CA2417803A1 - A hearing aid with an adaptive filter for suppression of acoustic feedback - Google Patents
A hearing aid with an adaptive filter for suppression of acoustic feedback Download PDFInfo
- Publication number
- CA2417803A1 CA2417803A1 CA002417803A CA2417803A CA2417803A1 CA 2417803 A1 CA2417803 A1 CA 2417803A1 CA 002417803 A CA002417803 A CA 002417803A CA 2417803 A CA2417803 A CA 2417803A CA 2417803 A1 CA2417803 A1 CA 2417803A1
- Authority
- CA
- Canada
- Prior art keywords
- hearing aid
- filter
- electrical signal
- aid according
- signal
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Granted
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
- H04R25/45—Prevention of acoustic reaction, i.e. acoustic oscillatory feedback
- H04R25/453—Prevention of acoustic reaction, i.e. acoustic oscillatory feedback electronically
-
- H—ELECTRICITY
- H04—ELECTRIC COMMUNICATION TECHNIQUE
- H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
- H04R2430/00—Signal processing covered by H04R, not provided for in its groups
- H04R2430/03—Synergistic effects of band splitting and sub-band processing
-
- 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
- H04R25/35—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception using translation techniques
- H04R25/353—Frequency, e.g. frequency shift or compression
-
- 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
Landscapes
- Health & Medical Sciences (AREA)
- General Health & Medical Sciences (AREA)
- Neurosurgery (AREA)
- Otolaryngology (AREA)
- Physics & Mathematics (AREA)
- Engineering & Computer Science (AREA)
- Acoustics & Sound (AREA)
- Signal Processing (AREA)
- Filters That Use Time-Delay Elements (AREA)
- Circuit For Audible Band Transducer (AREA)
- Tone Control, Compression And Expansion, Limiting Amplitude (AREA)
Abstract
The present invention relates to a hearing aid with an adaptive filter for suppression of acoustic feedback in the hearing aid. The hearing aid further comprises a controller that is adapted to compensate for acoustic feedback by determination of a first parameter of an acoustic feedback loop of the hearing aid and adjustment of a second parameter of the hearing aid in response to he first parameter whereby generation of undesired sounds is substantially avoided. Hereby a gain safety margin requirement is significantly reduced.
Claims (29)
1. A hearing aid comprising an input transducer (1) for transforming an acoustic input signal into a first electrical signal (4), a first filter bank (3) with bandpass filters for dividing the first electrical signal (4) into a set of bandpass filtered first electrical signals (4i), a processor (7) for generation of a second electrical signal (80) by individual processing of each of the bandpass filtered first electrical signals (4i, 86) and adding the processed electrical signals into the second electrical signal (80), an output transducer (5) for transforming the second electrical signal (80) into an acoustic output signal (6), a second filter bank (16) with bandpass filters for dividing the second electrical signal (80) into a set of bandpass filtered second electrical signals (80i), a first set of adaptive filters (10) with first filter coefficients for estimation of acoustic feedback by generation of third electrical signals (85) by filtering of the bandpass filtered second electrical signals (80i) and adapting the respective third signals (85) to respective signals on the input side of the processor (7) with respective first convergence rates, and a controller that is adapted to compensate for acoustic feedback by determination of a first parameter of an acoustic feedback loop of the hearing aid and adjustment of a second parameter of the hearing aid in response to the first parameter whereby generation of undesired sounds is substantially avoided.
2. A hearing aid according to claim 1, wherein at least one of the adaptive filters of the first set of adaptive filters (10) operates on a respective decimated bandpass filtered second electrical signal (80i).
3. A hearing aid according to claim 1 or 2, wherein the first filter bank (3) consists of a single bandpass filter.
4. A hearing aid according to claim 1 or 3, wherein the second filter bank (16) consists of a single bandpass filter, and the first set of adaptive filters consists of a single adaptive filter.
5. A hearing aid according to claim 1 or 2, wherein the bandpass filters of the second filter (16) bank are substantially identical to respective bandpass filters of the first filter bank (3).
6. A hearing aid according to claim 4, wherein the first set of adaptive filters filters the second electrical signal (80) and adapts to the first electrical signal (4).
7. A hearing aid according to claim 6, further comprising a combining node (9) for subtraction of the third signal (85) from the first electrical signal (4), and wherein the subtracted signal is fed to the processor (7).
8. A hearing aid according to claim 5, wherein the first set of adaptive filters filters the respective bandpass filtered second electrical signals (80i) and adapts to the respective bandpass filtered first electrical signals (4i).
