WO2001001731A1 - Procede de commande de la directionalite de la caracteristique de reception de son d'une aide auditive, et aide auditive dans laquelle est applique ledit procede - Google Patents

Procede de commande de la directionalite de la caracteristique de reception de son d'une aide auditive, et aide auditive dans laquelle est applique ledit procede Download PDF

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Publication number
WO2001001731A1
WO2001001731A1 PCT/DK2000/000339 DK0000339W WO0101731A1 WO 2001001731 A1 WO2001001731 A1 WO 2001001731A1 DK 0000339 W DK0000339 W DK 0000339W WO 0101731 A1 WO0101731 A1 WO 0101731A1
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WO
WIPO (PCT)
Prior art keywords
hearing aid
signal
signals
characteristic
omni
Prior art date
Application number
PCT/DK2000/000339
Other languages
English (en)
Inventor
Lars Baekgaard Jensen
Original Assignee
Widex A/S
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by Widex A/S filed Critical Widex A/S
Priority to CA002385812A priority Critical patent/CA2385812C/fr
Priority to DK00938590T priority patent/DK1203508T3/da
Priority to AT00938590T priority patent/ATE248496T1/de
Priority to AU53916/00A priority patent/AU766876B2/en
Priority to DE60004863T priority patent/DE60004863T2/de
Priority to EP00938590A priority patent/EP1203508B1/fr
Priority to JP2001506270A priority patent/JP3914768B2/ja
Publication of WO2001001731A1 publication Critical patent/WO2001001731A1/fr

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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
    • H04R25/40—Arrangements for obtaining a desired directivity characteristic
    • H04R25/407—Circuits for combining signals of a plurality of transducers
    • 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
    • H04R25/40—Arrangements for obtaining a desired directivity characteristic
    • H04R25/405—Arrangements for obtaining a desired directivity characteristic by combining a plurality of transducers
    • 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

