EP3192277A1 - Appareillage auditif et procédé pour le faire fonctionner - Google Patents

Appareillage auditif et procédé pour le faire fonctionner

Info

Publication number
EP3192277A1
EP3192277A1 EP15774872.4A EP15774872A EP3192277A1 EP 3192277 A1 EP3192277 A1 EP 3192277A1 EP 15774872 A EP15774872 A EP 15774872A EP 3192277 A1 EP3192277 A1 EP 3192277A1
Authority
EP
European Patent Office
Prior art keywords
switching
power supply
state
hearing instrument
hearing
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.)
Withdrawn
Application number
EP15774872.4A
Other languages
German (de)
English (en)
Inventor
Stefanie Beyfuß
Uwe Flaig
Anand Ganapathy
Frank Naumann
Uwe Rass
Gee Heng LER
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
Priority claimed from DE102014218053.8A external-priority patent/DE102014218053B4/de
Priority claimed from DE102014219017.7A external-priority patent/DE102014219017A1/de
Application filed by Siemens Medical Instruments Pte Ltd filed Critical Siemens Medical Instruments Pte Ltd
Publication of EP3192277A1 publication Critical patent/EP3192277A1/fr
Withdrawn legal-status Critical Current

Links

Classifications

    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R25/00—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception
    • H04R25/70—Adaptation of deaf aid to hearing loss, e.g. initial electronic fitting
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R1/00—Details of transducers, loudspeakers or microphones
    • H04R1/10—Earpieces; Attachments therefor ; Earphones; Monophonic headphones
    • H04R1/1041—Mechanical or electronic switches, or control elements
    • 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
    • H04R2225/41—Detection or adaptation of hearing aid parameters or programs to listening situation, e.g. pub, forest
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R2225/00—Details of deaf aids covered by H04R25/00, not provided for in any of its subgroups
    • H04R2225/61—Aspects relating to mechanical or electronic switches or control elements, e.g. functioning
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R2460/00—Details of hearing devices, i.e. of ear- or headphones covered by H04R1/10 or H04R5/033 but not provided for in any of their subgroups, or of hearing aids covered by H04R25/00 but not provided for in any of its subgroups
    • H04R2460/03—Aspects of the reduction of energy consumption in hearing devices
    • 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
    • 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
    • H04R25/603—Mounting or interconnection of hearing aid parts, e.g. inside tips, housings or to ossicles of mechanical or electronic switches or control elements

