WO1999051059A1 - Apparatus and methods for combining audio compression and feedback cancellation in a hearing aid - Google Patents
Apparatus and methods for combining audio compression and feedback cancellation in a hearing aid Download PDFInfo
- Publication number
- WO1999051059A1 WO1999051059A1 PCT/US1999/006642 US9906642W WO9951059A1 WO 1999051059 A1 WO1999051059 A1 WO 1999051059A1 US 9906642 W US9906642 W US 9906642W WO 9951059 A1 WO9951059 A1 WO 9951059A1
- Authority
- WO
- WIPO (PCT)
- Prior art keywords
- compression
- hearing aid
- feedback cancellation
- feedback
- signal
- Prior art date
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
- H04R25/35—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception using translation techniques
- H04R25/356—Amplitude, e.g. amplitude 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
- H04R25/45—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
- H04R2225/00—Details of deaf aids covered by H04R25/00, not provided for in any of its subgroups
- H04R2225/41—Detection or adaptation of hearing aid parameters or programs to listening situation, e.g. pub, forest
-
- H—ELECTRICITY
- H04—ELECTRIC COMMUNICATION TECHNIQUE
- H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
- H04R2225/00—Details of deaf aids covered by H04R25/00, not provided for in any of its subgroups
- H04R2225/43—Signal processing in hearing aids to enhance the speech intelligibility
-
- 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
Definitions
- the present invention relates to apparatus and methods for combining audio compression and feedback cancellation in audio systems such as hearing aids.
- ITE shell establishes an acoustic feedback path that limits the maximum possible gain to less than 40 dB for a small vent and even less for large vents.
- the acoustic feedback path includes the effects of the hearing aid amplifier, receiver, and microphone as well as the vent acoustics.
- the traditional procedure for increasing the stability of a hearing aid is to reduce the gain at high frequencies. Controlling feedback by modifying the system frequency response, however, means that the desired high-frequency response of the instrument must be sacrificed in order to maintain stability.
- Phase shifters and notch filters have also been tried, but have not proven to be very effective.
- a more effective technique is feedback cancellation, in which the feedback signal is estimated and subtracted from the microphone signal.
- multiband dynamic range compression allows compression to be controlled separately in different frequency bands.
- high frequency sounds such as speech consonants, can be made louder while loud environmental noises - rumbles, traffic noise, cocktail party babble - can be attenuated.
- the primary objective of the combined audio compression and feedback cancellation processing of the present invention is to eliminate "whistling" due to feedback in an unstable hearing aid amplification system, while make soft sounds louder without making loud sounds louder, in a selectable manner according to frequency.
- the feedback cancellation element of the present invention uses one or more filters to model the feedback path of the system and thereby subtract the expected feedback from the audio signal before hearing aid processing occurs.
- the hearing aid processing includes audio compression, for example multiband compression.
- the operation of the audio compression element may be responsive to information gleaned from the feedback cancellation element, the feedback cancellation may be responsive to information gleaned from the compression element, or both.
- a hearing aid comprises a microphone for converting sound into an audio signal, feedback cancellation means including means for estimating a physical feedback signal of the hearing aid, and means for modelling a signal processing feedback signal to compensate for the estimated physical feedback signal, subtracting means, connected to the output of the microphone and the output of the feedback cancellation means, for subtracting the signal processing feedback signal from the audio signal to form a compensated audio signal, a hearing aid processor including audio compression means, connected to the output of the subtracting means, for processing the compensated audio signal, and a speaker, connected to the output of the hearing aid processor, for converting the processed compensated audio signal into a sound signal.
- the feedback cancellation means provides information to the compression means , and the compression means adjusts its operation in accordance with this information. For example, an increase in the magnitude of the zero coefficient vector can indicate the presence of an incoming sinusoid, which is likely due to feedback oscillations in the hearing aid. The maximum gain of the audio compression at low levels can be reduced if the feedback cancellation means detects an increase in the magnitude of the zero coefficient vector.
- the compression means provides information, for example input signal power levels at various frequencies, to the feedback cancellation means, and the feedback cancellation element adjusts its operation in accordance with this information.
- the feedback cancellation adaptation constant can be adjusted based upon the power level of one or more of the frequency bands of the audio compressor.
- the adaptation time constant of the feedback cancellation element could be adjusted based on the output of one of the compression bands or a weighted combination of two or more bands.
- the compression means provides information to the feedback cancellation means, and the feedback cancellation means provides information to the compression means, and each element adjusts its operation in accordance with the information obtained from the other.
- Figure 1 is a flow diagram showing a hearing aid incorporating multiband audio compression.
- Figure 2 (prior art) is a block diagram showing a hearing aid incorporating feedback cancellation.
- Figure 3 is a block diagram showing a hearing aid according to the present invention, incorporating compression and feedback cancellation.
- Figure 4 is a block diagram showing a hearing aid according to the present invention, incorporating compression and feedback cancellation, wherein the compression element modifies its operation according to information from the feedback cancellation.
- Figure 5 is a block diagram showing a hearing aid according to the present invention, incorporating compression and feedback cancellation, wherein the feedback cancellation element modifies its operation according to information from the compression element.
- Figure 6 is a flow diagram showing a hearing aid according to the present invention, incorporating compression and feedback cancellation, wherein the compression element modifies its operation according to information from the feedback cancellation, and the feedback cancellation element modifies its operation according to information from the compression element.
- FIG. 1 is a flow diagram showing an example of a hearing aid 10 incorporating multiband audio compression 40.
- This invention is described in detail in Patent Application Serial Number 08/870,426, entitled “Spectral Sampling Multiband Audio Compressor.”
- An audio input signal 52 enters microphone 12, which generates input signal 54.
- Signal 54 is converted to a digital signal by analog to digital converter 15, which outputs digital signal 56.
- Digital signal 56 is received by filter bank 16, which is implemented as a Short Time Fourier Transform system, where the narrow bins of the Fourier Transform are grouped into overlapping sets to form the channels of the filter bank.
- filter bank 16 is implemented as a Short Time Fourier Transform system, where the narrow bins of the Fourier Transform are grouped into overlapping sets to form the channels of the filter bank.
- Wavelets, FIR filter banks, and IIR filter banks could be used as the foundation for filter bank design.
- Filter bank 16 filters signal 56 into a large number of heavily overlapping bands 58.
- Each band 58 is fed into a power estimation block 18, which integrates the power of the band and generates a power signal 60.
- Each power signal 60 is passed to a dynamic range compression gain calculation block, which calculates a gain 62 based upon the power signal 60 according to a predetermined function.
