that from the external sound pressure to the signal picked up by the vibration pick-up.
The above described feed forward approach may be supplemented by a microphone 8 measuring the sound pressure in the cavity 6 as in the feed back approach (se fig. 1). In relation to the feed forward approach, the transducer provides an error signal used for dynamic adjustment of the controller Da' for minimum deviation between sound pressure in the cavity and the desired signal at the eardrum which will probably be,
'ED PES™ EM™ HA™ Ta Q OV ^ AC™ EM ™ HA™ . T ' a
Hence, the additional internal microphone makes it possible to use an adaptive filter approach taking changes in transfer functions through human tissue into account. These changes could stem from facial expressions, jaw movements, temperature changes etc.
The feed forward embodiment of the anti-occlusion system has a transducer which provides a measure of the tissue vibrations and since this vibration contribution is known, an equivalent signal can be emitted in opposite phase from the receiver in order to cancel the influence of this signal in the cavity.
The feed forward embodiment above may also be implemented using digital signal processing, such that the signal from the vibration pick-up is converted with its own AD converter and the DA converter in fig. 2 instead becomes part of HTa .
In another embodiment the above mentioned adaptive adjustment is not included and the internal microphone is not included.
hi fig. 3 a transducer 10 for picking up body conducted sound is outlined. The transducer 10 is constructed on the basis of a cylindrically shaped Knowles FG microphone 11. A Knowles FG3453-C with a cut-off frequency of 125Hz is used. The transducer 10 consists of a microphone 11 equipped with an airtight cap 12 or bell of fluoride rubber. The rubber bell is 1.5 mm high measured from the top of the microphone and 0.15 mm thick at the top. The design provides good vibration sensitivity when suitable physical contact exists between the rubber and the surrounding tissue. This choice represents a very compact and yet simple transducer, and it ensures good sensitivity and a high degree of attenuation of air-borne sound. The transducer is mounted so that good contact to the skin is provided while leaving sufficient air in the cavity 13 in front of the microphone in order to avoid rectifying the signal.

Claims

1. Method for counteracting the occlusion effect of an electronic device delivering an audio signal to the ear, like a hearing aid or and active ear protector, where the electronic device comprises a transmission path with an external microphone (1) or input line, which receives a signal pES from the environment and a signal processor
(2) and a receiver (3) which receives a processed signal from the signal processor (2) and delivers sound signals to the ear, whereby an ear piece (4) is inserted into the ear canal (5) and totally or partially blocks the canal (5) whereby the sound conditions in the cavity (6) between the ear piece (4) and the tympanic membrane (7) are directly or indirectly determined, and whenever conditions leading to occlusion problems are determined, the transmission characteristic of the transmission path to the receiver
(3) counteracts the occlusion effect.
Method as claimed in claim 1, whereby the conditions leading to occlusion are determined by monitoring the activity of the users own voice, and when own voice activity is detected the amplification through the signal processor (2) in the frequency region below 1 kHz is reduced.
3. Method as claimed in claim 1, whereby the sound conditions in the cavity (6) are monitored by an additional microphone (8) which is acoustically coupled to the cavity (6), whereby the signal from the additional microphone (8) is used in a feed back loop (9) to the receiver (3) in order to attenuate the low frequency part of the sound in the cavity (6).
4. Method as claimed in claim 3, whereby the signal processor (2) amplifies the low frequency part of the signal from the external microphone in order to compensate for the attenuation of the useful part of the signal from the external microphone (1) or input line.
5. Method as claimed in claim 3 or claim 4, whereby the feed back loop (9) from the additional microphone (8) is activated by own voice activity of the user.
6. Method as claimed in claim 1, whereby the sound entering the cavity (6) from the tissue and causing the occlusion sound levels within the cavity (6) is captured by a vibration pick-up (10), and where the vibration signal is filtered in a filter Da' and combined with the signal which is captured by the external microphone (1) or input line of the device.
7. Method as claimed in claim 6, whereby an inward pointing microphone (8) monitors the sound pressure in the cavity (6), and where this signal is compared with the signal from the external microphone (1) or input line, and where the comparison result is used to control the shape of the filter Da' .
8. Method as claimed in claim 1 and 2, whereby the detection of own voice activity is carried out by the use of a vibration pick-up (10) in contact with a body portion of the user.
PCT/DK2003/000528 2002-09-02 2003-08-07 Method for counteracting the occlusion effects WO2004021740A1 (en)