Definitions

  • the present invention relates to a hearing instrument. Furthermore, the present invention relates to a method for operating such a hearing instrument.
  • Hearing instruments in particular hearing aids, are usually regarded as hearing instruments.
  • the latter are regularly used to supply a hearing-impaired person with acoustic ambient signals, which are processed and amplified for compensation or therapy of the respective hearing impairment.
  • Hearing devices in principle comprise one or more input transducers, a signal processing device with an amplifying device, d. H. an amplifier, and an output transducer.
  • the input transducer is typically provided by a sound receiver, e.g. a microphone, and / or an electromagnetic receiver, e.g. an induction coil formed.
  • the output transducer is usually used as an electroacoustic transducer, e.g. Miniature loudspeaker, or as an electromechanical transducer, e.g.
  • the electroacoustic transducer is often referred to as a handset or receiver.
  • the output transducer generates output signals that are routed to the patient's ear and produce a hearing sensation in the patient.
  • the essential electronic components of the signal processing device are usually arranged on a printed circuit board as a circuit carrier or connected thereto.
  • For power supply of the hearing aid is currently usually used in a housing of the hearing aid insertable battery, which must be replaced more or less regularly by a new battery.
  • Tinnitus maskers are used to treat tinnitus patients. They produce from the respective hearing impairment and depending on the principle of action also dependent on ambient noise acoustic output signals that can contribute to reducing the perception of annoying tinnitus or other ear noises.
  • Hearing instruments in particular hearing aids are known in various basic housing configurations.
  • the (hearing aid) housing that encloses all the functional components including the microphone and receiver is mostly carried in the ear canal.
  • Completely-in-Canal (CiC) hearing aids are similar to the IdO hearing aids, but are fully worn in the ear canal.
  • BTE hearing aids (behind-the-ear, behind-the-ear), a housing with components such as battery and signal processing device behind the ear is worn and a flexible sound tube, also referred to as a tube, directs the acoustic output signals of a receiver from the housing to the ear canal
  • So-called RiC-BtE hearing aids (Reeceiver-in-Canal behind-the-ear) are similar to BTE hearing aids, but the receiver is worn in the ear canal and instead of a sound tube, which sends acoustic signals to an ear piece, conducts a flexible cable as a receiver connection means electrical signals to the front mounted on the cable receiver.
  • hearing instruments In addition to good acoustic properties, which are favored for example by high-quality input transducers, output transducers as well as by complex signal processing device, today's hearing instruments increasingly aesthetic and cosmetic demands are made. In particular, hearing instruments should be as inconspicuous as possible. Furthermore, there is often the danger that hearing instruments may be damaged by penetrating fluids, such as sweat. Another requirement for a modern hearing instrument relates to the ease of use of the devices now equipped with many functions. The topic of ease of use also includes that hearing instruments should require little maintenance, for example in relation to the handling of the energy supply of the hearing instrument.
  • the invention has for its object to provide an easy-to-use hearing instrument.
  • the hearing instrument comprises a housing (also referred to as a hearing aid hull housing), at least one microphone and a loudspeaker (designated as a receiver). Furthermore, the hearing instrument comprises a signal processing unit and a power supply device (which is also referred to as a power supply unit). The latter includes energy supply electronics (also referred to as control and monitoring means). The hearing instrument also comprises a switching means which is adapted to accept at least two switching states. The power supply electronics is set up to control a switch-off state of the hearing instrument as a function of the switching state of the switching means.
  • the power supply electronics is generally designed as an electronic circuit and is used in particular for providing an operating voltage (also referred to as supply voltage) with a (eg by the manufacturer of the hearing instrument) predetermined voltage value for power supply of the hearing instrument, in particular the signal processing unit.
  • the power supply electronics comprises, for example, means for generating (converting) the operating voltage from an (output) voltage provided by an energy source (which is also referred to as a source voltage).
  • These means for generating the operating voltage are in particular by means for voltage stabilization, voltage increase and / or voltage reduction (eg. by up-converter and / or down-converter).
  • the power electronics is also permanently associated with the hearing instrument, that is inextricably linked thereto.
  • the respective microphone is used in particular for detecting sound from the surroundings of the hearing instrument and for converting it into an (electrical) sound signal.
  • the receiver is used, in particular, for outputting the audio signals, which are preferably processed by the signal processing unit (eg filtered, possibly selectively attenuated and / or amplified) to the hearing center of a user of the hearing instrument (in short: hearing aid wearer).
  • the microphone, the receiver, the signal processing unit and preferably also the power supply electronics are expediently arranged within the housing.
  • the energy supply device also comprises (at least) a repeatedly chargeable energy supply means as an energy source.
  • This repeatedly rechargeable energy supply means is referred to here and below in particular as an accumulator, battery cell, rechargeable battery cell or short battery.
  • Single battery cells, rechargeable battery cells or individual rechargeable storage elements are also referred to as a secondary cell, secondary element.
  • Interconnected rechargeable battery cells or storage elements are also referred to as rechargeable storage, battery pack or battery from secondary cells.
  • Rechargeable battery cells and interconnected rechargeable battery cells which may also be combined in a common housing, are commercially available in many variations, for example, in terms of output voltage, capacitance or form factor.
  • the energy supply electronics preferably also serve in particular for the energy management of the rechargeable energy supply means and, in particular in this connection, is also referred to as power management IC.
  • the energy supply electronics are expediently set up to determine the state of charge of the batteries. To monitor kuzelle and preferably to prevent deep discharge of the battery cell and thus their damage.
  • the hearing instrument in particular the energy supply electronics, is set up to recharge the energy supply means (in a state connected to the hearing instrument and thus to the energy supply electronics), in particular by means of externally provided energy.
  • the use of the rechargeable energy supply means advantageously makes it possible to reduce the frequency of exchanging discharged (one-way) battery cells and thus contributes to the simplification of the maintenance and the operability of the hearing instrument, since the energy supply means can conveniently remain in the hearing instrument for charging.
  • the energy supply means can conveniently remain in the hearing instrument for charging.
  • by eliminating the disposal of discharged battery cells costs for new battery cells and possibly also a burden on the environment can be reduced.
  • the hearing instrument in particular for the case in which the hearing instrument is a behind-the-ear hearing device (BTE hearing aid), preferably comprises a receiver connection means (eg a "receiver cable”) or a sound tube and an ear piece (possibly also referred to as earmold).
  • a receiver connection means eg a "receiver cable”
  • a sound tube e.g. a "receiver cable”
  • earmold e.g. "receiver cable”
  • the at least two switching states are referred to here and below in particular as the first switching state and as the second switching state.
  • the switching means is expediently adapted to assume the first switching state or the second switching state, in particular alternately. This means that the switching means is either in the first switching state or in the second switching state.
  • the signal processing unit is adapted to issue a control command when a change of the switching means from the first switching state to the second switching state within a predetermined (the signal processing unit associated) first time period a change back to the first switching state is detected.
  • the power supply electronics is configured to transition to an inactive state for triggering the switch-off state of the hearing instrument when the second switching state of the switching device is assigned to the switching state of the switching device from the first switching state to the second switching state, in particular for a predetermined one (associated with the energy supply electronics).
  • second period of time which is equal to or greater than the first period, is present.
  • the energy supply electronics is thus set up to regard the exceeding of the second time period as a "switch-off criterion" if the second switching state is continued.
  • the power supply electronics classifies it as a switch-off criterion, especially if the switching means (still) after the second time period.
  • the signal processing unit and the power supply electronics each respond to a differently long actuation of one and the same switching means, in particular due to a comparatively short existence of the second switching state by the signal processing unit, the control command is issued and due to a comparatively long existence the second switching state, the power supply electronics deactivated and thereby the hearing instrument off (ie offset in the off state) same switching means (in particular the hearing aid wearer) for the preferably selective activation of two different (switching) operations, each of which is carried out by a respective other "signal receiver” (ie from the signal processing unit or the power supply electronics).
  • an additional, separate switching means (or operating element) for triggering the respective operation of the signal processing unit or the power supply electronics can advantageously be dispensed with, so that the number of different switching means on the hearing instrument can be reduced.
  • a risk of confusion of different switching means by the hearing aid wearer can thus be reduced, which contributes to a simple "blind" operation of the hearing aid worn regularly on the ear (and consequently removed from the hearing aid wearer's gaze) and thus in turn simplifying the operability of the hearing instrument.
