WO1996003848A1 - Prothese auditive - Google Patents

Prothese auditive Download PDF

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Publication number
WO1996003848A1
WO1996003848A1 PCT/DE1995/000853 DE9500853W WO9603848A1 WO 1996003848 A1 WO1996003848 A1 WO 1996003848A1 DE 9500853 W DE9500853 W DE 9500853W WO 9603848 A1 WO9603848 A1 WO 9603848A1
Authority
WO
WIPO (PCT)
Prior art keywords
hearing aid
hearing
aid according
digital
amplifier
Prior art date
Application number
PCT/DE1995/000853
Other languages
German (de)
English (en)
Inventor
Johann Vielberth
Original Assignee
Institut Für Entwicklung Und Forschung Dr. Vielberth Kg
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
Priority claimed from DE19944425759 external-priority patent/DE4425759A1/de
Application filed by Institut Für Entwicklung Und Forschung Dr. Vielberth Kg filed Critical Institut Für Entwicklung Und Forschung Dr. Vielberth Kg
Publication of WO1996003848A1 publication Critical patent/WO1996003848A1/fr

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
    • H04R25/55—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception using an external connection, either wireless or wired
    • H04R25/552—Binaural
    • 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
    • H04R25/55—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception using an external connection, either wireless or wired
    • H04R25/558—Remote control, e.g. of amplification, frequency
    • 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 invention relates to a hearing aid according to the preamble of claim 1.
  • portable electrical hearing aids are known in various designs.
  • such a hearing aid consists of a microphone, a hearing amplifier and a receiver controlled by the amplifier, for example ear plug-in earphones.
  • a disadvantage of these hearing aids is that the frequency response and / or the transfer function of the hearing amplifier can only be adapted to the specific hearing impairment of the user to a very limited extent, e.g. the (hearing impairment) in certain frequency ranges an increase and / or in other frequency ranges a reduction in the degree of amplification is necessary in order to at least somewhat compensate for existing hearing damage.
  • the input signal supplied by the microphone is first converted into a digital signal in an analog-to-digital converter, which is then subjected to a program in an arithmetic unit or processed with a predetermined program that is matched to the hearing impairment of the respective user.
  • the processed sound signal is then converted into an analog audio signal in a digital-analog converter and fed to the listener via an amplifier.
  • the object of the invention is to show a hearing aid that has improved quality with little effort.
  • a hearing aid is designed in accordance with the characterizing part of patent claim 1.
  • the hearing aid according to the invention is designed, for example, as a portable hearing aid. Furthermore, the hearing aid according to the invention is preferably also designed such that the hearing amplifier forms a stationary device which is then connected to a receiving device via the transmission link, which is preferably a wireless transmission link and is preferably an infrared transmission link. This is small and handy and therefore carried out by the user easily and inconspicuously portable. Especially in this version with a stationary hearing amplifier, the device is suitable for connection to existing audio systems, for example to radio sets, stereo systems, television sets, etc.
  • the sound signal is transmitted stereophonically, i.e. there are two audio channels, each of which is assigned to at least one earpiece for each ear of the user, the transmission functions, i.e. Transmission and filter curves for each channel are stored individually adapted to the hearing damage of the left and right ear and are taken into account when processing the digital audio signals.
  • An individual frequency-dependent dynamic adaptation is also preferably carried out in the invention, i.e. an individual and frequency-dependent adjustment of the gain depending on the amplitude of the respective input signal.
  • the processing of the sound signal of the right and left channel takes place at different times, ie in the time-multiplex method, the switching frequency being well above the audible frequency range, ie well above 20 kHz.
  • the listeners are, for example, components of a headphone, on which the microphones are then also provided, so that they have the required spatial distance from one another and are carried at a location which ensures optimum reception and also corresponds best to natural hearing.
  • standardized transmission or filter curves are also stored, which take into account the general acoustic conditions in different local areas, for example in small rooms, large halls, outdoors, etc. which are superimposed on the individual curves in order to achieve an overall transfer function that is also adapted to the local conditions as possible.
  • the voltage and power supply takes place from a power supply unit and / or from one or more batteries, which are preferably rechargeable batteries, in which case the analog circuits, namely the output amplifiers for controlling the listeners, the input or microphone amplifiers, etc. are directly connected to the voltage or power supply, while the digital circuits are operated by the voltage supply via a DC / DC converter, which means that there is a coupling between the digital ones, especially if the power supply has a higher internal resistance or if the battery has a weakened internal resistance Circuits and the analog circuits in the field of power supply is reliably achieved.
  • the hearing aid according to the invention preferably also has the possibility of self-audiometry, ie the hearing aid has, for example, an audiometry device, so that the respective user is able to do so at home and without the help of a specialist (hearing care professional and / or doctor) his Hearing impairment or impairment of hearing optimally adapted transmission functions for both clocks to be individually determined and stored in the device.
  • the audiometry can be carried out under real conditions and where the hearing aid is actually to be used, taking into account the acoustic conditions prevailing at the place of use, etc.
  • the acoustic properties of these components are also taken into account in the audiometry.
