EP2053878B1 - Prothèse auditive utilisant un régulateur de commutation inductif en tant qu'émetteur radio - Google Patents

Prothèse auditive utilisant un régulateur de commutation inductif en tant qu'émetteur radio Download PDF

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Publication number
EP2053878B1
EP2053878B1 EP08164390.0A EP08164390A EP2053878B1 EP 2053878 B1 EP2053878 B1 EP 2053878B1 EP 08164390 A EP08164390 A EP 08164390A EP 2053878 B1 EP2053878 B1 EP 2053878B1
Authority
EP
European Patent Office
Prior art keywords
inductor
switching regulator
hearing apparatus
hearing
energy
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.)
Not-in-force
Application number
EP08164390.0A
Other languages
German (de)
English (en)
Other versions
EP2053878A2 (fr
EP2053878A3 (fr
Inventor
Jürgen Reithinger
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 Pte Ltd
Original Assignee
Siemens Medical Instruments Pte Ltd
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 Siemens Medical Instruments Pte Ltd filed Critical Siemens Medical Instruments Pte Ltd
Publication of EP2053878A2 publication Critical patent/EP2053878A2/fr
Publication of EP2053878A3 publication Critical patent/EP2053878A3/fr
Application granted granted Critical
Publication of EP2053878B1 publication Critical patent/EP2053878B1/fr
Not-in-force legal-status Critical Current
Anticipated expiration legal-status Critical

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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
    • H04R25/554—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
    • 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
    • H04R2225/61—Aspects relating to mechanical or electronic switches or control elements, e.g. functioning
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R25/00—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception
    • H04R25/35—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception using translation techniques
    • H04R25/353—Frequency, e.g. frequency shift or compression

