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WO2019193017A1 - Système auditif et appareil auxiliaire pour un tel système - Google Patents

Système auditif et appareil auxiliaire pour un tel système Download PDF

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Publication number
WO2019193017A1
WO2019193017A1 PCT/EP2019/058323 EP2019058323W WO2019193017A1 WO 2019193017 A1 WO2019193017 A1 WO 2019193017A1 EP 2019058323 W EP2019058323 W EP 2019058323W WO 2019193017 A1 WO2019193017 A1 WO 2019193017A1
Authority
WO
WIPO (PCT)
Prior art keywords
hearing
hearing aid
designed
hearing system
auxiliary device
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Ceased
Application number
PCT/EP2019/058323
Other languages
German (de)
English (en)
Inventor
Stefan Menzl
Hoong Yih Chan
Christoph Schmid
Maarten Barmentlo
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
Sivantos 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 Sivantos Pte Ltd filed Critical Sivantos Pte Ltd
Publication of WO2019193017A1 publication Critical patent/WO2019193017A1/fr
Anticipated expiration legal-status Critical
Ceased legal-status Critical Current

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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
    • H04R25/55—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
    • 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
    • H04R25/556—External connectors, e.g. plugs or modules
    • 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
    • H04R2225/55—Communication between hearing aids and external devices via a network for data exchange
    • 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
    • H04R25/558—Remote control, e.g. of amplification, frequency