Definitions

  • a method for controlling the directionality of the sound receiving characteristic of a hearing aid and a hearing aid for carrying out the method is a method for controlling the directionality of the sound receiving characteristic of a hearing aid and a hearing aid for carrying out the method.
  • the present invention relates to a method for controlling the directionality of the sound receiving characteristic of a hearing aid comprising spaced apart first and second sound receiving microphone means, a signal processor for processing signals supplied by said microphone means and an output transducer for emission of sound signals in response to output signals from the signal processor, said method comprising the steps of changing over said sound receiving characteristic between an omnidirectional characteristic and a directional characteristic and, when operating the hearing aid with said directional characteristic, combining the signals supplied by said first and second microphone means into an overall combined signal, which is supplied to the signal processor, an adjustable time or phase delay being imposed on at least one signal .
  • Hearing aids having a directional sound receiving characteristic are useful to improve speech perception in noisy environments, where human speech may be received simultaneously from different directions, as is the case e.g. in the noise environment frequently referred to as cocktail party noise.
  • a directional sound receiving characteristic e.g. in the shape of a cardioid or super cardioid characteristic
  • the speech perception in a hearing aid is improved by reduced reception of sound coming from the back of the user, while maintaining the level of sound coming from the area in front of the user.
  • the phase and time relationship in a hearing aid degrades the quality of the sound perceived by the user. It may sound like the result of a Doppler-effect .
  • the amplitude characteristic will change during transition between the omnidirectional and a directional characteristic, e.g. from a flat response to a response in which the amplitudes of higher frequencies will be increased. This increase may be in the area of 6 dB/octave . This results in the serious problem, that hearing aids of this type can not be perfectly fitted with an optimum transfer characteristic for both the omnidirectional and the directional characteristic.
  • the object of the present invention to provide a method of the kind defined, in which the deficiencies of the prior art hearing aid are remedied by effecting a smooth changeover between the omnidirectional characteristic and any directional characteristic substantially without changing the phase relationship or time delay and the amplitude characteristic of the signals.
  • the changeover between the omnidirectional characteristic and a directional characteristic and vice versa may be controllable or even automatic.
  • this object is achieved by a method of the kind defined, which is characterized in that said change-over of the sound receiving characteristic from the omnidirectional characteristic to the directional characteristic and vice versa is effected by controlled attenuation and time or phase delay of signals deriverd from both of the signals
  • the invention further relates to a hearing aid with controllable directionality of its sound receiving characteristic, comprising spaced apart first and second sound receiving microphone means, a signal processor for processing signals supplied by said microphone means and an output transducer for emission of sound signals in response to output signals from the signal processor, and further comprising change-over control means for change over of the sound receiving characteristic between an omnidirectional characteristic and a directional characteristic and combining means for combination of the signal from the first and second microphone means to provide an overall combined signal supplied to the signal processor, when operating the hearing aid with said directional characteristic, and adjustable time or phase delay means being provided for producing a phase-delayed modification of at least one signal .
  • fig. 1 is a schematic block diagram of the prior art hearing aid of US-A-5 , 757, 933
  • figs. 2 - 5 are graphic representations illustrating variation of the sound receiving characteristic of the hearing aid in fig. 1 between the omnidirectional characteristic and different directional shapes and concurrent variation of amplitude characteristics of the front and back microphones used therein
  • fig. 6 shows a schematic arrangement of the front end of a first embodiment of a hearing aid according to the present invention
  • figs. 7 to 10 are graphic representation corre- sponding to the representations in figs. 2 to 5 with respect the hearing aid shown in fig. 6, fig.
  • FIG. 11 shows a schematic arrangement of a second embodiment
  • fig. 12 shows a similar schematic arrangement of a third embodiment
  • fig. 13 schematically shows a further improvement of the arrangement shown in fig. 6,
  • fig. 14 shows a still further development of a hearing aid embodying the invention.
  • two non-directional microphone circuits including a front microphone MICF and a back microphone MICB.
  • the output signal from the front microphone MICF is supplied directly to the hearing aid signal processor via a summing node SN
  • the signal from the back microphone is supplied to the summing node SN via an inverter, an adjustable phase delay circuit and an attenuator with adjustable gain only by closure of a manually operated switch SW, whereby the sound receiving characteristic of the hearing is changed from the omnidirectional characteristic of front microphone
