EP1480492A2 - Système de bobine de transmission et télécommande pour une prothèse auditive - Google Patents

Système de bobine de transmission et télécommande pour une prothèse auditive Download PDF

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Publication number
EP1480492A2
EP1480492A2 EP04009708A EP04009708A EP1480492A2 EP 1480492 A2 EP1480492 A2 EP 1480492A2 EP 04009708 A EP04009708 A EP 04009708A EP 04009708 A EP04009708 A EP 04009708A EP 1480492 A2 EP1480492 A2 EP 1480492A2
Authority
EP
European Patent Office
Prior art keywords
coil
transmitter
coils
transmitter coil
coil system
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
EP04009708A
Other languages
German (de)
English (en)
Other versions
EP1480492A3 (fr
EP1480492B1 (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 GmbH
Original Assignee
Siemens Audiologische 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
Application filed by Siemens Audiologische Technik GmbH filed Critical Siemens Audiologische Technik GmbH
Publication of EP1480492A2 publication Critical patent/EP1480492A2/fr
Publication of EP1480492A3 publication Critical patent/EP1480492A3/fr
Application granted granted Critical
Publication of EP1480492B1 publication Critical patent/EP1480492B1/fr
Anticipated expiration legal-status Critical
Expired - Lifetime legal-status Critical Current

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Classifications

    • H—ELECTRICITY
    • H01—ELECTRIC ELEMENTS
    • H01F—MAGNETS; INDUCTANCES; TRANSFORMERS; SELECTION OF MATERIALS FOR THEIR MAGNETIC PROPERTIES
    • H01F19/00—Fixed transformers or mutual inductances of the signal type
    • H01F19/02—Audio-frequency transformers or mutual inductances, i.e. not suitable for handling frequencies considerably beyond the audio range
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; ELECTRIC HEARING AIDS; PUBLIC ADDRESS SYSTEMS
    • H04R25/00—Electric hearing aids
    • H04R25/55—Electric hearing aids using an external connection, either wireless or wired
    • H04R25/554—Electric hearing aids using an external connection, either wireless or wired using a wireless connection, e.g. between microphone and amplifier or using Tcoils
    • H—ELECTRICITY
    • H01—ELECTRIC ELEMENTS
    • H01F—MAGNETS; INDUCTANCES; TRANSFORMERS; SELECTION OF MATERIALS FOR THEIR MAGNETIC PROPERTIES
    • H01F21/00—Variable inductances or transformers of the signal type
    • H01F21/12—Variable inductances or transformers of the signal type discontinuously variable, e.g. tapped
    • H—ELECTRICITY
    • H01—ELECTRIC ELEMENTS
    • H01F—MAGNETS; INDUCTANCES; TRANSFORMERS; SELECTION OF MATERIALS FOR THEIR MAGNETIC PROPERTIES
    • H01F30/00—Fixed transformers not covered by group H01F19/00
    • H01F30/06—Fixed transformers not covered by group H01F19/00 characterised by the structure
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; ELECTRIC HEARING AIDS; PUBLIC ADDRESS SYSTEMS
    • H04R2225/00—Details of deaf aids covered by H04R25/00, not provided for in any of its subgroups
    • H04R2225/51—Aspects of antennas or their circuitry in or for hearing aids
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; ELECTRIC HEARING AIDS; PUBLIC ADDRESS SYSTEMS
    • H04R25/00—Electric hearing aids
    • H04R25/55—Electric hearing aids using an external connection, either wireless or wired
    • H04R25/558—Remote control, e.g. of amplification, frequency