Priority Applications (4)

Application Number Priority Date Filing Date Title
US10/526,229 US7477754B2 (en) 2002-09-02 2003-08-07 Method for counteracting the occlusion effects
DK03790755.7T DK1537759T3 (en) 2002-09-02 2003-08-07 Method to counteract occlusion effects
EP03790755.7A EP1537759B1 (en) 2002-09-02 2003-08-07 Method for counteracting the occlusion effects
AU2003247271A AU2003247271A1 (en) 2002-09-02 2003-08-07 Method for counteracting the occlusion effects

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
DKPA200201292 2002-09-02
DKPA200201292 2002-09-02

Publications (1)

Publication Number Publication Date
WO2004021740A1 true WO2004021740A1 (en) 2004-03-11

Family

ID=31970214

Family Applications (1)

Application Number Title Priority Date Filing Date
PCT/DK2003/000528 WO2004021740A1 (en) 2002-09-02 2003-08-07 Method for counteracting the occlusion effects

Country Status (5)

Country Link
US (1) US7477754B2 (en)
EP (1) EP1537759B1 (en)
AU (1) AU2003247271A1 (en)
DK (1) DK1537759T3 (en)
WO (1) WO2004021740A1 (en)

Cited By (19)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
DE102006047965A1 (en) * 2006-10-10 2008-01-17 Siemens Audiologische Technik Gmbh Method for the reduction of occlusion effects with acoustic device locking an auditory passage, involves using signal from transmission path of audio signal, and transmission function is observed by output of output converter
DE102006062246A1 (en) * 2006-12-22 2008-06-26 Sennheiser Electronic Gmbh & Co. Kg Earphone, particularly in-ear phone, comprises sound receiver, which is provided for receiving sound in auditory canal and electroacoustic transducer, which is provided for reproducing audio signals
EP1981310A1 (en) * 2007-04-11 2008-10-15 Oticon A/S Hearing instrument with linearized output stage
EP2104376A2 (en) 2008-03-20 2009-09-23 Siemens Medical Instruments Pte. Ltd. Method for active occlusion reduction with plausibility test and corresponding hearing aid
EP2224752A1 (en) * 2009-02-27 2010-09-01 Siemens Medical Instruments Pte. Ltd. Device and method for reducing subsonic effects in hearing devices with active occlusion reduction
EP2242289A1 (en) * 2009-04-01 2010-10-20 Starkey Laboratories, Inc. Hearing assistance system with own voice detection
US7929713B2 (en) 2003-09-11 2011-04-19 Starkey Laboratories, Inc. External ear canal voice detection
US8014548B2 (en) 2006-12-14 2011-09-06 Phonak Ag Hearing instrument, and a method of operating a hearing instrument
US8111849B2 (en) * 2006-02-28 2012-02-07 Rion Co., Ltd. Hearing aid
US8494201B2 (en) 2010-09-22 2013-07-23 Gn Resound A/S Hearing aid with occlusion suppression
EP2640095A1 (en) 2012-03-15 2013-09-18 Phonak AG Method for fitting a hearing aid device with active occlusion control to a user
US8594353B2 (en) 2010-09-22 2013-11-26 Gn Resound A/S Hearing aid with occlusion suppression and subsonic energy control
WO2014075195A1 (en) 2012-11-15 2014-05-22 Phonak Ag Own voice shaping in a hearing instrument
WO2014194932A1 (en) * 2013-06-03 2014-12-11 Phonak Ag Method for operating a hearing device and a hearing device
US9219964B2 (en) 2009-04-01 2015-12-22 Starkey Laboratories, Inc. Hearing assistance system with own voice detection
EP3182721A1 (en) * 2015-12-15 2017-06-21 Sony Mobile Communications, Inc. Controlling own-voice experience of talker with occluded ear
EP3340653A1 (en) * 2016-12-22 2018-06-27 GN Hearing A/S Active occlusion cancellation
CN108962214A (en) * 2012-11-02 2018-12-07 伯斯有限公司 Naturally degree is provided in ANR earphone
EP2040490B2 (en) † 2007-09-18 2021-02-24 Starkey Laboratories, Inc. Method and apparatus for a hearing assistance device using mems sensors