  • MICF MICF to a directional characteristic of varying shape.
  • the adjustable parameter omni represents the adjustable gain of the attenuator
  • T represents the adjustable time delay corresponding to the difference in arrival time for sound signals received by the front and back microphones MICF and MICB, respectively.
  • the graphic representations in figs . 2 and 3 illustrate the variation of the sound receiving characteristic of the hearing aid in figure 1 from the omnidirectional shape ND and various directional shapes Dl to D10 ranging from weak cardioid to super cardioid form for values of the adjustable parameter omni ranging from 0 to 1, measured at 1kHz and 100 Hz, respectively, whereas the graphic representations in figs. 4 and 5 show the variation in the amplitude characteristics of the signals received from the areas in front and back of the hearing aid, respectively, for correspondingly varying values of the parameter omni .
  • FIG. 6 shows, in principle, the front end of a first embodiment of a hearing aid according to the inventions including a change-over controller for controlling change of the directionality of sound receiving characteristic of the hearing aid from the omnidirectional characteristic to a directional characteristic and vice versa.
  • This change may be effected as a switch-over or as a gradual and smooth change-over.
  • the front end of the hearing aid comprises at least two microphone circuits, i.a. a front microphone Fmic and a back microphone Bmic and possibly optional preprocessing circuits for the electrical output signals from the microphones .
  • the distance between the two microphones may be as small as 1 mm or as wide as a few cm.
  • the front end further contains at least two controllable amplifiers or attenuators 1 and 2, at least one time or phase delay device 3 and at least three combining circuits 4, 5 and 6. It is to be understood that the combining circuits may contain positive as well as negative input terminals, so as to form adding or subtraction operations or combinations thereof .
  • the back microphone Bmic is connected to the controllable amplifier or attenuator 1 and to a first adding circuit 4.
  • the front microphone Fmic is connected directly to the controllable amplifier or attenuator 2 and to a second adding circuit 6.
  • the output of the controllable amplifier or attenuator 2 is further connected directly to a second input of the first adding circuit 4, whereas the output of the controllable amplifier 1 is directly connected to a positive input of a subtraction circuit 5.
  • a preferable controllable delay device 3 is included.
  • the adding and subtracting circuits will generally be referred to as combining circuits.
  • sounds from the environment of the hearing aid is picked up both by the front microphone Fmic and the back microphone Bmic.
  • the distance between the two microphones may be as small as 1 mm and as wide as a few cm.
  • the output signal of the front microphone Fmic is supplied to the combining circuit 6.
  • the output signal of the back microphone Bmic is supplied to the controllable attenuator or controllable amplifier 1, the gain of which may be controllably changed from zero to one, i.e. from no amplification to full amplification. This change-over may be effected as a switchover or as a controlled gradual change. This means that any amplification between zero and one may be controllably achieved.
  • the output signal, if any, of the front microphone Fmic is also supplied to a controllable attenuator or amplifier 2, the amplification of which may controllably be changed from zero to one, i.e. from no amplification to full amplification. Also in this case the change-over may be effected as a switch-over or as a gradual controlled change. This means that any amplification between zero and one may be achieved.
  • the output signal, if any, of the controllable attenuator or amplifier 1 is supplied to a second input of the combining circuit 4.
  • the output signal, if any, of combining circuit 5 is supplied to the controllable delay device 3, the delay of which may be controlled from as small as 1 ⁇ s up to 1000 ⁇ s or more.
  • the output signal, if any, of delay device 3 is supplied to the negative input of combining circuit 5, the output of which is supplied to the second input of the combining circuit 6.
  • the output signal of the front microphone Fmic may be attenuated in attenuator or controllable amplifier 2 before it is added to the undelayed output signal of the back microphone Bmic in the combining circuit 4, the output signal of which is then delayed in delay device 3 before being supplied to the combining circuit 5.
  • the controllable delay of delay device 3 will usually have the same value as the acoustical delay between the arrival times of sounds at the front microphone Fmic and at the back microphone Bmic. Preferably this delay is also adjustable and/or controllable.
  • the output signal of the attenuator or controllable amplifier 1 is supplied to the positive input of the combining circuit 5.
  • the delayed output signal of delay device 3 is subtracted from the attenuated output signal of amplifier or attenuator 1.
  • the output signal of the combining circuit 5 is supplied, as a processed signal to the combining circuit 6.
  • the output signal of the combining circuit 6 is then used as an input signal for further processing in the remaining components of the hearing aid such as the signal processor, which need not to be described here .
