WO2018179902A1 - Système de transmission d'énergie sans contact et aide auditive - Google Patents

Système de transmission d'énergie sans contact et aide auditive Download PDF

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Publication number
WO2018179902A1
WO2018179902A1 PCT/JP2018/004573 JP2018004573W WO2018179902A1 WO 2018179902 A1 WO2018179902 A1 WO 2018179902A1 JP 2018004573 W JP2018004573 W JP 2018004573W WO 2018179902 A1 WO2018179902 A1 WO 2018179902A1
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WO
WIPO (PCT)
Prior art keywords
power
telecoil
coil
power transmission
hearing aid
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Application number
PCT/JP2018/004573
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English (en)
Japanese (ja)
Inventor
末定　剛
Original Assignee
株式会社村田製作所
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Filing date
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Publication of WO2018179902A1 publication Critical patent/WO2018179902A1/fr

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    • H—ELECTRICITY
    • H01—ELECTRIC ELEMENTS
    • H01F—MAGNETS; INDUCTANCES; TRANSFORMERS; SELECTION OF MATERIALS FOR THEIR MAGNETIC PROPERTIES
    • H01F38/00—Adaptations of transformers or inductances for specific applications or functions
    • H01F38/14—Inductive couplings
    • H—ELECTRICITY
    • H02—GENERATION; CONVERSION OR DISTRIBUTION OF ELECTRIC POWER
    • H02J—CIRCUIT ARRANGEMENTS OR SYSTEMS FOR SUPPLYING OR DISTRIBUTING ELECTRIC POWER; SYSTEMS FOR STORING ELECTRIC ENERGY
    • H02J50/00—Circuit arrangements or systems for wireless supply or distribution of electric power
    • H02J50/10—Circuit arrangements or systems for wireless supply or distribution of electric power using inductive coupling
    • H02J50/12—Circuit arrangements or systems for wireless supply or distribution of electric power using inductive coupling of the resonant type
    • H—ELECTRICITY
    • H02—GENERATION; CONVERSION OR DISTRIBUTION OF ELECTRIC POWER
    • H02J—CIRCUIT ARRANGEMENTS OR SYSTEMS FOR SUPPLYING OR DISTRIBUTING ELECTRIC POWER; SYSTEMS FOR STORING ELECTRIC ENERGY
    • H02J50/00—Circuit arrangements or systems for wireless supply or distribution of electric power
    • H02J50/70—Circuit arrangements or systems for wireless supply or distribution of electric power involving the reduction of electric, magnetic or electromagnetic leakage fields
    • H—ELECTRICITY
    • H02—GENERATION; CONVERSION OR DISTRIBUTION OF ELECTRIC POWER
    • H02J—CIRCUIT ARRANGEMENTS OR SYSTEMS FOR SUPPLYING OR DISTRIBUTING ELECTRIC POWER; SYSTEMS FOR STORING ELECTRIC ENERGY
    • H02J7/00—Circuit arrangements for charging or depolarising batteries or for supplying loads from batteries
    • 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

