EP1349421B1 - Déconnexion de dispostifs de traitement de signal d' une prothèse auditive - Google Patents

Déconnexion de dispostifs de traitement de signal d' une prothèse auditive Download PDF

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Publication number
EP1349421B1
EP1349421B1 EP03004692A EP03004692A EP1349421B1 EP 1349421 B1 EP1349421 B1 EP 1349421B1 EP 03004692 A EP03004692 A EP 03004692A EP 03004692 A EP03004692 A EP 03004692A EP 1349421 B1 EP1349421 B1 EP 1349421B1
Authority
EP
European Patent Office
Prior art keywords
signal
preamplifier
signal line
hearing aid
signal processing
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.)
Expired - Lifetime
Application number
EP03004692A
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German (de)
English (en)
Other versions
EP1349421A2 (fr
EP1349421A3 (fr
Inventor
Gunter Sauer
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
Original Assignee
Siemens Audioligische Technik GmbH
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Filing date
Publication date
Application filed by Siemens Audioligische Technik GmbH filed Critical Siemens Audioligische Technik GmbH
Publication of EP1349421A2 publication Critical patent/EP1349421A2/fr
Publication of EP1349421A3 publication Critical patent/EP1349421A3/fr
Application granted granted Critical
Publication of EP1349421B1 publication Critical patent/EP1349421B1/fr
Anticipated expiration legal-status Critical
Expired - Lifetime legal-status Critical Current

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    • 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
    • H04R25/502—Customised settings for obtaining desired overall acoustical characteristics using analog signal processing
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R2460/00—Details of hearing devices, i.e. of ear- or headphones covered by H04R1/10 or H04R5/033 but not provided for in any of their subgroups, or of hearing aids covered by H04R25/00 but not provided for in any of its subgroups
    • H04R2460/03—Aspects of the reduction of energy consumption in hearing devices