Definitions

  • the invention relates to a transmitter coil system with a first and a second transmitter coil and with a coil core and a remote control for a hearing aid with such Transmitting coil system.
  • Transmission systems that are used as carriers e.g. generated by coils Using magnetic fields, data can be transmitted wirelessly short distances, i.e. e.g. over a few decimeters, energy efficient transfer.
  • Such inductive transmission systems work mostly at relatively low frequencies in the range of a few kilohertz to a few hundred kilohertz.
  • the transmission technology of long-wave inductive data transmission is due to the disadvantage of low Range rarely used. This disadvantage is due to the decrease in transmission field energy with the third power of Distance. To bridge somewhat larger distances (1-2m), are already having comparatively strong transmission powers strong fields.
  • a strong field with sufficient field strength can generated by a coil with many turns.
  • a such coils have a correspondingly high inductance and thus a correspondingly high AC resistance on.
  • the maximum current that can be sent through the coil can be obtained from the quotient of the supply voltage and AC resistance.
  • DE 199 15 846 C1 describes a partially implantable system known for the rehabilitation of a hearing impairment that a wireless telemetry device for the transmission of data between an implantable part of the system and an external one Unit.
  • the Coil body made of a stamped part with two end formings consists of a coil winding wound on the bobbin limit laterally.
  • the invention is based on the object of a transmitter coil system and to specify a remote control for a hearing aid, which despite a limited availability Supply voltage a sufficiently high transmission power in particular for data transmission.
  • the first task is with a transmitter coil system a first and a second transmitter coil and with one Solved coil core in that the first transmitter coil with a Excitation unit can be connected, the second transmitter coil as Part of a resonant resonant circuit can be used and the two transmitter coils next to each other on the coil core are wound so that both transmitter coils are loosely magnetically connected to each other are coupled.
  • both transmitter coils are loosely magnetic are coupled together. This is done, for example achieved that between the two transmitter coils a non-winding Space is arranged.
  • the loose coupling leads to one Excitation of the first transmitter coil using, for example alternating operating voltages by the excitation unit a resonantly excessive excitation of the second transmitter coil.
  • both transmitter coils are not of the same Magnetic field flow through, like that with a rigid Coupling is the case where both transmit coils are on top of each other and are not wrapped side by side around the coil core, i.e. the same magnetic field flows through them.
  • the loose coupling results in excitation of the second Transmitter coil with a phase shift that is rocking of the voltage applied to the second transmitter coil. Because of the larger voltage, a higher current flows, which in turn leads to a much higher transmission magnetic field leads. The transmission power is considerably stronger than that in Case of rigid coupling. That is, the coil system works much more effectively.
  • the invention does not make any additional voltage multipliers needs more, or batteries can to be used with less tension or less Batteries can be connected in series. This can also be done Save space or installation space.
  • Another advantage of the possibility of long-wave data transmission by means of the transmitter coil system lies in the problem-free Penetration of matter without noticeably influencing it. Especially when using the transmitter coil system with hearing aids this is vital since is sent in the area of the head and of course no influence of the tissue may take place.
  • the first transmitter coil fewer windings than the second transmitter coil. This enables a low-resistance low-loss, i.e. power-saving, Excitation of the first transmitter coil.
  • the resonantly excitable the second transmitter coil has many turns. Because the magnetic field determined by the sum of the currents in all turns this results in a strong transmission field. Know that second coil has a larger number of turns than the first Transmitter coil is, therefore, the generation of strong transmission fields very efficient.
  • the second transmitter coil forms a capacitor Resonant circuit.
  • the resonant circuit is not too high Goodness, i.e. has a broad quality distribution, which the covers both frequencies used.
  • the first transmitter coil consists of two sub-coils that are symmetrical arranged to the second transmitter coil on the coil core are.
  • the division into two sub-coils, for example with a center tap has the advantage of simpler power supply with fewer components (e.g. only two transistors) and represents a way of making the sub-coils symmetrical to arrange.
  • the symmetrical arrangement has in turn the advantage of a symmetrically radiated field.
  • the coil system is used for sending and receiving, in addition to the transmitter coil (the transmitter coils) Reception coil needed.
  • This receiving coil usually has significantly more turns than the transmitter coils, if possible high voltages when receiving weak magnetic fields to reach.
  • the receiving coil is advantageous to use the receiving coil as second coil to use. Especially if not is sent and received at the same time, but sending and Reception take place sequentially.
  • the use of a film capacitor is advantageous for the resonant circuit used for sending and receiving and its capacity is independent of the applied voltage is. This changes the vibration frequency of the Resonant circuit is not between the high voltages when sending and the low voltages on reception.
  • the invention do not need two independent transmitting or receiving coils two coil cores to be wound. Instead, you can both spools are wound on a single core. Thereby space can be saved. Especially under conditions like they are available with remote controls, is in the kHz frequency range relatively large coils little space.
  • the Saving a core enables a significantly smaller volume of the transmitting (receiving) coil system, or e.g. the remote control.
  • the combination of both Coils on a core are cheaper to manufacture than that Production of two completely separate coils.
  • the Receiver coil Since a receiving coil used as a second transmission coil in the Sending is heavily overloaded, it is advantageous that the Receiver coil to protect against destruction of a receiver coil belonging receiving unit via a protective circuit is connected to the receiving unit.