9. A hearing aid according to claim 8, further comprising a combining node (9) for subtraction of the third signals (85) from the respective bandpass filtered first electrical signals (4i), and wherein the subtracted signals are fed to the processor (7).
10. A hearing aid according to claim 6, further comprising a second adaptive filter (11) with second filter coefficients for suppression of feedback in the hearing aid by filtering the second electrical signal (80) into a fourth electrical signal (85), a combining node (9) for generation of a fifth electrical signal (86) by subtraction of the fourth electrical signal (85) from the first electrical signal (4) and for feeding the fifth electrical signal (86) to the respective bandpass filters of the first filter bank, and wherein the second filter coefficients are updated with a second convergence rate that is lower than the first convergence rate.
11. A hearing aid according to claim 8, further comprising a set of second adaptive filters (11) with second filter coefficients for suppression of feedback in the hearing aid by filtering the bandpass filtered second electrical signals (80i) into respective fourth electrical signals (85i), a combining node (9) for generation of fifth electrical signals (86i) by subtraction of the fourth electrical signals (85i) from the respective bandpass filtered first electrical signals (4i) and for feeding the fifth electrical signals (86i) to the processor (7), and wherein the second filter coefficients are updated with a second convergence rate that is lower than the first convergence rate.
12. A hearing aid according to any of the preceding claims, wherein the first parameter is an operating gain of the processor (7).
13. A hearing aid according to any of claims 1-11, wherein the first parameter is a parameter of the first set of adaptive filters.
14. A hearing aid according to claim 13, wherein the first parameter is the ratio between the magnitude of a signal (88) at an input of a first adaptive filter of the first set of adaptive filters (11) and the magnitude of a signal (89) at the corresponding output.
15. A hearing aid according to any of the preceding claims, wherein the second parameter is a gain of the processor (7).
16. A hearing aid according to any of claims 1-14, wherein the second parameter is the first convergence rate of the first filter coefficients.
17. A hearing aid according to any of claims 12-16 as dependent on claim 9 or 10, wherein the second parameter is the second convergence rate of the second filter coefficients.
18. A hearing aid according to any of the preceding claims, further comprising means for updating filter coefficients according to a leaky least mean square algorithm:
c i(n+1)=.lambda.(c i(n)-c i(0))+c i(0)+µu i(n)e(n) where c i(n+1) is the updated value of i'th filter coefficient, c i(n) is the current value of the i'th filter coefficient, c i(0) is the initial value of the i'th filter coefficient, u i(n) is the (n-i)'th sample of the processor output signal, e(n) is the current sample of the second electrical signal (86), .lambda.
is the leakage, and µ is the convergence, .lambda. and µ determining the first convergence rate.
c i(n+1)=.lambda.(c i(n)-c i(0))+c i(0)+µu i(n)e(n) where c i(n+1) is the updated value of i'th filter coefficient, c i(n) is the current value of the i'th filter coefficient, c i(0) is the initial value of the i'th filter coefficient, u i(n) is the (n-i)'th sample of the processor output signal, e(n) is the current sample of the second electrical signal (86), .lambda.
is the leakage, and µ is the convergence, .lambda. and µ determining the first convergence rate.
19. A hearing aid according to any of the preceding claims, further comprising means for updating filter coefficients according to a normalised Least Mean Square:
where u(n) is an N dimensional vector containing the latest N samples of the signal u, c(n) is a vector containing the current values of the N filter coefficients, c(0 is a vector containing the initial values of the N filter coefficients, c(n+1) is the updated values of the N filter coefficients, and e(n) is the current sample of the second electrical signal (86).
where u(n) is an N dimensional vector containing the latest N samples of the signal u, c(n) is a vector containing the current values of the N filter coefficients, c(0 is a vector containing the initial values of the N filter coefficients, c(n+1) is the updated values of the N filter coefficients, and e(n) is the current sample of the second electrical signal (86).
20. A hearing aid according to any of the preceding claims, further comprising means for updating filter coefficients according to a power normalised Least Mean Square algorithm.
P u(t+T)=.alpha.P u(t)+(1-.alpha.)u2(t) where .alpha. is a predetermined constant that determines the rate with which the P u estimate changes.
P u(t+T)=.alpha.P u(t)+(1-.alpha.)u2(t) where .alpha. is a predetermined constant that determines the rate with which the P u estimate changes.
