EP0836363A1 - Loudness limiter - Google Patents
Loudness limiter Download PDFInfo
- Publication number
- EP0836363A1 EP0836363A1 EP96115687A EP96115687A EP0836363A1 EP 0836363 A1 EP0836363 A1 EP 0836363A1 EP 96115687 A EP96115687 A EP 96115687A EP 96115687 A EP96115687 A EP 96115687A EP 0836363 A1 EP0836363 A1 EP 0836363A1
- Authority
- EP
- European Patent Office
- Prior art keywords
- loudness
- signal
- output
- input
- unit
- 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.)
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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
- H04R25/50—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 is directed to a method for limiting the signal transmitted to the human ear in dependence on an incoming acoustical signal and is further directed to a hearing apparatus which comprises an input acoustical/electric transducer, the output thereof being operationally connected to the input of a signal processor unit with a controllable spectral transfer characteristic, the output of this processor unit being operationally connected to the input of an output transducer for the human ear.
- Loudness of an audio signal is a psycho-acoustical entity.
- Several models have been developed to quantify the loudness which a standard individual will perceive dependent on incoming audio signals. We refer as examples to:
- the auditory filterbank is performing a transformation of the physical spectrum into a so-called excitation pattern.
- the excitation pattern, output response of the auditory filterbank can be calculated for arbitrary signal spectra, procedures are described in the literature (Moore).
- the loudness provided by the respective cochlear excitation is calculated from the contributions in each critical band, called the specific loudness and is further integrated or summed over all the bands of the auditory filterbank, yielding the total loudness of the signal spectrum.
- the parameters of the loudness model are known and standardised for normal hearing listeners and can be modified for impaired subjects accordingly, methods for the measurement of loudness model parameters of individual subjects have been proposed (S. Launer, "Loudness Perception in Listeners with Sensorineural hearing Impairment", Dissertation, Dept. of Physics, University of Oldenburg, Germany, 1995.)
- hearing aids necessitate a system for limiting the power of signals, as especially the sound pressure for electric/acoustical output transducers, which is transmitted to the human ear in dependence on incoming acoustical signals. Even under broader aspect and thus under the aspect of human ear protection in very loud environment, the need of such limiting is evident.
- PC peak clipping
- AGC automatic gain control
- the transmitted power is clamped to a threshold value.
- This has obviously the disadvantage that a considerable amount of harmonic distortion occurs as soon as the transmitted signal reaches the clipping level. It is thereby customary at hearing aids of this technique to provide the limiting threshold adjustable.
- the transmitted power is measured, compared to an admitted level and according to the result of this comparison the gain of the hearing aid apparatus is adjusted as by feedback control.
- the loudness of a transmitted signal is monitored or modelled as a test entity. This is performed by applying a model calculating the perceived loudness out of a spectrum representing an acoustical signal, and it is this loudness which is compared with a comfort loudness threshold which is standard and/or individually determined by experiments so as to limit the loudness of the transmitted signal.
- lowering the loudness is performed by lowering the loudness contributions in all or in a predominant part of the critical bands individually or by equal percentage.
- the inventive method is predominantly applied with hearing aid apparatus as the limiting apparatus.
- the spectral transfer characteristic of the apparatus is set or permanently adjusted in dependence on the loudness perceived by an individual carrying the hearing aid and of the reference loudness which would be perceived by a standard individual without hearing aid.
- the inventive hearing apparatus construed to perform the object as mentioned above comprises a presettable storing unit and a calculating unit with an input operationally connected to the output of the processor unit which calculating unit generates an output signal which is dependent on loudness of an acoustical signal represented by the signal at the input of the output transducer.
- the output of the presettable storing unit and the output of the calculating unit are operationally connected to respective inputs of a comparing unit, the output of which being operationally connected to adjusting inputs at the signal processor unit, thereby automatically adjusting its transfer characteristic.
- the transfer characteristic of the signal processor unit the resulting loudness as monitored by the calculating unit according to a preselected model is accordingly lowered down to reaching, e.g. in a negative feedback control loop or by iteration, the value as preset in the storing unit which accords to the loudness level of maximum acceptable loudness, MAL.
