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WO2018179902A1 - Contactless power transmission system and hearing aid - Google Patents

Contactless power transmission system and hearing aid 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
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.)
Ceased
Application number
PCT/JP2018/004573
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French (fr)
Japanese (ja)
Inventor
末定　剛
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Murata Manufacturing Co Ltd
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Murata Manufacturing Co Ltd
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Publication date
Application filed by Murata Manufacturing Co Ltd filed Critical Murata Manufacturing Co Ltd
Publication of WO2018179902A1 publication Critical patent/WO2018179902A1/en
Anticipated expiration legal-status Critical
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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

A power transmission device incorporated into a charger (1) is provided with a power transmission coil (L1), and a frequency conversion circuit (12) that generates alternating-current transmission power having a predetermined transmission frequency (f0) from input power and transmits the transmission power to a hearing aid 2 via the power transmission coil (L1). A power reception device incorporated into the hearing aid (2) is provided with a power reception coil (L2), and a rectifying and smoothing circuit (22) and a power conversion circuit (23) that receive the transmission power from the charger (1) via the power reception coil (L2). The hearing aid 2 is provided with a telecoil (L3). The transmission frequency (f0) is set higher than the self-resonant frequency (ft) of the telecoil.

Description

非接触電力伝送システム及び補聴器Non-contact power transmission system and hearing aid

　本発明は、送電装置と、補聴器に組み込まれる受電装置とを含む非接触電力伝送システムに関する。本発明はまた、非接触で受電する受電装置を備える補聴器に関する。 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.

　補聴器には、周囲の可聴音を取得するためのマイクロホンに加えて、音声信号から生成された磁界の変化を検出するためのテレコイルを備えたものがある。この磁界は、例えば、電話機の送受話器のスピーカ、磁気誘導ループ（ヒアリングループ）、などによって発生される。補聴器は、テレコイルにより磁界の変化を検出することにより、元の音声信号を取得することができる。例えば、特許文献１に、そのようなテレコイルを備えた補聴器が開示されている。 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. For example, Patent Document 1 discloses a hearing aid including such a telecoil.

特表２００４－５３１１７４号公報JP-T-2004-53174 Publication

　近年、非接触電力伝送を用いて受電してバッテリーに充電する補聴器及びその充電器が登場している。非接触電力伝送では、送電コイルと受電コイルの間の磁界結合が使用される場合が多い。 In recent years, hearing aids and their chargers that use non-contact power transmission to receive power and charge the battery have appeared. In non-contact power transmission, magnetic field coupling between a power transmission coil and a power reception coil is often used.

　本願の発明者は、非接触電力伝送を用いて受電する補聴器について、以下の課題を発見した。送電コイルと受電コイルの間の磁界結合を用いて非接触電力伝送を行う場合、テレコイルの自己共振周波数に近い周波数で電力を伝送し、伝送される電力の磁束がテレコイルに鎖交すると、テレコイルに電圧が誘起される。電力を伝送する周波数は、基本周波数とその逓倍の周波数を含む。これにより、テレコイルに接続されている素子及び回路が誤動作又は破壊する恐れがある。従って、テレコイルに接続されている素子及び回路の誤動作又は破壊を生じることなく、充電器から補聴器に非接触で電力を伝送することが求められる。 The inventor of the present application has discovered the following problems regarding a hearing aid that receives power using non-contact power transmission. When 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.

　本発明の目的は、テレコイルを備えた補聴器にも電力を伝送することができる非接触電力伝送システムを提供することにある。本発明の目的はまた、そのような補聴器を提供することにある。 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.

　本発明の第１の態様に係る非接触電力伝送システムによれば、
　送電装置及び受電装置を含む非接触電力伝送システムにおいて、
　前記送電装置は、
　送電コイルと、
　入力電力から所定の伝送周波数を有する交流の伝送電力を発生し、前記伝送電力を前記送電コイルを介して前記受電装置に送る送電回路とを備え、
　前記受電装置は、
　受電コイルと、
　前記送電装置から前記受電コイルを介して前記伝送電力を受ける受電回路とを備え、
　前記受電装置は、テレコイルを備える補聴器に組み込まれ、
　前記伝送周波数は前記テレコイルの自己共振周波数よりも高く設定される。 According to the non-contact power transmission system according to the first aspect of the present invention,
In a non-contact power transmission system including a power transmission device and a power reception device,
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.

　本態様によれば、伝送周波数をテレコイルの自己共振周波数よりも高く設定することにより、テレコイルを備えた補聴器にも非接触で電力を伝送することができる。 According to this aspect, by setting the transmission frequency 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.

　本発明の第２の態様に係る非接触電力伝送システムによれば、第１の態様に係る非接触電力伝送システムにおいて、
　前記伝送周波数は、１ＭＨｚより高く、かつ、１００ＭＨｚ未満に設定されてもよい。 According to the non-contact power transmission system according to the second aspect of the present invention, in the non-contact power transmission system according to the first aspect,
The transmission frequency may be set higher than 1 MHz and lower than 100 MHz.

　本態様によれば、伝送周波数を１ＭＨｚより高く設定することにより、テレコイルの部品のバラツキの影響を受けにくくすることができる。また、伝送周波数を１００ＭＨｚ未満に設定することにより、テレコイルにおける発熱及び損失を生じにくくすることができる。 According to this aspect, 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.