  • the remaining parts of the hearing aid may. as known in the art, comprise more than one signal processing channel having, and with such a structure either a common change-over controller or a separate controller for each channel may be provided.
  • the output signals of both microphones Fmic and Bmic may advantageously be converted into a digital representation before being supplied to the change-over controller with its components 1 to 6.
  • the function of the circuit in fig. 6 is as follows : For the directional mode of operation the signal transfer of the controllable attenuators 1 and 2 is set at zero, i.e. no signal is transferred.
  • the output signal of the front microphone Fmic is directly supplied to the second adding circuit 6.
  • the output signal of the back microphone Bmic is supplied via the first adding circuit 4 and delay device 3 to the negative input of the subtraction circuit 5, where the signal changes its polarity.
  • the output signal of the subtraction circuit 5 is then supplied to a second input of the second adding circuit 6.
  • the delayed signal from the back microphone Bmic is subtracted from the undelayed output signal of the front microphone Fmic .
  • the directional front characteristic may then be created by adjusting the delay T of the delay device to be the same as the acoustical delay A between the back microphone Bmic and the front microphone Fmic. With this delay the signals, that are first received at the back microphone Bmic and are later received at the front microphone Fmic, are then suppressed in the adding circuit 6, where the delayed signal of the back microphone is subtracted from the output signal of the front microphone .
  • This mode of operation results in an output signal from adding circuit 6, which is the result of the subtraction of the delayed output signal of the back microphone Bmic from the output signal of the front microphone Fmic, thus cancelling sound coming directly from the back of the user.
  • T ⁇ A By adjusting T ⁇ A, sound coming partly from the side of the user is cancelled, the direction of the cancelling effect is controlled by the ratio of T/A.
  • both attenuators 1 and 2 are set for a full signal transfer.
  • the output signals from the front microphone Fmic and the back microphone Bmic are supplied to the first adding circuit 4, where they are combined and supplied via delay device 3 to the subtraction circuit 5, where the combined and delayed signal is subtracted from the output signal of the back microphone Bmic.
  • the output signal of the subtraction circuit 5 is then supplied to the second adding circuit 6, where it is combined with the undelayed output signal of the front microphone Fmic.
  • the addition of these signals creates the omnidirectional characteristic .
  • This mode of operation results in an output signal from the adding circuit 6, which is generated by the addition of the signals from the front and back microphones from which the delayed front and back microphone signals are subtracted.
  • the sound signals received at the two microphones differ with respect to their arrival time at the respective microphones from a source, the distance of which is different for the two respective microphones .
  • This difference is the acoustical delay A and the relationship between the sound signals X front and X baC k received at the front and back microphones, respectively, may be generally expressed as
  • the combined signal Y from adding circuit 6 is
  • the parameter omni should preferably be substantially the same for both attenuators 1 and 2.
  • the delay T is selected equal to the delay A directly from the back microphone to the front microphone in the directional mode of operation, then the part of the sound signal X coming directly from the back of the user is suppressed to the maximum extent and a directional characteristic known as a cardioid characteristic is achieved.
  • the signal process described so far is preferably performed as a digital process in the time or frequency domain. If processing in the frequency domain is employed, it is advantageous to use microphone circuits, omni which are capable of generating a delayed microphone output signal in combination with a non-delayed microphone output signal. Such microphone circuits are described in applicants ' copending International Patent Application PCT/EP/99/00767.
  • Figs. 7 to 10 are graphic representations of sound receiving characteristics and amplitude response of a hearing aid embodying the front end part shown in fig.l and corresponding to the representations in figs. 2 to 5 and using the same reference designations as in these figures, As will appear from figs. 7 and 8 the part of the sound receiving characteristic representing the area in front of the user is unaffected by the change over between the omnidirectional characteristic ND and the various directional shapes Dl to D10 and as illustrated by fig. 10 the amplitude response of signals received from the area in front of the user is unaffected by the change over and remains the same irrespective of change of the sound receiving characteristic to suppress sounds coming from the area behind the user.
  • the adjustment or fitting of the hearing aid to compensate for the user's hearing impairment in quiet surroundings, where the omnidirectional characteristic is used will provide optimum listening performance also when the hearing aid is used in a more noisy environment using a directional shape of the sound receiving characteristic.
  • the circuit in fig. 11 is similar to the circuit in fig. 6 and includes a change-over controller with components 1 to 6. Similar components have been assigned the same reference numerals.