Definitions

  • the invention relates to a hearing system which has a hearing aid and an attachment. Furthermore, the invention relates to such an accessory.
  • a hearing aid is typically used to supply a hearing-impaired user.
  • An essential functionality of the hearing device is then to record sound signals from the environment of the user, to modify and then output the modified sound signals back to the user.
  • the modification of the sound signals is usually at least one gain, but in general the modification comprises an adaptation of the sound signals to the typically individual hearing profile of the user, with the aim of rendering the sound signals of the surroundings as understandable as possible.
  • a hearing aid has at least one microphone in order to record the sound signals of the surroundings, and at least one listener to output the modified sound signals to the user.
  • the microphone and handset are typically carried by the user at the head and in the immediate vicinity of the ear, e.g. behind the ear or in it. Accordingly, different types of hearing aids, e.g. so-called BTE hearing aids, ITE hearing aids, RIC hearing aids and the like.
  • a hearing aid Since a hearing aid is often worn by a user for a long time, corresponding design requirements arise. On the one hand, a hearing aid should be as light as possible. Along with this, a hearing aid should also be as small or inconspicuous as possible, which is often demanded from an optical point of view. At the same time, the hearing aid should be operable over as long a period as possible and should have the largest possible range of functions. However, these requirements are not readily compatible. So requires a long Running time and a large range of functions a powerful power supply, which requires a correspondingly large amount of space and weighs a lot.
  • an acoustic device is described with a neck loop, with two acoustic drivers, which are acoustically coupled to a housing of the neck loop and arranged at opposite ends of the housing.
  • a hearing system and an accessory for such a hearing system should be specified.
  • the hearing aid should be as light and compact as possible and at the same time be operable with as large a range of functions as possible and adequately supplied with energy.
  • the object is achieved by a hearing system with the Merkma- len according to claim 1 and by an additional device with the features of claim 28.
  • Advantageous embodiments, developments and variants are the subject of the dependent claims. The comments regarding the hearing system also apply mutatis mutandis to the attachment and vice versa.
  • the hearing system has a hearing aid and an attachment. Overall, the hearing system thus has two parts.
  • the hearing aid is used in particular to supply a hearing-impaired user.
  • the hearing device is designed to pick up sound signals from the environment and output them to a user of the hearing device.
  • the hearing device has at least one microphone and at least one earpiece.
  • the microphone picks up sound signals from the environment and converts these into an electrical input signal. From the electrical input signal, an electrical output signal is generated by the Input signal is modified in a signal processing.
  • the signal processing is either a part of the hearing aid or a part of the accessory or a part of a third device.
  • the microphone and the handset and possibly also the signal processing are housed in particular in a housing of the hearing aid.
  • the housing is designed such that it can be worn by the user on the head and in the vicinity of the ear, for example in the ear, on the ear or behind the ear.
  • the hearing aid is designed as a BTE hearing aid, ITO hearing aid or RIC hearing aid.
  • the hearing aid is designed for wired data exchange.
  • Wired is understood in particular that the data exchange takes place by means of a line and thus by means of an electrically conductive material.
  • the line connects the hearing aid and the auxiliary device in a connected state for the purpose of data exchange.
  • the wired data interfaces are separable from each other, i. the hearing aid and the accessory are detachably connectable by means of the line.
  • the data exchange is either mono-directional or bidirectional. It is essential that a wireless interface, that is to say an interface for wireless signal transmission, can be dispensed with in the hearing device and that, at least temporarily, a wired data transmission is used for data transmission. As a result, space in the hearing device is saved on the one hand. However, it is particularly advantageous that, on the other hand, energy is also saved during operation of the hearing device. This is based on the knowledge that a wireless interface requires a lot of energy.
  • the auxiliary device has a wireless interface for data exchange with the external data source.
  • the external data source also referred to as an external device, is in particular, for example, a multimedia device, a television, a telephone, a smartphone or a computer.
  • the data are in particular audio signals; in addition or alternatively, the data are control data for the hearing device.
  • the hearing aid and the auxiliary device each have a wired data interface. place, via which the hearing aid is connectable to the additional device and expediently also connected during operation, for wired data exchange with each other.
  • a core idea of the invention thus consists in particular in relocating the functionality of the wireless data exchange from the hearing device to an additional device and thereby making the hearing device more compact by dispensing with a wireless interface in order to make the hearing device at least more energy-efficient. provide a less energy-intensive way to exchange data compared to a wireless interface.
  • the additional device is accordingly designed for connection and communication with external data sources. Depending on the concrete design, this functionality is completely or temporarily absent for the hearing aid, but rather it communicates with external data sources accordingly via the additional device.
  • the auxiliary device With regard to a data exchange between the environment, especially an external data source, and the hearing aid, the auxiliary device is thus, so to speak, interposed and mediated between the hearing aid and the external data source.
  • a much more energy efficient wired data interface is used for data exchange between the attachment and the hearing aid .
  • the hearing device is designed only for wired data exchange and is free from a wireless interface, so that the above-mentioned advantages are particularly pronounced in this regard.
  • the hearing device has a wireless interface.
  • the hearing aid is designed to be binaural and has for this purpose two individual devices.
  • each of the individual devices has a wireless interface for exchanging data between the two individual devices.
  • the wireless interface only serves for data exchange between the two individual devices and otherwise not for data exchange with any other devices.
  • the said wireless interfaces of the hearing device are preferably also the only wireless interfaces of the hearing device.
  • the hearing device has an inductive wireless interface for data transmission by means of inductive coupling.
  • the wireless interface is thus designed such that a data exchange takes place by means of inductive coupling.
  • the wireless interface has an induction coil, which cooperates correspondingly with a corresponding induction coil of a device coupled for data exchange.
  • the hearing device is of binaural design and each individual device has a corresponding wireless interface, which then serves in particular exclusively for data exchange between the two individual devices of the binaural hearing device.
  • the hearing aid has one or more wireless interfaces, all of which are designed as near-field wireless interfaces.
  • the hearing aid has exclusively near-field wireless interfaces.
  • a near-field wireless interface is understood to mean, in particular, a wireless interface with a range of at most 1 m, preferably at most 20 cm.