- an inventive limiting apparatus comprises an input acoustical/electrical transducer 1, the output thereof being operationally connected to the input of a processor unit 3, the output of which being operationally connected to an output transducer, as shown to an output electrical/mechanical transducer 5.
- the signal processor unit 3 has a transfer characteristic T(f) as a function of frequency f (in Hz, Bark or ERB) which is adjustable at control inputs E 3 as examplified with the characteristics in unit-block 3.
- the transfer function T is preferably formed by a bank of filters e.g. in parallel structure, each filter defining and thus predominantly acting in a specific spectral band, e.g. according to the critical bands of human hearing.
- a calculating unit 7 has its input operationally connected to the output of processor unit 3 and calculates loudness L(S,P) of the output signal of unit 3. This unit performs calculation of loudness L following a selected loudness model, as e.g. disclosed in the EP-0 661 905 or in S. Launer, which both references are incorporated with respect to loudness modelling into the present description.
- Selected model parameters P are input to the calculation unit 7.
- the output of the calculation unit 7 representing loudness as a psychoacoustical entity is fed to an input of a comparing unit 9, the other input of which being operationally connected to a storing unit 11 which has been loaded with the MAL-value, be it of an individual or be it as a generic standard safety value. If the loudness L-value as calculated by unit 7 reaches or exceeds the MAL-value, the comparator unit 9 acts on an adjusting unit 13 wherein transfer function control signals applied to E 3 are adjusted so as to reduce loudness L(S,P) as modelled by calculation unit 7.
- the actual loudness as transmitted to the human ear and thus perceived is monitored and the signal transferred to the human ear is reduced as soon as the monitored loudness reaches MAL.
- the processor unit 30 is construed as a filter bank with a number of band-pass filters, e.g. in parallel structure, and acting preferably each predominantly in one of the critical frequency bands or realized as a Fast-Fourier transform unit. Attention is drawn to the EP-0 661 905, especially to figs. 12a to 16, and the respective description with respect to such filter bank provided for loudness correction on an individual "I" to which, via output transducer 5, loudness corrected acoustical signals are transmitted.
- calculating unit 70a calculates, according to a loudness model selected, the loudness L I (S,P I ) which the individual "I" will perceive and as corrected by the processor unit 30 of the hearing aid.
- the model parameters P I of the individual are entered into unit 70a, for instance the parameters according to the Leijon-model, whereabout the EP-0 661 905 or S. Launer (see above) shall be considered as integral part of the present application. We draw especially the attention to fig. 15 as well as to figs. 3 to 9 and the according description of EP-0 661 905.
- the signal input to the processor unit 30 is led to a calculating unit 70b which may be implied at the same hardware unit as unit 70a and may in fact be the same unit.
- standard (N) loudness L N (S,P N ) of the incoming signal S is calculated according to standard parameters P N as also described in the EP-0 661 905 and in Launer which, here too, shall be considered as integral parts of the present description.
- the output signal of the calculating units 70 respectively representing loudness L N and L I are operationally connected to a control unit 72 wherein the two loudness values are compared.
- the control unit 72 which acts with its outputs on the control inputs E 30 which control the loudness-relevant parameters P 30 at the processor unit 30, i.e.
- the perceived and calculated actual loudness L I is compared as a single time-varying value at comparing unit 90 with the MAL-value, output from storage 110.
- the comparison result i.e. the output of the comparator unit 90, acts on an encoder unit 112 which generates a number of output signals led to weighing unit 114 whereat the parameter values emitted from control unit 72 to adjust the transfer function of unit 30 are further adjusted, thereby preventing L I to increase over MAL.
- the spectrum a) of a signal A output from the processor unit 30 is shown over frequency e.g. scaled in Barks.
- the spectrum a) leads to loudness L Ia as represented by the area which is shaded under spectrum a) well above the MAL-value.