- Multipliers 22 multiply each band 58 by its respective gain 62 in order to generate scaled bands 64. Scaled bands 64 are summed in adder 24 to generate output signal 68. Output signal 68 may be provided to a receiver (not shown) in hea ⁇ ng aid 10 or may be further processed.
- Figure 2 is a block diagram showing a hea ⁇ ng aid incorporating feedback cancellation.
- This invention is desc ⁇ bed m detail in Patent Application Se ⁇ al Number 08/972,265, entitled "Feedback Cancellation Apparatus and Methods.
- Feedback path modelling 250 includes the running adaptation of the zero filter coefficients.
- the se ⁇ es combination of the frozen pole filter 206 and the zero filter 212 gives a model transfer function G(z) determined du ⁇ ng start-up.
- the coefficients of the pole model filter 206 are kept at values established du ⁇ ng start-up and no further adaptation of these values takes place du ⁇ ng normal hea ⁇ ng aid operation.
- Once the hea ⁇ ng aid processing is turned, on zero model filter 212 is allowed to continuously adapt in response to changes in the feedback path as will occur, for example, when a telephone handset is brought up to the ear.
- the LMS adaptation algo ⁇ thm is used by block 210
- the adaptation is d ⁇ ven by e ⁇ or signal e(n) which is the output of the summation 208.
- the inputs to the summation 208 are the signal from the microphone 202, and the feedback cancellation signal produced by the cascade of the delay 214 with the all-pole model filter 206 in se ⁇ es with the zero model filter 212.
- the zero filter coefficients are updated using LMS adaptation m block 210.
- Figure 3 is a block diagram showing a hea ⁇ ng aid 300 according to the present invention, incorporating compression 340 and feedback cancellation 350.
- Other types of hea ⁇ ng aid processing for example direction sensitivity or noise suppression, could also be incorporated into block 340.
- An example of a compression scheme which could be used is shown in block 40 of Figure 1, but the invention is by no means limited to this particular compression scheme. Many kinds of compression could be used.
- an example of feedback cancellation is shown in block 250 of Figure 2, but many other types of feedback cancellation could be used instead, including algo ⁇ thms operating in the frequency domain as well as in the time domain.
- Microphone 202 converts input sound 100 into an audio signal. Though this is not shown, the audio signal would generally be converted into a digital signal prior to processing.
- Feedback cancellation means 350 estimates a physical feedback signal of hearing aid 300, and models a signal processing feedback signal to compensate for the estimated physical feedback signal.
- Subtracting means 208 connected to the output of microphone 202 and the output of feedback cancellation means 350, subtracts the signal processing feedback signal from the audio signal to form a compensated audio signal.
- Compression processor 340 is connected to the output of subtracting means 208, for processing the compensated audio signal.
- Speaker 220 connected to amplifier 218 at the output of hearing aid processor 340, converts the processed compensated audio signal into a sound signal. If the processed compensated audio signal is a digital signal, it is converted back to analog (not shown).
- FIG 4 is a block diagram showing a hearing aid 400 which is very similar to hearing aid 300 of Figure 3, except that compression element 440 modifies its operation according to information from feedback cancellation 450.
- the types of information available and useful to compression block 440 will vary.
- a feedback cancellation block 450 identical to 250 of Figure 2 the coefficients of zero model 212 will change with time as feedback cancellation 350 attempts to compensation for feedback. Testing one or more of these coefficients to determine whether they are outside expected ranges in magnitude, or are changing faster than expected, gives a clue as to whether feedback cancellation 350 is having difficulty compensating for the feedback. For example, an increase in the magnitude of the zero coefficient vector might indicate the presence of an incoming sinusoid.
- signal 406 would indicate to compression block 440 to lower gain at low levels, either for all frequencies or for selected frequencies.
- compression block 440 is identical to compression block 100 of Figure 1, signal 406 would be used to generate a control signal for one or more gain calculation blocks 20.
- the gain for frequencies between 1.5 KHz and 3 KHz might be lowered temporarily, as these are often the frequencies at which hearing aids are unstable.
- the kneepoint between the linear amplification function of compression 440 and the compression function at higher signal levels could be moved to a higher signal level. Once the zero model coefficients begin behaving normally, the gain applied by compression 440 can be partially or completely restored to normal.
- the attack and/or release times of the compression 440 could be modified in response to changes in the zero model coefficients.
- the compressor release time for example, can be increased when the magnitude of the zero filter coefficient vector increases and returned to its normal value when the magnitude of the zero coefficient vector decreases, thus ensuring that the compression stays at lower gains for a longer period of time when the magnitude of the zero coefficient vector is larger than normal.
- FIG 5 is a block diagram showing a hearing aid 500 which is very similar to hearing aid 300 of Figure 3, except that feedback cancellation element 550 modifies its operation according to information from compression element 540.
- the adaptation time constant of feedback cancellation 550 could be adjusted based on the output of one of the compression bands.
- the adaptive filter (zero model 212 in Figure 2) used for feedback cancellation 550 adapts more rapidly and converges to a more accurate solution when the hearing aid input signal is broadband (e.g. White noise) than when it is na ⁇ owband (e.g. A tone). Better feedback cancellation system performance can be obtained by reducing the rate of adaptation when a na ⁇ owband input signal is detected.
- the rate of adaptation is directly proportional to the parameter ( in the LMS update equation below.
- the spectral analysis performed by the multiband compression can be used to determine the approximate bandwidth of the incoming signal.
- the rate of adaptation for the adaptive feedback cancellation filter weight updates is then decreased (( made smaller) as the estimated input signal bandwidth decreases.
- the magnitude of the step size used in the LMS adaptation 210 can be made inversely proportional to the power in one or more compression bands, for example as determined by power estimation blocks 18 (see Figure 1).
- the adaptive update of the zero filter weights becomes:
- b k ( n+ 1 ) b k ( n) + - ⁇ — e ⁇ n) d( n-k) , where ⁇ 2 ( n)
- ( ⁇ .+ 1) is the kth zero filter coefficient at time n+ 1
- e(n) is the error signal provided by subtraction means 208
- d(n-k) is the input to the adaptive filter at time n delayed by k samples
- s x 2 (n) is the estimated power at time n from compression 540
- the filtered hearing aid input power can be obtained from one of the frequency bands of compression 540 (from one of power estimation blocks 18 shown in Figure 1, for example).
- This adaptation approach offers the advantage of reduced computational requirements, since the power estimate is already available from compression 540, while giving much faster adaptation at lower signal levels than is possible with a system which does not use power normalization 506.