  • the signal processing unit and the power supply electronics are each adapted to the detection of the second switching state (ie, the change of the switching means from the first switching state to the second switching state) towards the first time period or the second time period (as a kind of time window)
  • the signal processing unit detects that the switching means returns to the first switching state within (ie before the expiry of) the first time period, it takes this as an intention
  • the power supply electronics is preferably set up in this case - ie when the switching means returns to the first switching state before the second time period expires - in particular the monitoring of the z abort over a long period of time (and thus to ignore the change of the switching means from the first to the second switching state).
  • the signal processing unit is further configured, in particular, to ignore the presence of the second switching state beyond the first time period and accordingly to issue a control command in this case. This means that the signal processing unit expediently outputs no control command when the hearing instrument is to be switched off by a correspondingly long-lasting operation of the switching means.
  • inactive state is understood here and below as meaning that the energy supply electronics are not completely (ie not galvanically) separated from the energy supply means, but rather are in particular put in a kind of "stand-by" mode.
  • the power supply electronics is preferably configured to prevent or at least delay a deep discharge of the power supply means.
  • a power supply of the signal processing unit ie the provision of the operating voltage, preferably does not take place in this inactive state, so that the signal processing unit and thus the essential functions of the hearing instrument (in particular reception, amplification). kung and output of sound signals) are "off” and thereby the energy consumption of the hearing instrument is significantly reduced.
  • the control command issued by the signal processing unit is preferably for selecting (i.e., setting) a (new) volume value - d. H.
  • a (new) volume value - d. H For the purpose of changing the volume - or for selecting a (different) "hearing program.”
  • the hearing program here and below is understood to mean, in particular, a directional effect, a frequency-dependent attenuation and / or amplification, and preferably a situation-specific selection of hearing device settings adapted to the hearing device wearer ,
  • the rechargeable power supply means of the hearing instrument is in the off state of the hearing instrument, d. H. in the inactive state of the power supply electronics rechargeable, in particular by means of corresponding, the hearing instrument (preferably fixed) associated means for energy transfer to the power supply means.
  • the hearing instrument preferably fixed
  • These means are in particular part of a so-called charging electronics, which in turn is in particular comprised by the power supply device, preferably by the power supply electronics.
  • the power supply electronics are thus also set up in particular to monitor (regulate) a charging process of the power supply means in the inactive state.
  • a duration is set for the first period of time (ie predetermined in the signal processing unit) which corresponds to the duration of the second time period.
  • the first time period and the second time period are the same length.
  • the signal processing unit is thus set up to output the control command whenever the switching means returns to the first switching state before reaching the switch-off criterion, namely the end of the second time span.
  • the two time periods are selected differently, in particular the second time period longer than the first time period. Ie. for the second period, a longer duration compared to the first period is set. In this case, therefore, only a short change from the first to the second switching state and back, d. H. only a brief operation of the switching means for triggering the control command. Thereby, the distinctness of the operation of the switching means for the hearing aid wearer directed to the respective operation (i.e., outputting the control command or turning off the hearing instrument) is increased, so that the operability of the hearing instrument is further simplified.
  • the first time period is set to a duration between 0.25 seconds and 1 second, in particular to about 0.5 seconds.
  • the second time period is in an advantageous embodiment of a Duration between 1, 5 and 5 seconds, in particular set to 2.5 to 3.5 seconds (ie deposited in the power electronics).
  • a change of the switching means from the second back to the first switching state which takes place between the end of the first time period and the end of the second time period, from both the signal processing unit and the power supply electronics as a faulty operation is discarded and thus no output of the control command and no shutdown of the hearing instrument takes place.
  • a change may also be associated with a third process, for example a change of the hearing program by the signal processing unit (if the first period of time is associated with a change in the volume).
  • the signal processing unit (and optionally the power supply electronics) is adapted to monitor the change of the switching means in the second switching state, whether within a third period of time, which is shorter than the first time period, a change back into the first switching state takes place, and possibly reject such a change as a faulty operation.
  • the risk of unintentional operation (incorrect operation) of the switching means by the hearing aid wearer which may occur, for example, in the case of a "through-the-hair stroking" with contact of the switching means, is effectively reduced set a duration of about 0.25 seconds.
  • the energy supply device is expediently connected to the signal processing unit by means of a power supply line (in particular directly).
  • a power supply line in particular directly.
  • the operating voltage is not applied to the power supply line - d. H. there is no energy supply.
  • the switching means is in particular for transmitting information about the respective switching state - preferably in the form of a corresponding switching signal - connected by means of a first switching line to the signal processing unit and by means of a second switching line with the power supply device, in particular the power supply electronics.
  • the switching means comprises (in addition) a reference potential terminal, to which the first switching line and the second switching line are connected in the second switching state. This means that the switching means is directed to put the first and the second switching line when switching to the second switching state to reference potential (eg., Ground potential or a "different" example provided by the hearing instrument reference potential).
  • a first signal voltage is applied to the first switching line, and a second signal voltage is applied to the second switching line.
  • the two signal voltages are thereby preferably provided by two voltage sources which are different from one another (that is to say from a correspondingly assigned first and from a correspondingly assigned second voltage source).
  • the respective voltage sources are associated, for example, correspondingly with the signal processing unit and the power supply electronics.
  • the first and the second signal voltage in particular also have different voltage values. In the context of the invention, it is also conceivable that both signal voltages have the same voltage value.
  • the detection of the second switching state of the switching means by the signal processing unit and by the power supply electronics is carried out in particular based on the detection of a change of the voltage value of the respective switching line associated signal voltage to reference potential. This change to reference potential thus represents a switching signal.
  • the switching means is, in particular, a key or a comparable element (for example a touch panel) which is operated without operation - d. H. without a corresponding touch or other operating event - remains in the first switching state or returns accordingly in the absence of the operation in the first switching state.
  • the switching means is a switch which is also referred to as a "double action tact switch", which has two differently high switching strokes relative to a rest position
  • Switching strokes assigned to different switching signals or switching operations which are triggered when the switch is fully actuated, starting from the rest position one after the other.
  • this switch is preferably contacted so that takes place at one of the two switching strokes, the interconnection of the two switching lines with reference potential.
  • the respective other switching stroke is preferably "unoccupied", ie in particular does not lead to any further switching signal Alternatively, the respective other switching stroke is assigned a different ("third") function.
  • the power supply electronics is set up to continue to monitor the switching state of the switching means in the inactive state and to (re) switch to the active state upon a change from the first switching state to the second switching state.
  • the corresponding second signal voltage is preferably also present in the inactive state at least on the second switching line.
  • the first switching line which serves to drive the signal processing unit, is expediently "switched off", that is to say in particular free of voltage, so that energy can be saved.
  • the energy supply electronics is preferably set up to transition to the active state when the second switching state exists, in particular for the second time period. This in turn effectively prevents inadvertent activation of the hearing instrument by a comparatively short (possibly unintentional) operation of the Wegmit means.
  • the hearing instrument is assigned, in particular, one of these separate remote controls for adjusting volume and various hearing programs.
  • This remote control is in particular configured to transmit to a corresponding input of the hearing aid wearer a switch-off command to the hearing instrument, in particular to the signal processing unit - for example by radio, inductively or acoustically.
  • the Signalverarbei processing unit is suitably arranged in this case to transmit this shutdown command - in particular by means of a corresponding signal line - to the power supply electronics, whereupon this goes into the inactive state.
  • an operation of the hearing instrument is prevented by means of the remote control, in particular due to the lack of power to the signal processing unit.
  • the hearing instrument in particular the energy supply device, in particular within the context of the charging electronics, comprises means for preferably inductive energy reception for a charging process of the energy supply means.
  • the hearing instrument is placed in this case (preferably in the off state), for example in a charging cradle.
  • the energy supply device for protection against contamination can be arranged or arranged permanently within the hearing aid housing.