Definitions

  • the present invention relates to a hearing apparatus with a switching regulator including an inductor and a transmitter including an antenna for wireless electromagnetic transmission of data.
  • a hearing device is understood here to mean any device for sound output which can be worn on or in the ear, in particular a hearing device, a headset, headphones and the like.
  • Hearing aids are portable hearing aids that are used to care for the hearing impaired.
  • different types of hearing aids such as behind-the-ear hearing aids (BTE), hearing aid with external receiver (RIC: receiver in the canal) and in-the-ear hearing aids (IDO), e.g. Concha hearing aids or canal hearing aids (ITE, CIC).
  • BTE behind-the-ear hearing aids
  • RIC hearing aid with external receiver
  • IDO in-the-ear hearing aids
  • ITE canal hearing aids
  • the hearing aids listed by way of example are worn on the outer ear or in the ear canal.
  • bone conduction hearing aids, implantable or vibrotactile hearing aids are also available on the market. The stimulation of the damaged hearing takes place either mechanically or electrically.
  • Hearing aids have in principle as essential components an input transducer, an amplifier and an output transducer.
  • the input transducer is usually a sound receiver, z. As a microphone, and / or an electromagnetic receiver, for. B. an induction coil.
  • the output transducer is usually used as an electroacoustic transducer, z. As miniature speaker, or as an electromechanical transducer, z. B. bone conduction, realized.
  • the amplifier is usually integrated in a signal processing unit. This basic structure is in FIG. 1 shown using the example of a behind-the-ear hearing aid. In a hearing aid housing 1 for carrying behind the ear are one or more microphones 2 to Built-in sound recording from the environment.
  • a signal processing unit 3 which is also integrated in the hearing aid housing 1, processes the microphone signals and amplifies them.
  • the output signal of the signal processing unit 3 is transmitted to a loudspeaker or earpiece 4, which outputs an acoustic signal.
  • the sound is optionally transmitted via a sound tube, which is fixed with an earmold in the ear canal, to the eardrum of the device carrier.
  • the power supply of the hearing device and in particular of the signal processing unit 3 is carried out by a likewise integrated into the hearing aid housing 1 battery. 5
  • the cell voltage which is higher than, for example, alkaline-manganese batteries or zinc-air batteries, must be reduced if the technology designed for 1.5 volt cells continues to be used should.
  • This technology which is currently in use, is designed for voltages below 1.5 volts to save energy.
  • lithium batteries deliver 3.0 volts and lithium batteries even nominally 3.6 volts to a maximum of 4.2 volts.
  • WO 2005/081583 A1 is a hearing aid with an antenna for receiving and transmitting electromagnetic signals known.
  • the hearing aid has a rechargeable battery that can be charged using a charging loop.
  • the antenna of the hearing device can be used as this charging loop on the secondary side of a charger.
  • pamphlet US 5,600,728 A shows a hearing device with Telecoil, which is used both for reception as a receiving antenna, as well as for an inductive switching regulator.
  • the inductive switching regulator transforms the supply voltage to the operating voltage of a memory module in the hearing device, which only has a very low energy requirement.
  • the object of the present invention is therefore to reduce the size of a hearing device having a transmitting device and a power supply with voltage regulation.
  • this object is achieved by a hearing device according to claim 1.
  • a component of the power supply namely the inductance of the switching regulator, at the same time for the data transmission of a transmitting device to use.
  • at least one component can be saved and consequently the installation space of the hearing apparatus can be reduced.
  • the inductance may comprise a partially open ring core. Due to the fact that the toroidal core is not completely closed, the magnetic flux is not completely guided in the toroidal core and can be used for electromagnetic data transmission.
  • an alternative embodiment is that the inductance in a cross-section 8-shaped, on one or has two sides open core.
  • the one or more openings serve to selectively effect electromagnetic emissions in order to realize a data transmission.
  • pulse width modulation pulse density modulation or amplitude modulation is used in the switching regulator for energy transmission.
  • modulation are characterized by the fact that they, as mentioned above, hardly affect the fundamental frequency and the fundamental phase of the signal of the switching regulator.
  • a further advantageous embodiment is that an additional inductance with a closed core is connected to the inductance switchable.
  • the additional inductance of the magnetic circuit is thus closed in the core, so that electromagnetic emissions are avoided as much as possible.
  • the hearing device here a hearing aid, an input transducer, in this case a microphone 10.
  • the microphone signal is fed to a signal processing unit 11, which in turn transmits an output signal to a receiver or loudspeaker 12.
  • the signal processing device 11 has a battery 13 with a downstream switching regulator 14.
  • the switching regulator 14 transforms the voltage supplied by the battery 13 to the desired operating voltage. If, for example, a lithium battery with 3 volts is used, the voltage is reduced below 1.5 volts, for example, with the aid of the switching regulator 14.
  • a rechargeable battery such as a lithium battery with nominally about 3.8 volts.
  • the voltage regulator 14 then regulates the battery voltage from 3.8 volts to, for example, 1.2 volts operating voltage.
  • the switching regulator 14 is an inductive switching regulator which has an inductance 15 for regulating the voltage.
  • the inductance is used to smooth the output voltage during switching operations.
  • FIG. 2 Furthermore, the hearing of FIG. 2 via a transmitter 16, which uses the inductance 15 as an antenna.
  • the inductance 15 is thus both part of the switching regulator 14 and the transmitter 16, which in FIG. 2 is indicated by the dashed line.
  • the inductor 15 thus has dual functionality.
  • the transmitter 16 is supplied as the signal processing unit 11 via the switching regulator 14 with energy.
  • the data to be transmitted is received by the transmitter 16 from the signal processing unit 11.
  • a single inductor 15 is used simultaneously for the switching regulator 14 and the transmitter 16, whereby a total of an inductance, which is known to require a lot of space, can be saved. So that the inductance can also be used as a transmitter or transmitting antenna, it must be able to radiate at least part of the magnetic energy. This can be achieved for example by an inductor z. B. does not have a closed ring core, but has a more or less large air gap in the ring.
  • FIG. 3 A first exemplary embodiment of such an inductor used according to the invention is shown in FIG FIG. 3 reproduced in plan view.
  • the inductor 15 here has a ring core 17 with a small gap 18.
  • the end faces 19, 20 of the gap 18 face each other, so that the magnetic field lines only slightly out of the gap. Consequently, only a weakly radiating antenna can be realized with this toroidal geometry.
  • FIG. 4 An example of this is in FIG. 4 shown. Again, it is an inductance 15 with a ring core 17.
  • the ring core 17 here has a large gap 21, wherein the end faces 22, 23 of the open ring core 17 are not directed towards each other. This geometry results in a completely different emission characteristic than in the example of FIG. 3 , In particular, the magnetic field lines extend far out of the gap 21, resulting in a stronger radiation.
  • any inductance whose core does not form a closed magnetic circuit If the core is closed, as mentioned, only a negligible proportion of the magnetic flux is conducted outside the core, which is unsuitable for an electromagnetic transmitter.
  • the geometry of the core of the inductance 15 is therefore to be optimized with regard to the emission characteristic, wherein a compromise is to be found with respect to as little energy loss as possible for the function of the switching regulator. For example, a linear dipole would be optimal for the transmitter, but unsuitable for the switching regulator, because it radiates almost all of the energy.
  • FIG. 5 A third embodiment of an inductor for common use for a switching regulator 14 and a transmitter 16 is shown in FIG FIG. 5 shown.
  • the core 24 has here in cross-section substantially the shape of an "8".
  • a winding 26 is wound.
  • the central web 25 is closed, while the two outer webs 27 and 28 each have a gap 29 and 30, respectively. These two gaps 29, 30 again provide the desired electromagnetic radiation.
  • the design of the inductor 15 is particularly suitable for SMD components, since they can be realized so very flat.
  • the pulse width modulation of the switching regulator can be realized independently of the modulations of the data transmission by means of conventional circuits.
  • a changing load of the switching regulator 14 would of course change the transmission energy due to the common use of the inductance 15.
  • the transmit power can be tuned to a system and its expected load by matching the radiated power and the shorted power by the geometry of the antenna or inductor, respectively.