  • the second task is performed by a remote control for a hearing aid with such a transmitter coil system solved.
  • Figure 1 shows a coil system 1 for a remote control a hearing aid.
  • the excitation frequencies are the used Dual frequency excitation at 116 kHz and 121 kHz.
  • the remote control is operated manually, so that a range of approx. 1-2 m is required to ensure good communication with the To enable hearing aid.
  • the remote control has one handy size on.
  • a battery serves as an energy source, which limits the available voltage.
  • the transmitter coil system 1 has a first transmitter coil 3, one second transmitter coil 5 and a coil core 7.
  • the first Transmitting coil 3 consists of two sub-coils 3A, 3B, for example be formed by tapping the center of a coil.
  • the sub-coils 3A, 3B each have 50 windings and take up approx. 10 mm of the approx. 35 mm long coil core.
  • On the first transmitter coil 3 closes an approximately 5 mm long non-winding space 9.
  • the second transmitter coil 5 On the other side of the non-winding Room 9 is the second transmitter coil 5 a length of approx. 20 mm with a number of windings of approx. 150 Turns.
  • the second transmitter coil forms with one not shown Capacitor of e.g. 2 nF a resonant circuit.
  • the coil core is a ferrite core with a diameter of approx. 6 mm.
  • the partial coils 3A, 3B are wound on one another and over one Center tap can be connected to a transmitter unit.
  • Figure 2 shows a symmetrical arrangement of a transmitter coil system 11, in which the first transmitter coil, which in turn in two sub-coils 13A, 13B is divided, symmetrically on the both ends of the second transmitter coil 15 is arranged. Between the sub-coils 13A, 13B and the second transmission coil 15 there are two non-winding spaces 17A, 17B.
  • the spools are wound around a coil core 19.
  • FIG. 3 shows the course of the voltages on the coils from FIG. 1.
  • the voltage U is plotted over time T over the first 100 microseconds.
  • the voltage value 21, which is applied to the partial coils 3A, 3B, is approximately 3.7 V.
  • the voltage profile U5, which is applied to the second transmitter coil 5, is shown in FIG.
  • the voltage value 23, which has set in after a rise time of 60 ⁇ s, is approximately 80 V. This corresponds to a significantly resonantly excessive voltage at the second transmitter coil 5 by a factor of ten. With rigid coupling there would be a maximum of a factor of three in the gain due to the number of windings.
  • FIG. 4 shows a remote control 100 for a hearing aid based on a schematic circuit diagram.
  • the excitation unit 101 is equipped with one or more transmitter coils 102.
  • the transmission coils are connected to a common core 103
  • the arrangement of the coils 102, 104 corresponds for example the arrangements of Figures 1 or 2.
  • Parallel to the receiving coil 104 is a resonant circuit capacitor 105 connected.
  • a protection circuit consisting of a Protection capacitor 106 and one connected in series Parallel connection of two anti-parallel diodes 107 and 108 connected.
  • the diodes 107 and 108 are connected to the input of a receiving unit 109.
  • the mode of operation of this circuit is described in more detail below explained.
  • the separate receiving coil 104 which is necessary anyway is wound on the same core next to the transmitter coils 102 and is loosely coupled to it. This will make the receiving coil 104, the complete with their associated capacitor 105 Represents resonant circuit 110 by the transmitter coils 102 also stimulated to vibrate. Since the receiving coil 104 in the Compared to the transmitter coils 102 has more turns in the resonantly excited resonant circuit 110 during the transmission process generated relatively high voltages due to the vibration effect of the oscillating circuit 110 despite the many turns again very high currents and thus radiated magnetic fields produce. Deliver the actual transmission coils 102 now only the radiated energy. Therefore needs not as much current to flow through the transmitter coils 102. The strong transmission field is now from that through the transmission coils 102 excited receiving coil 104 generated.
  • the frequency is also absolutely stable and can be specified from the outside. Tolerances of the components in the resonant circuits 110 therefore have no influence on the transmission frequency. They only have a certain effect on efficiency of the sending process.
  • the inductances of the transmission coils 102 change the Inductance of the loosely coupled receiving coil 104 so that the natural frequency of the resonant circuit 110 after changing the associated one Capacitance value of the resonant circuit capacitor 5 needs to be corrected.
  • the inductance of the resonant circuit 110 becomes smaller, i.e. the capacity of the resonant circuit 110 must be increased.
  • a suitable capacity can be used without Problems are interconnected in such a way that they can be used as Protection for the sensitive receiving unit 109 is used. There such a protection circuit 112 is needed anyway this circuit solution without additional components.
  • the Protection circuit 112 consists only of the correction capacitor 106 and the antiparallel connected diodes 107 and 108, the connected in parallel to the capacitor 105 of the resonant circuit 110 are.
  • the received signals are at the diodes 107, 108 tapped.
  • the diodes 107, 108 go into the conductive State and thus switch the upstream Capacitor 106 in parallel with the resonant circuit capacitor 105 of the Reception circuit. So that the resonance frequency of the resonant circuit 110 corrected for broadcasting. simultaneously are the signals at the input of the high impedance receiver limited to a maximum of approximately 0.7 V by the diodes 107, 108. The most of the voltage generated by the resonant circuit 110 then occurs the protective capacitor 106.
  • the reception signals are so small that block the diodes 107, 108.
  • the voltages of the received signals typically reach at most the mV range. Thereby is only the original resonant circuit capacitor 105 active.
  • the transmission coils 102 are switched off. That is, at least one connector of each transmitter coil 102 is open. This affects the resonant circuit 110 no longer out. So it can be based on its reception frequency which he is tuned to swing freely. The signal is thus almost no losses through the protection or correction capacitor 6 further transmitted to the protection diodes 107, 108. Because of the low reception voltage, these are diodes 107, 108 blocked. That the receive voltage can be at the diode connections in full from the high-resistance receiver input be removed.
  • reception coil is used as a transmission amplifier
  • the protective capacitor also serves as a correction capacitor