Definitions

  • the present invention relates to a non-contact power transmission system including a power transmission device and a power reception device incorporated in a hearing aid.
  • the present invention also relates to a hearing aid including a power receiving device that receives power without contact.
  • Some hearing aids include a telecoil for detecting a change in a magnetic field generated from an audio signal, in addition to a microphone for acquiring surrounding audible sounds.
  • This magnetic field is generated by, for example, a speaker of a telephone handset, a magnetic induction loop (a hyaline group), or the like.
  • the hearing aid can acquire the original audio signal by detecting the change of the magnetic field by the telecoil.
  • Patent Document 1 discloses a hearing aid including such a telecoil.
  • non-contact power transmission magnetic field coupling between a power transmission coil and a power reception coil is often used.
  • the inventor of the present application has discovered the following problems regarding a hearing aid that receives power using non-contact power transmission.
  • non-contact power transmission is performed using magnetic coupling between the power transmission coil and the power reception coil, power is transmitted at a frequency close to the self-resonance frequency of the telecoil, and when the transmitted magnetic flux is linked to the telecoil, A voltage is induced.
  • the frequency for transmitting power includes a fundamental frequency and a frequency obtained by multiplying the fundamental frequency. This may cause malfunction or destruction of elements and circuits connected to the telecoil. Therefore, it is required to transmit power from the charger to the hearing aid without contact without causing malfunction or destruction of the elements and circuits connected to the telecoil.
  • An object of the present invention is to provide a non-contact power transmission system that can transmit power to a hearing aid equipped with a telecoil. It is also an object of the present invention to provide such a hearing aid.
  • the power transmission device is: A power transmission coil; A power transmission circuit that generates AC transmission power having a predetermined transmission frequency from input power and sends the transmission power to the power receiving device via the power transmission coil;
  • the power receiving device is: A receiving coil; A power reception circuit that receives the transmission power from the power transmission device via the power reception coil,
  • the power receiving device is incorporated in a hearing aid including a telecoil,
  • the transmission frequency is set higher than the self-resonance frequency of the telecoil.
  • the transmission frequency may be set higher than 1 MHz and lower than 100 MHz.
  • the transmission frequency by setting the transmission frequency higher than 1 MHz, it is possible to make it less susceptible to variations in telecoil parts. Moreover, by setting the transmission frequency to less than 100 MHz, heat generation and loss in the telecoil can be made difficult to occur.
  • the direction of the axis around which the winding of the power receiving coil is wound may be different from the direction of the axis around which the winding of the telecoil is wound.
  • the electromagnetic coupling between the power receiving coil and the telecoil can be reduced by arranging the power receiving coil and the telecoil in this way. Thereby, malfunction or destruction of the element and circuit connected to the telecoil can be made less likely to occur.
  • the direction of the axis for winding the winding of the power receiving coil and the direction of the axis for winding the winding of the telecoil may be orthogonal to each other.
  • the electromagnetic coupling between the power receiving coil and the telecoil can be reduced by arranging the power receiving coil and the telecoil in this way. Thereby, malfunction or destruction of the element and circuit connected to the telecoil can be made less likely to occur.
  • the power transmission device is incorporated in a charger, When the hearing aid is arranged in the charger, the power transmission coil and the power reception coil overlap each other when viewed in the direction of the axis around which the winding of the power reception coil is wound, and the telecoil is the power transmission coil and the power reception coil. May be arranged in a region outside the region where they overlap each other.
  • the electromagnetic coupling between the telecoil, the power transmission coil, and the power reception coil can be reduced by arranging the power transmission coil, the power reception coil, and the telecoil in this manner. Thereby, malfunction or destruction of the element and circuit connected to the telecoil can be made less likely to occur.