　本発明の第３の態様に係る非接触電力伝送システムによれば、第１又は第２の態様に係る非接触電力伝送システムにおいて、
　前記受電コイルの巻線を巻回する軸の方向と、前記テレコイルの巻線を巻回する軸の方向とは互いに異なっていてもよい。 According to the non-contact power transmission system according to the third aspect of the present invention, in the non-contact power transmission system according to the first or second aspect,
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.

　本態様によれば、このように受電コイル及びテレコイルを配置することにより、受電コイルとテレコイルの間の電磁的な結合を低減することができる。これにより、テレコイルに接続されている素子及び回路の誤動作又は破壊をより生じにくくすることができる。 According to this aspect, 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.

　本発明の第４の態様に係る非接触電力伝送システムによれば、第３の態様に係る非接触電力伝送システムにおいて、
　前記受電コイルの巻線を巻回する軸の方向と、前記テレコイルの巻線を巻回する軸の方向とは互いに直交してもよい。 According to the non-contact power transmission system according to the fourth aspect of the present invention, in the non-contact power transmission system according to the third aspect,
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.

　本態様によれば、このように受電コイル及びテレコイルを配置することにより、受電コイルとテレコイルの間の電磁的な結合を低減することができる。これにより、テレコイルに接続されている素子及び回路の誤動作又は破壊をより生じにくくすることができる。 According to this aspect, 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.

　本発明の第５の態様に係る非接触電力伝送システムによれば、第１～第４のうちの１つの態様に係る非接触電力伝送システムにおいて、
　前記送電装置は充電器に組み込まれ、
　前記充電器に前記補聴器を配置したとき、前記受電コイルの巻線を巻回する軸の方向に見て、前記送電コイル及び前記受電コイルは互いに重なり、前記テレコイルは、前記送電コイル及び前記受電コイルが互いに重なる領域の外側の領域に配置されてもよい。 According to the non-contact power transmission system according to the fifth aspect of the present invention, in the non-contact power transmission system according to one of the first to fourth aspects,
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.

　本態様によれば、このように送電コイル、受電コイル、及びテレコイルを配置することにより、テレコイルと、送電コイル及び受電コイルとの間の電磁的な結合を低減することができる。これにより、テレコイルに接続されている素子及び回路の誤動作又は破壊をより生じにくくすることができる。 According to this aspect, 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.

　本発明の第６の態様に係る非接触電力伝送システムによれば、第５の態様に係る非接触電力伝送システムにおいて、
　前記充電器及び前記補聴器は、それぞれ筐体を有し、少なくとも一方に位置決め機構を有してもよい。 According to the non-contact power transmission system according to the sixth aspect of the present invention, in the non-contact power transmission system according to the fifth aspect,
Each of the charger and the hearing aid may have a casing, and at least one may have a positioning mechanism.

　本態様によれば、テレコイルと、送電コイル及び受電コイルとの間の電磁的な結合を低減するような配置を容易に実現することができる。 According to this aspect, it is possible to easily realize an arrangement that reduces the electromagnetic coupling between the telecoil, the power transmission coil, and the power reception coil.

　本発明の第７の態様に係る非接触電力伝送システムによれば、第１～第６のうちの１つの態様に係る非接触電力伝送システムにおいて、
　前記送電装置は充電器に組み込まれ、
　前記充電器に前記補聴器を配置したとき、前記送電コイルと前記受電コイルとの間の距離は前記送電コイルと前記テレコイルの間の距離よりも短くてもよい。 According to the non-contact power transmission system according to the seventh aspect of the present invention, in the non-contact power transmission system according to one of the first to sixth aspects,
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.

　本態様によれば、このように送電コイル、受電コイル、及びテレコイルを配置することにより、テレコイルと、送電コイル及び受電コイルとの間の電磁的な結合を低減することができる。これにより、テレコイルに接続されている素子及び回路の誤動作又は破壊をより生じにくくすることができる。 According to this aspect, 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.

　本発明の第８の態様に係る非接触電力伝送システムによれば、第１～第７のうちの１つの態様に係る非接触電力伝送システムにおいて、
　前記受電コイル及び前記テレコイルは、前記補聴器の筐体内に各素子が配置され、各素子間の距離のうち前記受電コイルと前記テレコイルの間の距離が最大であってもよい。 According to the non-contact power transmission system according to the eighth aspect of the present invention, in the non-contact power transmission system according to one of the first to seventh aspects,
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.

　本態様によれば、このように受電コイル及びテレコイルを配置することにより、受電コイルとテレコイルの間の電磁的な結合を低減することができる。これにより、テレコイルに接続されている素子及び回路の誤動作又は破壊をより生じにくくすることができる。 According to this aspect, 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.

　本発明の第９の態様に係る非接触電力伝送システムによれば、第１～第８のうちの１つの態様に係る非接触電力伝送システムにおいて、
　前記受電装置は、前記受電コイルと前記テレコイルの間にシールド導体をさらに備えてもよい。 According to the non-contact power transmission system according to the ninth aspect of the present invention, in the non-contact power transmission system according to one of the first to eighth aspects,
The power receiving device may further include a shield conductor between the power receiving coil and the telecoil.

　本態様によれば、シールド導体を備えたことにより、受電コイルとテレコイルの間の電磁的な結合を低減することができる。これにより、テレコイルに接続されている素子及び回路の誤動作又は破壊をより生じにくくすることができる。 According to this aspect, 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.