21. A hearing aid according to any of the preceding claims, further comprising means for updating filter coefficients according to a leaky sign least mean square algorithm:
c i(n+1)=.lambda.(c i(n)-c i(0))+c i(0)+µs u i(n) where c i(n+1) is the updated value of i'th filter coefficient, c i(n) is the current value of the i'th filter coefficient, c i(0) is the initial value of the i'th filter coefficient, u i(n) is the (n-i)'th sample of the processor output signal, e(n) is the current sample of the second electrical signal (86), .lambda.
is the leakage, and µ is the convergence, and µs is the sign of the e(n) signal multiplied by µ, .lambda.
and µ determining the first convergence rate.
c i(n+1)=.lambda.(c i(n)-c i(0))+c i(0)+µs u i(n) where c i(n+1) is the updated value of i'th filter coefficient, c i(n) is the current value of the i'th filter coefficient, c i(0) is the initial value of the i'th filter coefficient, u i(n) is the (n-i)'th sample of the processor output signal, e(n) is the current sample of the second electrical signal (86), .lambda.
is the leakage, and µ is the convergence, and µs is the sign of the e(n) signal multiplied by µ, .lambda.
and µ determining the first convergence rate.
22. A hearing aid according to any of the preceding claims, further comprising means for updating filter coefficients according to a leaky sign-sign least mean square algorithm:
c i(n+1)=.lambda.(c i(n)-c i(0))+c i(0)+µs sgn(u i(n)) where c i(n+1) is the updated value of i'th filter coefficient, c i(n) is the current value of the i'th filter coefficient, c i(0) is the initial value of the i'th filter coefficient, u i(n) is the (n-i)'th sample of the processor output signal, e(n) is the current sample of the second electrical signal (86), .lambda.
is the leakage, and µ is the convergence factor, and sgn(u i(n)) is the sign of u i(n), .lambda. and µ
determining the first convergence rate.
c i(n+1)=.lambda.(c i(n)-c i(0))+c i(0)+µs sgn(u i(n)) where c i(n+1) is the updated value of i'th filter coefficient, c i(n) is the current value of the i'th filter coefficient, c i(0) is the initial value of the i'th filter coefficient, u i(n) is the (n-i)'th sample of the processor output signal, e(n) is the current sample of the second electrical signal (86), .lambda.
is the leakage, and µ is the convergence factor, and sgn(u i(n)) is the sign of u i(n), .lambda. and µ
determining the first convergence rate.
23. A hearing aid according to any of the preceding claims, wherein at least one of the first and second sets of adaptive filters (10, 11) comprises a finite impulse response filter.
24. A hearing aid according to any of the preceding claims, wherein at least one of the first and second sets of adaptive filters (10, 11) comprises a warped finite impulse response filter.
25. A hearing aid according to any of the preceding claims, wherein the controller is adapted to adjust a second parameter of the hearing aid in response to the first parameter and in response to the actual acoustic environment.
26. A hearing aid comprising an input transducer (1) for transforming an acoustic input signal into a first electrical signal (4), a processor (7) for generation of a second electrical signal (80) by processing of the first electrical signals (4i, 86) into the second electrical signal (80), an output transducer (5) for transforming the second electrical signal (80) into an acoustic output signal (6), an adaptive filter (10) with filter coefficients for estimation of acoustic feedback by generation of third electrical signals (85) by filtering of the second electrical signal (80) and adapting the respective third signals (85) to respective signals on the input side of the processor (7), characterised in that the adaptive filter (10) is a warped adaptive filter.
27. A hearing aid according to claim 26, wherein the warped filter is a warped FIR filter.
28. A method of suppressing acoustic feedback in a hearing aid, comprising the steps of:
transforming an acoustic input signal into a first electrical signal (4), dividing the first electrical signal (4) into a set of bandpass filtered first electrical signals (4i), processing each of the bandpass filtered first electrical signals (4i, 86) individually, adding the processed electrical signals into a second electrical signal (80), transforming the second electrical signal (80) into an acoustic output signal (6), dividing the second electrical signal (80) into a set of bandpass filtered second electrical signals (80i),
transforming an acoustic input signal into a first electrical signal (4), dividing the first electrical signal (4) into a set of bandpass filtered first electrical signals (4i), processing each of the bandpass filtered first electrical signals (4i, 86) individually, adding the processed electrical signals into a second electrical signal (80), transforming the second electrical signal (80) into an acoustic output signal (6), dividing the second electrical signal (80) into a set of bandpass filtered second electrical signals (80i),
29 estimating acoustic feedback by generation of third electrical signals (85) by adaptive filtering of the bandpass filtered second electrical signals (80i) and adapting the filtered signals (85) to respective signals on the input side of the processor (7) with respective first convergence rates, and compensating for acoustic feedback by determining a first parameter of an acoustic feedback loop of the hearing aid, and adjusting a second parameter of the hearing aid in response to the first parameter whereby generation of undesired sounds is substantially avoided.
