EP2134106A1 - Appareil auditif et appareil de chargement en énergie et procédé correspondant - Google Patents

Appareil auditif et appareil de chargement en énergie et procédé correspondant Download PDF

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Publication number
EP2134106A1
EP2134106A1 EP09155856A EP09155856A EP2134106A1 EP 2134106 A1 EP2134106 A1 EP 2134106A1 EP 09155856 A EP09155856 A EP 09155856A EP 09155856 A EP09155856 A EP 09155856A EP 2134106 A1 EP2134106 A1 EP 2134106A1
Authority
EP
European Patent Office
Prior art keywords
hearing aid
energy
antenna
charging
unit
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Granted
Application number
EP09155856A
Other languages
German (de)
English (en)
Other versions
EP2134106B1 (fr
Inventor
Mihail Boguslavskij
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Sivantos Pte Ltd
Original Assignee
Siemens Medical Instruments Pte Ltd
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by Siemens Medical Instruments Pte Ltd filed Critical Siemens Medical Instruments Pte Ltd
Publication of EP2134106A1 publication Critical patent/EP2134106A1/fr
Application granted granted Critical
Publication of EP2134106B1 publication Critical patent/EP2134106B1/fr
Active legal-status Critical Current
Anticipated expiration legal-status Critical

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    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R25/00—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception
    • H04R25/55—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception using an external connection, either wireless or wired
    • H04R25/554—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception using an external connection, either wireless or wired using a wireless connection, e.g. between microphone and amplifier or using Tcoils
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R2225/00—Details of deaf aids covered by H04R25/00, not provided for in any of its subgroups
    • H04R2225/31—Aspects of the use of accumulators in hearing aids, e.g. rechargeable batteries or fuel cells
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R2225/00—Details of deaf aids covered by H04R25/00, not provided for in any of its subgroups
    • H04R2225/51—Aspects of antennas or their circuitry in or for hearing aids
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R25/00—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception
    • H04R25/60—Mounting or interconnection of hearing aid parts, e.g. inside tips, housings or to ossicles
    • H04R25/602—Mounting or interconnection of hearing aid parts, e.g. inside tips, housings or to ossicles of batteries