Definitions

  • the present invention relates to a signal processing device for hearing aids with a signal line for transmitting a signal to a hearing aid amplifier and a control device for switching on and off of the hearing aid signal source. Furthermore, the present invention relates to a hearing aid with one or more of these signal processing devices and a method for operating signal processing devices.
  • a signal processing device is understood as any device which can serve as a signal source for the hearing aid amplifier.
  • signal sources To a hearing aid system, several internal and external signal sources can be connected. Examples of such signal sources include microphones and telecoils with or without integrated preamplifier and / or integrated analog-to-digital converter. Due to the limited power supply possibilities, the problem arises of being able to switch on and off individual signal sources separately with their signal processing devices, if necessary. The signal sources should be placed in the case of shutdown in a state that has a low power consumption result ("standby mode").
  • a basic idea to solve the problem is that the signal sources to reduce the power consumption by the hearing aid amplifier are turned off when they are not needed. For this purpose, three approaches are already known.
  • the signal sources or signal processing devices are fed via a common supply line, they can work together by switching off the supply voltage be deactivated. Likewise, all signal sources can be activated by supplying the common supply line with voltage.
  • each individual source can be switched on or off separately from the hearing aid amplifier. In this case, however, individual supply lines have to be provided by the hearing aid amplifier for each signal source. This requires additional cables and additional connections to the hearing aid system.
  • a circuit for powering amplifiers in which an input signal in a preamplifier, which is fed by a supply source, is amplified.
  • the output signal of the preamplifier is supplied to the amplifier and control means.
  • the control means detects that the first signal has arrived at the terminal, the amplifier is driven with a large supply current.
  • the supply current for the amplifier is set to the savings current value.
  • the amplifier amplifies the output of the preamplifier, while the output of the amplifier in a playback device, for. As a speaker is played.
  • a hearing aid which has a special circuit for reducing power consumption.
  • a detector circuit compares the output level of a high frequency amplifier with a reference voltage and outputs a high level signal when the output level is higher than the reference voltage.
  • a power supply shutdown circuit turns on a switching element only when the high level signal is generated by the detector circuit and thereby applies the battery voltage to the electrical circuit of the hearing aid. If the output level of the amplifier is too low, the battery voltage is switched off to reduce power consumption.
  • this application relates only to a hearing aid with a signal source or a signal processing path.
  • the object of the present invention is to ensure the switching on and off of signal processing devices individually, without having to provide additional lines and connections.
  • this object is achieved by a signal processing device according to claim 1.
  • FIG. 1 shows a schematic circuit diagram of a hearing aid amplifier 1 to the two microphones 2 and 3 are each connected with an integrated preamplifier and AD converter and a telecoil 4 also with integrated amplifier and AD converter.
  • the two microphones 2, 3 and the telecoil 4 supply as signal sources the signals Signal 1, Signal 2 and Signal 3 via their own signal line to the hearing aid amplifier 1.
  • This supplies the signal sources 2, 3, 4 via a common line which is suitable for the three sources branched, with electricity.
  • This is indicated by the two lines with the names "ground” and "V_ttle”. It is essential here that only one voltage supply line with one ground terminal and one operating voltage pole leads from the hearing aid amplifier 1 to the signal sources, so that a common central voltage supply results.
  • a signal source 2 is shown, which is connected via a signal line 5 to the hearing aid amplifier 1.
  • the signal source 2 has a preamplifier 6 at the input of which a digital data signal 7 is present.
  • This data signal comes from a detector, not shown, for. As microphone, and a downstream AD converter, also not shown.
  • the signal 8 is present.
  • the input of the hearing aid amplifier 1, or the signal line 5, can be connected to ground with a first switch 9 in a low-impedance manner.
  • FIG. 3 shows a more detailed signal circuit diagram of the signal source 2.
  • the preamplifier 6 feeds the signal line 5 via a second switch 11.
  • the signal line 5 is tapped by a monitoring circuit 12.
  • This monitoring circuit 12 controls the second switch 11 and supplies a sampling or switching or control signal to a shutdown control device 13. This switches off the preamplifier 6 of the signal source 2 and possibly further power consumers on the basis of the switching signal from the monitoring circuit 12. If the signal at these sampling times 14 is below a predetermined threshold, the monitoring circuit 12 recognizes that the first switch 9 of the amplifier 1 is closed, so that the signal source 2 or the Preamplifier 6 can be turned off.
  • the signal line is always checked by the monitoring logic or circuit 12, when the data at the level "high” stand. If the signal line is then not also at the value "high", the signal source 2 is switched off.
  • the switched-off preamplifier 6 can not pull the signal line 5 to a level necessary for turning on "high". Therefore, it is necessary that in the signal source 2, a driver 15 with low power consumption remains active even during the off state of the preamplifier 6.
  • the output of the weak driver 15 is connected via the second switch 11 to the signal line 5.
  • the weak driver 15 can drive the signal line 5 back to the "high" level when the first switch 9 is opened again in the hearing aid amplifier 1.
  • the monitoring circuit 12 detects this, so that the signal source 2 is turned on again.
  • FIG. 4 finally shows the waveform in the signal line 5 at an analog signal source 2.
  • the analog signal of a detector is applied to the input of the preamplifier 6 and has the in FIG. 4
  • This waveform 16 moves between ground and a source voltage V_sammlung around a detector operating point.
  • V_ISE source voltage
  • the analog signal After preamplification, in normal operation, when the first switch 9 is open, the analog signal has substantially the same waveform, possibly with other signal values.
  • This preamplifier signal 17 moves around the operating point of the preamplifier 6. However, if the first switch 9 is closed, the output signal of the preamplifier 2 is pulled according to the waveform 18 to ground.
  • the monitoring circuit 12 recognizes, for example, based on the mean value, that the signal 18 no longer moves about the operating point of the preamplifier 6, so that the signal source 2 can be switched off.
  • the input of the hearing aid amplifier 1 is normally selected high impedance. If the amplifier input is switched to low impedance, this detects the respective signal source or component and switches off.
  • the hearing aid system may disable the signal source by changing any electrical characteristic of the signal input. For this purpose, the signal source must detect the corresponding electrical property of the signal input. At certain predefined values, the signal source may then turn itself off and put it in a lower power state.
  • an evaluation of the complex resistance of the signal input of the hearing aid system could take place.