Applications Claiming Priority (5)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| EP00610097A EP1191813A1 (en) | 2000-09-25 | 2000-09-25 | A hearing aid with an adaptive filter for suppression of acoustic feedback |
| EP00610097.8 | 2000-09-25 | ||
| EP00610124.0A EP1191814B2 (en) | 2000-09-25 | 2000-12-01 | A multiband hearing aid with multiband adaptive filters for acoustic feedback suppression. |
| EP00610124.0 | 2000-12-01 | ||
| PCT/DK2001/000604 WO2002025996A1 (en) | 2000-09-25 | 2001-09-20 | A hearing aid with an adaptive filter for suppression of acoustic feedback |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| CA2417803A1 true CA2417803A1 (en) | 2002-03-28 |
| CA2417803C CA2417803C (en) | 2010-11-23 |
Family
ID=26073700
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CA2417803A Expired - Fee Related CA2417803C (en) | 2000-09-25 | 2001-09-20 | A hearing aid with an adaptive filter for suppression of acoustic feedback |
Country Status (5)
| Country | Link |
|---|---|
| EP (2) | EP2066139A3 (en) |
| JP (1) | JP3899023B2 (en) |
| AU (2) | AU8959201A (en) |
| CA (1) | CA2417803C (en) |
| WO (1) | WO2002025996A1 (en) |
Cited By (1)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US11503415B1 (en) | 2021-04-23 | 2022-11-15 | Eargo, Inc. | Detection of feedback path change |
Families Citing this family (38)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JP4681163B2 (en) * | 2001-07-16 | 2011-05-11 | パナソニック株式会社 | Howling detection and suppression device, acoustic device including the same, and howling detection and suppression method |
| US7277554B2 (en) * | 2001-08-08 | 2007-10-02 | Gn Resound North America Corporation | Dynamic range compression using digital frequency warping |
| DE10242700B4 (en) * | 2002-09-13 | 2006-08-03 | Siemens Audiologische Technik Gmbh | Feedback compensator in an acoustic amplification system, hearing aid, method for feedback compensation and application of the method in a hearing aid |
| DE10245667B4 (en) | 2002-09-30 | 2004-12-30 | Siemens Audiologische Technik Gmbh | Feedback compensator in an acoustic amplification system, hearing aid, method for feedback compensation and application of the method in a hearing aid |
| US7885991B2 (en) | 2003-03-04 | 2011-02-08 | Oticon A/S | Digital filter having a fir filter and a warped fir filter, and a listening device including such a digital filter |
| US7092532B2 (en) | 2003-03-31 | 2006-08-15 | Unitron Hearing Ltd. | Adaptive feedback canceller |
| AU2003236382B2 (en) * | 2003-08-20 | 2011-02-24 | Phonak Ag | Feedback suppression in sound signal processing using frequency transposition |
| US7756276B2 (en) | 2003-08-20 | 2010-07-13 | Phonak Ag | Audio amplification apparatus |
| AU2004201374B2 (en) | 2004-04-01 | 2010-12-23 | Phonak Ag | Audio amplification apparatus |
| ATE397840T1 (en) * | 2003-08-21 | 2008-06-15 | Widex As | HEARING AID WITH ACOUSTIC FEEDBACK SUPPRESSION |
| EP1730992B1 (en) | 2004-03-23 | 2017-05-10 | Oticon A/S | Hearing aid with anti feedback system |
| KR20050119758A (en) * | 2004-06-17 | 2005-12-22 | 한양대학교 산학협력단 | Hearing aid having noise and feedback signal reduction function and signal processing method thereof |
| DE102004050304B3 (en) † | 2004-10-14 | 2006-06-14 | Siemens Audiologische Technik Gmbh | Method for reducing feedback in an acoustic system and signal processing device |
| JP4658137B2 (en) * | 2004-12-16 | 2011-03-23 | ヴェーデクス・アクティーセルスカプ | Hearing aid to estimate feedback model gain |
| EP1949755B1 (en) | 2005-10-11 | 2010-05-12 | Widex A/S | Hearing aid and a method of processing input signals in a hearing aid |
| CA2626072C (en) | 2005-10-18 | 2015-06-23 | Widex A/S | Equipment for programming a hearing aid and a hearing aid |