- Feedback compensation 550 will also adjust faster when normalized based on compression 540 input power rather than feedback compensation 550 input power, because the latter signal has been compressed, raising the level of less intense signals and thus reducing the adaptation step size after power normalization.
- LMS adapt block 210 can overflow the accumulator if the input signal to hea ⁇ ng aid 500 is too high. By testing the power level of the input signal to compression 540, it is possible to determine whether the input signal is high enough to make such an overflow likely, and freeze the filter coefficients until the high input signal level drops to normal.
- s ⁇ 2 (n) is the estimated power at time n of the hea ⁇ ng aid mput signal
- g is the gain in the filter band used to estimate power
- q is the gam in pole fdter 206
- q is the maximum safe power level to avoid overflow
- the adaptive filter update is not performed for that data block. Rather, the filter coefficients are frozen at their cu ⁇ ent level until the high input signal level drops to normal.
- the magnitude of the step size used in the LMS adaptation is the magnitude of the step size used in the LMS adaptation
- the 210 can be made dependent on the envelope fluctuations detected in one or more compression bands.
- a sinusoid will have very little fluctuation in its signal envelope, while noise will typically have large fluctuations.
- the envelope fluctuations can be estimated by detecting the peaks and valleys of the signal and taking the running difference between these two values. The adaptation step size can then be made smaller as the detected envelope fluctuations decrease.
- Figure 6 is a flow diagram showing a hearing aid 600 which is very similar to hearing aid 300 of Figure 3, except that feedback cancellation element 650 modifies its operation according to information from compression element 640, and compression element 640 modifies its operation according to information from feedback cancellation 650.
Abstract
Description
Claims
Priority Applications (5)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
DK99914175.7T DK1068773T4 (en) | 1998-04-01 | 1999-03-26 | Apparatus and method for combining audio compression and feedback suppression in a hearing aid |
AT99914175T ATE286344T1 (en) | 1998-04-01 | 1999-03-26 | DEVICE AND METHOD FOR COMBINING AUDIO COMPRESSION AND FEEDBACK CANCELLATION IN A HEARING AID |
AU32075/99A AU3207599A (en) | 1998-04-01 | 1999-03-26 | Apparatus and methods for combining audio compression and feedback cancellation in a hearing aid |
DE69922940.5T DE69922940T3 (en) | 1998-04-01 | 1999-03-26 | Apparatus and method for combining audio compression and feedback cancellation in a hearing aid |
EP99914175.7A EP1068773B2 (en) | 1998-04-01 | 1999-03-26 | Apparatus and methods for combining audio compression and feedback cancellation in a hearing aid |
Applications Claiming Priority (4)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US8037698P | 1998-04-01 | 1998-04-01 | |
US60/080,376 | 1998-04-01 | ||
US09/165,825 | 1998-10-02 | ||
US09/165,825 US6434246B1 (en) | 1995-10-10 | 1998-10-02 | Apparatus and methods for combining audio compression and feedback cancellation in a hearing aid |
Publications (1)
Publication Number | Publication Date |
---|---|
WO1999051059A1 true WO1999051059A1 (en) | 1999-10-07 |
Family
ID=26763435
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
PCT/US1999/006642 WO1999051059A1 (en) | 1998-04-01 | 1999-03-26 | Apparatus and methods for combining audio compression and feedback cancellation in a hearing aid |
Country Status (6)
Country | Link |
---|---|
US (1) | US6434246B1 (en) |
EP (1) | EP1068773B2 (en) |
AT (1) | ATE286344T1 (en) |
AU (1) | AU3207599A (en) |
DE (1) | DE69922940T3 (en) |
WO (1) | WO1999051059A1 (en) |
Cited By (9)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
WO2001095578A2 (en) * | 2001-10-05 | 2001-12-13 | Phonak Ag | Method for verifying the availability of a signal component and device for carrying out said method |
US6434247B1 (en) | 1999-07-30 | 2002-08-13 | Gn Resound A/S | Feedback cancellation apparatus and methods utilizing adaptive reference filter mechanisms |
US6650124B2 (en) | 2001-10-05 | 2003-11-18 | Phonak Ag | Method for checking an occurrence of a signal component and device to perform the method |
EP1453355A1 (en) * | 2003-02-26 | 2004-09-01 | Bernafon AG | Signal processing in a hearing aid |
EP1748677A2 (en) | 2005-07-25 | 2007-01-31 | Siemens Audiologische Technik GmbH | Hearing device and method for the adjustment of an amplifying characteristic |
EP2506602A3 (en) * | 2011-03-31 | 2015-06-10 | Siemens Medical Instruments Pte. Ltd. | Hearing aid and method for operating the same |
EP1191814B2 (en) † | 2000-09-25 | 2015-07-29 | Widex A/S | A multiband hearing aid with multiband adaptive filters for acoustic feedback suppression. |
US9712908B2 (en) | 2013-11-05 | 2017-07-18 | Gn Hearing A/S | Adaptive residual feedback suppression |
US10602282B2 (en) | 2008-12-23 | 2020-03-24 | Gn Resound A/S | Adaptive feedback gain correction |
Families Citing this family (146)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US5796842A (en) * | 1996-06-07 | 1998-08-18 | That Corporation | BTSC encoder |
US8908872B2 (en) * | 1996-06-07 | 2014-12-09 | That Corporation | BTSC encoder |
JP4312389B2 (en) * | 1998-11-09 | 2009-08-12 | ヴェーデクス・アクティーセルスカプ | Method for measuring, correcting or adjusting the output signal of a hearing aid having a model processor in the field, and a hearing aid for implementing the method |
US7117149B1 (en) * | 1999-08-30 | 2006-10-03 | Harman Becker Automotive Systems-Wavemakers, Inc. | Sound source classification |