Families Citing this family (20)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
ES2832803T3 (en) * 2003-12-05 2021-06-11 3M Innovative Properties Co Method and apparatus for the objective evaluation of the acoustic performance of an in-ear device
DK2028877T3 (en) * 2007-08-24 2012-05-21 Oticon As Hearing aid with anti-feedback system
US8879763B2 (en) 2008-12-31 2014-11-04 Starkey Laboratories, Inc. Method and apparatus for detecting user activities from within a hearing assistance device using a vibration sensor
US9473859B2 (en) 2008-12-31 2016-10-18 Starkey Laboratories, Inc. Systems and methods of telecommunication for bilateral hearing instruments
US8630437B2 (en) * 2010-02-23 2014-01-14 University Of Utah Research Foundation Offending frequency suppression in hearing aids
US9282412B2 (en) 2011-01-05 2016-03-08 Koninklijke Philips N.V. Seal-quality estimation for a seal for an ear canal
US9269342B2 (en) 2012-05-25 2016-02-23 Bose Corporation In-ear active noise reduction earphone
US9082388B2 (en) 2012-05-25 2015-07-14 Bose Corporation In-ear active noise reduction earphone
EP2699021B1 (en) 2012-08-13 2016-07-06 Starkey Laboratories, Inc. Method and apparatus for own-voice sensing in a hearing assistance device
US9635475B2 (en) 2013-05-01 2017-04-25 Starkey Laboratories, Inc. Hearing assistance device with balanced feed-line for antenna
WO2014177214A1 (en) 2013-05-02 2014-11-06 Phonak Ag Hearing instrument comprising an ear canal microphone with active control loop
EP3251376B1 (en) 2015-01-22 2022-03-16 Eers Global Technologies Inc. Active hearing protection device and method therefore
US9401158B1 (en) 2015-09-14 2016-07-26 Knowles Electronics, Llc Microphone signal fusion
FR3044197A1 (en) 2015-11-19 2017-05-26 Parrot AUDIO HELMET WITH ACTIVE NOISE CONTROL, ANTI-OCCLUSION CONTROL AND CANCELLATION OF PASSIVE ATTENUATION, BASED ON THE PRESENCE OR ABSENCE OF A VOICE ACTIVITY BY THE HELMET USER.
US9779716B2 (en) 2015-12-30 2017-10-03 Knowles Electronics, Llc Occlusion reduction and active noise reduction based on seal quality
US9830930B2 (en) 2015-12-30 2017-11-28 Knowles Electronics, Llc Voice-enhanced awareness mode
US9812149B2 (en) 2016-01-28 2017-11-07 Knowles Electronics, Llc Methods and systems for providing consistency in noise reduction during speech and non-speech periods
EP3687188B1 (en) * 2019-01-25 2022-04-27 ams AG A noise cancellation enabled audio system and method for adjusting a target transfer function of a noise cancellation enabled audio system
CN113645534A (en) * 2021-08-31 2021-11-12 歌尔科技有限公司 Earphone blocking effect eliminating method and earphone
DE102021132434A1 (en) 2021-12-09 2023-06-15 Elevear GmbH Device for active noise and/or occlusion suppression, corresponding method and computer program