| AU2005232314B2 (en) | 2005-11-11 | 2010-08-19 | Phonak Ag | Feedback compensation in a sound processing device |
| EP2317778B1 (en) | 2006-03-03 | 2019-05-08 | Widex A/S | Hearing aid and method of utilizing gain limitation in a hearing aid |
| JP4860712B2 (en) * | 2006-03-09 | 2012-01-25 | ヴェーデクス・アクティーセルスカプ | Hearing aid with adaptive feedback suppression |
| AU2006341496B2 (en) * | 2006-03-31 | 2010-04-29 | Widex A/S | Hearing aid and method of estimating dynamic gain limitation in a hearing aid |
| EP2002690B2 (en) | 2006-04-01 | 2019-11-27 | Widex A/S | Hearing aid, and a method for control of adaptation rate in anti-feedback systems for hearing aids |
| DE102006023723A1 (en) | 2006-05-19 | 2007-11-22 | Siemens Audiologische Technik Gmbh | Hearing device with feedback detection and corresponding method |
| US8280088B2 (en) | 2006-05-19 | 2012-10-02 | Siemens Audiologische Technik Gmbh | Hearing apparatus with feedback detection and corresponding method |
| DK2003928T3 (en) | 2007-06-12 | 2019-01-28 | Oticon As | Online anti-feedback system for a hearing aid |
| EP2232890A2 (en) | 2008-01-22 | 2010-09-29 | Phonak AG | Method for determining a maximum gain in a hearing device as well as a hearing device |
| MY159890A (en) * | 2008-04-18 | 2017-02-15 | Dolby Laboratories Licensing Corp | Method and apparatus for maintaining speech audibiliy in multi-channel audio with minimal impact on surround experience |
| US10602282B2 (en) * | 2008-12-23 | 2020-03-24 | Gn Resound A/S | Adaptive feedback gain correction |
| EP2217007B1 (en) | 2009-02-06 | 2014-06-11 | Oticon A/S | Hearing device with adaptive feedback suppression |
| WO2010040863A2 (en) * | 2010-01-15 | 2010-04-15 | Phonak Ag | A method for operating a hearing device as well as a hearing device |
| WO2012076044A1 (en) | 2010-12-08 | 2012-06-14 | Widex A/S | Hearing aid and a method of improved audio reproduction |
| US8675901B2 (en) * | 2011-10-14 | 2014-03-18 | Panasonic Corporation | Howling suppression device, hearing aid, howling suppression method, and integrated circuit |
| US9148733B2 (en) | 2012-12-28 | 2015-09-29 | Gn Resound A/S | Hearing aid with improved localization |
| US9148735B2 (en) | 2012-12-28 | 2015-09-29 | Gn Resound A/S | Hearing aid with improved localization |
| US9338561B2 (en) * | 2012-12-28 | 2016-05-10 | Gn Resound A/S | Hearing aid with improved localization |
| US9100762B2 (en) | 2013-05-22 | 2015-08-04 | Gn Resound A/S | Hearing aid with improved localization |
| US9712908B2 (en) | 2013-11-05 | 2017-07-18 | Gn Hearing A/S | Adaptive residual feedback suppression |
| US9432778B2 (en) | 2014-04-04 | 2016-08-30 | Gn Resound A/S | Hearing aid with improved localization of a monaural signal source |
| DK3273608T3 (en) * | 2016-07-20 | 2022-03-14 | Sennheiser Electronic Gmbh & Co Kg | ADAPTIVE FILTER UNIT FOR USE AS AN ECO COMPENSATOR |
Family Cites Families (10)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US5016280A (en) | 1988-03-23 | 1991-05-14 | Central Institute For The Deaf | Electronic filters, hearing aids and methods |
| US5402496A (en) * | 1992-07-13 | 1995-03-28 | Minnesota Mining And Manufacturing Company | Auditory prosthesis, noise suppression apparatus and feedback suppression apparatus having focused adaptive filtering |
| DK169958B1 (en) | 1992-10-20 | 1995-04-10 | Gn Danavox As | Hearing aid with compensation for acoustic feedback |
| US5500902A (en) * | 1994-07-08 | 1996-03-19 | Stockham, Jr.; Thomas G. | Hearing aid device incorporating signal processing techniques |
| WO1996032776A2 (en) † | 1995-04-03 | 1996-10-17 | Philips Electronics N.V. | Signal amplification system with automatic equalizer |
| US6097824A (en) * | 1997-06-06 | 2000-08-01 | Audiologic, Incorporated | Continuous frequency dynamic range audio compressor |