  • permanent is meant the duration of several or many charging or operating cycles, or the life or operating life of the power supply
  • a permanent duration is differentiated from (conventional) batteries, which are removed when they are “empty”
  • a major advantage of rechargeable power supplies over disposable batteries is that they do not need to be removed after discharge and thus also eliminates the need for a battery door. if necessary, be accessible only small-area contact surfaces from the outside, whereby the risk of contamination of the interior of the housing is greatly reduced.
  • the method according to the invention is used in particular for operating the above-described hearing instrument.
  • the signal processing unit detects whether the switching means is in the first or the second switching state and issues a control command if the switching means changes back into the first switching state within the predetermined first time span. From the power supply electronics is accordingly also detects whether the switching means is in the first or in the second switching state, wherein the power supply electronics for triggering the switch-off state of the hearing instrument changes to the inactive state when the second switching state of the switching means for the predetermined second time period exists.
  • the energy supply electronics are designed to control at least one connection (ie in particular the energy supply line) between the energy supply means and the signal processing unit as a function of the switching state of the switching means "Control" is understood in particular as an interruption of the connection between the energy supply means and the signal processing unit, so that (at least by the signal processing unit) no power is withdrawn.
  • the switching means comprises a means of the group of feeler elements, switches, wire connection and switch which can be influenced by a magnetic field.
  • a probe element may for example comprise a type of flip-flop, so that an actuation of the probe element can be stored.
  • pushing and releasing the probe element may define a first switching state, and a second depression and release of the probe element may define a second switching state.
  • the power supply electronics can control the switch-off state of the hearing instrument as a function of these switching states of the switching means.
  • the switching means may be designed as a wire connection, through which a circuit may be closed or opened.
  • a switch which can be influenced by a magnetic field is, for example, a per se known reed switch or reed contact, in which contact tongues of mostly an iron-nickel alloy are magnetically actuated and thus establish a connection.
  • the switching means can be operated by the hearing aid wearer.
  • the hearing aid wearer can actuate the switching means and put the hearing instrument in the off state, if he does not need the hearing instrument, for example.
  • the switching means comprises an openable flap, wherein the surface of the flap is adapted in the closed state to the shape of the Hörommeerumpfgephaseuses.
  • hearing aid wearers are accustomed to selecting a function of the hearing instrument, for example, by opening a battery door of a commercially available hearing instrument.
  • a battery door as such is no longer necessary, it may be advantageous to a battery flap-like switching means, i. a switching means with an openable flap to provide, to maintain a familiar operation on the opening and closing of this flap.
  • a flap with surface adapted to the shape of the hearing aid body i.
  • a surface that is substantially adapted to the shape of the hearing aid housing is compliant and can help prevent injuries and damage.
  • the switching means in the open state has a switching state in which at least one line connection is interrupted.
  • a broken line connection is advantageous because it can achieve a high resistance that promotes a low power off state.
  • the switching means is additionally designed to open and close at least one connection, ie in particular of the energy supply line, between the energy supply means and the signal processing unit.
  • a switching means for example a wire bridge, which can interrupt an electrical connection, for example a connection to a positive operating voltage, between the energy supply means, eg the battery cell, and the signal processing unit, eg an electronic circuit, an effective switch-off state can be achieved.
  • the switching means is designed for opening and closing three or four connections, wherein two connections are designed for connecting the energy supply means to the signal processing unit and / or to the energy supply electronics.
  • two electrical connections may relate to a positive and a negative operating voltage (i.e., a positive or negative voltage value, respectively), the third electrical connection may be, for example, to a contact of the power electronics controlling the shut-off state of the hearing instrument.
  • the third and fourth electrical connections can, for example, connect two contacts of the power supply electronics and thus control the switch-off state of the hearing instrument.
  • the switching means has a first component and a second component, wherein the first component of the switching means is arranged on a first component of the hearing instrument and wherein the second component of the switching means is arranged on a second component of the hearing instrument.
  • the switching means thus consists of two components or parts which are arranged on different objects or components of the hearing instrument, wherein the components have a relative motion. can perform to each other.
  • the switching means may be a contact pin which can be inserted into a spring clip or a plug connector which can be closed or revealed by the relative movement.
  • the components of the switching means can be arranged, for example, on the power supply device, on or in the hearing aid body housing or on or in a battery flap-like flap.
  • the relative movement may be a pushing movement or a turning or tilting movement.
  • the hearing instrument has at least one sealing device.
  • the sealing device By means of this sealing device, the switching means can be sealed, at least in a closed switching state, in particular in the latter embodiment.
  • Silicone-containing sealing rings or sealing caps for example, protect the switching device against dirt, moisture and sweat. If the switching means is made in two parts and the closing operation of the switching means is based on a relative movement of the two parts, the sealing action can be effected, for example, during a closing operation by a positive contact of the sealing ring with a part of the switching means.
  • the hearing instrument has at least one sealing device and an activatable limiting means.
  • the activated limiting means By the activated limiting means, the relative movement between the first component of the hearing instrument and the second component of the hearing instrument is limited and by the sealing means, the switching means is sealed in an open switching state.
  • a limiting means limits a relative movement between the two components of the hearing instrument, without affecting the switching action of the circuit means. With the feature of this embodiment it is achieved that the sealing means still exists in the open switching state, ie when the deflection of the relative movement is generally greater than in a closed switching state, the sealing effect of the sealing device still exists.
  • A can be, for example, a mechanical stop.
  • the limiting means limits the relative movement only in an activated state. In a non-activated state, the relative movement of two components of the hearing instrument can therefore be greater and the sealing effect of the sealing device need not necessarily be maintained.
  • the energy supply means comprises an accumulator, in particular formed by the battery cell, which comprises or the lithium.
  • Lithium-containing accumulators are, for example, lithium-ion accumulators and lithium-polymer accumulators. These have a high energy density and a high charging efficiency, making them very well suited for hearing instruments.
  • the disadvantage is that they are sensitive, for example, with regard to the operation, in particular the discharge currents and the Entladehubs, and the charge, in particular the end-of-charge voltage and the strength of the charging currents, and are therefore monitored as possible in these modes.
  • the power supply electronics is expediently set up.
  • a hearing instrument is used for an extended period of time, e.g. is not used in storage prior to sale, one of the hearing instruments according to the invention described above is of great advantage, since by bringing the hearing instrument in the off state, a deep discharge and thus a degradation or even destruction of the accumulator can be avoided.
  • a power supply device for a hearing instrument to be considered, which includes the rechargeable power supply means and the power supply electronics (or also: the control and monitoring means).
  • the power supply device preferably forms together with the Hörommeerumpfgephinuse, the at least one microphone, the receiver, the signal processing unit and the switching means and possibly the receiver connection means or the sound tube and the earpiece a hearing instrument of the type described above.
  • This basic idea of the above invention describes a power supply device which can be arranged in a hearing instrument, preferably arranged, and which contains a repeatedly chargeable energy supply means, e.g. a lithium-ion secondary battery, and a power supply electronics, which can control a shut-off state of the hearing instrument by reading a state of a switching means. Further embodiments of this basic idea result from analogous transfers of features from the previously described embodiments of the hearing instruments according to the invention.
  • a repeatedly chargeable energy supply means e.g. a lithium-ion secondary battery
  • the hearing instrument comprises the power supply device in addition to the hearing aid housing, the at least one microphone, the receiver, and the signal processing unit, the latter having the energy supply electronics which can be assigned to the hearing instrument, in particular permanently assigned thereto.
  • the energy supply device has a receiving device for (preferably reversible) mechanical reception of the at least one rechargeable energy supply means (into the housing) described above and for electrically contacting the or each energy supply means with the power supply electronics Hearing instrument recorded.
  • the hearing instrument comprises - especially in the event that it is the hearing aid is a behind-the-ear hearing aid (BTE hearing aid) - preferably the above-described (hearing aid housing, the at least one microphone, the receiver, and optionally the receiver connection means or the sound tube and the ear piece.
  • BTE hearing aid behind-the-ear hearing aid