Citations (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5201006A (en) * 1989-08-22 1993-04-06 Oticon A/S Hearing aid with feedback compensation
US5577511A (en) * 1995-03-29 1996-11-26 Etymotic Research, Inc. Occlusion meter and associated method for measuring the occlusion of an occluding object in the ear canal of a subject
US5875254A (en) * 1997-12-18 1999-02-23 Siemens Hearing Instruments, Inc. Binaural hearing aid with integrated retrieval line and microphone
EP1154673A1 (en) * 2000-05-12 2001-11-14 Oticon A/S Combining two signals in a hearing aid
WO2002017838A1 (en) * 2000-09-01 2002-03-07 Nacre As Ear protection with verification device
US20030012391A1 (en) * 2001-04-12 2003-01-16 Armstrong Stephen W. Digital hearing aid system

Family Cites Families (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4985925A (en) * 1988-06-24 1991-01-15 Sensor Electronics, Inc. Active noise reduction system
US5267321A (en) * 1991-11-19 1993-11-30 Edwin Langberg Active sound absorber
US6754359B1 (en) * 2000-09-01 2004-06-22 Nacre As Ear terminal with microphone for voice pickup

Patent Citations (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5201006A (en) * 1989-08-22 1993-04-06 Oticon A/S Hearing aid with feedback compensation
US5577511A (en) * 1995-03-29 1996-11-26 Etymotic Research, Inc. Occlusion meter and associated method for measuring the occlusion of an occluding object in the ear canal of a subject
US5875254A (en) * 1997-12-18 1999-02-23 Siemens Hearing Instruments, Inc. Binaural hearing aid with integrated retrieval line and microphone
EP1154673A1 (en) * 2000-05-12 2001-11-14 Oticon A/S Combining two signals in a hearing aid
WO2002017838A1 (en) * 2000-09-01 2002-03-07 Nacre As Ear protection with verification device
US20030012391A1 (en) * 2001-04-12 2003-01-16 Armstrong Stephen W. Digital hearing aid system