  • the hearing aid according to the invention is in principle also suitable as a hearing amplifier for the telephone.
  • FIG. 1 shows a very simplified block or functional diagram of a first embodiment of the hearing aid according to the invention
  • FIG. 2 shows a more detailed block diagram of the hearing aid according to FIG. 1;
  • FIG. 3 shows a further possible embodiment of the hearing aid according to the invention.
  • the hearing aid shown in FIG. 1, which enables hearing-impaired people to take part in conversations, discussions, lectures, music events, etc., consists of two microphones 1 and 2, two loudspeakers or listeners 3 and 2, in accordance with the very simplified functional diagram of FIG. 1 4, the latter being part of a headphone for stereophonic hearing, namely the speaker 3 for a left and the speaker 4 for a right channel, and from the hearing amplifier 6.
  • the microphones 1 and 2 are spatially offset from one another, specifically the microphone 1 for the left channel and the microphone 2 for the right channel.
  • the two microphones 1 and 2 are also attached to the headphones or to a bracket of these headphones.
  • the aforementioned elements are connected via a flexible multi-wire line 5 to the hearing amplifier, which is generally designated 6 in FIG. 1.
  • FIG. 2 shows the design of the device generally designated G1 there or of the hearing amplifier 6 in more detail.
  • the central element of the hearing amplifier is a microprocessor 7. These are assigned:
  • an input element 12 for manual input of commands, for example for switching on and off, switching etc. of the device or various functions and a CODEC module 13, which has at least two analog-digital converters for converting the analog audio signals of microphones 1 and 2 into digital signals and at least two digital-analog converters for converting digital audio signals back into analog audio signals. Signals for their reproduction on the speakers 3 and 4.
  • the hearing amplifier 6 also contains a circuit 14, for each microphone 1 and 2 an input amplifier 15, which is connected on the input side to a microphone 1 or 2 and on the output side to the analog-digital converter of the CODEC circuit 13, and two output amplifiers 16 has, each of which is connected with its input to the output of a digital-to-analog converter of the CODEC circuit 13 and with its output to a loudspeaker 3 or 4.
  • the hearing amplifier 6 finally has a power supply 17 formed by a plurality of batteries, preferably a plurality of rechargeable batteries, to which the circuit 14 or the amplifiers 15 and 16 there are connected directly.
  • the remaining elements of the hearing amplifier 6, in particular all digital circuits or elements for digital data processing, especially also the CODEC circuit 13, are connected to the voltage supply 1 via a direct voltage-direct voltage converter (DC-DC converter) 18. In this way, decoupling between the digital circuits and the analog circuits is also achieved in the area of the voltage supply, in order to effectively avoid interference.
  • DC-DC converter direct voltage-direct voltage converter
  • the power supply is formed by an internal or external power supply unit to which the hearing amplifier can be connected.
  • the microprocessor 7 with the components assigned to it essentially serves to achieve a predetermined frequency response or a predetermined pass curve (transfer function) for the hearing amplifier 6, taking into account special transfer or filter curves that are stored for the respective user and take into account their hearing impairment individually, as well as other standardized filter curves that do not take into account the specific hearing impairments of the respective user, but are generally valid and take into account special environmental conditions under which the hearing aid is used for optimal hearing, for example by filtering out low frequencies and / or high frequencies or noise etc.
  • the filter curves are each stored as a data record, for example in the memory 8.
  • the individual filter curves are created and stored separately for the left and right channels and for the left and right ears, respectively, in such a way that certain frequency ranges are raised or lowered in accordance with the hearing impairment in order to compensate for hearing losses.
  • the individual filter curves are determined by listening tests and then read into the memory 8 via the interface 11.
  • the CODEC circuit 13 is continuously switched over in such a way that the audio signals for the left channel and the right channel are offset in time or processed and amplified on the loudspeakers in the time-multiplex method 3 and 4 reproduced are, so that despite the stereophonic recording, editing, amplification and reproduction of the sound signals and in particular also despite the individual processing of the signals of the right and left channel, a minimal circuit complexity and low power consumption are ensured, so that the audio amplifier is relatively small despite high quality and compact and thus can be designed to be optimally portable by the user.
  • the microphones 1 and 2 are provided on the headphones 3 and 4 with the earphones or on the carrying bracket there or on these earphones 3 and 4, the hearing amplifier 6 can be accommodated in a pocket of a piece of clothing, which also contributes to convenient use.
  • the digital processing of the audio signals also makes it possible to effectively suppress acoustic feedback between the microphones 1 and 2 and the listeners 3 and 4.
  • the switching frequency with which the CODEC circuit 13 is periodically switched between the channels is well above the audible frequency range and is, for example, approximately 24 to 25 kHz.
  • the audiometric device 19 generally designates an audiometry device for self-audiometry, ie with this device the user is able to perform an own audiometry, ie an individual adaptation, on the basis of acoustic signals of different frequencies reproduced in the listeners 3 and 4 the transfer or filter curves as well as an individual Make dynamic adjustments for the left and right canal or for the left and right ear separately.
  • the audiometric device 19 has a control circuit 20, a speech memory 21, a generator 22 for the test frequencies and a data memory 23.
  • the device 19 can be activated via the input 12 or via a button.