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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)
  • Amplifiers (AREA)
  • Dc Digital Transmission (AREA)
  • Stereophonic System (AREA)
  • Stereo-Broadcasting Methods (AREA)
  • Selective Calling Equipment (AREA)
  • Signal Processing Not Specific To The Method Of Recording And Reproducing (AREA)
  • Electronic Switches (AREA)

Claims (8)

  1. Dispositif ( 2, 3, 4 ) de traitement du signal pour des prothèses auditives comprenant
    un circuit ( 12 ) de contrôle d'une ligne ( 5 ) de signal,
    un préamplificateur ( 6 ) pour amplifier un signal et
    un dispositif ( 13 ) de commande commandé par le circuit ( 12 ) de contrôle et par lequel le préamplificateur ( 6 ) peut être mis en circuit et hors circuit,
    caractérisé par
    un étage ( 15 ) d'attaque qui a une consommation de puissance plus petite que le préamplificateur ( 6 ), et
    un dispositif ( 11 ) de commutation qui commute en étant commandé par le circuit ( 12 ) de contrôle entre le préamplificateur ( 6 ) et l'étage ( 15 ) d'attaque, de manière à avoir sur la ligne ( 5 ) de signal soit le signal de sortie du préamplificateur ( 6 ), soit le signal de sortie de l'étage ( 15 ) d'attaque, le préamplificateur ( 6 ) étant mis hors circuit par le dispositif ( 13 ) de commande lorsque l'étage ( 15 ) d'attaque est branché sur la ligne ( 5 ) de signal.
  2. Dispositif de traitement de signal suivant la revendication 1, dans lequel d'autres composants d'une prothèse auditive peuvent être mis en circuit et hors circuit par le dispositif ( 13 ) de commande.
  3. Dispositif de traitement de signal suivant la revendication 1 ou 2, dans lequel un signal de tension binaire statique à la ligne ( 5 ) de signal et un contrôle s'effectuent par le circuit ( 12 ) de contrôle toujours à un niveau de tension "high".
  4. Dispositif de traitement de signal suivant la revendication 1 ou 2, dans lequel un signal analogique de tension s'applique à la ligne ( 5 ) de signal et une composante continue du signal analogique de tension est contrôlée par le circuit ( 12 ) de contrôle.
  5. Prothèse auditive comprenant un ou plusieurs dispositifs ( 2, 3, 4 ) de traitement du signal suivant l'une des revendications 1 à 4, qui a un amplificateur ( 1 ) dont l'entrée est reliée à la ligne ( 5 ) de signal respective de chacun des dispositifs ( 2, 3, 4 ) de traitement du signal, la ligne ( 5 ) de signal respective pouvant être mise à la masse ou à une tension d'alimentation par un commutateur ( 9 ).
  6. Procédé de commande d'un dispositif ( 2, 3, 4 ) de traitement du signal pour des prothèses auditives par
    branchement d'un préamplificateur ( 6 ) sur une ligne ( 5 ) de signal,
    contrôle de la ligne ( 5 ) de signal,
    commutation de la ligne ( 5 ) de signal du préamplificateur ( 6 ) à l'étage ( 15 ) d'attaque qui a une consommation de puissance plus petite que le préamplificateur ( 6 ), conformément à un résultat de contrôle lors du contrôle de la ligne ( 5 ) de signal, et
    mise hors circuit de l'amplificateur ( 6 ) lorsque l'étage ( 15 ) d'attaque est branché sur la ligne ( 5 ) de signal.
  7. Procédé suivant la revendication 8, dans lequel la ligne ( 5 ) de signal par laquelle le signal est transmis du dispositif ( 2, 3, 4 ) de traitement du signal à un amplificateur ( 1 ) de la prothèse auditive est mise à la masse ou à une tension d'alimentation à petite valeur ohmique en amont de l'amplificateur ( 1 ) de la prothèse auditive lorsque le dispositif ( 2, 3, 4 ) de traitement du signal est mis hors circuit.
  8. Procédé suivant la revendication 6 ou 7, dans lequel d'autres composants d'une prothèse auditive sont mis hors circuit par la mise hors circuit du préamplificateur ( 6 ).
EP03004692A 2002-03-14 2003-03-03 Déconnexion de dispostifs de traitement de signal d' une prothèse auditive Expired - Lifetime EP1349421B1 (fr)