ATE289152T1 (en) | 1999-09-10 | 2005-02-15 | Starkey Lab Inc | AUDIO SIGNAL PROCESSING |
US6480610B1 (en) * | 1999-09-21 | 2002-11-12 | Sonic Innovations, Inc. | Subband acoustic feedback cancellation in hearing aids |
WO2001050459A1 (en) * | 1999-12-31 | 2001-07-12 | Octiv, Inc. | Techniques for improving audio clarity and intelligibility at reduced bit rates over a digital network |
BR0107191A (en) * | 2000-09-08 | 2002-07-16 | Koninkl Philips Electronics Nv | Methods to estimate a compression gain obtainable in the compression of a given audio signal, to record an audio signal in a recording medium, and to transmit an audio signal, a device for estimating a compression gain obtainable in the compression of a given data audio signal, recording device to record an audio signal on a recording medium, and transmitter to transmit an audio signal |
US20020075965A1 (en) * | 2000-12-20 | 2002-06-20 | Octiv, Inc. | Digital signal processing techniques for improving audio clarity and intelligibility |
US6754356B1 (en) * | 2000-10-06 | 2004-06-22 | Gn Resound As | Two-stage adaptive feedback cancellation scheme for hearing instruments |
US20030023429A1 (en) * | 2000-12-20 | 2003-01-30 | Octiv, Inc. | Digital signal processing techniques for improving audio clarity and intelligibility |
US7236929B2 (en) * | 2001-05-09 | 2007-06-26 | Plantronics, Inc. | Echo suppression and speech detection techniques for telephony applications |
US7433462B2 (en) * | 2002-10-31 | 2008-10-07 | Plantronics, Inc | Techniques for improving telephone audio quality |
US7725315B2 (en) * | 2003-02-21 | 2010-05-25 | Qnx Software Systems (Wavemakers), Inc. | Minimization of transient noises in a voice signal |
US8073689B2 (en) * | 2003-02-21 | 2011-12-06 | Qnx Software Systems Co. | Repetitive transient noise removal |
US7895036B2 (en) * | 2003-02-21 | 2011-02-22 | Qnx Software Systems Co. | System for suppressing wind noise |
US8326621B2 (en) | 2003-02-21 | 2012-12-04 | Qnx Software Systems Limited | Repetitive transient noise removal |
US7885420B2 (en) * | 2003-02-21 | 2011-02-08 | Qnx Software Systems Co. | Wind noise suppression system |
US7949522B2 (en) | 2003-02-21 | 2011-05-24 | Qnx Software Systems Co. | System for suppressing rain noise |
US8271279B2 (en) | 2003-02-21 | 2012-09-18 | Qnx Software Systems Limited | Signature noise removal |
US7092532B2 (en) * | 2003-03-31 | 2006-08-15 | Unitron Hearing Ltd. | Adaptive feedback canceller |
WO2004105430A1 (en) * | 2003-05-26 | 2004-12-02 | Dynamic Hearing Pty Ltd | Oscillation suppression |
US20040240690A1 (en) * | 2003-05-27 | 2004-12-02 | Blamey Peter J. | Oscillation detection |
WO2004105429A1 (en) * | 2003-05-26 | 2004-12-02 | Dynamic Hearing Pty Ltd | Oscillation detection |
US7809150B2 (en) * | 2003-05-27 | 2010-10-05 | Starkey Laboratories, Inc. | Method and apparatus to reduce entrainment-related artifacts for hearing assistance systems |
AU2003236382B2 (en) * | 2003-08-20 | 2011-02-24 | Phonak Ag | Feedback suppression in sound signal processing using frequency transposition |
AU2004201374B2 (en) * | 2004-04-01 | 2010-12-23 | Phonak Ag | Audio amplification apparatus |
US7756276B2 (en) * | 2003-08-20 | 2010-07-13 | Phonak Ag | Audio amplification apparatus |
US7519193B2 (en) * | 2003-09-03 | 2009-04-14 | Resistance Technology, Inc. | Hearing aid circuit reducing feedback |
CN1939092B (en) * | 2004-02-20 | 2015-09-16 | Gn瑞声达A/S | Eliminate method and the hearing aids of feedback |
EP1730992B1 (en) * | 2004-03-23 | 2017-05-10 | Oticon A/S | Hearing aid with anti feedback system |
US7691960B2 (en) * | 2004-05-19 | 2010-04-06 | Akzo Nobel N.V. | Citric acid based emulsifiers for oilfield applications exhibiting low fluorescence |
US20070106530A1 (en) * | 2004-05-26 | 2007-05-10 | Blamey Peter J | Oscillation suppression |
US20050285935A1 (en) * | 2004-06-29 | 2005-12-29 | Octiv, Inc. | Personal conferencing node |
US20050286443A1 (en) * | 2004-06-29 | 2005-12-29 | Octiv, Inc. | Conferencing system |
US7610196B2 (en) * | 2004-10-26 | 2009-10-27 | Qnx Software Systems (Wavemakers), Inc. | Periodic signal enhancement system |
US8543390B2 (en) | 2004-10-26 | 2013-09-24 | Qnx Software Systems Limited | Multi-channel periodic signal enhancement system |
US8170879B2 (en) * | 2004-10-26 | 2012-05-01 | Qnx Software Systems Limited | Periodic signal enhancement system |
US7716046B2 (en) * | 2004-10-26 | 2010-05-11 | Qnx Software Systems (Wavemakers), Inc. | Advanced periodic signal enhancement |
US7949520B2 (en) | 2004-10-26 | 2011-05-24 | QNX Software Sytems Co. | Adaptive filter pitch extraction |
US8306821B2 (en) * | 2004-10-26 | 2012-11-06 | Qnx Software Systems Limited | Sub-band periodic signal enhancement system |
US7680652B2 (en) | 2004-10-26 | 2010-03-16 | Qnx Software Systems (Wavemakers), Inc. | Periodic signal enhancement system |
DE102004053776B4 (en) * | 2004-11-08 | 2007-10-31 | Siemens Audiologische Technik Gmbh | Method for amplifying an acoustic signal and corresponding acoustic system |
US8284947B2 (en) * | 2004-12-01 | 2012-10-09 | Qnx Software Systems Limited | Reverberation estimation and suppression system |
US8027833B2 (en) | 2005-05-09 | 2011-09-27 | Qnx Software Systems Co. | System for suppressing passing tire hiss |
US8311819B2 (en) | 2005-06-15 | 2012-11-13 | Qnx Software Systems Limited | System for detecting speech with background voice estimates and noise estimates |
US8170875B2 (en) | 2005-06-15 | 2012-05-01 | Qnx Software Systems Limited | Speech end-pointer |
US8553899B2 (en) * | 2006-03-13 | 2013-10-08 | Starkey Laboratories, Inc. | Output phase modulation entrainment containment for digital filters |
US8116473B2 (en) | 2006-03-13 | 2012-02-14 | Starkey Laboratories, Inc. | Output phase modulation entrainment containment for digital filters |