- this is detected and the transfer function of unit 30 is adjusted, e.g. to result in a signal A according to characteristic b) which now and according to the hatched surface area below characteristic b) accords with a loudness L Ib well below MAL.
- the signal transferred to the human ear is limited according to psychoacoustical loudness perception of the human ear and not by preselecting any physical limit values.
Abstract
Description
- E. Zwicker, "Psychoakustik", Springer Verlag Berlin, Hochschultext, 1982;
- A. Leijon "Hearing Aid Gain for Loudness-Density Normalization in Cochlear Hearing Losses with Impaired Frequency Resolution", Ear and Hearing, Vol. 12, No. 4, 1990;
- EP-0 661 905 of the same applicant as the present application;
- H. Dillon, "Compression? Yes, but for low or high frequencies, for low or high intensities, and with what response times?", Ear and Hearing, Vol. 17, No. 4, 1996.
- L(P):
- loudness
- L'k (Sk(f),Pk):
- specific loudness, loudness contribution of the frequency band no. k
- Pk:
- band specific model parameters
- Sk(f):
- the physical spectrum of the signal in band no. k out of the physical spectrum S(f).
- P:
- the entity of Pk parameters
- providing a limiting hearing apparatus which generates from an input acoustical signal an output signal which is transmitted to the human ear with a controllable transfer characteristic;
- storing at the apparatus a threshold value;
- generating at the apparatus a signal which is dependent on loudness of the signal transmitted to the human ear and
- reducing loudness of the transmitted signal to the ear by automatically adjusting parameters of the transfer characteristic which determine the loudness of the signal transmitted to the human ear as soon as the signal dependent on loudness of said transmitted signal reaches the threshold value.
- fig. 1
- a highly simplified functional block/signal flow diagram of an inventive limiting apparatus performing the inventive method,
- fig. 2
- a functional block/signal flow diagram of a hearing aid apparatus construed according to the present invention and in today's preferred form,
- fig. 3
- heuristically the spectrum of a signal at the output of the inventive apparatus leading to over-loudness and limited to a loudness below or on MAL.
Claims (8)
- A method for limiting a signal transmitted to the human ear in dependence on an incoming acoustical signal,
characterized by the steps of:providing a limiting hearing apparatus generating from an input acoustical signal (S) a signal (A) transmitted to the human ear with a controllable transfer characteristic;storing at said apparatus a threshold value (MAL);generating at said apparatus a signal dependent on loudness of said transmitted signal (L(S,P); LI(S,PI));reducing loudness of said transmitted signal (A) to the ear by adjusting parameters of said transfer characteristic which determine the loudness (L; LI) of said signal (A) transmitted to the ear as soon as said signal dependent on loudness (L; LI) of said transmitted signal (A) reaches said threshold value (MAL). - The method of claim 1, characterized by implementing said limiting hearing apparatus into a hearing aid apparatus.
- The method of claim 1 or 2, characterized by the steps of individually adjusting said transfer characteristic in dependence on loudness as perceived by a specific individual and of loudness as perceived by a standard.
- The method of claim 2 or 3, further comprising the steps of:calculating loudness (LN(S,PN)) as perceived by a standard on an acoustical signal (S) input to said apparatus;calculating loudness (LI(S,PI)) as perceived from the individual on said acoustical signal and dependent on loudness of said transmitted signal (A);calculating a desired hearing aid transfer characteristic from said calculated loudnesses of standard and individual;adjusting said transfer characteristic (T) of said hearing aid according to said desired transfer characteristic;performing said limiting by additionally adjusting said desired transfer characteristic in dependence on said loudness of said transmitted signal (A) and said threshold value (MAL).
- A hearing apparatus, comprisingan input acoustical/electric transducer (1), the output thereof being operationally connected to the input ofa signal processor unit (3; 30) with a controllable transfer characteristic (T), the output thereof being operationally connected to an input ofan output transducer (5) for the human ear,a presettable storing unit (11; 110);a calculating unit (7; 70a), the input thereof being operationally connected to the output of said processor unit (3, 30) and generating an output signal which is dependent on loudness of an acoustical signal represented by said signal at the input of said output transducer (5), wherebythe outputs of said calculating unit (7; 70a) and of said presettable unit (11; 110) are operationally connected to respective inputs of a comparing unit (9; 72);the output of said comparing unit (9; 72) is operationally connected to adjusting inputs (E3; E30) for said characteristic of said processor unit (3; 30).