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  • Engineering & Computer Science (AREA)
  • Computer Networks & Wireless Communication (AREA)
  • Power Engineering (AREA)
  • Neurosurgery (AREA)
  • Health & Medical Sciences (AREA)
  • General Health & Medical Sciences (AREA)
  • Multimedia (AREA)
  • Otolaryngology (AREA)
  • Physics & Mathematics (AREA)
  • Acoustics & Sound (AREA)
  • Signal Processing (AREA)
  • Near-Field Transmission Systems (AREA)
  • Selective Calling Equipment (AREA)
  • Transmitters (AREA)
EP04009708A 2003-05-22 2004-04-23 Système de bobine de transmission et télécommande pour une prothèse auditive Expired - Lifetime EP1480492B1 (fr)

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
DE10323219A DE10323219B3 (de) 2003-05-22 2003-05-22 Sendespulensystem und Fernbedienung für ein Hörhilfsgerät
DE10323219 2003-05-22

Publications (3)

Publication Number Publication Date
EP1480492A2 true EP1480492A2 (fr) 2004-11-24
EP1480492A3 EP1480492A3 (fr) 2007-09-19
EP1480492B1 EP1480492B1 (fr) 2010-09-29

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ID=33039275

Family Applications (1)

Application Number Title Priority Date Filing Date
EP04009708A Expired - Lifetime EP1480492B1 (fr) 2003-05-22 2004-04-23 Système de bobine de transmission et télécommande pour une prothèse auditive

Country Status (6)

Country Link
US (1) US7277553B2 (fr)
EP (1) EP1480492B1 (fr)
AT (1) ATE483331T1 (fr)
AU (1) AU2004202225B2 (fr)
DE (2) DE10323219B3 (fr)
DK (1) DK1480492T3 (fr)

Cited By (10)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
EP1981253A1 (fr) 2007-04-10 2008-10-15 Oticon A/S Interface utilisateur pour un dispositif de communications
EP2117180A1 (fr) 2008-05-07 2009-11-11 Oticon A/S Lien sans fil unidirectionnel à courte distance
EP2239964A1 (fr) * 2009-04-07 2010-10-13 Siemens Medical Instruments Pte. Ltd. Agencement d'appareil auditif doté d'un collier de support équipé d'une antenne intégrée et procédé correspondant de transmission sans fil de données
EP1883165A3 (fr) * 2006-07-28 2011-07-27 Siemens Audiologische Technik GmbH Système de réception et procédé destiné à la transmission d'informations pour un dispositif otologique
EP2400665A1 (fr) 2010-06-22 2011-12-28 Oticon A/S Entrée/sortie d'excursion de tension élevée activée dans un procédé CI standard utilisant une transformation d'impédance passive
EP2400546A1 (fr) 2010-06-22 2011-12-28 Oticon A/S Protection ESD dans un procédé BI-CMOS ou CMOS standard qui accepte des entrées/sorties à haute tension
EP2472907A1 (fr) 2010-12-29 2012-07-04 Oticon A/S Système d'écoute comportant un dispositif d'alerte et dispositif d'écoute
US8358795B2 (en) 2006-07-28 2013-01-22 Siemens Audiologische Technik Gmbh Receiver system and method for transmitting information for an otological device
US8514965B2 (en) 2010-03-10 2013-08-20 Oticon A/S Wireless communication system with a modulation bandwidth comparable to or exceeding the bandwidth of the transmitter and/or receiver antennas
US8526879B2 (en) 2007-04-11 2013-09-03 Oticon A/S Wireless communication device for inductive coupling to another device