US7844453B2 (en) | 2006-05-12 | 2010-11-30 | Qnx Software Systems Co. | Robust noise estimation |
WO2008051570A1 (en) | 2006-10-23 | 2008-05-02 | Starkey Laboratories, Inc. | Entrainment avoidance with an auto regressive filter |
EP2077061A2 (en) | 2006-10-23 | 2009-07-08 | Starkey Laboratories, Inc. | Entrainment avoidance with pole stabilization |
DK2095681T5 (en) * | 2006-10-23 | 2016-07-25 | Starkey Labs Inc | AVOIDING FILTER DRIVING WITH A FREQUENCY DOMAIN TRANSFORMATION ALgorithm |
US8326620B2 (en) | 2008-04-30 | 2012-12-04 | Qnx Software Systems Limited | Robust downlink speech and noise detector |
US8335685B2 (en) * | 2006-12-22 | 2012-12-18 | Qnx Software Systems Limited | Ambient noise compensation system robust to high excitation noise |
US20080231557A1 (en) * | 2007-03-20 | 2008-09-25 | Leadis Technology, Inc. | Emission control in aged active matrix oled display using voltage ratio or current ratio |
US8904400B2 (en) * | 2007-09-11 | 2014-12-02 | 2236008 Ontario Inc. | Processing system having a partitioning component for resource partitioning |
US8850154B2 (en) | 2007-09-11 | 2014-09-30 | 2236008 Ontario Inc. | Processing system having memory partitioning |
US8694310B2 (en) | 2007-09-17 | 2014-04-08 | Qnx Software Systems Limited | Remote control server protocol system |
WO2009049320A1 (en) | 2007-10-12 | 2009-04-16 | Earlens Corporation | Multifunction system and method for integrated hearing and communiction with noise cancellation and feedback management |
US9082397B2 (en) * | 2007-11-06 | 2015-07-14 | Nokia Technologies Oy | Encoder |
WO2009059631A1 (en) * | 2007-11-06 | 2009-05-14 | Nokia Corporation | Audio coding apparatus and method thereof |
US8209514B2 (en) * | 2008-02-04 | 2012-06-26 | Qnx Software Systems Limited | Media processing system having resource partitioning |
BRPI0915203A2 (en) | 2008-06-17 | 2016-02-16 | Earlens Corp | device, system and method for transmitting an audio signal, and device and method for stimulating a target tissue |
KR20110086804A (en) | 2008-09-22 | 2011-08-01 | 사운드빔, 엘엘씨 | Balanced armature devices and methods for hearing |
DE102009014540A1 (en) * | 2009-03-24 | 2010-10-07 | Siemens Medical Instruments Pte. Ltd. | Method for operating a hearing device with increased feedback compensation and hearing device |
DE102009018812B4 (en) | 2009-04-24 | 2015-05-28 | Siemens Medical Instruments Pte. Ltd. | Method for operating a hearing device and hearing device with a crossover network |
DE102009021310B4 (en) | 2009-05-14 | 2011-02-24 | Siemens Medical Instruments Pte. Ltd. | Binaural hearing apparatus and method for operating a binaural hearing apparatus with frequency distortion |
US8355517B1 (en) | 2009-09-30 | 2013-01-15 | Intricon Corporation | Hearing aid circuit with feedback transition adjustment |
US8659170B2 (en) * | 2010-01-20 | 2014-02-25 | Taiwan Semiconductor Manufacturing Company, Ltd. | Semiconductor device having conductive pads and a method of manufacturing the same |
DE102010006154B4 (en) * | 2010-01-29 | 2012-01-19 | Siemens Medical Instruments Pte. Ltd. | Hearing aid with frequency shift and associated method |
US9654885B2 (en) | 2010-04-13 | 2017-05-16 | Starkey Laboratories, Inc. | Methods and apparatus for allocating feedback cancellation resources for hearing assistance devices |
US8903109B2 (en) * | 2010-06-23 | 2014-12-02 | Stmicroelectronics, Inc. | Frequency domain multiband dynamics compressor with automatically adjusting frequency band boundary locations |
US8634578B2 (en) | 2010-06-23 | 2014-01-21 | Stmicroelectronics, Inc. | Multiband dynamics compressor with spectral balance compensation |
US9142207B2 (en) | 2010-12-03 | 2015-09-22 | Cirrus Logic, Inc. | Oversight control of an adaptive noise canceler in a personal audio device |
US8908877B2 (en) | 2010-12-03 | 2014-12-09 | Cirrus Logic, Inc. | Ear-coupling detection and adjustment of adaptive response in noise-canceling in personal audio devices |
EP2656639B1 (en) | 2010-12-20 | 2020-05-13 | Earlens Corporation | Anatomically customized ear canal hearing apparatus |
US9214150B2 (en) | 2011-06-03 | 2015-12-15 | Cirrus Logic, Inc. | Continuous adaptation of secondary path adaptive response in noise-canceling personal audio devices |
US9076431B2 (en) | 2011-06-03 | 2015-07-07 | Cirrus Logic, Inc. | Filter architecture for an adaptive noise canceler in a personal audio device |
US9824677B2 (en) | 2011-06-03 | 2017-11-21 | Cirrus Logic, Inc. | Bandlimiting anti-noise in personal audio devices having adaptive noise cancellation (ANC) |
US8848936B2 (en) | 2011-06-03 | 2014-09-30 | Cirrus Logic, Inc. | Speaker damage prevention in adaptive noise-canceling personal audio devices |
US8958571B2 (en) * | 2011-06-03 | 2015-02-17 | Cirrus Logic, Inc. | MIC covering detection in personal audio devices |
US8948407B2 (en) | 2011-06-03 | 2015-02-03 | Cirrus Logic, Inc. | Bandlimiting anti-noise in personal audio devices having adaptive noise cancellation (ANC) |
US9318094B2 (en) | 2011-06-03 | 2016-04-19 | Cirrus Logic, Inc. | Adaptive noise canceling architecture for a personal audio device |
US9325821B1 (en) * | 2011-09-30 | 2016-04-26 | Cirrus Logic, Inc. | Sidetone management in an adaptive noise canceling (ANC) system including secondary path modeling |
EP2590436B1 (en) * | 2011-11-01 | 2014-05-14 | Phonak AG | Binaural hearing device and method to operate the hearing device |
WO2013067145A1 (en) * | 2011-11-04 | 2013-05-10 | Northeastern University | Systems and methods for enhancing place-of-articulation features in frequency-lowered speech |
US9014387B2 (en) | 2012-04-26 | 2015-04-21 | Cirrus Logic, Inc. | Coordinated control of adaptive noise cancellation (ANC) among earspeaker channels |