　本発明の第１０の態様に係る非接触電力伝送システムによれば、第１～第９のうちの１つの態様に係る非接触電力伝送システムにおいて、
　前記受電コイルはフレキシブル基板に形成されてもよい。 According to the non-contact power transmission system according to the tenth aspect of the present invention, in the non-contact power transmission system according to one of the first to ninth aspects,
The power receiving coil may be formed on a flexible substrate.

　本態様によれば、フレキシブル基板を用いることにより、補聴器の筐体の内部に受電コイルを配置する自由度を向上することができる。 According to this aspect, by using the flexible substrate, it is possible to improve the degree of freedom of disposing the power receiving coil inside the housing of the hearing aid.

　本発明の第１１の態様に係る補聴器によれば、
　充電器から非接触で電力供給を受ける補聴器であって、
　所定の共振周波数を有する共振回路を構成する受電コイルと、
　前記充電器から、前記受電コイルを介して、所定の伝送周波数を有する交流の伝送電力を受ける受電回路と、
　マイクロホンと、
　テレコイルと、
　前記マイクロホン又は前記テレコイルによって取得された音声信号を処理する信号処理回路とを備え、
　前記受電コイルを含む共振回路の共振周波数は前記テレコイルの自己共振周波数よりも高く設定される。 According to the hearing aid pertaining to the eleventh aspect of the present invention,
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.

　本態様によれば、受電コイルを含む共振回路の共振周波数をテレコイルの自己共振周波数よりも高く設定することにより、テレコイルを備えた補聴器にも非接触で電力を伝送することができる。 According to this aspect, by setting the resonance frequency of the resonance circuit including the power receiving coil 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.

　本発明の一態様に係る非接触電力伝送システムによれば、伝送周波数をテレコイルの自己共振周波数よりも高く設定することにより、テレコイルを備えた補聴器にも電力を伝送することができる。 According to the non-contact power transmission system according to one aspect of the present invention, 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.

実施形態に係る非接触電力伝送システムを備えた充電器１及び補聴器２を含む充電システムの構成を示す、斜め上方からみた透視図である。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. 図１の補聴器２が充電器１の上に配置された状態を示す、側方からみた断面図である。It is sectional drawing seen from the side which shows the state by which the hearing aid 2 of FIG. 1 has been arrange | positioned on the charger 1. FIG. 図１の充電システムの構成を示すブロック図である。It is a block diagram which shows the structure of the charging system of FIG. 図１の受電コイルＬ２及びテレコイルＬ３の周波数特性を概略的に示す図である。It is a figure which shows roughly the frequency characteristic of the receiving coil L2 and the telecoil L3 of FIG. 実施形態の第１の変形例に係るを備えた充電器１及び補聴器２Ａを含む充電システムの構成を示す、側方からみた断面図である。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. 実施形態の第２の変形例に係るを備えた充電器１及び補聴器２Ｂを含む充電システムの構成を示す、側方からみた断面図である。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.

　以下、図面を参照して、本発明の実施形態について説明する。各図面において同じ番号は同様の構成要素を示す。 Hereinafter, embodiments of the present invention will be described with reference to the drawings. In each drawing, the same number shows the same component.

　図１は、実施形態に係る非接触電力伝送システムを備えた充電器１及び補聴器２を含む充電システムの構成を示す、斜め上方からみた透視図である。図２は、図１の補聴器２が充電器１の上に配置された状態を示す、側方からみた断面図である。実施形態に係る非接触電力伝送システムは、充電器１に組み込まれた送電装置と、補聴器２に組み込まれた受電装置とを含む。図１の充電システムは、図２に示すように補聴器２が充電器１の上に配置されたとき、充電器１から補聴器２に非接触で電力を伝送し、補聴器２のバッテリーに充電する。 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. When the hearing aid 2 is disposed on the charger 1 as shown in FIG. 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.

　充電器１は、回路基板１０及びコイル基板１１を備える。回路基板１０は、入力電力から交流の伝送電力を発生し、伝送電力を送電コイルＬ１を介して補聴器２に送る送電回路を含む。コイル基板１１には送電コイルＬ１が形成される。補聴器２は、回路基板２０及びコイル基板２１を備える。回路基板２０は、充電器１から受電コイルＬ２を介して伝送電力を受ける受電回路と、音声信号を処理する信号処理回路とを含む。処理された音声信号は、レシーバ２９で可聴音に変換されてユーザの耳に出力される。また、コイル基板２１には受電コイルＬ２が形成され、受電コイルＬ２は送電コイルＬ１と電磁的に結合する。補聴器２はテレコイルＬ３をさらに備える。テレコイルＬ３は回路基板２０に設けられてもよい。 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. In addition, 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.

　充電器１の筐体は、補聴器２の筐体を収容する凹部１ａを備える。 The housing of the charger 1 includes a recess 1 a that houses the housing of the hearing aid 2.

　図３は、図１の充電システムの構成を示すブロック図である。 FIG. 3 is a block diagram showing the configuration of the charging system of FIG.

　充電器１は、周波数変換回路１２、キャパシタＣ１、及び送電コイルＬ１を備える。 The charger 1 includes a frequency conversion circuit 12, a capacitor C1, and a power transmission coil L1.