- The apparatus of claim 5, characterized by said transducers (1, 5) and said processor unit (3; 30) being part of a hearing aid apparatus.
- The apparatus of claim 6, characterized bya second calculating unit (70b), the input thereof being operationally connected to the output of said input transducer (1) and generating an output signal representing a standard loudness of an acoustical signal input to said input transducer (1);the outputs of said one and said further calculating units (70a, 70b) being operationally connected to a third calculating unit (72);the output of said further calculating unit (72) being operationally connected to said adjusting inputs (E30).
- The apparatus of the claims 5 to 7, characterized by the facts that said processor unit (3; 30) comprises a predetermined number of band-pass filters, each predominantly acting in a respective spectral band, said adjusting inputs (E3; E30) being operationally connected to adjusting inputs of said filters.
Priority Applications (4)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
AT96115687T ATE249134T1 (en) | 1996-10-01 | 1996-10-01 | VOLUME LIMIT |
DE69629814T DE69629814T2 (en) | 1996-10-01 | 1996-10-01 | Volume Limit |
EP96115687A EP0836363B1 (en) | 1996-10-01 | 1996-10-01 | Loudness limiter |
DK96115687T DK0836363T3 (en) | 1996-10-01 | 1996-10-01 | Limits to sound impressions |
Applications Claiming Priority (1)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
EP96115687A EP0836363B1 (en) | 1996-10-01 | 1996-10-01 | Loudness limiter |
Publications (2)
Publication Number | Publication Date |
---|---|
EP0836363A1 true EP0836363A1 (en) | 1998-04-15 |
EP0836363B1 EP0836363B1 (en) | 2003-09-03 |
Family
ID=8223242
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
EP96115687A Expired - Lifetime EP0836363B1 (en) | 1996-10-01 | 1996-10-01 | Loudness limiter |
Country Status (4)
Country | Link |
---|---|
EP (1) | EP0836363B1 (en) |
AT (1) | ATE249134T1 (en) |
DE (1) | DE69629814T2 (en) |
DK (1) | DK0836363T3 (en) |
Cited By (10)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
WO2009124035A3 (en) * | 2008-03-31 | 2009-12-30 | Cochlear Americas | Objective fiting of a hearing prosthesis |
US8019432B2 (en) | 2005-10-31 | 2011-09-13 | Cochlear Limited | Provision of stimulus components having variable perceptability to stimulating device recipient |
EP2369859A2 (en) | 2008-05-30 | 2011-09-28 | Phonak Ag | Method for adapting sound in a hearing aid device by frequency modification and such a device |
US8190268B2 (en) | 2004-06-15 | 2012-05-29 | Cochlear Limited | Automatic measurement of an evoked neural response concurrent with an indication of a psychophysics reaction |
US8213653B2 (en) | 2006-05-10 | 2012-07-03 | Phonak Ag | Hearing device |
US8260430B2 (en) | 2010-07-01 | 2012-09-04 | Cochlear Limited | Stimulation channel selection for a stimulating medical device |
US8401656B2 (en) | 2002-06-26 | 2013-03-19 | Cochlear Limited | Perception-based parametric fitting of a prosthetic hearing device |
US8571675B2 (en) | 2006-04-21 | 2013-10-29 | Cochlear Limited | Determining operating parameters for a stimulating medical device |
US9392378B2 (en) | 2011-08-15 | 2016-07-12 | Oticon A/S | Control of output modulation in a hearing instrument |
US9744356B2 (en) | 2004-06-15 | 2017-08-29 | Cochlear Limited | Automatic determination of the threshold of an evoked neural response |
Families Citing this family (1)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US10842418B2 (en) | 2014-09-29 | 2020-11-24 | Starkey Laboratories, Inc. | Method and apparatus for tinnitus evaluation with test sound automatically adjusted for loudness |
