EP0175909A1 - Appareil auditif - Google Patents

Appareil auditif Download PDF

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Publication number
EP0175909A1
EP0175909A1 EP85110215A EP85110215A EP0175909A1 EP 0175909 A1 EP0175909 A1 EP 0175909A1 EP 85110215 A EP85110215 A EP 85110215A EP 85110215 A EP85110215 A EP 85110215A EP 0175909 A1 EP0175909 A1 EP 0175909A1
Authority
EP
European Patent Office
Prior art keywords
hearing aid
signals
control
microphone
ultrasound
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Granted
Application number
EP85110215A
Other languages
German (de)
English (en)
Other versions
EP0175909B1 (fr
Inventor
Dieter Busch
Friedrich Harless
Gerhard Krauss
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Sivantos GmbH
Siemens AG
Original Assignee
Siemens AG
Siemens Audioligische Technik GmbH
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
Family has litigation
First worldwide family litigation filed litigation Critical https://patents.darts-ip.com/?family=6244081&utm_source=google_patent&utm_medium=platform_link&utm_campaign=public_patent_search&patent=EP0175909(A1) "Global patent litigation dataset” by Darts-ip is licensed under a Creative Commons Attribution 4.0 International License.
Application filed by Siemens AG, Siemens Audioligische Technik GmbH filed Critical Siemens AG
Priority to AT85110215T priority Critical patent/ATE73288T1/de
Publication of EP0175909A1 publication Critical patent/EP0175909A1/fr
Application granted granted Critical
Publication of EP0175909B1 publication Critical patent/EP0175909B1/fr
Anticipated expiration legal-status Critical
Expired - Lifetime legal-status Critical Current

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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
    • H04R25/55—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
    • H04R25/55—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
    • H04R25/554—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 using a wireless connection, e.g. between microphone and amplifier or using Tcoils