  • the energy supply electronics are arranged in a region that can be assigned to the hearing instrument, for example within the (hearing aid housing) housing, ie not with the at least one energy supply device (eg the battery cell) Battery pack forms.
  • the receiving device of the hearing instrument is designed for mechanically receiving the rechargeable energy supply means in the housing and for making electrical contact with the power supply electronics.
  • strips or clamps can hold the rechargeable energy supply means in a predeterminable position within the housing by means of a positive or non-positive, reversible connection.
  • the power supply means and in particular contacts of the power supply means designed for this purpose are electrically connected to the power supply electronics, for example by means of spring contacts, so that the power supply means can deliver electrical energy to the power supply electronics.
  • the hearing instrument which has the energy supply device with the receiving device for the rechargeable energy supply device, expediently likewise comprises the above-described switching device, which is set up for operation in particular for the reversible change between the first and the second switching state.
  • the signal processing unit is in this case adapted to output the above-described control command when the second switching state of the switching means for the first period of time exists.
  • the power supply electronics is also configured to go into the inactive state when the second switching state of the switching means for the second period exists.
  • the power supply electronics is arranged on a printed circuit board, which also includes electronic components of the signal processing unit, ie carries.
  • This concept provides a space-saving and cost-effective way to integrate the power electronics in the hearing instrument by electrical components of the power electronics are arranged on the same circuit board as electronic components of the signal processing unit.
  • Electronic components of the signal processing unit may be essential electronic components of the hearing instrument, such as an amplifier, a processor for signal processing, and the like.
  • the circuit board can also be used for the electrical connection of components of the power supply electronics with each other and components of the signal processing unit.
  • the receiving device is arranged on the circuit board, which also includes electronic components of the signal processing unit.
  • the receiving device is arranged on the printed circuit board or printed circuit board, on which electronic components of the signal processing unit are also arranged, a space-saving arrangement can be achieved, as is known.
  • means, such as clamps or angles can serve both for mechanically accommodating the at least one rechargeable battery cell in the hearing aid housing and for electrically contacting the at least one rechargeable battery cell with the energy supply electronics.
  • metallic strips can be used for this purpose.
  • the optionally present charging electronics are set up to charge the power supply means accommodated in the housing by the receiving device.
  • the charging electronics or components of the charging electronics allow a charging function of the rechargeable power supply means. Because rechargeable Energy supply means are partially sensitive, for example, with respect to charging currents, charging voltages, etc., the charging electronics is preferably tuned to the réelleladende energy supply means.
  • Means for charging the rechargeable power supply means accommodated in the hearing aid body housing can be, for example, means for electrically connecting an external voltage source to the charging electronics. Such means may, for example, be embodied as a socket or as metallic contacts that are connectable and durable by magnetic holding forces with cables.
  • the energy supply device (in particular the charging electronics) comprises, as a means for wireless, in particular inductive energy reception, a flatly extended antenna, for example in the form of a planar spiral.
  • the charging electronics are designed to charge the at least one rechargeable energy supply means accommodated in the hearing aid body housing according to an inductive charging method.
  • a surface-extended antenna can be arranged on the printed circuit board, which also includes electronic components of the signal processing unit.
  • the rechargeable energy supply means extends flat and arranged in a recorded in the hearing aid housing housing state over the areally extended antenna and / or over the power supply electronics and / or via electronic components of the signal processing unit.
  • rechargeable energy supply means in particular rechargeable battery cells often have a disc-shaped base
  • it may be advantageous to superimpose a planar antenna of this type the base of which, for example in the case of a planar spiral, is also essentially disc-shaped.
  • a layer arrangement may be advantageous in terms of area, if the area covered by the energy supply means is replaced by grains. components of the power supply electronics and / or the signal processing unit is used.
  • the (hearing aid body) housing be capsuled in a state in which the rechargeable power supply means is accommodated in the housing.
  • the rechargeable power supply means in particular the rechargeable battery cell or rechargeable battery cells has standardized dimensions.
  • rechargeable power supply means of different manufacturers can be used, whereby cost advantages can result.
  • the hearing instrument system is characterized in that it comprises one of the previously described hearing instruments according to the invention and the rechargeable energy supply means, wherein the energy supply means is received by the receiving device in the hearing aid housing and electrically contacted with the power supply electronics.
  • a hearing instrument system has one or more of the features according to the invention of the above-described hearing instruments according to the invention.
  • the rechargeable energy supply means may also be firmly integrated into the hearing instrument, for example by means of
  • Soldering tags is soldered to a circuit board, which also include electronic components of the signal processing unit.
  • FIG. 1 is a schematic representation of a hearing instrument according to the prior
  • FIG. 1 an embodiment of a hearing instrument according to the invention
  • FIG. 3 is a schematic diagram of a signal processing unit, a power supply device and a switching means of the hearing instrument of FIG. 2,
  • FIG. 6 shows an alternative embodiment of the hearing instrument according to the invention in a view according to FIG. 1, FIG.
  • FIG. 7 shows an alternative exemplary embodiment of the signal processing unit, the energy supply device and the switching means of the hearing instrument according to FIG. 6, in the view according to FIG.
  • FIG. 14-1 6 in a schematic detailed view of another embodiment of the
  • FIG. 17 in view of FIG. 1 shows a further embodiment of the hearing instrument according to the invention
  • FIG. 18 is a schematic detail view of the hearing instrument according to FIG. 17.
  • BTE hearing aid in short: hearing aid 1
  • the hearing device 1 comprises electronic components which are combined to form a signal processing unit 4, two microphones 5, a battery cell 6 serving as energy supply means and a receiver 7. These are all inside the housing 3
  • the hearing aid 1 comprises a sound tube 8 leading away from the housing 3 and an earpiece 9 arranged at the end.
  • the hearing aid 1 comprises a switching means 1 1, which is arranged on the housing 3 and connected to the signal processing unit 4 signal transmission technology.
  • this hearing instrument is also a BTE hearing aid which is referred to below as hearing aid 1 for short.
  • the hearing aid 1 thus also comprises the microphones 5 arranged in the housing 3, the signal processing unit 4, the receiver 7, and the sound tube 8 and the earpiece 9 arranged outside the housing 3.
  • the hearing aid 1 comprises a power supply device 15 for providing a predetermined operating voltage (ie an operating voltage with a predetermined voltage value) is set up and provided to the signal processing unit 4 and is coupled thereto by means of a power supply line 17 to the signal processing unit 4 (galvanic).
  • the energy supply device 15 has a (in Fig.
  • the power supply device 15 specifically the power supply electronics as a means for charging the power supply means an antenna for wireless, specifically for the inductive reception of energy.
  • the power supply electronics is set up to monitor and regulate a charging process of the battery cell.
  • the power supply electronics is set up to convert (specifically reduce) and stabilize a source voltage drawn from the battery cell during operation of the hearing device 1 to the predetermined voltage value of the operating voltage.
  • the energy supply device 15 is embodied as a separate unit from the signal processing unit 4-which is used to process audio signals detected by the microphones 5.
  • the power supply device 15 eliminates the hearing aid 1 according to the invention, a change of the battery cell in the event that the latter is discharged or at least can not ensure a sufficient power supply of the signal processing unit 4.
  • the rechargeable cell can be recharged particularly user-friendly within the hearing device 1 (specifically of the housing 3), for example by means of an inductive charging tray.
  • the switching means 1 1 of the hearing aid 1 is used in this case as such a control element and is for this purpose by means of a first switching line 19 with the signal processing unit 4 and by means of a second switching line 20 to the power supply device 15, specifically with the power supply electronics signal transmission technology connected.
  • the switching means 1 1 is also adapted to take alternately two different switching states, namely a first switching state and a second switching state.
  • Switching means 1 1 is concretely a key which changes during operation, ie at a sufficiently high tactile pressure, from the first to the second switching state and when the operation ceases from the second back into the first switching state changes.
  • the two switching lines 1 9 and 20 are used to transmit information about the respective switching state of the switching means 1 1 to the signal processing unit 4 and to the Energy fixturessei device 1 5 - in the form of a respective switching signal.
  • the operation of the switching means 1 1 is shown in more detail with reference to a schematic diagram.
  • the switching means 1 1 has a plurality of terminals, two of which represent the first switching line 1 9 and the second switching line 20, and two further terminals each form a reference potential terminal 22 for the respective switching line 1 9 or 20.
  • the switching means 1 1 is unconfirmed.
  • a first signal voltage Si is applied to the first switching line 1 9 with a first voltage value Vi.
  • the second switching line 20 is correspondingly a second signal voltage S 2 with a second, different from the first voltage value Vi voltage value V 2 .