　充電器１において、キャパシタＣ１及び送電コイルＬ１は、所定の共振周波数を有するＬＣ共振回路を構成する。周波数変換回路１２は、商用電力などの電源３から交流の入力電力の供給を受け、入力電力から所定の伝送周波数ｆ０を有する交流の伝送電力を発生し、伝送電力を送電コイルＬ１を介して補聴器２に送る送電回路である。伝送周波数ｆ０は可聴音の周波数よりもずっと高く、例えば、１ＭＨｚより高く、かつ、１００ＭＨｚ未満に設定される。キャパシタＣ１及び送電コイルＬ１を含むＬＣ共振回路の共振周波数は、伝送周波数ｆ０に一致するように設定される。キャパシタＣ１及び送電コイルＬ１を含むＬＣ共振回路の共振周波数は、必ずしも伝送周波数ｆ０に一致していなくてもよく、この共振周波数の近傍の帯域に伝送周波数ｆ０が含まれるように設定されてもよい。周波数変換回路１２は、例えば、交流の入力電力をいったん直流電力に変換するコンバータ回路（例えば、ＡＣアダプタなど）と、直流電力を交流電力に変換するインバータ回路とを含む。 In the charger 1, 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.

　周波数変換回路１２、キャパシタＣ１、及び送電コイルＬ１は、非接触電力伝送システムの送電装置として、充電器１に組み込まれる。 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.

　周波数変換回路１２は、例えば、図１の回路基板１０に設けられる。 The frequency conversion circuit 12 is provided, for example, on the circuit board 10 in FIG.

　補聴器２は、キャパシタＣ２、受電コイルＬ２、テレコイルＬ３、整流平滑回路２２、電力変換回路２３、充電回路２４、バッテリー２５、マイクロホン２６、ミキサ２７、及び信号処理回路２８を備える。 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.

　補聴器２において、キャパシタＣ２及び受電コイルＬ２は、所定の共振周波数を有するＬＣ共振回路を構成する。キャパシタＣ２及び受電コイルＬ２を含むＬＣ共振回路の共振周波数は、キャパシタＣ１及び送電コイルＬ１を含むＬＣ共振回路の共振周波数に一致し、さらに、伝送周波数ｆ０に一致するように設定される。キャパシタＣ２及び受電コイルＬ２を含むＬＣ共振回路の共振周波数は、必ずしも伝送周波数ｆ０に一致していなくてもよく、この共振周波数の近傍の帯域に伝送周波数ｆ０が含まれるように設定されてもよい。図２に示すように補聴器２が充電器１の上に配置されたとき、送電コイルＬ１及び受電コイルＬ２は少なくとも部分的に互いに重畳し、このとき、受電コイルＬ２は送電コイルＬ１と電磁的に結合する。整流平滑回路２２及び電力変換回路２３は、受電コイルＬ２が送電コイルＬ１と電磁的に結合しているとき、充電器１から受電コイルＬ２を介して伝送電力を受ける受電回路である。整流平滑回路２２は、充電器１から受電コイルＬ２を介して受けた交流の伝送電力を整流及び平滑化する。電力変換回路２３は、整流平滑回路２２により整流及び平滑化された電力を安定化する。充電回路２４は、電力変換回路２３により安定化された電力をバッテリー２５に充電する。 In the hearing aid 2, 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. 2, when the hearing aid 2 is disposed on the charger 1, the power transmission coil L1 and the power reception coil L2 are at least partially overlapped with each other, and at this time, the power reception coil L2 is electromagnetically coupled to the power transmission coil L1. Join. 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.

　なお、キャパシタＣ２および受電コイルＬ２が構成するＬＣ共振回路は、直列共振回路であってもよいし、並列共振回路であっても良い。 Note that 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.

　キャパシタＣ２、受電コイルＬ２、整流平滑回路２２、及び電力変換回路２３は、非接触電力伝送システムの受電装置として、補聴器２に組み込まれる。 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.

　補聴器２において、マイクロホン２６は、周囲の可聴音を電気信号に変換することにより、可聴音に対応する音声信号を生成する。テレコイルＬ３は、周囲の磁界の変化を電気信号に変換することにより、磁界の変化に対応する音声信号を生成する。テレコイルＬ３は、寄生容量Ｃ３を有し、テレコイルＬ３のインダクタンスと寄生容量Ｃ３とにより並列共振回路が形成される。ミキサ２７は、マイクロホン２６又はテレコイルＬ３によって取得された音声信号を後段の信号処理回路２８に送る。信号処理回路２８は、マイクロホン又はテレコイルＬ３によって取得された音声信号を処理する。ミキサ２７及び信号処理回路２８は、バッテリー２５に充電された電力により動作する。信号処理回路２８は、音声信号をアナログ的に処理してもよく、ディジタル的に処理してもよい。音声信号をディジタル的に処理する場合、信号処理回路２８は、例えば、前置増幅器、Ａ／Ｄ変換器、ディジタル信号処理（ＤＳＰ）回路、及びシグマデルタ変換器などを含む。ＤＳＰ回路は、例えば、入力された信号を所望の周波数特性及び圧縮関数にしたがって処理して、ユーザの聴覚障害を補償するのに適した信号を生成する。信号処理回路２８の出力信号は、レシーバ２９に送られる。 In the hearing aid 2, 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. When processing an audio signal 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.