  • the user then first receives, for example, some information and explanations for carrying out the self-audiometry from the voice memory 21. Furthermore, explanations and / or instructions are given to the user during the audiometry, which are transmitted via the earphones 3 and 4, respectively.
  • the control circuit 20 causes the audio frequency generator 22 to emit test frequencies in the listening area, specifically a test frequency in a test phase with, for example, a continuously or step-wise increasing amplitude. As soon as the user has the desired auditory impression, he confirms this by pressing input 12 accordingly. The corresponding amplitude or dynamic value is stored in the data memory 23.
  • each test phase After the end of each test phase there is another test phase with a different tone frequency and again e.g. with increasing amplitude over time until the number of possible test phases is reached.
  • the corresponding value of the amplitude or dynamics of the audio frequency is stored in the memory 23 for each test phase.
  • test phases and thus the number of sound frequencies and their frequency are fixed, for example, but can also be varied according to certain criteria, depending on the measurement result.
  • the audiometry is independent for the left and right channels.
  • the individual pass curves for the left and right channels are created from the data stored in the memory 23 by the microprocessor 7 and stored in the memory 8.
  • the advantage of the audiometric device 19 is that each user is able to determine his individual filter or transmission curves for storage in the memory 8, so it is not necessary to have these individual filter or transmission curves determined outside the home and then read into the memory 8 via the interface 1 1.
  • Another advantage of the audiometric device 19 is that the user can adapt the device at any time immediately and individually with regard to the transmission functions or dynamics to the existing environment in order to enable optimal hearing.
  • the 24 in FIG. 2 also designates a display device controlled by the microprocessor 7, on which the user also receives visual information, for example if the result of the self-audiometry which differs greatly from the norm indicates that the search for a specialist, for example, a doctor would be appropriate.
  • the display device 24 consists of at least one lamp, but can also be a display.
  • the individual functions of the audiometric device 19 are shown as separate blocks 20-23. It goes without saying that these functions can also be taken over by other elements, for example by the microprocessor 7 with a corresponding design of the program stored in the memory 9.
  • FIG. 3 shows, as a further embodiment, a device G2 which is intended for connection to an audio device, for example to hi-fi audio systems or to television sets is.
  • the device shown in FIG. 3 therefore differs from the device G1 of FIG. 2 essentially in that connections 25 and 26 are provided instead of the microphones 1 and 2, specifically for connection to the audio output of the respective audio device, namely the connection 25 for the left channel and the connection 26 for the right channel, the input amplifiers 15 being of course adapted to the signal levels occurring in this application.
  • infrared transmission diodes 27 and 28 are provided on a transmitter 29 controlled by the CODEC circuit.
  • the two infrared transmitter diodes 27 and 28 each deliver an audio signal modulated on a different carrier for the left channel and the right channel.
  • the receiver 30 designates a receiving device which has two receiving diodes 31 (for the left channel) and 32 (for the right channel), two demodulators 33, the output amplifiers 16 and the two earphones 3 and 4, with one preferably not also on the receiving device 30 volume control shown is provided. While the device G2 is arranged in a stationary manner, the receiver 30 is designed to be portable, in such a way that it is carried by the user.
  • the device G2 corresponds to the device G1 in its general function
  • FIG. 3 also those elements which correspond in function to the elements of the device G 1 are designated with the same reference numerals as in FIG. 2.
  • the device G2 allows, in the same way as described above for the device G1, an individual dynamic adaptation and individual adaptation of the filter or pass curves or transfer function to the respective user and also individually for the left and right channel or for the left and right Ear.
  • the device G2 thus also enables people with limited hearing or hearing impairments to participate in voice and / or music transmissions in an optimal manner.
  • the peculiarity of the device G2 also consists in the fact that the audio signals modified by individual adaptation are transmitted over the transmission path formed between the transmitter diodes 27 and 28 and the receive diodes 31 and 32, so that the greater complexity in terms of circuitry is also present in the stationary device G2 , while the receiver 30 can be made very small and handy and thus in particular also convenient and inconspicuously portable, and in spite of a stereophonic, high-quality transmission.
  • a special feature of the device G2 is that the transmission of the audio signals via the transmission path formed between the infrared transmit diodes 27 and 28 and the infrared receive diodes 31 and 32 takes place in an analog manner, i.e. by analog modulated carrier frequencies, so that only simple demodulators are necessary in the receiving device 30, which also contributes to simplification and compact design and to a reduction in the power consumption of the receiving devices 30.
  • the data determined during the audiometry and / or the transmission functions or pass-through or filter curves created therefrom can also be read out via the interface 11, so that the device can even be used by a person skilled in the art of audiometry.
  • connection 25 and 26 light detectors or an infrared light receiver device having such detectors can also be provided, such as are suitable, for example, for coupling to infrared outputs in audio devices.
  • light detectors or an infrared light receiver device having such detectors can also be provided, such as are suitable, for example, for coupling to infrared outputs in audio devices.
  • Display device 26 connection, 28 infrared transmitter diode
  • Infrared receiver 32 1 infrared receiver diode ⁇ emodulator