  • signal processing units 7 and 8 are placed at the outputs of the at least two microphones, i.e. the front microphone Fmic and the back microphone Bmic.
  • the processed output signals of the two signal processing units 7 and 8 are then supplied to the change-over controller with components 1 to 6.
  • the signal processing units 7 and 8 may perform an equalizing function on the two output signals of the two microphones and/or may contain various filters, e.g. band pass filters. With the use of band pass filters the microphone signals may be split up into several bands, each equipped with its own change-over controller.
  • the respective output signals from the adding circuits 6 in the various bands or channels may then be combined into a composite combined signal to be further processed in the remaining stages of the hearing aid.
  • Fig. 12 shows a similar circuit diagram of a third embodiment, so that for the same components the same reference numerals are used.
  • this circuit the time delay for the output signals of the two microphones Fmic and Bmic is effected in separate delay units 3a and 3b representing the delay device 3.
  • the function is similar to the function of the circuits of figs. 6 and 11.
  • a control unit 9 is shown, which may control the attenuation of the controllable attenuators 1 and 2 as well as the delays of delay units 3a and 3b.
  • This embodiment of the invention is of special advantage in combination with microphone input circuits, which are capable of supplying a delayed microphone signal together with an undelayed microphone signal for a hearing aid. Such a circuit has been disclosed and described in applicants' copending Inter- national Patent Application PCT/EP99/00767.
  • Fig. 13 schematically shows a further improvement of the front end circuit of a hearing aid including a change-over controller as described so far with reference to fig. 6. Similar components have been designated with the same reference numerals as before.
  • the resulting amplitude response of the output signals of the adding means 6 will - of course - in the relevant frequency range - rise with 6 dB per octave compared to the amplitude response of a single microphone .
  • the change-over controller of the present invention could also be adapted to perform this compensation filtering. Therefore there will be no need to add a filter at the output of the adding circuit 6.
  • an additional subtraction circuit 10 is arranged between the adding circuit 4 and the delay device 3, an the output signal of the adding circuit 6 is directly supplied to the negative input of adding means 10 in a feedback loop.
  • controllable amplifier or attenuator 11 into the feedback loop.
  • the output signal of the change-over controller is fed back from the adding circuit 6 via the controllable attenuator 11 to the negative input of subtraction circuit 10.
  • the output signal of attenuator 11 is subtracted in the subtraction circuit 10 from the output signal of adding circuit 4.
  • subtraction circuit 5 and adding circuit 6 are supplied to the delay device 3 and hence to the negative input of the subtraction circuit 5, the positive input of which is connected to the output of the controllable attenuator 1.
  • subtraction circuit 5 and adding circuit 6 could also be combined into a single combining circuit, provided this has, in every respect, the same properties as the two separate adding means 5 and 6.
  • the gain factor of attenuator 11 should be one or unity for the filtering being able to perform the 6 dB per octave fall at very low frequencies. However, this would probably result in a loop gain of unity so that the circuit might become unstable. Therefore, it is preferred to have the gain of the amplifier or attenuator 11 set to a little less than one or unity.
  • the change-over means comprises a first adding circuit 12 connected with the front and back microphones Fmic and Bmic and a first subtraction circuit 13 having a positive input connected with the front microphone Fmic and a negative input connected with the back microphone Bmic.
  • First and second phase delay devices 14 and 15 are connected with the first subtraction and adding circuits 13 and 12, respectively.
  • a second adding circuit 16 is connected with the first subtraction circuit 13 and the first phase delay device 14 and a second subtracting circuit 17 has its positive input connected with the first adding circuit 12 and its negative input connected with second phase delay device 15.
  • a first controllable attenuator 18 acts on the signal from the second adding circuit 16 for attenuation of this signlal by a factor (1 - omni) / 2 and a second controllable attenuator 19 acts on the signal from the second subtraction circuit
  • a third adding circuit 20 is connected with the first and second attenuators 18 and 19 for addition of the signals therefrom to provide the overall combined signal to be supplied to the signal processor.
  • the microphones used in the described embodiments are preferably omnidirectional microphones.
  • both microphones When two microphones are used in the omnidirectional mode of operation, both microphones generate an electrical noise signal N. These two noise signals have a similar power:
  • N back is the noise signal from the back microphone Bmic
  • N front is the noise signal from the front microphone Fmic
  • the noise signals N are random signals . Therefore, the resulting signal amplitude is less than twice the single amplitude . Thus , a 3 dB-noise reduction results .
  • the total noise signal can be calculated as :