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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)
  • Near-Field Transmission Systems (AREA)

Claims (7)

  1. Prothèse auditive comprenant
    - un dispensateur ( 13 ) d'énergie et
    - un dispositif ( 16 ) d'émission y compris une antenne pour l'émission sans fil électromagnétique de données,
    caractérisée par
    - un régleur ( 14 ) de commutation inductif y compris une inductance ( 15 ) qui sert à alimenter en énergie la prothèse auditive et le dispositif ( 16 ) d'émission et qui transforme, en une tension de fonctionnement, une tension fournie par le dispensateur ( 13 ) d'énergie, dans laquelle
    - l'inductance ( 15 ) du régleur ( 14 ) de commutation est identique à celle de l'antenne du dispositif ( 16 ) d'émission et sert à lisser la tension de fonctionnement dans des processus de commutation du régleur de commutation.
  2. Prothèse auditive suivant la revendication 1, dans laquelle l'inductance ( 15 ) a un noyau ( 17 ) toroïdale partiellement ouvert.
  3. Prothèse auditive suivant la revendication 1, dans laquelle l'inductance a un noyau ( 24 ) de section transversale en forme de 8 et ouvert sur un côté ou deux côtés.
  4. Prothèse auditive suivant l'une des revendications précédentes, dans laquelle la fréquence fondamentale et la phase fondamentale du signal du régleur ( 14 ) de commutation ne sont pas sensiblement modifiées lors du réglage, tandis qu'elles sont modifiées ou l'une d'entre elles l'est pour la transmission de données dans le signal du dispositif ( 16 ) d'émission.
  5. Prothèse auditive suivant la revendication 4, dans laquelle une modulation d'impulsion en largeur, une modulation d'impulsion en densité ou une modulation d'amplitude est utilisée dans le régleur ( 14 ) de commutation pour la transmission d'énergie.
  6. Prothèse auditive suivant la revendication 4 ou 5, dans laquelle une modulation en fréquence ou une modulation en phase est utilisée dans le dispositif ( 16 ) d'émission pour la transmission de données.
  7. Prothèse auditive suivant l'une des revendications précédentes, dans laquelle une inductance supplémentaire ayant un noyau fermé peut être raccordée avec possibilité de connexion à l'inductance ( 15 ).
EP08164390.0A 2007-10-26 2008-09-16 Prothèse auditive utilisant un régulateur de commutation inductif en tant qu'émetteur radio Not-in-force EP2053878B1 (fr)