  • the two switching lines 1 9 and 20 are not short-circuited to each other, but refer in the first switching state of their respective signal voltage Si or S 2 associated voltage Vi or V 2 of respectively associated, separate (not shown) voltage sources.
  • the switching means 1 1 is actuated and the first and the second switching line 1 9 and 20 are connected to the respective reference potential terminal 22, so that the respective voltage value Vi or V 2 of the signal voltages Si and S 2 drops to reference potential V B (see Figures 4 and 5).
  • the two switching lines 1 9 and 20 are connected to ground potential.
  • the signal processing unit 4 and the power supply electronics are each adapted to switch between the first and the second switching state based on the change of the voltage value Vi or V 2 of the voltage applied to the respective switching line 1 9 or 20 signal voltage Si or S 2 to reference potential V. B or from reference potential V B back to detect.
  • the signal processing unit 4 is further configured to output (as a "first operation") a control command for setting a new volume value, if a change of the switching means 1 1 from the first switch In the second switching state - ie upon detection of a change in the voltage value V-1 of the first signal voltage Si to reference potential V B - the signal processing unit 4 within a (the signal processing unit 4 associated) first time period Ti a change from the second switching state back into the registered first switching state (see Fig. 4 and 5).
  • the power supply electronics of the power supply device 15 is configured to transition (as a "second operation") to an inactive state when the power supply device 15 detects that (upon the change of the switching means 11 from the first switching state to the second switching state) Switching state for a (the power supply electronics associated) second period T 2 (ie, reference potential V B on the second switching line 20) is present (see Fig. 4 and 5)
  • the power electronics goes into the inactive state when the end of second time period T 2, the switching means 1 1 still is in the second switching state.
  • the operating voltage is not prepared for the signal processing unit 4 and provided by the power supply electronics, so that the signal processing unit 4 (and hence the hearing aid 1) in a "shutdown" is located.
  • FIG. 4 shows two diagrams in which the time t is plotted on the horizontal axis (time axis) and a voltage V on the vertical axis, the diagrams being shown congruently with their time axes (temporally).
  • the same duration for example 3 seconds, is set for the first and second time periods Ti and T 2 .
  • any change of the switching means 1 1 from the second switching state back to the first switching state within the first or second time period Ti or T 2 - ie before the end of the two periods Ti and T 2 - leads to an output of the control command by the signal processing unit 4. Only when the switching means 1 1 longer than the periods ⁇ or T 2 remains in the second switching state, the power supply electronics goes into the inactive state.
  • the second time period T 2 is selected to be greater than the first time period ⁇ .
  • the duration of the first time Span ⁇ is set to 0.5 seconds.
  • the duration of the second period is 3 seconds.
  • FIG. 6 shows a further exemplary embodiment of the hearing device 1. It also includes the housing 3 to be supported behind the external ear 2 of the hearing device wearer, the two microphones 5, the receiver 7, the sound tube 8, the ear piece 9, the power supply device 1 5 (also referred to as the power supply unit) and the signal processing unit 4 includes electronic components.
  • the acoustic signal generated by the receiver 7 is passed through the sound tube 8 to the ear piece 9, which is inserted into the ear canal 1 0 of the hearing aid wearer.
  • the switching means 1 1 is arranged, which can influence the signal processing unit 4.
  • the power supply device 1 5 comprises the non-illustrated repeatedly rechargeable power supply means, here a lithium polymer accumulator, and the (also referred to as control and monitoring means) power supply electronics.
  • the hearing aid 1 further comprises a second switching means 24, which comprises a flap 25.
  • the second switching means 24 is designed to accept at least two switching states and the power supply electronics is designed to control a switch-off state of the hearing aid 1 as a function of the switching state of the second switching means 24.
  • the power supply device 1 5 is permanently disposed within the housing 3 for protection against contamination.
  • the surface of the openable flap 25 of the second switching means 24 is adapted in the closed state to the shape of the housing 3.
  • the energy supply device 15 comprises here as energy supply means an accumulator 27, and the power supply electronics, shown here as electronic circuit 28.
  • the second switching means 24, here a switch or a closer may assume two states in this exemplary embodiment, an open or high-impedance state and a closed or conductive state.
  • the power supply electronics is designed, depending on the switching state of the switching means 24, a shutdown state of a hearing instrument, here schematically by the signal processing unit 4, as a consumer of electrical power of the hearing aid, indicated to control.
  • the control takes place in this embodiment, characterized in that upon detection of the open state of the switching means 24 supply lines, for example, a positive and a negative supply voltage, are interrupted by the power supply to the signal processing unit 4 by the power supply electronics, indicated by two open switches in the power supply electronics (ie in the electronic circuit 28). By opening the electrical connections, the signal processing unit 4 is de-energized and the hearing aid 1 is in a shutdown state.
  • supply lines for example, a positive and a negative supply voltage
  • Fig. 8 shows schematically and by way of example a further embodiment of the power supply device 15 and the second switching means 24 for controlling the power supply means 15.
  • the switching means 24 has in this case three switches, the connections between the power supply means (the accumulator 27) and the power supply electronics (the electronic circuit 28).
  • the switches are shown in a non-conducting or open state.
  • Supply lines for example, a positive and a negative supply voltage, from the power supply means to the power supply electronics are interrupted, as well as a control line, indicated by a signal applied to the top of the power supply electronics (the electronic circuit 28).
  • the power supply device 15 comprises as rechargeable power supply means the accumulator 27 and the power supply electronics in the form of the electronic circuit 28.
  • the switching means 24th can electrical connections between the power supply means and the signal processing unit 4 controlled, ie open or closed. In the illustrated state, the signal processing unit 4, in particular the voltage supply lines, is disconnected from the power supply means, whereby the hearing aid 1 is in a switch-off state.
  • a control line indicated by a signal applied to the top of the power supply electronics (the electronic circuit 28), high impedance, whereby the power supply electronics itself can go into a power-off state in which the power electronics receives no or very little electrical power.
  • the repeatedly rechargeable energy supply means (in the present case the accumulator 27) of the hearing aid 1 in the off state is rechargeable.
  • the hearing device 1 may be placed in the off state in a charging cradle and charged by an inductive charging method, which is regulated in particular by the power supply electronics.
  • FIGS. 10 and 11 schematically and by way of example depict an exemplary embodiment of the second switching means 24 with three ports, each in an open state or in a conducting state.
  • a terminal 35 of a positive operating voltage of the power supply means with a terminal 34 of a positive operating voltage of the power supply device 15 and a terminal 31 of a negative operating voltage of the power supply means with a terminal 30 of a negative operating voltage of the power supply device 15 are connectable.
  • the connection 31 of the negative operating voltage of the energy supply means can be connected to a control connection 32 of the energy supply device 15.
  • a closed state of the switching means 24 is thus the negative operating voltage of the power supply means to the control terminal 32, in an open state, the control terminal 32 is high impedance.
  • the power supply device 15, in particular its power supply electronics, can control the switch-off state of the hearing device 1 as a function of the switching state of the switching device 24.
  • FIGS. 12 and 13 illustrate schematically and by way of example one embodiment of the second switching means 24 with four ports, each in an open state or in a conductive state.
  • a terminal 35 of a positive operating voltage of the power supply means with a terminal 34 of a positive operating voltage of the power supply device 15 and a terminal 31 of a negative operating voltage of the power supply means with a terminal 30 of a negative operating voltage of the power supply device 15 are connectable.
  • a control terminal 32 of the power supply device 15 with a further control terminal 32 'of the power supply device 15 is connected by a wire bridge 33.
  • control connection 32 In a closed state of the switching means 24, the control connection 32 is thus short-circuited to the further control connection 32 '; in an open state, the control connection 32 and the further control connection are high-impedance.
  • the power supply device 15, in particular its power supply electronics, can control the switch-off state of the hearing device 1 as a function of the switching state of the switching device 24.
  • FIGS. 14, 15 and 16 each show diagrammatically and by way of example the hearing aid 1 according to the invention, specifically a behind-the-ear hearing aid, with a further exemplary embodiment of the (second) switching means 24 in a closed, sealed state, in an open, sealed state and shown in an open, unsealed condition.
  • the hearing aid 1 comprises, inter alia, the housing 3 and the power supply device 15, which is connected to the flap 25 (of the switching means 24).
  • the power supply device 15 includes the (not shown) repeatedly chargeable power supply means, such as a lithium-ion battery, and a not shown control and monitoring means (ie the power electronics).
  • the flap 25 is designed similar to a battery cover of a conventional hearing aid in order to offer the user a familiar operation of the hearing aid 1.
  • the flap 25 comprises an axis 36, through which a relative movement of the flap 25 is executable.
  • the switching means 24 consists of two components or parts which are arranged on different objects or components of the hearing aid 1.
  • the first component 24 'of the switching means 24, here contact pins, is arranged on the power supply device 15,