US9142205B2 (en) | 2012-04-26 | 2015-09-22 | Cirrus Logic, Inc. | Leakage-modeling adaptive noise canceling for earspeakers |
US9076427B2 (en) | 2012-05-10 | 2015-07-07 | Cirrus Logic, Inc. | Error-signal content controlled adaptation of secondary and leakage path models in noise-canceling personal audio devices |
US9319781B2 (en) | 2012-05-10 | 2016-04-19 | Cirrus Logic, Inc. | Frequency and direction-dependent ambient sound handling in personal audio devices having adaptive noise cancellation (ANC) |
US9123321B2 (en) | 2012-05-10 | 2015-09-01 | Cirrus Logic, Inc. | Sequenced adaptation of anti-noise generator response and secondary path response in an adaptive noise canceling system |
US9082387B2 (en) | 2012-05-10 | 2015-07-14 | Cirrus Logic, Inc. | Noise burst adaptation of secondary path adaptive response in noise-canceling personal audio devices |
US9318090B2 (en) | 2012-05-10 | 2016-04-19 | Cirrus Logic, Inc. | Downlink tone detection and adaptation of a secondary path response model in an adaptive noise canceling system |
US9532139B1 (en) | 2012-09-14 | 2016-12-27 | Cirrus Logic, Inc. | Dual-microphone frequency amplitude response self-calibration |
US9107010B2 (en) | 2013-02-08 | 2015-08-11 | Cirrus Logic, Inc. | Ambient noise root mean square (RMS) detector |
US9369798B1 (en) | 2013-03-12 | 2016-06-14 | Cirrus Logic, Inc. | Internal dynamic range control in an adaptive noise cancellation (ANC) system |
US9106989B2 (en) | 2013-03-13 | 2015-08-11 | Cirrus Logic, Inc. | Adaptive-noise canceling (ANC) effectiveness estimation and correction in a personal audio device |
US9414150B2 (en) | 2013-03-14 | 2016-08-09 | Cirrus Logic, Inc. | Low-latency multi-driver adaptive noise canceling (ANC) system for a personal audio device |
US9215749B2 (en) | 2013-03-14 | 2015-12-15 | Cirrus Logic, Inc. | Reducing an acoustic intensity vector with adaptive noise cancellation with two error microphones |
US9208771B2 (en) | 2013-03-15 | 2015-12-08 | Cirrus Logic, Inc. | Ambient noise-based adaptation of secondary path adaptive response in noise-canceling personal audio devices |
US9635480B2 (en) | 2013-03-15 | 2017-04-25 | Cirrus Logic, Inc. | Speaker impedance monitoring |
US9502020B1 (en) | 2013-03-15 | 2016-11-22 | Cirrus Logic, Inc. | Robust adaptive noise canceling (ANC) in a personal audio device |
US9467776B2 (en) | 2013-03-15 | 2016-10-11 | Cirrus Logic, Inc. | Monitoring of speaker impedance to detect pressure applied between mobile device and ear |
US20140270291A1 (en) | 2013-03-15 | 2014-09-18 | Mark C. Flynn | Fitting a Bilateral Hearing Prosthesis System |
US10206032B2 (en) | 2013-04-10 | 2019-02-12 | Cirrus Logic, Inc. | Systems and methods for multi-mode adaptive noise cancellation for audio headsets |
US9066176B2 (en) | 2013-04-15 | 2015-06-23 | Cirrus Logic, Inc. | Systems and methods for adaptive noise cancellation including dynamic bias of coefficients of an adaptive noise cancellation system |
US9462376B2 (en) | 2013-04-16 | 2016-10-04 | Cirrus Logic, Inc. | Systems and methods for hybrid adaptive noise cancellation |
US9478210B2 (en) | 2013-04-17 | 2016-10-25 | Cirrus Logic, Inc. | Systems and methods for hybrid adaptive noise cancellation |
US9460701B2 (en) | 2013-04-17 | 2016-10-04 | Cirrus Logic, Inc. | Systems and methods for adaptive noise cancellation by biasing anti-noise level |
US9578432B1 (en) | 2013-04-24 | 2017-02-21 | Cirrus Logic, Inc. | Metric and tool to evaluate secondary path design in adaptive noise cancellation systems |
US9264808B2 (en) | 2013-06-14 | 2016-02-16 | Cirrus Logic, Inc. | Systems and methods for detection and cancellation of narrow-band noise |
US9392364B1 (en) | 2013-08-15 | 2016-07-12 | Cirrus Logic, Inc. | Virtual microphone for adaptive noise cancellation in personal audio devices |
US9666176B2 (en) | 2013-09-13 | 2017-05-30 | Cirrus Logic, Inc. | Systems and methods for adaptive noise cancellation by adaptively shaping internal white noise to train a secondary path |
US9620101B1 (en) | 2013-10-08 | 2017-04-11 | Cirrus Logic, Inc. | Systems and methods for maintaining playback fidelity in an audio system with adaptive noise cancellation |
US10219071B2 (en) | 2013-12-10 | 2019-02-26 | Cirrus Logic, Inc. | Systems and methods for bandlimiting anti-noise in personal audio devices having adaptive noise cancellation |
US9704472B2 (en) | 2013-12-10 | 2017-07-11 | Cirrus Logic, Inc. | Systems and methods for sharing secondary path information between audio channels in an adaptive noise cancellation system |
US10382864B2 (en) | 2013-12-10 | 2019-08-13 | Cirrus Logic, Inc. | Systems and methods for providing adaptive playback equalization in an audio device |
US9369557B2 (en) | 2014-03-05 | 2016-06-14 | Cirrus Logic, Inc. | Frequency-dependent sidetone calibration |
US9479860B2 (en) | 2014-03-07 | 2016-10-25 | Cirrus Logic, Inc. | Systems and methods for enhancing performance of audio transducer based on detection of transducer status |
US9648410B1 (en) | 2014-03-12 | 2017-05-09 | Cirrus Logic, Inc. | Control of audio output of headphone earbuds based on the environment around the headphone earbuds |
US10034103B2 (en) | 2014-03-18 | 2018-07-24 | Earlens Corporation | High fidelity and reduced feedback contact hearing apparatus and methods |
US9319784B2 (en) | 2014-04-14 | 2016-04-19 | Cirrus Logic, Inc. | Frequency-shaped noise-based adaptation of secondary path adaptive response in noise-canceling personal audio devices |
US9997171B2 (en) * | 2014-05-01 | 2018-06-12 | Gn Hearing A/S | Multi-band signal processor for digital audio signals |
JP6351538B2 (en) * | 2014-05-01 | 2018-07-04 | ジーエヌ ヒアリング エー/エスGN Hearing A/S | Multiband signal processor for digital acoustic signals. |