　整流平滑回路２２、電力変換回路２３、充電回路２４、バッテリー２５、ミキサ２７、及び信号処理回路２８は、例えば、図１の回路基板２０に設けられる。 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.

　レシーバ２９は、信号処理回路２８の出力信号を可聴音に変換して出力する。 The receiver 29 converts the output signal of the signal processing circuit 28 into an audible sound and outputs it.

　図３の充電システムにおいて、周波数変換回路１２の送電電流と、周波数変換回路１２からキャパシタＣ１及び送電コイルＬ１への入力電圧とを検出することで、周波数変換回路１２から補聴器２をみたときのインピーダンスを検出できる。このインピーダンスを検出することで、例えば、充電器１に補聴器２が載置されたか否かを判定できる。充電器１に補聴器２を載置したとき、充電器１のＬＣ共振回路と補聴器２のＬＣ共振回路とが電磁的に結合して、複合共振による周波数ピークが現れる。そして、インピーダンスの周波数特性を検出し、周波数ピークの有無を検出することで、補聴器２の有無を判定できる。 In the charging system of FIG. 3, the impedance when the hearing aid 2 is viewed from the frequency conversion circuit 12 by detecting the transmission current of the frequency conversion circuit 12 and the input voltage from the frequency conversion circuit 12 to the capacitor C1 and the transmission coil L1. Can be detected. By detecting this impedance, for example, it can be determined whether or not the hearing aid 2 is placed on the charger 1. When 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. And 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.

　図４は、図１の受電コイルＬ２及びテレコイルＬ３の周波数特性を概略的に示す図である。 FIG. 4 is a diagram schematically showing frequency characteristics of the receiving coil L2 and the telecoil L3 in FIG.

　テレコイルＬ３は、人間の可聴領域である数Ｈｚ以上かつ三十ｋＨｚ以下の周波数で使用され、それを超える数十ｋＨｚ以上かつ数百ｋＨｚ以下の自己共振周波数ｆｔを有する。自己共振周波数ｆｔは、図３に示すテレコイルＬ３のインダクタンスとテレコイルＬ３の寄生容量Ｃ３の並列共振回路により定まる。前述のように、非接触電力伝送システムにおいて、基本周波数もしくはその逓倍の周波数がテレコイルＬ３の自己共振周波数ｆｔに近い周波数で電力を伝送し、伝送される電力の磁束がテレコイルＬ３に鎖交すると、テレコイルに大きな電圧が誘起され、高電圧が誘起される。これはテレコイルＬ３と寄生容量Ｃ３が並列共振回路を構成しており、自己共振周波数ｆｔに近い周波数において並列共振回路のインピーダンスが大きくなっているためである。そして誘起された高電圧により、テレコイルＬ３に接続されている素子及び回路が破壊する恐れがある。この課題を解決するために、本実施形態では、非接触電力伝送システムの伝送周波数ｆ０をテレコイルＬ３の自己共振周波数ｆｔよりも高く設定している。非接触電力伝送システムの伝送周波数ｆ０をテレコイルＬ３の自己共振周波数ｆｔよりも高く設定することによって、ＬＣ共振回路の共振周波数もテレコイルＬ３の自己共振周波数ｆｔよりも高く設定される。なおＬＣ共振回路の共振周波数は、必ずしも伝送周波数ｆ０に一致している必要はないが、テレコイルＬ３の自己共振周波数ｆｔよりも高いことが望ましい。テレコイルＬ３などのコイルは部品のバラつきが大きいので、望ましくは、伝送周波数ｆ０は１ＭＨｚ以上に設定される。 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. As described above, in the non-contact power transmission system, when 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. This is because 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. In order to solve this problem, in this embodiment, the transmission frequency f0 of the non-contact power transmission system is set higher than the self-resonance frequency ft of the telecoil L3. By setting the transmission frequency f0 of the non-contact power transmission system 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.

　また、寄生容量Ｃ３に加えて、さらに別のキャパシタがテレコイルＬ３に並列接続されてもよい。この場合、テレコイルＬ３のインダクタンス、テレコイルＬ３の寄生容量Ｃ３、及び別のキャパシタの容量により、並列共振回路が形成される。 Further, in addition to the parasitic capacitance C3, another capacitor may be connected in parallel to the telecoil L3. In this case, 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.

　また、一般的には、テレコイルＬ３は、フェライトなどのコアに導線を巻回することにより、又は、フェライトを含む複数の配線基板を積層することにより形成される。フェライトを含むテレコイルＬ３は、一般的には、数百ＭＨｚを超える周波数での動作をサポートしていない。この周波数帯では、テレコイルＬ３で受信した信号は熱（すなわち損失）になる。従って、テレコイルＬ３における発熱及び損失を避けるために、望ましくは、伝送周波数ｆ０は１００ＭＨｚ未満に設定される。 In general, 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.

　非接触電力伝送システムの伝送周波数ｆ０をこのように設定することにより、充電器１は、テレコイルＬ３を備えた補聴器２にも非接触で電力を伝送することができる。充電器１から補聴器２に非接触で電力を伝送しても、補聴器２の誤動作及び破壊を抑制し、より安全性を向上することができる。 By setting the transmission frequency f0 of the non-contact power transmission system in this way, 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.