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
US98276907P 2007-10-26 2007-10-26
DE102007051307A DE102007051307B4 (de) 2007-10-26 2007-10-26 Hörvorrichtung mit Nutzung eines induktiven Schaltreglers als Funksender

Publications (3)

Publication Number Publication Date
EP2053878A2 EP2053878A2 (fr) 2009-04-29
EP2053878A3 EP2053878A3 (fr) 2013-03-27
EP2053878B1 true EP2053878B1 (fr) 2014-07-23

Family

ID=40289284

Family Applications (1)

Application Number Title Priority Date Filing Date
EP08164390.0A Not-in-force EP2053878B1 (fr) 2007-10-26 2008-09-16 Prothèse auditive utilisant un régulateur de commutation inductif en tant qu'émetteur radio

Country Status (4)

Country Link
US (1) US8224003B2 (fr)
EP (1) EP2053878B1 (fr)
DE (1) DE102007051307B4 (fr)
DK (1) DK2053878T3 (fr)

Cited By (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US9426588B2 (en) 2012-03-16 2016-08-23 Sonova Ag Antenna for hearing device, ear tip and hearing device provided with such an antenna

Families Citing this family (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US8363872B2 (en) * 2009-04-14 2013-01-29 Dan Wiggins Magnetic earpiece coupling
US9319807B2 (en) 2012-02-28 2016-04-19 Cochlear Limited Device with combined antenna and transducer
DE102021200642B3 (de) 2021-01-25 2022-03-17 Sivantos Pte. Ltd. Hörgerät

Citations (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5600728A (en) * 1994-12-12 1997-02-04 Satre; Scot R. Miniaturized hearing aid circuit

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ZA892468B (en) * 1988-04-11 1989-12-27 Uniscan Ltd Improvements in or relating to cutting elements foactuator and communication system r rotary drill bits
AT395224B (de) * 1990-08-23 1992-10-27 Mikron Ges Fuer Integrierte Mi Kontaktloses, induktives datenuebertragungssystem
US6265100B1 (en) * 1998-02-23 2001-07-24 Research International, Inc. Rechargeable battery
JP3476000B2 (ja) * 1998-11-05 2003-12-10 三菱マテリアル株式会社 重畳したタグの識別方式
US7206426B1 (en) * 2000-01-07 2007-04-17 Etymotic Research, Inc. Multi-coil coupling system for hearing aid applications
DE10236469B3 (de) * 2002-08-08 2004-02-12 Siemens Audiologische Technik Gmbh Drahtlos programmierbares Hörhilfsgerät
DE10305833B3 (de) * 2003-02-12 2004-08-12 Siemens Audiologische Technik Gmbh Datenübertragungseinrichtung für Hörgeräte
US7742614B2 (en) * 2004-02-19 2010-06-22 Oticon A/S Hearing aid with antenna for reception and transmission of electromagnetic signals
US7151430B2 (en) * 2004-03-03 2006-12-19 Telefonaktiebolaget Lm Ericsson (Publ) Method of and inductor layout for reduced VCO coupling
DE102006024713B3 (de) * 2006-05-26 2007-08-30 Siemens Audiologische Technik Gmbh Hörvorrichtung mit einer Schwingkreisschaltung und entsprechendes Verfahren

Patent Citations (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5600728A (en) * 1994-12-12 1997-02-04 Satre; Scot R. Miniaturized hearing aid circuit

Cited By (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US9426588B2 (en) 2012-03-16 2016-08-23 Sonova Ag Antenna for hearing device, ear tip and hearing device provided with such an antenna
US10021495B2 (en) 2012-03-16 2018-07-10 Sonova Ag Antenna for hearing device, ear tip and hearing device provided with such an antenna

Also Published As

Publication number Publication date
DE102007051307A1 (de) 2009-04-30
US8224003B2 (en) 2012-07-17
US20090110221A1 (en) 2009-04-30
DK2053878T3 (da) 2014-10-20
EP2053878A2 (fr) 2009-04-29
EP2053878A3 (fr) 2013-03-27
DE102007051307B4 (de) 2011-02-17

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