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  • 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)
  • Circuit For Audible Band Transducer (AREA)
  • Networks Using Active Elements (AREA)
  • Circuits Of Receivers In General (AREA)
  • Stereophonic System (AREA)

Abstract

L'invention concerne le changement de la caractéristique de réception de son d'une aide auditive équipée d'un premier et d'un second microphone séparés (Fmic, Bmic), passant de l'état de caractéristique omnidirectionnelle à l'état de caractéristique directionnelle, changement obtenu par une atténuation commandée et un retard temporel ou de phase de signaux dérivés des signaux (Xavant, Xarrière) du premier et du second microphone, avant de former un signal global combiné (Y) à transmettre au processeur de signaux de l'aide auditive. Le signal global combiné (Y) est déterminé par Y = Xavant * (1 - omni * e?-jφT¿) + X¿arrière? * omni - e?-jφT¿), omni étant un paramètre de commande d'atténuation réglable correspondant, de préférence, à 0 ≤ omni ≤ 1, et T étant un retard temporel correspondant au retard acoustique entre le premier et le second microphone. Par conséquent, le changement d'état de la caractéristique omnidirectionnelle à toute forme désirée de caractéristique directionnelle représente un léger changement n'affectant sensiblement pas la relation de phase, le retard temporel et la caractéristique d'amplitude de l'aide auditive.
PCT/DK2000/000339 1999-06-24 2000-06-23 Procede de commande de la directionalite de la caracteristique de reception de son d'une aide auditive, et aide auditive dans laquelle est applique ledit procede WO2001001731A1 (fr)

Priority Applications (7)

Application Number Priority Date Filing Date Title
CA002385812A CA2385812C (fr) 1999-06-24 2000-06-23 Procede de commande de la directionalite de la caracteristique de reception de son d'une aide auditive, et aide auditive dans laquelle est applique ledit procede
DK00938590T DK1203508T3 (da) 1999-06-24 2000-06-23 Fremgangsmåde til styring af retningsafhængigheden af lydmodtagelseskarakteristikken for et høreapparat og et høreapparat til udførelse af fremgangsmåden
AT00938590T ATE248496T1 (de) 1999-06-24 2000-06-23 Eine methode zur regelung der richtwirkung der schallempfangscharakteristik eines hörgerätes und ein hörgerät zur ausführung der methode
AU53916/00A AU766876B2 (en) 1999-06-24 2000-06-23 A method for controlling the directionality of the sound receiving characteristic of a hearing aid and a hearing aid for carrying out the method
DE60004863T DE60004863T2 (de) 1999-06-24 2000-06-23 EINE METHODE ZUR REGELUNG DER RICHTWIRKUNG DER SCHALLEMPFANGSCHARAkTERISTIK EINES HÖRGERÄTES UND EIN HÖRGERÄT ZUR AUSFÜHRUNG DER METHODE
EP00938590A EP1203508B1 (fr) 1999-06-24 2000-06-23 Procede de commande de la directionalite de la caracteristique de reception de son d'une aide auditive, et aide auditive dans laquelle est applique ledit procede
JP2001506270A JP3914768B2 (ja) 1999-06-24 2000-06-23 補聴器の受音特性の指向性を制御する方法およびその方法を実施するための補聴器

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
PCT/EP1999/004375 WO2001001732A1 (fr) 1999-06-24 1999-06-24 Prothese auditive possedant des caracteristiques directionnelles pouvant etre commandees
EPPCT/EP99/04375 1999-06-24

Publications (1)

Publication Number Publication Date
WO2001001731A1 true WO2001001731A1 (fr) 2001-01-04

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PCT/EP1999/004375 WO2001001732A1 (fr) 1999-06-24 1999-06-24 Prothese auditive possedant des caracteristiques directionnelles pouvant etre commandees
PCT/DK2000/000339 WO2001001731A1 (fr) 1999-06-24 2000-06-23 Procede de commande de la directionalite de la caracteristique de reception de son d'une aide auditive, et aide auditive dans laquelle est applique ledit procede