  • Each of the charger and the hearing aid may have a casing, and at least one may have a positioning mechanism.
  • the power transmission device is incorporated in a charger, When the hearing aid is arranged in the charger, the distance between the power transmission coil and the power reception coil may be shorter than the distance between the power transmission coil and the telecoil.
  • the electromagnetic coupling between the telecoil, the power transmission coil, and the power reception coil can be reduced by arranging the power transmission coil, the power reception coil, and the telecoil in this manner. Thereby, malfunction or destruction of the element and circuit connected to the telecoil can be made less likely to occur.
  • Each element of the power receiving coil and the telecoil may be arranged in a housing of the hearing aid, and a distance between the power receiving coil and the telecoil may be a maximum of a distance between the elements.
  • the electromagnetic coupling between the power receiving coil and the telecoil can be reduced by arranging the power receiving coil and the telecoil in this way. Thereby, malfunction or destruction of the element and circuit connected to the telecoil can be made less likely to occur.
  • the power receiving device may further include a shield conductor between the power receiving coil and the telecoil.
  • the shield conductor by providing the shield conductor, electromagnetic coupling between the power receiving coil and the telecoil can be reduced. Thereby, malfunction or destruction of the element and circuit connected to the telecoil can be made less likely to occur.
  • the power receiving coil may be formed on a flexible substrate.
  • a hearing aid that is contactlessly powered by a charger, A power receiving coil constituting a resonant circuit having a predetermined resonant frequency; A power receiving circuit that receives AC transmission power having a predetermined transmission frequency from the charger via the power receiving coil; A microphone, Telecoil, A signal processing circuit for processing an audio signal acquired by the microphone or the telecoil, The resonance frequency of the resonance circuit including the power receiving coil is set to be higher than the self resonance frequency of the telecoil.
  • the resonance frequency of the resonance circuit including the power receiving coil is set to be higher than the self-resonance frequency of the telecoil, it is possible to transmit electric power to a hearing aid equipped with the telecoil without contact.
  • power can be transmitted to a hearing aid equipped with a telecoil by setting the transmission frequency higher than the self-resonance frequency of the telecoil.
  • FIG. It is the perspective view seen from diagonally upward which shows the structure of the charging system containing the charger 1 and the hearing aid 2 provided with the non-contact electric power transmission system which concerns on embodiment. It is sectional drawing seen from the side which shows the state by which the hearing aid 2 of FIG. 1 has been arrange
  • FIG. It is a block diagram which shows the structure of the charging system of FIG. It is a figure which shows roughly the frequency characteristic of the receiving coil L2 and the telecoil L3 of FIG. It is sectional drawing seen from the side which shows the structure of the charging system containing the charger 1 and the hearing aid 2A provided with which concerns on the 1st modification of embodiment. It is sectional drawing seen from the side which shows the structure of the charging system containing the charger 1 and the hearing aid 2B provided with which concern on the 2nd modification of embodiment.
  • FIG. 1 is a perspective view illustrating a configuration of a charging system including a charger 1 and a hearing aid 2 provided with a non-contact power transmission system according to the embodiment, as viewed from obliquely above.
  • FIG. 2 is a cross-sectional view seen from the side, showing a state in which the hearing aid 2 of FIG. 1 is disposed on the charger 1.
  • the non-contact power transmission system according to the embodiment includes a power transmission device incorporated in the charger 1 and a power reception device incorporated in the hearing aid 2.
  • the charging system of FIG. 1 transmits power from the charger 1 to the hearing aid 2 in a non-contact manner and charges the battery of the hearing aid 2.
  • the charger 1 includes a circuit board 10 and a coil board 11.
  • the circuit board 10 includes a power transmission circuit that generates AC transmission power from input power and transmits the transmission power to the hearing aid 2 via the power transmission coil L1.
  • a power transmission coil L1 is formed on the coil substrate 11.
  • the hearing aid 2 includes a circuit board 20 and a coil board 21.