Definitions

  • the invention relates to hearing aids according to the preamble of claim 1.
  • Devices of this type are known, for example, from DE-OS 19 38 381.
  • Hearing aids should be as small as possible so that they can be worn inconspicuously.
  • the volume of these devices should also be changeable in operation. For this you need adjustment devices that can be operated from the outside, so that the device can be set when it is in operation. With the small devices, however, there is only a small area available for attaching actuators, which are also accessible when the device is being carried.
  • a hearing aid was therefore proposed, the components of which are distributed over two housings, of which the first contains a transmitter which is connected wirelessly to the second, in which the parts of a hearing aid and one on the Transmitter tuned receiver. It was no longer necessary to design the device so that its actuators are accessible from the outside. Rather, it was possible to attach the actual actuator elements to a housing, which can be carried in the pocket, so that actuators are attached on the one hand regardless of a special shape can and that on the other hand can be adjusted under direct eye control.
  • antennas are required for the transmission, which, particularly in the case of miniature hearing aids, only take up a very limited amount of space.
  • the invention has for its object to provide a remote control in a hearing aid according to the preamble of claim 1, which can be accommodated in the actual hearing aid in a very space-saving manner.
  • This object is achieved by the measures specified in the characterizing part of patent claim 1.
  • Refinements and developments of the invention are specified in the subclaims.
  • the invention is based on the knowledge that the microphone of the hearing aid can also be used as a receiving element for the control signals if energy is used as the medium for transmitting the control signals, which the microphone of the hearing aid can convert into electrical signals that are generated by the other signals can be separated and applied to tax organs.
  • miniature microphones such as those used in small hearing aids, also respond to sound that is no longer recordable by human hearing.
  • Microphones that are used in hearing aids usually transmit in the ultrasound range up to 25 kHz with sufficient sensitivity.
  • there is an evaluable resonance in the range of ultrasound between 45 kHz and 50 kHz.
  • control signals can then be transmitted to the hearing aid and brought into effect there.
  • the main one Liche advantage of such a receiving arrangement is that no additional receiving antenna is required for the control signals in the hearing aid.
  • microphones are suitable in the sense of the present invention which have a transmission range up to approx. 25 kHz or which operate at even higher frequencies, e.g. between 45 kHz and 50 kHz, have a pronounced resonance. This resonance occurs in some of the usual miniature microphones because the dimensions of their housing correspond to the wavelength of the ultrasound range.
  • the structure of a remote control receiver that can be installed in a small hearing aid must be designed so that it leaves space for the hearing aid elements in the housing even with the smallest available dimensions.
  • Both the hearing aid amplifier and the circuit of the remote control can be designed as IC modules because the integration represents a possibility of accommodating the required component expenditure in a hearing device housing. It is also important that the required supply of electrical current can only come from a miniature battery, which must also be housed in the housing of the hearing aid. So you can only start from voltages that are in the order of 1.0 to 1.5 V. The current consumption of the control circuit should not exceed 10% of the current for the final stage of the hearing aid, so that a sufficient operating time can still be achieved with one battery charge. This marginal operation can be implemented by using a low-voltage, low-voltage CMOS technology which, in view of the low operating voltage, requires particular effort in the technological manufacturing process of a CMOS circuit.
  • FIG. 1 shows a hearing aid device which comprises a hearing device part 1 and a remote control part 2.
  • the hearing aid part begins in the usual way with the input transducers, i.e. a microphone 3 and an induction pick-up coil 4, which can be connected alternately to the hearing aid circuit via a changeover switch 5.
  • the signal recorded in FIGS. 3 and / or 4 then passes via a controllable amplifier 6, which serves as a presetting for the amplification, via a sound diaphragm 7 to a potentiometer 8, from which it then reaches a driver amplifier 9 and, after this, a power amplifier 10 .
  • the amplified signal in a final transmitter 14 i.e. an earpiece, again converted into sound, which can be fed to the ear of the hearing impaired.
  • Part 2 of the device has a connection 12 to the microphone 3.
  • the signals thus pass from the microphone directly to a high-pass filter 13, which separates the actual control signals from the audio signals, from this to a rectifier 14 and then to a low-pass filter 15, the combination from the rectifier 14 and the low pass 15 represents a demodulator for amplitude-modulated signals in the usual sense, which causes the signals to be in a form suitable for further digital processing.
  • the signal coming from the low pass 15 then comes to a Schmitt trigger 16, in which it is recognized whether the signal is large enough for further processing. In this Schmitt trigger, both the interference clearance point and the range of the transmission channel are defined.
  • the signal is then fed to a shift register 17 for code recognition, from which it reaches a decoder 18; there the signal is decrypted so that it reaches connections 5, connections 5, sound panel 7 or electronic, ie remote-controlled, potentiometer 8 via connections 19, 20, 21 and 22.
  • the lines 19 to 22 also have connections 23, to which a manually operable control 25 can be connected, which is shown in FIG.
  • the manual control shown in Figure 2 has actuation buttons 24.1 to 24.4, with which the debouncing circuits and pulse shapers contained in the button control 25 can be changed so that the connecting plugs 19.1 to 22.1, which can be connected to the sockets of the lines 19 to 22 Corresponding signals arrive at the switch 5, the sound shield 7 or the electronic potentiometer 8, which result in an adjustment of the hearing aid in the desired sense by switching the hearing coil and microphone at the switch 5 and the desired change in the audio frequency response takes place at the sound shield 7.
  • the volume is increased via the line 21 in that control pulses come.
  • the amplification can be reduced via line 22 by means of opposite signals.
  • a keyboard 24.5 to 24.8 is provided for remote control, as in FIG. It also consists of four switches. As in FIG. 2, these switches are connected to a key control 30, in which, by pressing the keys 24.5 to 24.8, signals similar to those when the keys 24.1 to 24.4 in FIG. 2 are generated. These signals are encoded in a subsequent encoder 31 in such a way that a unique digital code word is assigned to each command of keys 24.5 to 24.8. The control signal treated in this way then comes into a parallel-to-serial converter 32, where it is processed for serial output on the transmission link.
  • This signal is then fed to the modulation of a clock frequency control 33, to which the signals of a timer 34, which defines the duration of the logical 0, and the signals of a timer 35, which specifies the duration of the logical 1, also arrive.
  • the signal 10 is processed so that it then arrives at a clock frequency generator 36, where it is modulated with the clock frequency in the ultrasound range.
  • the intensity of the signals is increased in an amplifier 37 so that they are then emitted via a loudspeaker 38 and can act on the microphone 3.
  • the switch 5 can be adjusted via the remote control according to FIG. 3 in such a way that an assigned pulse sequence takes place in the remote control by pressing the button 24.5.
  • a signal is received via the loudspeaker which is received by the microphone 3.
  • the control signal is separated from the sound signal by the selection elements 13 to 16 of the remote control part of the hearing device.
  • the code recognition of 17 then occurs, where it is recognized whether there are no interference pulses were received with.
  • the above-mentioned assigned pulse sequence is then recognized, so that a signal comes to the connection 19. It then causes in switch 5 that the microphone 3 is connected.
  • a switchover to the induction pick-up coil 4 or its switching on takes place when the next similar pulse sequence comes again.
  • the sound screen 7 is actuated via the connection 20 by pressing the button 24.6.
  • Another assigned pulse train is used.
  • the volume in the electronic potentiometer 8 is changed via the connections 21 and 22 by pressing the buttons 24.7 and 24.8.
  • the corresponding control signals are generated by repeating assigned pulse sequences, i.e. in the key control, a generator produces pulses which generate the assigned pulse sequences in the encoder 31 and prepare them for transmission in the parallel-serial converter 32.
  • the clock frequency control 33 and the clock frequency generator 36 operate analogously, as described in the last section.
  • the loudspeaker 38 can leave a signal which gives a signal in the microphone 3 which, after passing through the elements 13 to 16, is checked in the code recognition 17 for incorrect transmission.
  • the decoder 18 is then used to increase the volume on the one hand when the button 24.6 is pressed and on the other hand to decrease the volume of the hearing aid when the button 24.5 is pressed.