| US6434246B1 (en) † | 1995-10-10 | 2002-08-13 | Gn Resound As | Apparatus and methods for combining audio compression and feedback cancellation in a hearing aid |
| US5771299A (en) * | 1996-06-20 | 1998-06-23 | Audiologic, Inc. | Spectral transposition of a digital audio signal |
| AU744008B2 (en) * | 1997-04-16 | 2002-02-14 | Semiconductor Components Industries, Llc | Filterbank structure and method for filtering and separating an information signal into different bands, particularly for audio signals in hearing aids |
| DE19802568C2 (en) | 1998-01-23 | 2003-05-28 | Cochlear Ltd | Hearing aid with compensation of acoustic and / or mechanical feedback |
-
2000
- 2000-12-01 EP EP09155301A patent/EP2066139A3/en not_active Withdrawn
- 2000-12-01 EP EP00610124.0A patent/EP1191814B2/en not_active Expired - Lifetime
-
2001
- 2001-09-20 AU AU8959201A patent/AU8959201A/en active Pending
- 2001-09-20 JP JP2002528238A patent/JP3899023B2/en not_active Expired - Fee Related
- 2001-09-20 CA CA2417803A patent/CA2417803C/en not_active Expired - Fee Related
- 2001-09-20 AU AU2001289592A patent/AU2001289592B2/en not_active Ceased
- 2001-09-20 WO PCT/DK2001/000604 patent/WO2002025996A1/en active IP Right Grant
Cited By (1)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US11503415B1 (en) | 2021-04-23 | 2022-11-15 | Eargo, Inc. | Detection of feedback path change |
Also Published As
| Publication number | Publication date |
|---|---|
| EP1191814B1 (en) | 2009-09-09 |
| JP3899023B2 (en) | 2007-03-28 |
| WO2002025996A1 (en) | 2002-03-28 |
| EP1191814A1 (en) | 2002-03-27 |
| EP2066139A2 (en) | 2009-06-03 |
| AU2001289592B2 (en) | 2005-04-14 |
| CA2417803C (en) | 2010-11-23 |
| AU8959201A (en) | 2002-04-02 |
| EP1191814B2 (en) | 2015-07-29 |
| EP2066139A3 (en) | 2010-06-23 |
| JP2004509543A (en) | 2004-03-25 |
Similar Documents
| Publication | Publication Date | Title |
|---|---|---|
| CA2417803A1 (en) | A hearing aid with an adaptive filter for suppression of acoustic feedback | |
| EP1721488B1 (en) | Hearing aid comprising adaptive feedback suppression system | |
| EP1068773B1 (en) | Apparatus and methods for combining audio compression and feedback cancellation in a hearing aid | |
| EP2291006B1 (en) | Feedback cancellation device | |
| JP4860712B2 (en) | Hearing aid with adaptive feedback suppression | |
| KR100253539B1 (en) | Adaptive noise reduction circuit for a sound reproduction system | |
| EP1992193B1 (en) | Hearing aid and method of utilizing gain limitation in a hearing aid | |
| EP1033063B1 (en) | Feedback cancellation apparatus and methods | |
| EP1191813A1 (en) | A hearing aid with an adaptive filter for suppression of acoustic feedback | |
| US20020064291A1 (en) | Feedback cancellation apparatus and methods utilizing adaptive reference filter mechanisms | |
| AU2001289592A1 (en) | A hearing aid with an adaptive filter for suppression of acoustic feedback | |
| EP2080408A1 (en) | Entrainment avoidance with an auto regressive filter | |
| JP2004509543A5 (en) | ||
| CN113078884A (en) | Adaptive algorithm with addition of non-linear fitting | |
| EP1305975B1 (en) | Adaptive microphone array system with preserving binaural cues | |
| CN113676157B (en) | Self-adaptive filtering algorithm for counteracting direct current bias | |
| DK1068773T4 (en) | Apparatus and method for combining audio compression and feedback suppression in a hearing aid | |
| Ji et al. | An Efficient Adaptive Feedback cancellation using by Independent component analysis for hearing aids | |
| JPH05197391A (en) | Adaptive processor | |
| JP2000174592A (en) | Adaptive filter |
Legal Events
| Date | Code | Title | Description |
|---|---|---|---|
| EEER | Examination request | ||
| MKLA | Lapsed |
Effective date: 20200921 |