  • the circuit board 20 includes a power receiving circuit that receives transmission power from the charger 1 via the power receiving coil L2, and a signal processing circuit that processes an audio signal. The processed audio signal is converted into an audible sound by the receiver 29 and output to the user's ear.
  • a power receiving coil L2 is formed on the coil substrate 21, and the power receiving coil L2 is electromagnetically coupled to the power transmitting coil L1.
  • the hearing aid 2 further includes a telecoil L3.
  • the telecoil L3 may be provided on the circuit board 20.
  • the housing of the charger 1 includes a recess 1 a that houses the housing of the hearing aid 2.
  • FIG. 3 is a block diagram showing the configuration of the charging system of FIG.
  • the charger 1 includes a frequency conversion circuit 12, a capacitor C1, and a power transmission coil L1.
  • the capacitor C1 and the power transmission coil L1 constitute an LC resonance circuit having a predetermined resonance frequency.
  • the frequency conversion circuit 12 receives supply of AC input power from a power source 3 such as commercial power, generates AC transmission power having a predetermined transmission frequency f0 from the input power, and transmits the transmission power to the hearing aid via the power transmission coil L1.
  • 2 is a power transmission circuit to be sent to 2.
  • the transmission frequency f0 is set to be much higher than the frequency of the audible sound, for example, higher than 1 MHz and lower than 100 MHz.
  • the resonance frequency of the LC resonance circuit including the capacitor C1 and the power transmission coil L1 is set to coincide with the transmission frequency f0.
  • the resonance frequency of the LC resonance circuit including the capacitor C1 and the power transmission coil L1 does not necessarily coincide with the transmission frequency f0, and may be set so that the transmission frequency f0 is included in a band near the resonance frequency.
  • the frequency conversion circuit 12 includes, for example, a converter circuit (for example, an AC adapter) that once converts AC input power into DC power, and an inverter circuit that converts DC power into AC power.
  • the frequency conversion circuit 12, the capacitor C1, and the power transmission coil L1 are incorporated in the charger 1 as a power transmission device of the non-contact power transmission system.
  • the frequency conversion circuit 12 is provided, for example, on the circuit board 10 in FIG.
  • the hearing aid 2 includes a capacitor C2, a power receiving coil L2, a telecoil L3, a rectifying / smoothing circuit 22, a power conversion circuit 23, a charging circuit 24, a battery 25, a microphone 26, a mixer 27, and a signal processing circuit 28.
  • the capacitor C2 and the power receiving coil L2 constitute an LC resonance circuit having a predetermined resonance frequency.
  • the resonance frequency of the LC resonance circuit including the capacitor C2 and the power receiving coil L2 is set to match the resonance frequency of the LC resonance circuit including the capacitor C1 and the power transmission coil L1, and further to the transmission frequency f0.
  • the resonance frequency of the LC resonance circuit including the capacitor C2 and the power receiving coil L2 does not necessarily coincide with the transmission frequency f0, and may be set so that the transmission frequency f0 is included in a band near the resonance frequency. . As shown in FIG.
  • the rectifying and smoothing circuit 22 and the power conversion circuit 23 are power reception circuits that receive transmission power from the charger 1 via the power reception coil L2 when the power reception coil L2 is electromagnetically coupled to the power transmission coil L1.
  • the rectifying / smoothing circuit 22 rectifies and smoothes the AC transmission power received from the charger 1 via the power receiving coil L2.
  • the power conversion circuit 23 stabilizes the power rectified and smoothed by the rectifying and smoothing circuit 22.
  • the charging circuit 24 charges the battery 25 with the power stabilized by the power conversion circuit 23.
  • the LC resonance circuit formed by the capacitor C2 and the power receiving coil L2 may be a series resonance circuit or a parallel resonance circuit.
  • the capacitor C2, the power receiving coil L2, the rectifying / smoothing circuit 22, and the power conversion circuit 23 are incorporated in the hearing aid 2 as a power receiving device of the non-contact power transmission system.
  • the microphone 26 generates an audio signal corresponding to the audible sound by converting the surrounding audible sound into an electric signal.
  • the telecoil L3 generates an audio signal corresponding to the change in the magnetic field by converting the change in the surrounding magnetic field into an electric signal.
  • the telecoil L3 has a parasitic capacitance C3, and a parallel resonance circuit is formed by the inductance of the telecoil L3 and the parasitic capacitance C3.