　また、以下に説明するように、送電コイルＬ１、受電コイルＬ２、及びテレコイルＬ３を所定の位置関係で配置することにより、テレコイルＬ３と、送電コイルＬ１及び受電コイルＬ２との間の電磁的な結合を低減することができる。 In addition, as described below, 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.

　電磁的な結合を低減するための第１の配置として、図１及び図２に示すように、受電コイルＬ２及びテレコイルＬ３は、受電コイルＬ２の巻線を巻回する軸の方向と、テレコイルＬ３の巻線を巻回する軸の方向とは互いに異なるように配置される。例えば、受電コイルＬ２及びテレコイルＬ３は、受電コイルＬ２の巻線を巻回する軸の方向と、テレコイルＬ３の巻線を巻回する軸の方向とは互いに直交するように配置される。図１及び図２を参照すると、受電コイルＬ２の巻線はＺ軸に平行な軸の周りに巻回され、テレコイルＬ３の巻線は、ＸＹ平面に平行な軸の周りに、例えばＸ軸に平行な軸の周りに巻回されている。受電コイルＬ２及びテレコイルＬ３をこのように配置することにより、受電コイルＬ２の巻線を巻回する軸の方向とテレコイルＬ３の巻線を巻回する軸の方向とが一致している場合に比べて、テレコイルＬ３に送電コイルＬ１から発生した磁束が鎖交することを抑制することができ、送電コイルＬ１および受電コイルＬ２とテレコイルＬ３の間の電磁的な結合は低減する。 As a first arrangement for reducing electromagnetic coupling, as shown in FIGS. 1 and 2, 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. For example, 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. 1 and 2, the winding of the receiving coil L2 is wound around an axis parallel to the Z axis, and 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. By arranging the power receiving coil L2 and the telecoil L3 in this manner, the direction of the axis around which the winding of the power receiving coil L2 is wound and the direction of the axis around which the winding of the telecoil L3 is wound coincide with each other. Thus, the magnetic flux generated from the power transmission coil L1 can be prevented from interlinking with the telecoil L3, and electromagnetic coupling between the power transmission coil L1 and the power reception coil L2 and the telecoil L3 is reduced.

　電磁的な結合を低減するための第２の配置として、送電コイルＬ１、受電コイルＬ２、及びテレコイルＬ３は、図２に示すように補聴器２が充電器１の上に配置されたとき、以下の位置関係を有するように配置される。受電コイルＬ２の巻線を巻回する軸（Ｚ軸に平行な軸）の上の一点から見て、送電コイルＬ１及び受電コイルＬ２は、少なくとも部分的に互いに重なるように配置される。このとき、送電コイルＬ１及び受電コイルＬ２は互いに電磁的に結合する。また、受電コイルＬ２の巻線を巻回する軸の上の一点から見て、すなわち受電コイルＬ２の巻線を巻回する軸の方向に見て、テレコイルＬ３は、送電コイルＬ１及び受電コイルＬ２が互いに重なる領域（すなわち、電力が伝送される領域）の外側の領域に配置される。充電器１の筐体及び補聴器２の筐体は、このような送電コイルＬ１、受電コイルＬ２、及びテレコイルＬ３の位置関係を実現するように、特定の形状を有して形成される。図１及び図２の場合、充電器１の筐体において、補聴器２の筐体を収容する凹部１ａを備える。凹部１ａは充電器１と補聴器２の位置決め機構である。送電コイルＬ１、受電コイルＬ２、及びテレコイルＬ３を決まった位置に配置できるのであれば、充電器１の筐体及び補聴器２の筐体は、充電器１の凹部１ａ及びそれに対応する補聴器２の形状に限らず、任意の形状を有してもよい。送電コイルＬ１、受電コイルＬ２、及びテレコイルＬ３をこのように配置することにより、送電コイルＬ１及び受電コイルＬ２が互いに重畳する領域の内部にテレコイルＬ３を配置する場合に比べて、送電コイルＬ１及び受電コイルＬ２と、テレコイルＬ３との間の電磁的な結合は低減する。 As a second arrangement for reducing electromagnetic coupling, 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 | positions so that it may have a positional relationship. 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. Further, 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. In the case of FIG.1 and FIG.2, in the housing | casing of the charger 1, the recessed part 1a which accommodates the housing | casing of the hearing aid 2 is provided. 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. By arranging the power transmission coil L1, the power reception coil L2, and the telecoil L3 in this manner, 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.

　電磁的な結合を低減するための第３の配置として、送電コイルＬ１、受電コイルＬ２、及びテレコイルＬ３は、図２に示すように補聴器２が充電器１の上に配置されたとき、送電コイルＬ１と受電コイルＬ２の間の距離が送電コイルＬ１とテレコイルＬ３の間の距離よりも短くなるように配置される。送電コイルＬ１、受電コイルＬ２、及びテレコイルＬ３をこのように配置することにより、送電コイルＬ１とテレコイルＬ３の間の距離が送電コイルＬ１と受電コイルＬ２の間の距離よりも短くなるように配置される場合に比べて、送電コイルＬ１とテレコイルＬ３の間の電磁的な結合は低減する。 As a third arrangement for reducing electromagnetic coupling, 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 | positions so that the distance between L1 and the receiving coil L2 may become shorter than the distance between the power transmission coil L1 and the telecoil L3. By arranging the power transmission coil L1, the power reception coil L2, and the telecoil L3 in this way, 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. Compared to the case where the electromagnetic coil is coupled, the electromagnetic coupling between the power transmission coil L1 and the telecoil L3 is reduced.