Families Citing this family (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
KR100591814B1 (ko) * 2005-02-21 2006-06-20 주식회사 팬택앤큐리텔 청각 장애인을 위한 오디오 신호 출력 방법과 그를 이용한이동통신 단말기
DE102005020315A1 (de) 2005-05-02 2006-11-09 Siemens Audiologische Technik Gmbh Hörgerätefernbedienung als Netzwerkkomponente und entsprechende Verwendung
DE102007011841C5 (de) 2007-03-12 2015-05-13 Siemens Audiologische Technik Gmbh Übertragungsverfahren mit dynamischer Sendeleistungsanpassung und entsprechendes Hörgerätesystem
EP2056626B1 (fr) * 2007-11-02 2012-07-25 Oticon A/S Principe de transmission sans fil
US20140085757A1 (en) * 2012-09-21 2014-03-27 Enphase Energy, Inc. Surge blocking inductor

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Cited By (13)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
EP1883165A3 (fr) * 2006-07-28 2011-07-27 Siemens Audiologische Technik GmbH Système de réception et procédé destiné à la transmission d'informations pour un dispositif otologique
US8358795B2 (en) 2006-07-28 2013-01-22 Siemens Audiologische Technik Gmbh Receiver system and method for transmitting information for an otological device
EP1981253A1 (fr) 2007-04-10 2008-10-15 Oticon A/S Interface utilisateur pour un dispositif de communications
US8526879B2 (en) 2007-04-11 2013-09-03 Oticon A/S Wireless communication device for inductive coupling to another device
EP2117180A1 (fr) 2008-05-07 2009-11-11 Oticon A/S Lien sans fil unidirectionnel à courte distance
US8340332B2 (en) 2009-04-07 2012-12-25 Siemens Medical Instruments Pte. Ltd. Hearing aid configuration with a lanyard with integrated antenna and associated method for wireless transmission of data
EP2239964A1 (fr) * 2009-04-07 2010-10-13 Siemens Medical Instruments Pte. Ltd. Agencement d'appareil auditif doté d'un collier de support équipé d'une antenne intégrée et procédé correspondant de transmission sans fil de données
US8514965B2 (en) 2010-03-10 2013-08-20 Oticon A/S Wireless communication system with a modulation bandwidth comparable to or exceeding the bandwidth of the transmitter and/or receiver antennas
EP2400546A1 (fr) 2010-06-22 2011-12-28 Oticon A/S Protection ESD dans un procédé BI-CMOS ou CMOS standard qui accepte des entrées/sorties à haute tension
EP2400665A1 (fr) 2010-06-22 2011-12-28 Oticon A/S Entrée/sortie d'excursion de tension élevée activée dans un procédé CI standard utilisant une transformation d'impédance passive
US8639195B2 (en) 2010-06-22 2014-01-28 Oticon A/S High voltage swing input/output enabled in a standard IC process using passive impedance transformation
EP2472907A1 (fr) 2010-12-29 2012-07-04 Oticon A/S Système d'écoute comportant un dispositif d'alerte et dispositif d'écoute
US8760284B2 (en) 2010-12-29 2014-06-24 Oticon A/S Listening system comprising an alerting device and a listening device

Also Published As

Publication number Publication date
US20050036638A1 (en) 2005-02-17
DE502004011693D1 (de) 2010-11-11
DK1480492T3 (da) 2011-01-31
ATE483331T1 (de) 2010-10-15
AU2004202225A1 (en) 2004-12-09
US7277553B2 (en) 2007-10-02
EP1480492A3 (fr) 2007-09-19
AU2004202225B2 (en) 2009-04-23
DE10323219B3 (de) 2004-12-09
EP1480492B1 (fr) 2010-09-29

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