  • the mixer 27 sends the audio signal acquired by the microphone 26 or the telecoil L3 to the signal processing circuit 28 at the subsequent stage.
  • the signal processing circuit 28 processes the audio signal acquired by the microphone or the telecoil L3.
  • the mixer 27 and the signal processing circuit 28 operate with electric power charged in the battery 25.
  • the signal processing circuit 28 may process the audio signal analogly or digitally.
  • the signal processing circuit 28 includes, for example, a preamplifier, an A / D converter, a digital signal processing (DSP) circuit, and a sigma delta converter.
  • the DSP circuit for example, processes the input signal according to a desired frequency characteristic and compression function to generate a signal suitable for compensating the hearing impairment of the user.
  • the output signal of the signal processing circuit 28 is sent to the receiver 29.
  • the rectifying / smoothing circuit 22, the power conversion circuit 23, the charging circuit 24, the battery 25, the mixer 27, and the signal processing circuit 28 are provided, for example, on the circuit board 20 in FIG.
  • the receiver 29 converts the output signal of the signal processing circuit 28 into an audible sound and outputs it.
  • this impedance for example, it can be determined whether or not the hearing aid 2 is placed on the charger 1.
  • the LC resonance circuit of the charger 1 and the LC resonance circuit of the hearing aid 2 are electromagnetically coupled, and a frequency peak due to composite resonance appears.
  • the presence or absence of the hearing aid 2 can be determined by detecting the frequency characteristics of the impedance and detecting the presence or absence of a frequency peak.
  • FIG. 4 is a diagram schematically showing frequency characteristics of the receiving coil L2 and the telecoil L3 in FIG.
  • the telecoil L3 is used at a frequency of several Hz or more and 30 kHz or less, which is a human audible region, and has a self-resonant frequency ft of several tens of kHz or more and several hundred kHz or less.
  • the self-resonant frequency ft is determined by the parallel resonance circuit of the inductance of the telecoil L3 and the parasitic capacitance C3 of the telecoil L3 shown in FIG.
  • the fundamental frequency or the multiplied frequency thereof is transmitted at a frequency close to the self-resonant frequency ft of the telecoil L3, and the magnetic flux of the transmitted power is linked to the telecoil L3, A large voltage is induced in the telecoil, and a high voltage is induced.
  • the telecoil L3 and the parasitic capacitance C3 form a parallel resonance circuit, and the impedance of the parallel resonance circuit is large at a frequency close to the self-resonance frequency ft. Then, the induced high voltage may destroy the elements and circuits connected to the telecoil L3.
  • the transmission frequency f0 of the non-contact power transmission system is set higher than the self-resonance frequency ft of the telecoil L3.
  • the resonance frequency of the LC resonance circuit is also set higher than the self-resonance frequency ft of the telecoil L3.
  • the resonance frequency of the LC resonance circuit does not necessarily coincide with the transmission frequency f0, but is desirably higher than the self-resonance frequency ft of the telecoil L3. Since the coil such as the telecoil L3 has a large variation in parts, the transmission frequency f0 is desirably set to 1 MHz or more.
  • another capacitor may be connected in parallel to the telecoil L3.
  • a parallel resonant circuit is formed by the inductance of the telecoil L3, the parasitic capacitance C3 of the telecoil L3, and the capacitance of another capacitor.
  • the telecoil L3 is formed by winding a conductive wire around a core such as ferrite, or by laminating a plurality of wiring substrates containing ferrite.
  • the telecoil L3 including ferrite generally does not support operation at a frequency exceeding several hundred MHz. In this frequency band, the signal received by the telecoil L3 becomes heat (that is, loss). Therefore, in order to avoid heat generation and loss in the telecoil L3, the transmission frequency f0 is desirably set to less than 100 MHz.
  • the charger 1 can transmit power to the hearing aid 2 provided with the telecoil L3 in a non-contact manner. Even if power is transmitted from the charger 1 to the hearing aid 2 in a non-contact manner, malfunction and destruction of the hearing aid 2 can be suppressed, and safety can be further improved.
  • electromagnetic coupling between the telecoil L3, the power transmission coil L1, and the power reception coil L2 by arranging the power transmission coil L1, the power reception coil L2, and the telecoil L3 in a predetermined positional relationship. Can be reduced.