　テレコイルＬ３と、送電コイルＬ１及び受電コイルＬ２との間の電磁的な結合を低減することにより、送電コイルＬ１から受電コイルＬ２に電力を伝送するとき、テレコイルＬ３に電圧が誘起されにくくすることができる。従って、テレコイルＬ３に接続されている素子及び回路の誤動作又は破壊をより生じにくくすることができる。 By reducing the electromagnetic coupling between the telecoil L3 and the power transmission coil L1 and the power reception coil L2, when power is transmitted from the power transmission coil L1 to the power reception coil L2, it is difficult to induce a voltage in the telecoil L3. it can. Therefore, malfunction or destruction of the elements and circuits connected to the telecoil L3 can be made less likely to occur.

　テレコイルＬ３と、送電コイルＬ１及び受電コイルＬ２との間の電磁的な結合を低減するために、上述した第１～第３の配置のうちのすべてを採用することに代えて、第１～第３の配置のうちの１つ又は２つを採用してもよい。 In order to reduce the electromagnetic coupling between the telecoil L3 and the power transmission coil L1 and the power reception coil L2, instead of adopting all of the first to third arrangements described above, the first to second One or two of the three arrangements may be employed.

　コイル基板１１及びコイル基板２１は、リジッド基板であってもよく、フレキシブル基板であってもよい。例えば、受電コイルＬ２をフレキシブル基板に形成することにより、小型の補聴器２であっても、その筐体の内部に受電コイルＬ２を配置する自由度を向上することができる。 The coil substrate 11 and the coil substrate 21 may be rigid substrates or flexible substrates. For example, by forming the power receiving coil L2 on the flexible substrate, the degree of freedom of disposing the power receiving coil L2 inside the housing can be improved even in a small hearing aid 2.

　次に、図５及び図６を参照して、実施形態の変形例に係る非接触電力伝送システムについて説明する。 Next, a non-contact power transmission system according to a modification of the embodiment will be described with reference to FIGS. 5 and 6.

　図５は、実施形態の第１の変形例に係る非接触電力伝送システムを備えた充電器１及び補聴器２Ａを含む充電システムの構成を示す、側方からみた断面図である。図５の補聴器２Ａは、図１及び図２の補聴器２の各構成要素に加えて、受電コイルＬ２とテレコイルＬ３の間にシールド導体３１をさらに備える。シールド導体３１を備えることにより、図１及び図２の補聴器２の場合に比べて、受電コイルＬ２とテレコイルＬ３の間の電磁的な結合を低減することができる。なお、シールド導体３１は、金属によって構成されていてもよく、フェライトなどの磁性材料によって構成されていてもよい。 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. By providing the shield conductor 31, the electromagnetic coupling between the receiving coil L2 and the telecoil L3 can be reduced as compared with the case of the hearing aid 2 of FIGS. In addition, the shield conductor 31 may be comprised with the metal and may be comprised with magnetic materials, such as a ferrite.

　図６は、実施形態の第２の変形例に係る非接触電力伝送システムを備えた充電器１及び補聴器２Ｂを含む充電システムの構成を示す、側方からみた断面図である。図６の補聴器２Ｂは、図１及び図２の補聴器２と比較して、補聴器２Ｂの筐体において、回路基板２０及びテレコイルＬ３の位置が変更されている。具体的には、受電コイルＬ２及びテレコイルＬ３は、図１及び図２の補聴器２の場合と比較して、それらの間の距離がより増大するように、望ましくは最大化するように配置される。受電コイルＬ２及びテレコイルＬ３をこのように配置することにより、図１及び図２の補聴器２の場合に比べて、受電コイルＬ２とテレコイルＬ３の間の電磁的な結合を低減することができる。 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. Specifically, 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. . By arranging the power receiving coil L2 and the telecoil L3 in this manner, 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.

　図５のシールド導体３１と、図６の受電コイルＬ２及びテレコイルＬ３の配置とは、互いに組み合わされてもよい。 5 and the arrangement of the receiving coil L2 and the telecoil L3 in FIG. 6 may be combined with each other.

　本発明の一態様に係る非接触電力伝送システムによれば、テレコイルを備えた補聴器にも電力を伝送することができる。 According to the non-contact power transmission system according to an aspect of the present invention, power can be transmitted to a hearing aid equipped with a telecoil.

１…充電器、
１ａ…凹部、
２，２Ａ，２Ｂ…補聴器、
３…電源、
１０…回路基板、
１１…コイル基板、
１２…周波数変換回路、
２０…回路基板、
２１…コイル基板、
２２…整流平滑回路、
２３…電力変換回路、
２４…充電回路、
２５…バッテリー、
２６…マイクロホン、
２７…ミキサ、
２８…信号処理回路、
２９…レシーバ、
３１…シールド導体、
Ｃ１，Ｃ２…キャパシタ、
Ｃ３…寄生容量、
Ｌ１…送電コイル、
Ｌ２…受電コイル、
Ｌ３…テレコイル。 1 ... charger,
1a ... recess,
2, 2A, 2B ... hearing aids,
3 ... Power supply,
10 ... circuit board,
11 ... Coil substrate,
12 ... Frequency conversion circuit,
20 ... circuit board,
21 ... Coil substrate,
22 ... rectifying and smoothing circuit,
23 ... Power conversion circuit,
24. Charging circuit,
25 ... Battery,
26 ... Microphone,
27. Mixer,
28: Signal processing circuit,
29 ... Receiver,
31 ... Shield conductor,
C1, C2 ... capacitors,
C3: parasitic capacitance,
L1 ... power transmission coil,
L2 ... receiving coil,
L3 ... Telecoil.