US9609416B2 (en) | 2014-06-09 | 2017-03-28 | Cirrus Logic, Inc. | Headphone responsive to optical signaling |
US10181315B2 (en) | 2014-06-13 | 2019-01-15 | Cirrus Logic, Inc. | Systems and methods for selectively enabling and disabling adaptation of an adaptive noise cancellation system |
EP3169396B1 (en) | 2014-07-14 | 2021-04-21 | Earlens Corporation | Sliding bias and peak limiting for optical hearing devices |
US9478212B1 (en) | 2014-09-03 | 2016-10-25 | Cirrus Logic, Inc. | Systems and methods for use of adaptive secondary path estimate to control equalization in an audio device |
US9924276B2 (en) | 2014-11-26 | 2018-03-20 | Earlens Corporation | Adjustable venting for hearing instruments |
US9552805B2 (en) | 2014-12-19 | 2017-01-24 | Cirrus Logic, Inc. | Systems and methods for performance and stability control for feedback adaptive noise cancellation |
US10026388B2 (en) | 2015-08-20 | 2018-07-17 | Cirrus Logic, Inc. | Feedback adaptive noise cancellation (ANC) controller and method having a feedback response partially provided by a fixed-response filter |
US9578415B1 (en) | 2015-08-21 | 2017-02-21 | Cirrus Logic, Inc. | Hybrid adaptive noise cancellation system with filtered error microphone signal |
DK3139636T3 (en) * | 2015-09-07 | 2019-12-09 | Bernafon Ag | HEARING DEVICE, INCLUDING A BACKUP REPRESSION SYSTEM BASED ON SIGNAL ENERGY LOCATION |
DK3355801T3 (en) | 2015-10-02 | 2021-06-21 | Earlens Corp | Adapted ear canal device for drug delivery |
US10178483B2 (en) | 2015-12-30 | 2019-01-08 | Earlens Corporation | Light based hearing systems, apparatus, and methods |
US11350226B2 (en) | 2015-12-30 | 2022-05-31 | Earlens Corporation | Charging protocol for rechargeable hearing systems |
US10492010B2 (en) | 2015-12-30 | 2019-11-26 | Earlens Corporations | Damping in contact hearing systems |
US10013966B2 (en) | 2016-03-15 | 2018-07-03 | Cirrus Logic, Inc. | Systems and methods for adaptive active noise cancellation for multiple-driver personal audio device |
CN109952771A (en) | 2016-09-09 | 2019-06-28 | 伊尔兰斯公司 | Contact hearing system, device and method |
WO2018093733A1 (en) | 2016-11-15 | 2018-05-24 | Earlens Corporation | Improved impression procedure |
US10751524B2 (en) * | 2017-06-15 | 2020-08-25 | Cochlear Limited | Interference suppression in tissue-stimulating prostheses |
WO2019173470A1 (en) | 2018-03-07 | 2019-09-12 | Earlens Corporation | Contact hearing device and retention structure materials |
WO2019199680A1 (en) | 2018-04-09 | 2019-10-17 | Earlens Corporation | Dynamic filter |
WO2020078521A1 (en) * | 2018-10-14 | 2020-04-23 | Al Shalash Taha Kais Taha | Enhance the contrast between the peaks and valleys in speech spectrum |
DK3955594T3 (en) * | 2020-08-10 | 2023-07-03 | Oticon As | FEEDBACK CONTROL USING A CORRELATION MEASURE |
Citations (4)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US4852175A (en) * | 1988-02-03 | 1989-07-25 | Siemens Hearing Instr Inc | Hearing aid signal-processing system |
US4879749A (en) * | 1986-06-26 | 1989-11-07 | Audimax, Inc. | Host controller for programmable digital hearing aid system |
EP0415677A2 (en) * | 1989-08-30 | 1991-03-06 | Gn Danavox A/S | Hearing aid having compensation for acoustic feedback |
US5027410A (en) * | 1988-11-10 | 1991-06-25 | Wisconsin Alumni Research Foundation | Adaptive, programmable signal processing and filtering for hearing aids |
Family Cites Families (14)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US3894195A (en) * | 1974-06-12 | 1975-07-08 | Karl D Kryter | Method of and apparatus for aiding hearing and the like |
US3947636A (en) * | 1974-08-12 | 1976-03-30 | Edgar Albert D | Transient noise filter employing crosscorrelation to detect noise and autocorrelation to replace the noisey segment |
US4689818A (en) | 1983-04-28 | 1987-08-25 | Siemens Hearing Instruments, Inc. | Resonant peak control |
US4718099A (en) * | 1986-01-29 | 1988-01-05 | Telex Communications, Inc. | Automatic gain control for hearing aid |
US4731850A (en) | 1986-06-26 | 1988-03-15 | Audimax, Inc. | Programmable digital hearing aid system |
US5016280A (en) | 1988-03-23 | 1991-05-14 | Central Institute For The Deaf | Electronic filters, hearing aids and methods |
US5091952A (en) † | 1988-11-10 | 1992-02-25 | Wisconsin Alumni Research Foundation | Feedback suppression in digital signal processing hearing aids |
US5019952A (en) | 1989-11-20 | 1991-05-28 | General Electric Company | AC to DC power conversion circuit with low harmonic distortion |
DK170600B1 (en) † | 1992-03-31 | 1995-11-06 | Gn Danavox As | Hearing aid with compensation for acoustic feedback |
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 |
EP0855129A1 (en) * | 1995-10-10 | 1998-07-29 | AudioLogic, Incorporated | Digital signal processing hearing aid with processing strategy selection |
US6097824A (en) * | 1997-06-06 | 2000-08-01 | Audiologic, Incorporated | Continuous frequency dynamic range audio compressor |
US6072884A (en) * | 1997-11-18 | 2000-06-06 | Audiologic Hearing Systems Lp | Feedback cancellation apparatus and methods |
-
1998
- 1998-10-02 US US09/165,825 patent/US6434246B1/en not_active Expired - Lifetime
-
1999
- 1999-03-26 DE DE69922940.5T patent/DE69922940T3/en not_active Expired - Lifetime
- 1999-03-26 AT AT99914175T patent/ATE286344T1/en not_active IP Right Cessation
- 1999-03-26 EP EP99914175.7A patent/EP1068773B2/en not_active Expired - Lifetime
- 1999-03-26 AU AU32075/99A patent/AU3207599A/en not_active Abandoned
- 1999-03-26 WO PCT/US1999/006642 patent/WO1999051059A1/en active IP Right Grant
Patent Citations (4)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US4879749A (en) * | 1986-06-26 | 1989-11-07 | Audimax, Inc. | Host controller for programmable digital hearing aid system |