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JP (1) JP3914768B2 (fr)
AT (1) ATE248496T1 (fr)
AU (2) AU4776999A (fr)
CA (2) CA2479675C (fr)
DE (1) DE60004863T2 (fr)
DK (1) DK1203508T3 (fr)
WO (2) WO2001001732A1 (fr)

Cited By (12)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
EP1307072A2 (fr) * 2001-10-17 2003-05-02 Siemens Audiologische Technik GmbH Procédé pour actionner une prothèse auditive et prothèse auditive
KR20040028889A (ko) * 2004-02-24 2004-04-03 장순석 반대쪽 방향의 소리도 잘 들을 수 있는 한쪽 귓속형보청기 구조 설계
EP1499160A2 (fr) 2003-07-16 2005-01-19 Siemens Audiologische Technik GmbH Prothèse auditive directionnelle
EP1513371A3 (fr) * 2004-10-19 2005-04-13 Phonak Ag Procédé pour actionner une prothèse auditive et prothèse auditive
US7010134B2 (en) 2001-04-18 2006-03-07 Widex A/S Hearing aid, a method of controlling a hearing aid, and a noise reduction system for a hearing aid
EP1653768A2 (fr) 2004-11-02 2006-05-03 Siemens Audiologische Technik GmbH Procédé pour réduire la puissance perturbatrice dans un microphone directionnel et système électro-acoustique correspondant
AU2004202688B2 (en) * 2003-06-20 2007-04-05 Siemens Audiologische Technik Gmbh Method For Operation Of A Hearing Aid, As Well As A Hearing Aid Having A Microphone System In Which Different Directional Characteristics Can Be Set
US8126176B2 (en) 2009-02-09 2012-02-28 Panasonic Corporation Hearing aid
US8189833B2 (en) 2005-10-11 2012-05-29 Widex A/S Hearing aid and a method of processing input signals in a hearing aid
EP2373065B1 (fr) 2010-03-17 2016-01-13 Sivantos Pte. Ltd. Dispositif auditif et procédé de production d'une caractéristique de direction omnidirectionnelle
US10244334B2 (en) 2016-10-10 2019-03-26 Widex A/S Binaural hearing aid system and a method of operating a binaural hearing aid system
US10284978B2 (en) 2005-10-18 2019-05-07 Widex A/S Equipment for programming a hearing aid and a hearing aid