  • the second component 24 "of the switching means 24, here a spring clip is arranged on the housing 3. In the state shown in FIG closed and the surface of the flap 25 is adapted in the closed state to the shape of the housing 3.
  • the hearing aid 1 has two sealing devices, by means of which the switching means 24 is sealed in the closed switching state
  • the first sealing device 40 is a sealing lip made of rubber the flap 25 is arranged and which hugs in the closed state of the flap 25 circumferentially on the inside of the housing 3.
  • the second sealing means 42 is a silicone-containing sealing ring, which is arranged in the interior of the housing 3 and the circumferentially form-fitting part of the power supply device 15, at the end of the first part 24 'of the switching means 24 is arranged is, seals.
  • a limiting means 44 in the form of a tongue which is arranged on the flap 25, engages in the housing 3 a.
  • In the closed state of the hearing aid 1 have a slot 46 of the limiting means 44 and a pin 48 which is arranged on the housing 3 and engages in the slot 46, (for solving the problem of the invention) no essential function.
  • FIG. 15 shows the hearing aid 1 according to FIG. 14 in an open, sealed state.
  • the flap 25 is slightly opened.
  • the opening resulting from a relative movement 50 is sufficient to move the switching means 24 from the closed state to the open state characterized that the first component 24 'of the switching means 24 is not in contact with the second component 24 "of the switching means 24.
  • the switching means 24 can thus be operated, controlled or influenced by a user. because the pin 48 blocks further opening of the flap 25 at one end of the oblong hole 46 of the limiting means 44.
  • the switching means 24 is opened and also the flap 25 is opened, but nevertheless the hearing aid 1 is in a sealed state, because the limitation of the relative movement 50 by the limiting means 44, the first sealing means 40 and the second sealing means 42 the same sealing function, as in the closed state. That is, even in the open state of the switching means 24, the power supply means 15 and in particular the switching means 24 against dirt, moisture and sweat protected, with the Wennwirk ung the circuit means 26 is not affected by the limiting means 44. In contrast to conventional hearing instruments, which must be opened for the replacement of empty (discharged) batteries, this state can be maintained over many charging cycles of the power supply device 15.
  • the hearing aid 1 according to Figs. 14 and 15 is shown in an open, unsealed condition.
  • the limiting means 44 limits relative movement of the flap 25 in an activated state.
  • a non-activated state which can be brought about for example by removing the pin 48 of FIG. 15, the relative movement 50 'of the flap 25 may be greater than that In this state, there is no sealing effect by the first sealing device 40 or by the second sealing device 42. It is conceivable that this state in which the hearing aid 1 is not protected against dirt and moisture, for example for a Programming the hearing instrument by a hearing care professional or for the replacement of a defective power supply device 15 is used.
  • the transfer of the limiting means 44 from an active to a non-active state can be limited to skilled workers by appropriate design measures, such as the requirement of special tools, so that in the everyday Use of the hearing instrument 1 only the states shown in Figure 12 and Figure 13 occur in which the hearing instrument is sealed.
  • Hearing instruments with a power supply device integrated in the hearing instrument offer advantages in maintenance, since the power supply device is embedded in the housing of the hearing aid protected.
  • a power supply device advantageously has at least two operating modes: an active mode in which the hearing instrument is supplied with electrical energy and a switch-off mode in which the energy supply device is more or less switched off and no current flows.
  • the shutdown mode is particularly important for warehousing, engl, shelf life, important to avoid a deep discharge of a battery of the power supply device.
  • a user of the hearing instrument should be able to switch between these two operating modes.
  • the invention describes several alternatives as to how advantageously control of the modes could be carried out.
  • the power supply device also engl. Called a power module, a rechargeable power supply, e.g. a rechargeable battery, and power electronics used as an integrated electrical circuit, e.g. in the form of a power management IC, may be executed.
  • the power management IC may have a dedicated pin, the state of which, depending for example on a voltage value or a resistance value, decides whether the power supply device and thus the hearing instrument is operated in the active mode or in the shutdown mode.
  • the power supply device is placed within a housing similar to a known battery holder, and a switching means is in the form of a known battery door or battery cover. Since the power supply device does not need to be changed like a battery, it can be sealed down to any contacts, thereby preventing sweat, moisture and others
  • the switching means in the form of a battery door is easily opens, there is no contact between the power supply and contact holders of the hearing instrument, whereby the dedicated pin of the power electronics is contactless and puts the power supply in the off state.
  • By closing the switching means in the form of a battery door contacts of the power supply device are pressed into the contact holder of the hearing instrument, whereby the dedicated pin of the power supply electronics contacted and the power supply device leaves the off state.
  • an additional switch or push-button may be placed on the hearing instrument to place the power supply in a shut-off state.
  • FIG. 17 shows a further exemplary embodiment of the hearing instrument according to the invention.
  • This hearing instrument is again a BTE hearing aid 1 referred to as BTE hearing aid. It also comprises the housing 3 to be worn behind the earpiece 2 of the hearing device wearer, the two microphones 5, the receiver 7, the sound tube 8, the ear piece 9, the power supply device 15 and the signal processing unit 4, which comprises electronic components.
  • the acoustic signal generated by the receiver 7 is passed through the sound tube 8 to the ear piece 9, which is inserted into the ear canal 10 of the hearing aid wearer.
  • the switching means 1 1 is arranged, which can influence the signal processing unit 4.
  • the energy supply device 15 comprises a (not shown), the hearing aid 1 assignable (specifically assigned), power supply electronics, for providing a predetermined (operating or) supply voltage, and a recording device, not shown, for mechanically receiving at least one rechargeable energy supply means (a rechargeable battery). or battery cell, for example in the form of the accumulator 27) in the housing 3 and for electrical contacting of the accumulator 27 with the power supply electronics.
  • the accumulator 27, here a lithium polymer accumulator, is arranged or received in the housing 3 in this embodiment.
  • Such a trained hearing aid 1 with recorded rechargeable battery 27 forms an inventive hearing instrument system.
  • FIG. 18 shows diagrammatically and by way of example components of the hearing device 1 according to FIG. 17 with a flatly extended antenna 60 for wireless energy reception in a state in which the accumulator 27 is not received in the hearing device 1.
  • a printed circuit board 62 is arranged, which carries electronic components 64 of the signal processing unit 4 of the hearing aid 1 and components of the power supply device 15.
  • the energy supply device 15 comprises the energy supply electronics (in the form of the electronic circuit 28), which is arranged on the same circuit board 62, which also comprises electronic components 64 of the signal processing unit 4, and is thus associated with the hearing aid 1.
  • the power supply electronics serves to provide a predetermined supply voltage for the power supply of the hearing aid 1.
  • the energy supply device 15 further comprises a receiving device 66 and 67, wherein the component 66 of the receiving device for mechanically receiving the accumulator 27 in the housing 3 and the component 67 of the receiving device for electrically contacting the accumulator 27 with the power supply electronics (the electronic circuit 28) is designed ,
  • the component 66 of the receiving device is in this embodiment, a clip which is adapted to the outer contour of the accumulator 27 and can enclose this form-fitting manner.
  • the component 66 of the receiving device with the inserted accumulator 27 by means of a rotation axis 70 can be screwed into the housing 3 and positionable in a predetermined position over the circuit board 62 that the substantially flat surfaces of the circuit board 62 and the accumulator 27th are aligned in parallel and the component 67 of the receiving device electrically connects or contacts the accumulator 27 with the power supply electronics.
  • the flap 68 can be closed.
  • the hearing aid 1 can also be designed without flap 68 and the accumulator 27 can after opening the housing 3, for example by screws or Snap locks is apparently designed to be reversibly inserted into a receiving device, which includes, for example, brackets.
  • the clamps for holding the accumulator 27 may be disposed on the circuit board 62, for example, and also make electrical contact between the accumulator 27 and the power supply electronics.
  • the hearing aid 1 shown in FIG. 18 and in particular the power supply device 15 also includes charging electronics integrated in the power supply electronics, and means 72 and 73 for charging the rechargeable battery 27 accommodated in the housing 3.
  • examples are given Components for two different charging methods shown.
  • a first charging method electrical energy is supplied via two contacts 72 and 73 of the charging electronics and thus the power supply electronics, which performs the charging process of the accumulator 27 controlled.
  • a charging cable for example, by means of magnets and magnetic force to the contacts 72 and 73 are adhesively coupled.
  • an externally applied electromagnetic alternating field is coupled into the planar, spiral-shaped coil (antenna 60).
  • the injected alternating currents are supplied to the charging electronics and thus to the power supply electronics, which carries out the charging process of the rechargeable battery cell 12 in a controlled manner.
  • the two charging methods can alternatively be used from each other.
  • the invention proposes, inter alia, a hearing instrument in which an accumulator and a power supply electronics are separated from each other, wherein the power supply electronics is arranged in the housing of the hearing instrument.
  • this has the advantage that high-quality electronics can continue to be used in the event of a battery change and, on the other hand, in the development of a hearing instrument, in any hearing aid type, the electronics can be adapted to the spatial conditions, as a result of which the devices can be kept small.