Landscapes

  • 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)
  • Selective Calling Equipment (AREA)
  • Adornments (AREA)
  • Finger-Pressure Massage (AREA)
EP85110215A 1984-08-28 1985-08-14 Appareil auditif Expired - Lifetime EP0175909B1 (fr)

Priority Applications (1)

Application Number Priority Date Filing Date Title
AT85110215T ATE73288T1 (de) 1984-08-28 1985-08-14 Hoerhilfegeraet.

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
DE3431584 1984-08-28
DE19843431584 DE3431584A1 (de) 1984-08-28 1984-08-28 Hoerhilfegeraet

Publications (2)

Publication Number Publication Date
EP0175909A1 true EP0175909A1 (fr) 1986-04-02
EP0175909B1 EP0175909B1 (fr) 1992-03-04

Family

ID=6244081

Family Applications (1)

Application Number Title Priority Date Filing Date
EP85110215A Expired - Lifetime EP0175909B1 (fr) 1984-08-28 1985-08-14 Appareil auditif

Country Status (6)

Country Link
US (1) US4845755A (fr)
EP (1) EP0175909B1 (fr)
JP (1) JPH0642760B2 (fr)
AT (1) ATE73288T1 (fr)
DE (2) DE3431584A1 (fr)
DK (1) DK167262B1 (fr)