  • the power receiving coil L2 and the telecoil L3 are arranged in the direction of the axis around which the winding of the power receiving coil L2 is wound, and the telecoil L3. Are arranged so as to be different from directions of the axes around which the windings are wound.
  • the receiving coil L2 and the telecoil L3 are disposed so that the direction of the axis around which the winding of the receiving coil L2 is wound and the direction of the axis around which the winding of the telecoil L3 is wound are orthogonal to each other.
  • the winding of the receiving coil L2 is wound around an axis parallel to the Z axis
  • the winding of the telecoil L3 is rotated around an axis parallel to the XY plane, for example, to the X axis. It is wound around a parallel axis.
  • the power transmission coil L1, the power reception coil L2, and the telecoil L3 are as follows when the hearing aid 2 is arranged on the charger 1 as shown in FIG. It arrange
  • the power transmission coil L1 and the power reception coil L2 are arranged so as to at least partially overlap each other when viewed from one point on the axis (the axis parallel to the Z axis) around which the winding of the power reception coil L2 is wound. At this time, the power transmission coil L1 and the power reception coil L2 are electromagnetically coupled to each other.
  • the telecoil L3 includes the power transmission coil L1 and the power reception coil L2 when viewed from one point on the axis around which the winding of the power receiving coil L2 is wound, that is, in the direction of the axis around which the winding of the power receiving coil L2 is wound. Are arranged in a region outside the region where they overlap each other (that is, the region where power is transmitted).
  • the casing of the charger 1 and the casing of the hearing aid 2 are formed to have a specific shape so as to realize such a positional relationship between the power transmission coil L1, the power reception coil L2, and the telecoil L3.
  • the recessed part 1a which accommodates the housing
  • the recess 1 a is a positioning mechanism for the charger 1 and the hearing aid 2. If the power transmission coil L1, the power reception coil L2, and the telecoil L3 can be arranged at fixed positions, the housing of the charger 1 and the housing of the hearing aid 2 are shaped as the concave portion 1a of the charger 1 and the hearing aid 2 corresponding thereto. It may have any shape without being limited to.
  • the power transmission coil L1 and the power reception coil are compared with the case where the telecoil L3 is disposed inside the region where the power transmission coil L1 and the power reception coil L2 overlap each other. Electromagnetic coupling between the coil L2 and the telecoil L3 is reduced.
  • the power transmission coil L1, the power reception coil L2, and the telecoil L3 are arranged such that when the hearing aid 2 is disposed on the charger 1, as shown in FIG. It arrange
  • the distance between the power transmission coil L1 and the telecoil L3 is arranged to be shorter than the distance between the power transmission coil L1 and the power reception coil L2.
  • the electromagnetic coupling between the power transmission coil L1 and the telecoil L3 is reduced.
  • the first to second One or two of the three arrangements may be employed.
  • the coil substrate 11 and the coil substrate 21 may be rigid substrates or flexible substrates.
  • the degree of freedom of disposing the power receiving coil L2 inside the housing can be improved even in a small hearing aid 2.
  • FIG. 5 is a side sectional view showing a configuration of a charging system including a charger 1 and a hearing aid 2A including a contactless power transmission system according to a first modification of the embodiment.
  • the hearing aid 2A in FIG. 5 further includes a shield conductor 31 between the power receiving coil L2 and the telecoil L3 in addition to the components of the hearing aid 2 in FIGS.
  • the shield conductor 31 may be comprised with the metal and may be comprised with magnetic materials, such as a ferrite.
  • FIG. 6 is a side sectional view showing a configuration of a charging system including a charger 1 and a hearing aid 2B including a contactless power transmission system according to a second modification of the embodiment.
  • the hearing aid 2B in FIG. 6 is different from the hearing aid 2 in FIGS. 1 and 2 in that the positions of the circuit board 20 and the telecoil L3 are changed in the housing of the hearing aid 2B.
  • the receiving coil L2 and the telecoil L3 are preferably arranged to maximize so that the distance between them is increased compared to the case of the hearing aid 2 of FIGS. .
  • electromagnetic coupling between the power receiving coil L2 and the telecoil L3 can be reduced as compared with the case of the hearing aid 2 of FIGS.
  • power can be transmitted to a hearing aid equipped with a telecoil.