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  • Engineering & Computer Science (AREA)
  • Computer Networks & Wireless Communication (AREA)
  • Health & Medical Sciences (AREA)
  • General Health & Medical Sciences (AREA)
  • Neurosurgery (AREA)
  • Otolaryngology (AREA)
  • Physics & Mathematics (AREA)
  • Acoustics & Sound (AREA)
  • Signal Processing (AREA)
  • Circuit For Audible Band Transducer (AREA)

Abstract

L'invention concerne une prothèse auditive qui permet à des sujets affectés de déficiences auditives, de prendre part à des manifestations telles que des conférences ou des concerts, etc. Les signaux acoustiques reçus par des microphones sont traités de manière numérique au moyen de fonctions de transmission individuelles. Les signaux numériques ainsi traités sont convertis en signaux audio analogiques pour être restitués à des écouteurs.
PCT/DE1995/000853 1994-07-21 1995-07-01 Prothese auditive WO1996003848A1 (fr)

Applications Claiming Priority (6)

Application Number Priority Date Filing Date Title
DEP4425759.7 1994-07-21
DE19944425759 DE4425759A1 (de) 1994-07-21 1994-07-21 Tragbare Hörhilfe
DE19515348 1995-04-26
DE19515348.0 1995-04-26
DE19518199.9 1995-05-18
DE19518199 1995-05-18

Publications (1)

Publication Number Publication Date
WO1996003848A1 true WO1996003848A1 (fr) 1996-02-08

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ID=27206605

Family Applications (1)

Application Number Title Priority Date Filing Date
PCT/DE1995/000853 WO1996003848A1 (fr) 1994-07-21 1995-07-01 Prothese auditive

Country Status (1)

Country Link
WO (1) WO1996003848A1 (fr)

Cited By (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO1997014267A1 (fr) * 1995-10-12 1997-04-17 Audiologic, Inc. Prothese auditive a capacite d'essai in situ
DE19703320A1 (de) * 1997-01-30 1997-06-19 Arno Klinkhamer Individueller Höradapter
EP1767054A2 (fr) * 2004-06-15 2007-03-28 Johnson and Johnson Consumer Companies, Inc. Prothese acoustique programmable integree a un appareil a ecouteur, procede d'utilisation, et systeme de programmation correspondant
WO2009010572A1 (fr) * 2007-07-18 2009-01-22 Dietmar Ruwisch Appareil auditif à module d'initialisation et adaptation à l'utilisateur