US4852175A (en) * | 1988-02-03 | 1989-07-25 | Siemens Hearing Instr Inc | Hearing aid signal-processing system |
US5027410A (en) * | 1988-11-10 | 1991-06-25 | Wisconsin Alumni Research Foundation | Adaptive, programmable signal processing and filtering for hearing aids |
EP0415677A2 (en) * | 1989-08-30 | 1991-03-06 | Gn Danavox A/S | Hearing aid having compensation for acoustic feedback |
Non-Patent Citations (2)
Title |
---|
KATES J M: "FEEDBACK CANCELLATION IN HEARING AIDS: RESULTS FROM A COMPUTER SIMULATION", IEEE TRANSACTIONS ON SIGNAL PROCESSING, vol. 39, no. 3, 1 March 1991 (1991-03-01), pages 553 - 562, XP000224129, ISSN: 1053-587X * |
KATES J M: "OPTIMAL ESTIMATION OF HEARING-AID COMPRESSION PARAMETERS", JOURNAL OF THE ACOUSTICAL SOCIETY OF AMERICA, vol. 94, no. 1, 1 July 1993 (1993-07-01), pages 1 - 12, XP000383978, ISSN: 0001-4966 * |
Cited By (12)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US6434247B1 (en) | 1999-07-30 | 2002-08-13 | Gn Resound A/S | Feedback cancellation apparatus and methods utilizing adaptive reference filter mechanisms |
EP1191814B2 (en) † | 2000-09-25 | 2015-07-29 | Widex A/S | A multiband hearing aid with multiband adaptive filters for acoustic feedback suppression. |
WO2001095578A2 (en) * | 2001-10-05 | 2001-12-13 | Phonak Ag | Method for verifying the availability of a signal component and device for carrying out said method |
WO2001095578A3 (en) * | 2001-10-05 | 2002-12-19 | Phonak Ag | Method for verifying the availability of a signal component and device for carrying out said method |
US6650124B2 (en) | 2001-10-05 | 2003-11-18 | Phonak Ag | Method for checking an occurrence of a signal component and device to perform the method |
EP1453355A1 (en) * | 2003-02-26 | 2004-09-01 | Bernafon AG | Signal processing in a hearing aid |
AU2004200726B2 (en) * | 2003-02-26 | 2008-12-11 | Bernafon Ag | Signal processing in a hearing aid |
EP1748677A2 (en) | 2005-07-25 | 2007-01-31 | Siemens Audiologische Technik GmbH | Hearing device and method for the adjustment of an amplifying characteristic |
EP1748677A3 (en) * | 2005-07-25 | 2009-10-21 | Siemens Audiologische Technik GmbH | Hearing device and method for the adjustment of an amplifying characteristic |
US10602282B2 (en) | 2008-12-23 | 2020-03-24 | Gn Resound A/S | Adaptive feedback gain correction |
EP2506602A3 (en) * | 2011-03-31 | 2015-06-10 | Siemens Medical Instruments Pte. Ltd. | Hearing aid and method for operating the same |
US9712908B2 (en) | 2013-11-05 | 2017-07-18 | Gn Hearing A/S | Adaptive residual feedback suppression |
Also Published As
Publication number | Publication date |
---|---|
EP1068773A1 (en) | 2001-01-17 |
EP1068773B1 (en) | 2004-12-29 |
DE69922940T3 (en) | 2018-01-11 |
EP1068773B2 (en) | 2017-07-12 |
US20020094100A1 (en) | 2002-07-18 |
AU3207599A (en) | 1999-10-18 |
ATE286344T1 (en) | 2005-01-15 |
DE69922940D1 (en) | 2005-02-03 |
DE69922940T2 (en) | 2005-12-29 |
US6434246B1 (en) | 2002-08-13 |
Similar Documents
Publication | Publication Date | Title |
---|---|---|
EP1068773B1 (en) | Apparatus and methods for combining audio compression and feedback cancellation in a hearing aid | |
US6072884A (en) | Feedback cancellation apparatus and methods | |
EP1228665B1 (en) | Feedback cancellation apparatus and methods utilizing an adaptive reference filter | |
US6219427B1 (en) | Feedback cancellation improvements | |
US6498858B2 (en) | Feedback cancellation improvements | |
US6831986B2 (en) | Feedback cancellation in a hearing aid with reduced sensitivity to low-frequency tonal inputs | |
US7933424B2 (en) | Hearing aid comprising adaptive feedback suppression system | |
US7974428B2 (en) | Hearing aid with acoustic feedback suppression | |
US9628923B2 (en) | Feedback suppression | |
US10117029B2 (en) | Method of operating a hearing aid system and a hearing aid system | |
US9712908B2 (en) | Adaptive residual feedback suppression | |
DK1068773T4 (en) | Apparatus and method for combining audio compression and feedback suppression in a hearing aid | |
KR100363252B1 (en) | Adaptive feedback cancellation apparatus and method for multi-band compression hearing aids | |
JP3084883B2 (en) | Noise reduction device | |
US20240129659A1 (en) | Noise canceling audio headset | |
CN117177120A (en) | Noise-reducing audio earphone |
Legal Events
Date | Code | Title | Description |
---|---|---|---|
AK | Designated states |
Kind code of ref document: A1 Designated state(s): AL AM AT AU AZ BA BB BG BR BY CA CH CN CU CZ DE DK EE ES FI GB GE GH GM HR HU ID IL IS JP KE KG KP KR KZ LC LK LR LS LT LU LV MD MG MK MN MW MX NO NZ PL PT RO RU SD SE SG SI SK SL TJ TM TR TT UA UG UZ VN YU ZW |
|
AL | Designated countries for regional patents |
Kind code of ref document: A1 Designated state(s): GH GM KE LS MW SD SL SZ UG ZW AM AZ BY KG KZ MD RU TJ TM AT BE CH CY DE DK ES FI FR GB GR IE IT LU MC NL PT SE BF BJ CF CG CI CM GA GN GW ML MR NE SN TD TG |
|
121 | Ep: the epo has been informed by wipo that ep was designated in this application | ||
DFPE | Request for preliminary examination filed prior to expiration of 19th month from priority date (pct application filed before 20040101) | ||
WWE | Wipo information: entry into national phase |
Ref document number: 1999914175 Country of ref document: EP |
|
NENP | Non-entry into the national phase |
Ref country code: KR |
|
WWP | Wipo information: published in national office |
Ref document number: 1999914175 Country of ref document: EP |
|
REG | Reference to national code |
Ref country code: DE Ref legal event code: 8642 |
|
WWG | Wipo information: grant in national office |
Ref document number: 1999914175 Country of ref document: EP |