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  • Engineering & Computer Science (AREA)
  • Power Engineering (AREA)
  • Physics & Mathematics (AREA)
  • Computer Networks & Wireless Communication (AREA)
  • Health & Medical Sciences (AREA)
  • General Health & Medical Sciences (AREA)
  • Neurosurgery (AREA)
  • Otolaryngology (AREA)
  • Acoustics & Sound (AREA)
  • Signal Processing (AREA)
  • Electromagnetism (AREA)
  • Charge And Discharge Circuits For Batteries Or The Like (AREA)

Abstract

Un dispositif de transmission d'énergie incorporé dans un chargeur (1) est pourvu d'une bobine de transmission d'énergie (L1) et d'un circuit de conversion de fréquence (12) qui génère une énergie de transmission de courant alternatif ayant une fréquence de transmission prédéterminée (f0) à partir de l'énergie d'entrée et qui transmet l'énergie de transmission à une aide auditive (2) par l'intermédiaire de la bobine de transmission d'énergie (L1). Un dispositif de réception d'énergie incorporé dans l'aide auditive (2) est pourvu d'une bobine de réception d'énergie (L2) ainsi que d'un circuit de redressement et de lissage (22) et d'un circuit de conversion d'énergie (23) qui reçoivent l'énergie de transmission provenant du chargeur (1) par l'intermédiaire de la bobine de réception d'énergie (L2). L'aide auditive (2) est pourvue d'une bobine téléphonique (L3). La fréquence de transmission (f0) est réglée à une valeur supérieure à la fréquence propre (ft) de la bobine téléphonique.
PCT/JP2018/004573 2017-03-31 2018-02-09 Système de transmission d'énergie sans contact et aide auditive WO2018179902A1 (fr)

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
JP2017-069721 2017-03-31
JP2017069721A JP2020109879A (ja) 2017-03-31 2017-03-31 非接触電力伝送システム及び補聴器

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WO2018179902A1 true WO2018179902A1 (fr) 2018-10-04

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Citations (7)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP2010527226A (ja) * 2007-05-08 2010-08-05 モジョ モビリティー インコーポレイテッド ポータブルデバイスの誘導充電システムおよび方法
JP2011172076A (ja) * 2010-02-19 2011-09-01 Nec Corp 音声送受信機器ユニット
JP2013502116A (ja) * 2009-08-11 2013-01-17 ヴェーデクス・アクティーセルスカプ 補聴器用保管システム
JP2013128385A (ja) * 2011-11-16 2013-06-27 Nec Tokin Corp 非接触電力伝送システム
WO2014155424A1 (fr) * 2013-03-29 2014-10-02 パナソニック株式会社 Appareil de communications
JP2015138985A (ja) * 2014-01-20 2015-07-30 日立マクセル株式会社 ウエアラブル型の小形電気機器
JP2016213224A (ja) * 2015-04-30 2016-12-15 Tdk株式会社 コイル、非接触受電装置、及び携帯用電子機器

Patent Citations (7)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP2010527226A (ja) * 2007-05-08 2010-08-05 モジョ モビリティー インコーポレイテッド ポータブルデバイスの誘導充電システムおよび方法
JP2013502116A (ja) * 2009-08-11 2013-01-17 ヴェーデクス・アクティーセルスカプ 補聴器用保管システム
JP2011172076A (ja) * 2010-02-19 2011-09-01 Nec Corp 音声送受信機器ユニット
JP2013128385A (ja) * 2011-11-16 2013-06-27 Nec Tokin Corp 非接触電力伝送システム
WO2014155424A1 (fr) * 2013-03-29 2014-10-02 パナソニック株式会社 Appareil de communications
JP2015138985A (ja) * 2014-01-20 2015-07-30 日立マクセル株式会社 ウエアラブル型の小形電気機器
JP2016213224A (ja) * 2015-04-30 2016-12-15 Tdk株式会社 コイル、非接触受電装置、及び携帯用電子機器

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