Definitions

  • the invention relates to a specified in claim 1 hearing aid with an antenna for wireless transmission and reception, a specified in claim 11 energy charger for loading a hearing aid and a specified in claim 13 method for loading the hearing aid.
  • Hearing aids are portable hearing aids that are used to care for the hearing impaired.
  • different types of hearing aids such as behind-the-ear hearing aids and in-the-ear hearing aids are provided.
  • the hearing aids listed by way of example are worn on the outer ear or in the ear canal.
  • bone conduction hearing aids, implantable or vibrotactile hearing aids are also available on the market. The stimulation of the damaged hearing takes place either mechanically or electrically.
  • Hearing aids have in principle as essential components an input transducer, an amplifier and an output transducer.
  • the input transducer is usually a sound receiver, z. As a microphone, and / or an electromagnetic receiver, for. B. an induction coil.
  • the output transducer is usually used as an electroacoustic transducer, z. As miniature speaker, or as an electromechanical transducer, z. B. bone conduction, realized.
  • the amplifier is usually integrated in a signal processing unit.
  • FIG. 1 illustrated by the example of a behind-the-ear hearing aid 1.
  • a hearing aid housing 7 for carrying behind the ear one or more microphones 2 are incorporated for receiving the sound from the environment.
  • a signal processing unit 3 which is also integrated into the hearing aid housing 7, processes the microphone signals and amplifies them.
  • the output signal of the signal processing unit 3 is transmitted to a loudspeaker or receiver 4, which emits an acoustic signal.
  • the sound is optionally transmitted via a sound tube, which is fixed with an earmold in the ear canal, to the eardrum of the device carrier.
  • the power supply of the hearing aid 1 and in particular the signal processing unit 3 is effected by a battery 5 also arranged in the hearing aid housing 7.
  • a coil 6 arranged in the hearing aid housing 7, data can be inductively exchanged with another hearing aid or with a remote control contactlessly.
  • Charging batteries or batteries of a hearing aid often means taking the battery or the battery out of the hearing aid, plug it into a charger and charge. After charging, the usually very small and poorly manageable battery must be removed from the charger and reinserted into the hearing aid.
  • An alternative charging method is that the battery is left in the hearing aid and loaded there by wire.
  • appropriate metallic contacts should be provided on the hearing aid. A disadvantage of these contacts is that they usually stick out of the housing and are not flush with it. As a result, they can easily pollute.
  • the transmitter works with a transmitter coil and the receiver of the energy also uses a coil to absorb the energy.
  • Such coils are relatively large, which runs contrary to the ever-desired goal of miniaturization especially in hearing aids.
  • the DE 197 45 101 A1 relates to an in-the-ear hearing aid with a hearing aid charging circuit with a coil for wireless recording of electrical energy. Data from a voltage measurement can also be received via the coil.
  • the object is achieved with the devices of the independent claims 1 or 10 and the method of independent claim 12.
  • the invention comprises a hearing aid with a rechargeable energy storage unit for power supply and with an antenna for wireless transmission and reception of electromagnetic signals.
  • An energy charging unit is disposed between the antenna and the energy storage unit, wherein in a charging operation to the antenna electromagnetically transmitted energy via the energy charging unit in the Energy storage unit is fed.
  • the energy charging unit may comprise a charge controller for regulating a voltage induced in the antenna and a charge state monitoring unit for detecting an amount of energy flowing from and into the energy storage unit. As a result, the voltage is smoothed and regulated, and the charging current is measured.
  • the charge controller and the state of charge control unit can be electrically connected to a control logic unit, wherein the control logic unit switches between the charging mode and a communication mode.
  • This offers the advantage that it is easy to switch between a charging mode and a communication mode.
  • the antenna may be formed as an antenna coil, wherein the energy is transmitted inductively. As a result, sufficient amounts of energy in the near field of electric fields can be transmitted.
  • a Schottky diode can be connected in parallel with a parasitic diode which rectifies the induced voltage between the antenna and the ground.
  • the advantage of this is the increase of the charging current and thus the effectiveness of the charging process.
  • the hearing aid may include a transceiver module for wirelessly transmitting and receiving electromagnetic signals via the antenna. This data can be transmitted to and from the hearing aid.
  • first data of an energy charger can be transmitted to the hearing aid during the charging operation, wherein the transmitted to the antenna electromagnetic Energy is modulated.
  • the transceiver module can determine the first data from the modulated energy. This brings the advantage of a simple data transfer parallel to the loading operation.
  • second data can be transmitted from the transceiver module to the energy charger.
  • status information about the state of charge of a battery can be transmitted.
  • Switching between the charging mode and the communication mode can advantageously be time-controlled or protocol-controlled. This brings the advantage of a versatile control.
  • the invention also provides an energy charger for inductive charging of the hearing aid according to the invention.
  • a communication unit in the energy charger modulates the electromagnetic energy transmitted from the energy charger to the antenna for transmission of data. This offers the advantage that data can be transferred parallel to the loading.
  • the data transmission unit in the energy charger can receive inductively transmitted data. As a result, data of the hearing aid can be evaluated.
  • the invention also provides a method for charging a rechargeable energy storage unit of a hearing aid with an antenna for wireless transmission and reception of electromagnetic signals.
  • electromagnetic energy is transmitted to the antenna of the hearing aid. This is fed electrically via an energy charger in the energy storage unit.
  • first data of the energy charger be transmitted to the hearing aid during the charging operation, wherein the transmitted to the antenna electromagnetic energy is modulated.
  • second data can be transmitted from the hearing device to the energy charger.
  • FIG. 2 shows a block diagram of a hearing aid 1 and an associated energy charger 8. In FIG. 2 only those components are shown that are necessary for an understanding of the invention.
  • an antenna coil 6 is arranged, which in conjunction with a transmitting / receiving unit 9 and a power supply unit 10, a bidirectional wireless data transfer between the hearing aid 1 and a peripheral unit, for example, another hearing aid or a remote control allows.