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
DE10211364 2002-03-14
DE10211364A DE10211364B4 (de) 2002-03-14 2002-03-14 Abschalten von Signalverarbeitungsvorrichtungen eines Hörgeräts

Publications (3)

Publication Number Publication Date
EP1349421A2 EP1349421A2 (fr) 2003-10-01
EP1349421A3 EP1349421A3 (fr) 2008-01-23
EP1349421B1 true EP1349421B1 (fr) 2008-08-06

Family

ID=27797780

Family Applications (1)

Application Number Title Priority Date Filing Date
EP03004692A Expired - Lifetime EP1349421B1 (fr) 2002-03-14 2003-03-03 Déconnexion de dispostifs de traitement de signal d' une prothèse auditive

Country Status (5)

Country Link
US (1) US6920226B2 (fr)
EP (1) EP1349421B1 (fr)
AT (1) ATE404029T1 (fr)
DE (2) DE10211364B4 (fr)
DK (1) DK1349421T3 (fr)

Families Citing this family (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
DE10344366B3 (de) * 2003-09-24 2005-04-21 Siemens Audiologische Technik Gmbh Hörhilfegerät mit automatischer Umschaltung der Spannungsversorgung für externe Komponenten und entsprechendes Verfahren
US7529587B2 (en) 2003-10-13 2009-05-05 Cochlear Limited External speech processor unit for an auditory prosthesis
DE602004010317T2 (de) * 2004-02-05 2008-10-16 Phonak Ag Verfahren zum Betreiben eines Hörhilfegerätes und Hörhilfegerät
DE102004023049B4 (de) * 2004-05-11 2006-05-04 Siemens Audiologische Technik Gmbh Hörgerätevorrichtung mit einer Schalteinrichtung zum An- und Abschalten sowie entsprechendes Verfahren
DE102006046703A1 (de) 2006-10-02 2008-04-17 Siemens Audiologische Technik Gmbh Hörvorrichtung mit gesteuerten Eingangskanälen und entsprechendes Verfahren

Family Cites Families (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
NL170210C (nl) 1972-03-25 1982-10-01 Philips Nv Elektronische schakeling.
JPS554160A (en) * 1978-06-26 1980-01-12 Seiko Epson Corp Hearing aid
JPS60123198A (ja) * 1983-12-08 1985-07-01 Nippon Gakki Seizo Kk 補聴器
EP0676909A1 (fr) * 1994-03-31 1995-10-11 Siemens Audiologische Technik GmbH Prothèse auditive programmable
JP4336458B2 (ja) * 1999-10-15 2009-09-30 フォーナック アーゲー 両耳用補聴器の同期化方法

Also Published As

Publication number Publication date
US20040008854A1 (en) 2004-01-15
ATE404029T1 (de) 2008-08-15
EP1349421A2 (fr) 2003-10-01
US6920226B2 (en) 2005-07-19
DE10211364A1 (de) 2003-10-09
DE50310270D1 (de) 2008-09-18
EP1349421A3 (fr) 2008-01-23
DE10211364B4 (de) 2004-02-05
DK1349421T3 (da) 2008-11-24

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