Citations (4)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US4475230A (en) * | 1981-08-07 | 1984-10-02 | Rion Kabushiki Kaisha | Hearing aid |
EP0237203A2 (en) * | 1986-03-12 | 1987-09-16 | Beltone Electronics Corporation | Hearing aid circuit |
WO1994023548A1 (en) * | 1993-04-07 | 1994-10-13 | Central Institute For The Deaf | Adaptive gain and filtering circuit for a sound reproduction system |
EP0661905A2 (en) * | 1995-03-13 | 1995-07-05 | Phonak Ag | Method for the fitting of hearing aids, device therefor and hearing aid |
-
1996
- 1996-10-01 DE DE69629814T patent/DE69629814T2/en not_active Expired - Lifetime
- 1996-10-01 EP EP96115687A patent/EP0836363B1/en not_active Expired - Lifetime
- 1996-10-01 DK DK96115687T patent/DK0836363T3/en active
- 1996-10-01 AT AT96115687T patent/ATE249134T1/en not_active IP Right Cessation
Patent Citations (4)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US4475230A (en) * | 1981-08-07 | 1984-10-02 | Rion Kabushiki Kaisha | Hearing aid |
EP0237203A2 (en) * | 1986-03-12 | 1987-09-16 | Beltone Electronics Corporation | Hearing aid circuit |
WO1994023548A1 (en) * | 1993-04-07 | 1994-10-13 | Central Institute For The Deaf | Adaptive gain and filtering circuit for a sound reproduction system |
EP0661905A2 (en) * | 1995-03-13 | 1995-07-05 | Phonak Ag | Method for the fitting of hearing aids, device therefor and hearing aid |
Cited By (13)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US8401656B2 (en) | 2002-06-26 | 2013-03-19 | Cochlear Limited | Perception-based parametric fitting of a prosthetic hearing device |
US8694113B2 (en) | 2002-06-26 | 2014-04-08 | Cochlear Limited | Parametric fitting of a cochlear implant |
US8190268B2 (en) | 2004-06-15 | 2012-05-29 | Cochlear Limited | Automatic measurement of an evoked neural response concurrent with an indication of a psychophysics reaction |
US9744356B2 (en) | 2004-06-15 | 2017-08-29 | Cochlear Limited | Automatic determination of the threshold of an evoked neural response |
US10449357B2 (en) | 2004-06-15 | 2019-10-22 | Cochlear Limited | Automatic determination of the threshold of an evoked neural response |
US8019432B2 (en) | 2005-10-31 | 2011-09-13 | Cochlear Limited | Provision of stimulus components having variable perceptability to stimulating device recipient |
US8571675B2 (en) | 2006-04-21 | 2013-10-29 | Cochlear Limited | Determining operating parameters for a stimulating medical device |
US8213653B2 (en) | 2006-05-10 | 2012-07-03 | Phonak Ag | Hearing device |
WO2009124035A3 (en) * | 2008-03-31 | 2009-12-30 | Cochlear Americas | Objective fiting of a hearing prosthesis |
US8945216B2 (en) | 2008-03-31 | 2015-02-03 | Cochlear Limited | Objective fitting of a hearing prosthesis |
EP2369859A2 (en) | 2008-05-30 | 2011-09-28 | Phonak Ag | Method for adapting sound in a hearing aid device by frequency modification and such a device |
US8260430B2 (en) | 2010-07-01 | 2012-09-04 | Cochlear Limited | Stimulation channel selection for a stimulating medical device |
US9392378B2 (en) | 2011-08-15 | 2016-07-12 | Oticon A/S | Control of output modulation in a hearing instrument |
Also Published As
Publication number | Publication date |
---|---|
DE69629814T2 (en) | 2004-08-05 |
DK0836363T3 (en) | 2003-12-15 |
DE69629814D1 (en) | 2003-10-09 |
ATE249134T1 (en) | 2003-09-15 |
EP0836363B1 (en) | 2003-09-03 |
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