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DE10310579B4 (de) 2003-03-11 2005-06-16 Siemens Audiologische Technik Gmbh Automatischer Mikrofonabgleich bei einem Richtmikrofonsystem mit wenigstens drei Mikrofonen
DE60322447D1 (de) * 2003-09-19 2008-09-04 Widex As Verfahren zur steuerung der richtcharakteristik eiür ein hörgerät mit steuerbarer richtcharakteristik
US20100329490A1 (en) * 2008-02-20 2010-12-30 Koninklijke Philips Electronics N.V. Audio device and method of operation therefor
US9668065B2 (en) 2015-09-18 2017-05-30 Sonion Nederland B.V. Acoustical module with acoustical filter
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US7010134B2 (en) 2001-04-18 2006-03-07 Widex A/S Hearing aid, a method of controlling a hearing aid, and a noise reduction system for a hearing aid
EP1307072A2 (fr) * 2001-10-17 2003-05-02 Siemens Audiologische Technik GmbH Procédé pour actionner une prothèse auditive et prothèse auditive
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US7340073B2 (en) 2003-06-20 2008-03-04 Siemens Audiologische Technik Gmbh Hearing aid and operating method with switching among different directional characteristics
AU2004202688B2 (en) * 2003-06-20 2007-04-05 Siemens Audiologische Technik Gmbh Method For Operation Of A Hearing Aid, As Well As A Hearing Aid Having A Microphone System In Which Different Directional Characteristics Can Be Set
US7209568B2 (en) 2003-07-16 2007-04-24 Siemens Audiologische Technik Gmbh Hearing aid having an adjustable directional characteristic, and method for adjustment thereof
DE10331956C5 (de) * 2003-07-16 2010-11-18 Siemens Audiologische Technik Gmbh Hörhilfegerät sowie Verfahren zum Betrieb eines Hörhilfegerätes mit einem Mikrofonsystem, bei dem unterschiedliche Richtcharakteistiken einstellbar sind
EP1499160A2 (fr) 2003-07-16 2005-01-19 Siemens Audiologische Technik GmbH Prothèse auditive directionnelle
AU2004203135B2 (en) * 2003-07-16 2007-03-08 Sivantos Gmbh Hearing Aid, as well as a Method for Operation of a Hearing Aid having a Microphone System in which Different Directional Characteristics can be Set
KR20040028889A (ko) * 2004-02-24 2004-04-03 장순석 반대쪽 방향의 소리도 잘 들을 수 있는 한쪽 귓속형보청기 구조 설계
US7995781B2 (en) 2004-10-19 2011-08-09 Phonak Ag Method for operating a hearing device as well as a hearing device
US7653205B2 (en) 2004-10-19 2010-01-26 Phonak Ag Method for operating a hearing device as well as a hearing device
EP1513371A3 (fr) * 2004-10-19 2005-04-13 Phonak Ag Procédé pour actionner une prothèse auditive et prothèse auditive
DE102004052912A1 (de) * 2004-11-02 2006-05-11 Siemens Audiologische Technik Gmbh Verfahren zur Reduktion von Störleistungen bei einem Richtmikrophon und entsprechendes Akustiksystem
EP1653768A3 (fr) * 2004-11-02 2010-06-02 Siemens Audiologische Technik GmbH Procédé pour réduire la puissance perturbatrice dans un microphone directionnel et système électro-acoustique correspondant
EP1653768A2 (fr) 2004-11-02 2006-05-03 Siemens Audiologische Technik GmbH Procédé pour réduire la puissance perturbatrice dans un microphone directionnel et système électro-acoustique correspondant
US8135142B2 (en) 2004-11-02 2012-03-13 Siemens Audiologische Technic Gmbh Method for reducing interferences of a directional microphone
US8189833B2 (en) 2005-10-11 2012-05-29 Widex A/S Hearing aid and a method of processing input signals in a hearing aid
US10284978B2 (en) 2005-10-18 2019-05-07 Widex A/S Equipment for programming a hearing aid and a hearing aid
US8126176B2 (en) 2009-02-09 2012-02-28 Panasonic Corporation Hearing aid
EP2373065B1 (fr) 2010-03-17 2016-01-13 Sivantos Pte. Ltd. Dispositif auditif et procédé de production d'une caractéristique de direction omnidirectionnelle
EP2373065B2 (fr) † 2010-03-17 2018-10-03 Sivantos Pte. Ltd. Dispositif auditif et procédé de production d'une caractéristique de direction omnidirectionnelle
US10244334B2 (en) 2016-10-10 2019-03-26 Widex A/S Binaural hearing aid system and a method of operating a binaural hearing aid system

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DE60004863D1 (de) 2003-10-02
AU766876B2 (en) 2003-10-23
AU4776999A (en) 2001-01-31
CA2385812A1 (fr) 2001-01-04
WO2001001732A1 (fr) 2001-01-04
DE60004863T2 (de) 2004-05-06
DK1203508T3 (da) 2003-09-22
CA2385812C (fr) 2005-06-07
ATE248496T1 (de) 2003-09-15
CA2479675C (fr) 2006-06-06
JP3914768B2 (ja) 2007-05-16
JP2003503924A (ja) 2003-01-28
AU5391600A (en) 2001-01-31
CA2479675A1 (fr) 2001-01-04

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