  • the power supply unit 10 is powered by a rechargeable battery 5.
  • the antenna coil 6 for non-contact or wireless charging of the battery 5 with electrical energy provided for the data transmission antenna coil 6 is used.
  • the particular challenge of using the antenna coil 6 as a receiver for a power transmission system is that it does not affect the functionality of the wireless data transmission.
  • no additional semiconductor switches, such as FET transistors may be connected to the antenna coil 6, since they would degrade the parameters of the input resonant circuit due to their parasitic properties. This would unduly reduce the range of wireless data transmission. It is therefore not possible to separate the antenna coil 6 for the purpose of energy transfer by means of a semiconductor switch from the transmitting / receiving unit 9 and connect to a power transmission rectifier.
  • the invention makes use of the fact that a parasitic diode 13 exists from one end of the antenna coil 6 to the ground.
  • the parasitic diode 13 is due to the semiconductor manufacturing process and can be used for rectifying a voltage induced in the antenna coil 6. This makes it possible to convert the transmitting / receiving circuit of a hearing aid almost without change in a power transmission circuit.
  • the power supply unit 10 of the antenna coil 6 is disconnected and switched for a charge controller 11 and a state of charge control unit 12 between the antenna coil 6 and the battery 5.
  • An output of the coil 6 is connected to an input of the charge controller 11.
  • An output of the charge controller 11 is connected to an input of the state of charge control unit 12 whose output is coupled to the input of the battery 5.
  • the antenna coil 6 is used as an antenna for wireless data transmission.
  • a charging mode is activated, and the voltage induced in the antenna coil 6 is rectified by the parasitic diode 13.
  • the rectified voltage is regulated by the charge controller 11.
  • the amount of charge flowed out of the battery 5 or into the battery 5 is detected by the state of charge control unit 12. Both are connected via a communication interface, not shown, with the control logic.
  • the control logic is to control the switching of the states “charging” and "wireless communication". During a half-wave of the induced voltage, a pulsating current flows through the parasitic diode 13, which then leads to a charging current in the battery 5 after a smoothing.
  • the functionality of the parasitic diode 13 is supported by parallel connection of a Schottky diode 14. Due to the semiconductor manufacturing process, the Schottky diode can not be realized in the semiconductor chip itself, but must be connected externally to the chip.
  • an existing wireless data transmission system of the hearing device 1 can be retained and the antenna coil 6 can be shared for the transmission of energy.
  • the transmitting unit 9 is blocked in the hearing aid 1 by the strong, externally applied magnetic field of the energy charger 8.
  • the existing transmitting / receiving unit 9 of the hearing aid 1 is shared.
  • the field of the energy charger 8 is modulated accordingly.
  • the modulated signal is thus on the one hand for energy transmission and on the other hand for data transmission used by the power charger 8 to the hearing aid 1.
  • For data transmission from the hearing aid 1 to the energy charger 8 is timed, eg in the time slot method in which after a predefined time, the transmission direction is changed, or protocol controlled, for example by handshaking, the field of the power charger 8 off.
  • the energy charger 8 then enters a receive mode.
  • the hearing aid 1 transmits data with the existing transceiver unit 9.
  • FIG. 3 shows an inventive example of a protocol-controlled communication sequence between a hearing aid 1 and a power charger 8.
  • a starting state "hearing aid absent" HA is no hearing aid 1 in the energy charger 8.
  • the energy charger 8 changes continuously from a transmission mode SM in a reception mode RM and vice versa.
  • the energy charger 8 sends a charge start signal 100 to the hearing aid 1.
  • the signal "go-to-transfer mode" 101 is sent. Since there is no hearing aid 1 in the energy charger 8 no response 200 comes back. Subsequently, a hearing aid 1 is inserted into the energy charger 8. This creates the state "hearing aid inserted" HI.
  • the hearing aid 1 now receives the signals "Start charging” 100 and "Go-to-transfer mode” 101 and in response sends the packet 201 back to the energy charger 8.
  • the energy charger 8 then switches to the energy transmission mode 102. During the energy charge, transmission packets 101, 201 can continue to be exchanged.
  • the power charger 8 sends the command "Quit charging” 103 to the hearing aid 1. The charging is stopped.
  • the power charger 8 continuously or periodically transmits, for example, every 3 seconds, commands to transition to a charging mode and a request to send data. This can be done with a low energy so that the energy charger 8 consumes as little power in the unused state. No data coming back from the hearing aid 1, which is detected in the charger as a state "no hearing aid" HA and displayed accordingly. If there is an answer, which may include, for example, the type of hearing aid 1, the battery state of charge or the required charge current, the expected duration of the charging process is displayed on the energy charger 8 and the charging process begins. In this case, the energy charger 8 sends requests to the hearing aid at regular intervals to notify the status, and immediately thereafter returns to the receive mode RM.
  • the power charger 8 Upon completion of the charging process, the power charger 8 sends the command to the hearing aid to stop charging and go into a sleep mode with low power consumption. If the hearing aid 1 prematurely removed from the charging tray of the power charger 8, which is detected and displayed in the energy charger 8 based on the missing answers. The hearing aid 1 recognizes the state "I am removed from the charging cradle" in that no requests from the energy charging device 8 arrive more.
  • the transitions between the states in the hearing aid 1 and in the energy charger 8 can each be controlled with a state machine. This can both be hard-wired into hardware and implemented as a software-controlled microcontroller.
EP09155856.9A 2008-05-13 2009-03-23 Appareil auditif et appareil de chargement en énergie et procédé correspondant Active EP2134106B1 (fr)

Applications Claiming Priority (1)

Application Number Priority Date Filing Date Title
DE102008023352.8A DE102008023352B4 (de) 2008-05-13 2008-05-13 Hörgerät

Publications (2)

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EP2134106A1 true EP2134106A1 (fr) 2009-12-16
EP2134106B1 EP2134106B1 (fr) 2015-11-25

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US (1) US8344689B2 (fr)
EP (1) EP2134106B1 (fr)
DE (1) DE102008023352B4 (fr)
DK (1) DK2134106T3 (fr)

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Also Published As

Publication number Publication date
DK2134106T3 (da) 2016-02-29
US20090285426A1 (en) 2009-11-19
DE102008023352B4 (de) 2014-02-06
DE102008023352A1 (de) 2009-11-19
EP2134106B1 (fr) 2015-11-25
US8344689B2 (en) 2013-01-01

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