Cited By (44)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US7929713B2 (en) 2003-09-11 2011-04-19 Starkey Laboratories, Inc. External ear canal voice detection
US9036833B2 (en) 2003-09-11 2015-05-19 Starkey Laboratories, Inc. External ear canal voice detection
US9369814B2 (en) 2003-09-11 2016-06-14 Starkey Laboratories, Inc. External ear canal voice detection
US8111849B2 (en) * 2006-02-28 2012-02-07 Rion Co., Ltd. Hearing aid
US8218802B2 (en) 2006-10-10 2012-07-10 Siemens Audiologische Technik Gmbh Hearing aid having an occlusion reduction unit and method for occlusion reduction
DE102006047965A1 (en) * 2006-10-10 2008-01-17 Siemens Audiologische Technik Gmbh Method for the reduction of occlusion effects with acoustic device locking an auditory passage, involves using signal from transmission path of audio signal, and transmission function is observed by output of output converter
US8014548B2 (en) 2006-12-14 2011-09-06 Phonak Ag Hearing instrument, and a method of operating a hearing instrument
DE102006062246A1 (en) * 2006-12-22 2008-06-26 Sennheiser Electronic Gmbh & Co. Kg Earphone, particularly in-ear phone, comprises sound receiver, which is provided for receiving sound in auditory canal and electroacoustic transducer, which is provided for reproducing audio signals
AU2008201536B2 (en) * 2007-04-11 2010-12-16 Oticon A/S Hearing instrument with linearized output stage
US8130991B2 (en) 2007-04-11 2012-03-06 Oticon A/S Hearing instrument with linearized output stage
US8229148B2 (en) 2007-04-11 2012-07-24 Oticon A/S Hearing instrument with linearized output stage
EP1981310A1 (en) * 2007-04-11 2008-10-15 Oticon A/S Hearing instrument with linearized output stage
EP2040490B2 (en) † 2007-09-18 2021-02-24 Starkey Laboratories, Inc. Method and apparatus for a hearing assistance device using mems sensors
DE102008015264A1 (en) 2008-03-20 2009-10-01 Siemens Medical Instruments Pte. Ltd. Method for active occlusion reduction with plausibility check and corresponding hearing device
EP2104376A2 (en) 2008-03-20 2009-09-23 Siemens Medical Instruments Pte. Ltd. Method for active occlusion reduction with plausibility test and corresponding hearing aid
US8553917B2 (en) 2008-03-20 2013-10-08 Siemens Medical Instruments Pte, Ltd Method for actively reducing occlusion comprising plausibility check and corresponding hearing apparatus
EP2224752A1 (en) * 2009-02-27 2010-09-01 Siemens Medical Instruments Pte. Ltd. Device and method for reducing subsonic effects in hearing devices with active occlusion reduction
US9094766B2 (en) 2009-04-01 2015-07-28 Starkey Laboratories, Inc. Hearing assistance system with own voice detection
US10652672B2 (en) 2009-04-01 2020-05-12 Starkey Laboratories, Inc. Hearing assistance system with own voice detection
US10171922B2 (en) 2009-04-01 2019-01-01 Starkey Laboratories, Inc. Hearing assistance system with own voice detection
US11388529B2 (en) 2009-04-01 2022-07-12 Starkey Laboratories, Inc. Hearing assistance system with own voice detection
US10225668B2 (en) 2009-04-01 2019-03-05 Starkey Laboratories, Inc. Hearing assistance system with own voice detection
US9712926B2 (en) 2009-04-01 2017-07-18 Starkey Laboratories, Inc. Hearing assistance system with own voice detection
US9219964B2 (en) 2009-04-01 2015-12-22 Starkey Laboratories, Inc. Hearing assistance system with own voice detection
US9699573B2 (en) 2009-04-01 2017-07-04 Starkey Laboratories, Inc. Hearing assistance system with own voice detection
US10715931B2 (en) 2009-04-01 2020-07-14 Starkey Laboratories, Inc. Hearing assistance system with own voice detection
US8477973B2 (en) 2009-04-01 2013-07-02 Starkey Laboratories, Inc. Hearing assistance system with own voice detection
EP2242289A1 (en) * 2009-04-01 2010-10-20 Starkey Laboratories, Inc. Hearing assistance system with own voice detection
EP3169085A1 (en) * 2009-04-01 2017-05-17 Starkey Laboratories, Inc. Hearing assistance system with own voice detection
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
US9319814B2 (en) 2012-03-15 2016-04-19 Sonova Ag Method for fitting a hearing aid device with active occlusion control to a user
EP2640095A1 (en) 2012-03-15 2013-09-18 Phonak AG Method for fitting a hearing aid device with active occlusion control to a user
CN108962214A (en) * 2012-11-02 2018-12-07 伯斯有限公司 Naturally degree is provided in ANR earphone
CN108962214B (en) * 2012-11-02 2023-11-03 伯斯有限公司 Providing ambient naturalness in an ANR headset
US9271091B2 (en) 2012-11-15 2016-02-23 Sonova Ag Own voice shaping in a hearing instrument
WO2014075195A1 (en) 2012-11-15 2014-05-22 Phonak Ag Own voice shaping in a hearing instrument
US9584932B2 (en) 2013-06-03 2017-02-28 Sonova Ag Method for operating a hearing device and a hearing device
WO2014194932A1 (en) * 2013-06-03 2014-12-11 Phonak Ag Method for operating a hearing device and a hearing device
US9949048B2 (en) 2015-12-15 2018-04-17 Sony Mobile Communications Inc Controlling own-voice experience of talker with occluded ear
CN106888414A (en) * 2015-12-15 2017-06-23 索尼移动通讯有限公司 The control of the own voices experience of the speaker with inaccessible ear
EP3182721A1 (en) * 2015-12-15 2017-06-21 Sony Mobile Communications, Inc. Controlling own-voice experience of talker with occluded ear
EP3340653A1 (en) * 2016-12-22 2018-06-27 GN Hearing A/S Active occlusion cancellation
US10405111B2 (en) 2016-12-22 2019-09-03 Gn Hearing A/S Active occlusion cancellation