Citations (9)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
DE2744364A1 (de) * 1977-10-01 1979-04-05 Bosch Gmbh Robert Elektroakustisches verstaerkergeraet
DE3205685A1 (de) * 1982-02-17 1983-08-25 Robert Bosch Gmbh, 7000 Stuttgart Hoergeraet
WO1989004583A1 (fr) * 1987-11-12 1989-05-18 Nicolet Instrument Corporation Systeme d'aide auditive programmable et adaptatif avec unite de traitement de signaux
EP0339819A2 (fr) * 1988-04-11 1989-11-02 Central Institute For The Deaf Filtre électronique
DE3826294A1 (de) * 1988-08-03 1990-02-08 Bosch Gmbh Robert Freisprecheinrichtung fuer kommunikationssysteme
EP0363609A1 (fr) * 1988-10-13 1990-04-18 Siemens Audiologische Technik GmbH Appareil de programmation digital pour appareils de correction auditive
WO1991015902A1 (fr) * 1990-03-30 1991-10-17 Lott Thomas M Dispositif d'aide auditive
EP0487413A1 (fr) * 1990-11-23 1992-05-27 Société ALPHA I Dispositif électronique formant prothèse auditive programmable miniature, en particulier du type intra-conduit
US5239588A (en) * 1988-12-21 1993-08-24 Davis Murray A Hearing aid

Patent Citations (9)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
DE2744364A1 (de) * 1977-10-01 1979-04-05 Bosch Gmbh Robert Elektroakustisches verstaerkergeraet
DE3205685A1 (de) * 1982-02-17 1983-08-25 Robert Bosch Gmbh, 7000 Stuttgart Hoergeraet
WO1989004583A1 (fr) * 1987-11-12 1989-05-18 Nicolet Instrument Corporation Systeme d'aide auditive programmable et adaptatif avec unite de traitement de signaux
EP0339819A2 (fr) * 1988-04-11 1989-11-02 Central Institute For The Deaf Filtre électronique
DE3826294A1 (de) * 1988-08-03 1990-02-08 Bosch Gmbh Robert Freisprecheinrichtung fuer kommunikationssysteme
EP0363609A1 (fr) * 1988-10-13 1990-04-18 Siemens Audiologische Technik GmbH Appareil de programmation digital pour appareils de correction auditive
US5239588A (en) * 1988-12-21 1993-08-24 Davis Murray A Hearing aid
WO1991015902A1 (fr) * 1990-03-30 1991-10-17 Lott Thomas M Dispositif d'aide auditive
EP0487413A1 (fr) * 1990-11-23 1992-05-27 Société ALPHA I Dispositif électronique formant prothèse auditive programmable miniature, en particulier du type intra-conduit

Cited By (9)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO1997014267A1 (fr) * 1995-10-12 1997-04-17 Audiologic, Inc. Prothese auditive a capacite d'essai in situ
US6118877A (en) * 1995-10-12 2000-09-12 Audiologic, Inc. Hearing aid with in situ testing capability
DE19703320A1 (de) * 1997-01-30 1997-06-19 Arno Klinkhamer Individueller Höradapter
EP1767054A2 (fr) * 2004-06-15 2007-03-28 Johnson and Johnson Consumer Companies, Inc. Prothese acoustique programmable integree a un appareil a ecouteur, procede d'utilisation, et systeme de programmation correspondant
EP1767054A4 (fr) * 2004-06-15 2009-06-10 Johnson & Johnson Consumer Prothese acoustique programmable integree a un appareil a ecouteur, procede d'utilisation, et systeme de programmation correspondant
WO2009010572A1 (fr) * 2007-07-18 2009-01-22 Dietmar Ruwisch Appareil auditif à module d'initialisation et adaptation à l'utilisateur
CN101755468A (zh) * 2007-07-18 2010-06-23 迪特马·鲁伊沙克 包括初始化模块的用户可调解的助听器
US8406441B2 (en) 2007-07-18 2013-03-26 Dietmar Ruwisch User-adaptable hearing aid comprising an initialization module
CN101755468B (zh) * 2007-07-18 2014-09-17 迪特马·鲁伊沙克 包括初始化模块的用户可调节的助听器

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