Claims (11)

　送電装置及び受電装置を含む非接触電力伝送システムにおいて、
　前記送電装置は、
　送電コイルと、
　入力電力から所定の伝送周波数を有する交流の伝送電力を発生し、前記伝送電力を前記送電コイルを介して前記受電装置に送る送電回路とを備え、
　前記受電装置は、
　受電コイルと、
　前記送電装置から前記受電コイルを介して前記伝送電力を受ける受電回路とを備え、
　前記受電装置は、テレコイルを備える補聴器に組み込まれ、
　前記伝送周波数は前記テレコイルの自己共振周波数よりも高く設定される、
非接触電力伝送システム。 In a non-contact power transmission system including a power transmission device and a power reception device,
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-resonant frequency of the telecoil,
Non-contact power transmission system. 　前記伝送周波数は、１ＭＨｚより高く、かつ、１００ＭＨｚ未満に設定される、
請求項１記載の非接触電力伝送システム。 The transmission frequency is set to be higher than 1 MHz and lower than 100 MHz.
The contactless power transmission system according to claim 1. 　前記受電コイルの巻線を巻回する軸の方向と、前記テレコイルの巻線を巻回する軸の方向とは互いに異なる、
請求項１又は２記載の非接触電力伝送システム。 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 are different from each other.
The contactless power transmission system according to claim 1 or 2. 　前記受電コイルの巻線を巻回する軸の方向と、前記テレコイルの巻線を巻回する軸の方向とは互いに直交する、
請求項３記載の非接触電力伝送システム。 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 are orthogonal to each other.
The contactless power transmission system according to claim 3. 　前記送電装置は充電器に組み込まれ、
　前記充電器に前記補聴器を配置したとき、前記受電コイルの巻線を巻回する軸の方向に見て、
　前記送電コイル及び前記受電コイルは互いに重なり、
　前記テレコイルは、前記送電コイル及び前記受電コイルが互いに重なる領域の外側の領域に配置される、
請求項１～４のうちの１つに記載の非接触電力伝送システム。 The power transmission device is incorporated in a charger,
When the hearing aid is arranged in the charger, seeing in the direction of the axis around which the winding of the power receiving coil is wound,
The power transmission coil and the power reception coil overlap each other,
The telecoil is disposed in a region outside the region where the power transmission coil and the power reception coil overlap each other.
The contactless power transmission system according to any one of claims 1 to 4. 　前記充電器及び前記補聴器は、それぞれ筐体を有し、少なくとも一方に位置決め機構を有する、
請求項５記載の非接触電力伝送システム。 The charger and the hearing aid each have a housing, and at least one has a positioning mechanism.
The contactless power transmission system according to claim 5. 　前記送電装置は充電器に組み込まれ、
　前記充電器に前記補聴器を配置したとき、前記送電コイルと前記受電コイルの間との距離は、前記送電コイルと前記テレコイルとの間の距離よりも短い、
請求項１～６のうちの１つに記載の非接触電力伝送システム。 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 is shorter than the distance between the power transmission coil and the telecoil.
The contactless power transmission system according to any one of claims 1 to 6. 　前記補聴器の筐体内に各素子が配置され、各素子間の距離のうち前記受電コイルと前記テレコイルの間の距離が最大である、
請求項１～７のうちの１つに記載の非接触電力伝送システム。 Each element is disposed in the housing of the hearing aid, and the distance between the power receiving coil and the telecoil is the maximum among the distances between the elements.
The contactless power transmission system according to any one of claims 1 to 7. 　前記受電装置は、前記受電コイルと前記テレコイルの間にシールド導体をさらに備える、
請求項１～８のうちの１つに記載の非接触電力伝送システム。 The power receiving device further includes a shield conductor between the power receiving coil and the telecoil,
The contactless power transmission system according to any one of claims 1 to 8. 　前記受電コイルはフレキシブル基板に形成される、
請求項１～９のうちの１つに記載の非接触電力伝送システム。 The power receiving coil is formed on a flexible substrate.
The contactless power transmission system according to any one of claims 1 to 9. 　充電器から非接触で電力供給を受ける補聴器であって、
　所定の共振周波数を有する共振回路を構成する受電コイルと、
　前記充電器から、前記受電コイルを介して、所定の伝送周波数を有する交流の伝送電力を受ける受電回路と、
　マイクロホンと、
　テレコイルと、
　前記マイクロホン又は前記テレコイルによって取得された音声信号を処理する信号処理回路とを備え、
　前記受電コイルを含む共振回路の共振周波数は前記テレコイルの自己共振周波数よりも高く設定される、
補聴器。 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 higher than the self-resonance frequency of the telecoil.
hearing aid.
PCT/JP2018/004573 2017-03-31 2018-02-09 Contactless power transmission system and hearing aid Ceased WO2018179902A1 (en)

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