Also Published As

Publication number Publication date
DK1537759T3 (en) 2014-10-27
EP1537759A1 (en) 2005-06-08
AU2003247271A1 (en) 2004-03-19
US20060120545A1 (en) 2006-06-08
US7477754B2 (en) 2009-01-13
EP1537759B1 (en) 2014-07-23

Similar Documents

Publication Publication Date Title
EP1537759B1 (en) Method for counteracting the occlusion effects
EP3005731B1 (en) Method for operating a hearing device and a hearing device
US5033090A (en) Hearing aid, especially of the in-the-ear type
EP1795045B1 (en) Acoustically transparent occlusion reduction system and method
US10136228B2 (en) Hearing aid device and method for feedback reduction
DK2434780T3 (en) Hearing aid with suppression of occlusion and managing infralydsenergi
EP2434780B1 (en) Hearing aid with occlusion suppression and subsonic energy control
KR102180662B1 (en) Voice intelligibility enhancement system
DK2224752T3 (en) Apparatus and method for reducing trinlydvirkninger of hearing devices with active okklusionsreduktion
US8594353B2 (en) Hearing aid with occlusion suppression and subsonic energy control
US20080130929A1 (en) Hearing device with interference sound suppression and corresponding method
US10973626B2 (en) Implantable microphone management
EP3937508A1 (en) Earpiece, hearing device and system for active occlusion cancellation
CA2245788A1 (en) Noise-reducing stethoscope
US8655001B1 (en) In-the-canal hearing aid using two microphones
JPH10126893A (en) Haring aid
CN108574921B (en) Method for operating a hearing device and hearing device
US20230328462A1 (en) Method, device, headphones and computer program for actively suppressing the occlusion effect during the playback of audio signals
US20180234775A1 (en) Method for operating a hearing device and hearing device
US11722815B2 (en) Implantable microphone management
JP6953984B2 (en) Earphones and signal processing methods for earphones
EP4124060A1 (en) Hearing instrument
US20230300547A1 (en) Method for operating a hearing aid and hearing aid
US20230136161A1 (en) Apparatus and method for performing active occulsion cancellation with audio hear-through
AU2005291830B2 (en) Acoustically transparent occlusion reduction system and method

Legal Events

Date Code Title Description
AK Designated states

Kind code of ref document: A1

Designated state(s): AE AG AL AM AT AU AZ BA BB BG BR BY BZ CA CH CN CO CR CU CZ DE DK DM DZ EC EE ES FI GB GD GE GH GM HR HU ID IL IN IS JP KE KG KP KR KZ LC LK LR LS LT LU LV MA MD MG MK MN MW MX MZ NO NZ OM PH PL PT RO RU SC SD SE SG SK SL TJ TM TN TR TT TZ UA UG US UZ VC VN YU ZA ZM ZW

AL Designated countries for regional patents

Kind code of ref document: A1

Designated state(s): AT BE BG CH CY CZ DE DK EE ES FI FR GB GR HU IE IT LU MC NL PT RO SE SI SK TR

121 Ep: the epo has been informed by wipo that ep was designated in this application
WWE Wipo information: entry into national phase

Ref document number: 2003790755

Country of ref document: EP

ENP Entry into the national phase

Ref document number: 2006120545

Country of ref document: US

Kind code of ref document: A1

WWE Wipo information: entry into national phase

Ref document number: 10526229

Country of ref document: US

WWP Wipo information: published in national office

Ref document number: 2003790755

Country of ref document: EP

WWP Wipo information: published in national office

Ref document number: 10526229

Country of ref document: US

NENP Non-entry into the national phase

Ref country code: JP

WWW Wipo information: withdrawn in national office

Country of ref document: JP