Cited By (9)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
EP0298323A1 (fr) * 1987-07-07 1989-01-11 Siemens Aktiengesellschaft Appareil aide ouie
EP0335542A2 (fr) * 1988-03-30 1989-10-04 3M Hearing Health Aktiebolag Prothèse auditive avec capacité de saisie de données
EP0340594A1 (fr) * 1988-05-06 1989-11-08 Siemens Audiologische Technik GmbH Dispositif de prothèse auditive à commande à distance sans fil
WO1991012783A1 (fr) * 1990-03-02 1991-09-05 Roger Tari Dispositif d'aide a l'audition comportant une prothese auditive implantee et autonome a conduction osseuse directe
EP0480097A1 (fr) * 1990-10-12 1992-04-15 Siemens Audiologische Technik GmbH Prothèse auditive avec mémoire pour données
EP0828404A2 (fr) * 1996-09-06 1998-03-11 Türk + Türk Electronic GmbH Prothèse auditive et dispositif de commande pour la programmation de la prothèse
WO1999039547A1 (fr) * 1998-01-28 1999-08-05 Richard Obler Procede permettant de stimuler un nerf avec un courant d'excitation variable et dispositif pour la production d'un courant d'excitation variable
DE4419901C2 (de) * 1994-06-07 2000-09-14 Siemens Audiologische Technik Hörhilfegerät
EP1196008A3 (fr) * 2000-10-04 2006-07-12 Sonionmicrotronic Nederland B.V. Amplificateur intégré avec telebobine et traitement de signal

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US4918737A (en) * 1987-07-07 1990-04-17 Siemens Aktiengesellschaft Hearing aid with wireless remote control
EP0298323A1 (fr) * 1987-07-07 1989-01-11 Siemens Aktiengesellschaft Appareil aide ouie
EP0335542A3 (fr) * 1988-03-30 1991-09-11 3M Hearing Health Aktiebolag Prothèse auditive avec capacité de saisie de données
EP0335542A2 (fr) * 1988-03-30 1989-10-04 3M Hearing Health Aktiebolag Prothèse auditive avec capacité de saisie de données
EP0340594A1 (fr) * 1988-05-06 1989-11-08 Siemens Audiologische Technik GmbH Dispositif de prothèse auditive à commande à distance sans fil
WO1991012783A1 (fr) * 1990-03-02 1991-09-05 Roger Tari Dispositif d'aide a l'audition comportant une prothese auditive implantee et autonome a conduction osseuse directe
FR2659009A1 (fr) * 1990-03-02 1991-09-06 Tari Roger Dispositif d'aide a l'audition comportant une prothese auditive implantee et autonome a conduction osseuse directe.
EP0480097A1 (fr) * 1990-10-12 1992-04-15 Siemens Audiologische Technik GmbH Prothèse auditive avec mémoire pour données
US5210803A (en) * 1990-10-12 1993-05-11 Siemens Aktiengesellschaft Hearing aid having a data storage
DE4419901C2 (de) * 1994-06-07 2000-09-14 Siemens Audiologische Technik Hörhilfegerät
EP0828404A2 (fr) * 1996-09-06 1998-03-11 Türk + Türk Electronic GmbH Prothèse auditive et dispositif de commande pour la programmation de la prothèse
EP0828404A3 (fr) * 1996-09-06 2003-05-14 Türk + Türk Electronic GmbH Prothèse auditive et dispositif de commande pour la programmation de la prothèse
WO1999039547A1 (fr) * 1998-01-28 1999-08-05 Richard Obler Procede permettant de stimuler un nerf avec un courant d'excitation variable et dispositif pour la production d'un courant d'excitation variable
EP1196008A3 (fr) * 2000-10-04 2006-07-12 Sonionmicrotronic Nederland B.V. Amplificateur intégré avec telebobine et traitement de signal

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DK388185D0 (da) 1985-08-27
DE3431584A1 (de) 1986-03-13
US4845755A (en) 1989-07-04
DK388185A (da) 1986-03-01
JPS6162300A (ja) 1986-03-31
ATE73288T1 (de) 1992-03-15
EP0175909B1 (fr) 1992-03-04
JPH0642760B2 (ja) 1994-06-01
DE3585479D1 (de) 1992-04-09
DK167262B1 (da) 1993-09-27

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