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  • Health & Medical Sciences (AREA)
  • General Health & Medical Sciences (AREA)
  • Neurosurgery (AREA)
  • Otolaryngology (AREA)
  • Physics & Mathematics (AREA)
  • Engineering & Computer Science (AREA)
  • Acoustics & Sound (AREA)
  • Signal Processing (AREA)
  • Battery Mounting, Suspending (AREA)

Abstract

L'invention concerne un appareillage auditif (1) qui comprend une unité de traitement de signal (4) et un dispositif d'alimentation en énergie (15). Cet appareillage comprend également une électronique d'alimentation en énergie (28) et, dans un mode de fonctionnement normal, un moyen d'alimentation en énergie (27) rechargeable. Ledit appareillage auditif (1) comporte en outre un moyen de commutation (11, 24) qui est conçu pour adopter au moins deux états de commutation, l'électronique de l'alimentation en énergie (15) étant conçue pour commander un état de coupure de l'appareillage auditif (1) en fonction de l'état de commutation du moyen de commutation (11, 24).
EP15774872.4A 2014-09-10 2015-09-10 Appareillage auditif et procédé pour le faire fonctionner Withdrawn EP3192277A1 (fr)

Applications Claiming Priority (3)

Application Number Priority Date Filing Date Title
DE102014218053.8A DE102014218053B4 (de) 2014-09-10 2014-09-10 Hörinstrument mit Stromversorgungseinheit und Stromversorgungseinheit für ein Hörinstrument
DE102014219017.7A DE102014219017A1 (de) 2014-09-22 2014-09-22 Hörinstrument mit Energieversorgungseinrichtung und Hörinstrumentensystem mit Energieversorgungseinrichtung
PCT/EP2015/070775 WO2016038165A1 (fr) 2014-09-10 2015-09-10 Appareillage auditif et procédé pour le faire fonctionner

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EP3192277A1 true EP3192277A1 (fr) 2017-07-19

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DE102019207680B3 (de) * 2019-05-24 2020-10-29 Sivantos Pte. Ltd. Hörgerät, Receivereinheit sowie Verfahren zum Betrieb eines Hörgerätes
TWI761874B (zh) * 2020-07-07 2022-04-21 鉭騏實業有限公司 耳鳴屏蔽裝置及其訊號處理方法
CN112291671B (zh) * 2020-11-30 2023-01-20 歌尔科技有限公司 充电盒和耳机组件

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US8238590B2 (en) * 2008-03-07 2012-08-07 Bose Corporation Automated audio source control based on audio output device placement detection
US8270658B2 (en) * 2008-04-28 2012-09-18 Hearing Enhancement Group Position sensing apparatus and method for active headworn device

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