  • Such near-field wireless interfaces are particularly energy-poor and, in particular, also suitable for data exchange between two individual devices of a binaural hearing device.
  • the hearing aid is of binaural design and has for this purpose two individual devices which each have at least one microphone and at least one earpiece and are thereby adapted to pick up sound signals from the environment and output them to a user of the hearing device.
  • Each of the two individual devices accordingly has a housing in which at least one microphone is arranged in each case.
  • single device also has a handset, which is arranged in the housing or connected thereto.
  • the two individual devices are worn on the sides of the head, so that each individual device is assigned to one ear.
  • a monoaural hearing aid with only a single device is suitable.
  • the statements relating to a monaural hearing device are analogously applicable to a binaural hearing aid and vice versa.
  • the hearing aid is operable in a single operation and without the additional device.
  • the hearing aid expediently an independent power supply, in particular a battery.
  • the hearing device has a limited scope of functions, since now no more wireless interface is available and communication, ie a data exchange with external data sources is no longer possible.
  • the hearing device has at least one basic function which can be executed independently of a connection to the additional device.
  • the basic function is an output of amplified or at least modified sound signals from the environment in such a way that a hearing damage of the user is compensated.
  • the basic function is therefore preferably the care of a hearing-impaired user.
  • the accessory is designed as a neck band, which is portable by the user in the neck and around the neck.
  • the neckband is formed in a suitable embodiment such that it rests on the user's collarbone when worn.
  • the accessory has a higher weight than the hearing aid and can then wear much more comfortable in the neck than if the corresponding components and functions in the hearing aid and implemented on, should be worn in or behind the ear.
  • the attachment front heavier than the rear, ie in particular that the weight of the neck band predominantly determined by its front. This prevents the accessory from unintentionally rotating around the user's neck when worn.
  • Another advantage is especially in the only short distance to the hearing aid in the region of the ear.
  • the wired data interface therefore only needs to bridge the distance from the shoulder, neck or neck to the ear, making it compact and unobtrusive.
  • a neckband can advantageously inconspicuously wear under clothing.
  • the neckband and generally the additional device is designed like a jewel in order to achieve a visually appealing appearance.
  • the attachment is designed as a neck band generally U-shaped and then around the neck can be applied.
  • the neck band then has two legs, which are respectively guided over the shoulders forward and toward the chest.
  • the two legs are closable on the front side, so that the additional device can then be guided completely around the neck in the manner of a chain or a collar.
  • configurations of the neckband as a chain or a collar are also advantageous.
  • the accessory in general, and the neckband in particular, have a front and a back, the back being positioned at the neck when worn and the front facing the front and the user's chest.
  • the attachment is generally stiff, i. with a stiff case.
  • only the front is stiff and the back is flexible.
  • the front side is flexible.
  • a flexible front or back is suitably made of a plastic or a stolen-like fabric. Regardless of whether the back is stiff or flexible, this is interchangeable in an expedient embodiment and preferably from a set with backs in several sizes selectable so that a user can select an individually matching back so that the attachment then optimally to the specific Anatomy of the user is set.
  • the wired data interface of the additional device has at least one connection which communicates with the hearing device is connectable.
  • the connection can be connected to the single device and is also connected to the single device in a connected state.
  • the hearing aid has a correspondingly complementary connection.
  • the hearing device is preferably dispensed with a line and such mounted in a suitable embodiment as part of the connection to the attachment, so that the connection is particularly flexible to the hearing aid feasible.
  • connection is, for example, a plug or a socket, which can be connected correspondingly to a socket or a plug on the hearing device.
  • connection for magnetic connection to the hearing device is formed.
  • the connection is thus formed magnetically, so that the connection is held in the connected state, in particular solely by magnetic force on the hearing aid.
  • Any other mechanical connection of the hearing aid to the auxiliary device is dispensed with in particular.
  • the hearing aid has a battery compartment and the connection is designed as a cover for the battery compartment.
  • connection is designed as a bayonet connection, as a screw connection or as an audio shoe.
  • Such connections provide a particularly secure connection, which is particularly important in the case of head movements of the user of importance, since there is a potential risk that the connection between the accessory and hearing aid is accidentally solved.
  • the additional device has a signal processing, which is designed to modify the sound signals which are recorded by the microphone and forward for output to the listener. The input signals which are generated by the microphone of the hearing aid are thus transmitted via the wired data interface to the signal processing of the additional device, processed there, in particular modified or amplified and then in the reverse direction via the wired data interface to the listener of the hearing aid Issue sent. This results in particular in the advantage that the hearing aid is relieved.
  • the functionality of the hearing device in particular the basic function, is advantageously transferred in whole or in part to the auxiliary device, so that the hearing aid saves energy accordingly.
  • signal processing is completely dispensed with in the hearing device.
  • the hearing device has its own signal processing, which is then deactivated in the connected state, in particular, and whose functionality is then taken over by the signal processing of the additional device, is particularly preferred.
  • the additional device is designed for beamforming the hearing device or for contralateral redirecting of sound signals and, for this purpose, has in particular a microphone, which is preferably integrated into the additional device.
  • beamforming is meant, in particular, that directional hearing is realized, that is, that sound sources are amplified from a certain direction relative to other directions.
  • a beamformer is used, which combines the input signals of several different microphones, in particular of the same individual device, in an appropriate manner to form an output signal.
  • the Beamformer is then correspondingly part of the accessory, so again, the energy consumption of the hearing aid itself is reduced.
  • the hearing aid itself is then not designed for beamforming, a variant in which the hearing aid is however also designed for beamforming, but is also suitable.
  • the hearing aid In the contralateral redirection of sound signals, in short also as CROS (Contralateral Routing Of Signal), the hearing aid is designed such that the listener and the microphone will be worn at different locations and thus the sound signals are forwarded at one ear to the other ear. This is especially beneficial if one of the ears is completely deaf. The sound signals on this deaf ear are then forwarded to the other, comparatively healthier ear.
  • the attachment accordingly has a CROS unit.
  • the hearing aid either has no CROS unit or, in a variant, has its own additional CROS unit, which is then preferably used only in the non-connected state, ie if the hearing aid is not connected to the additional device.
  • the hearing aid has a battery and the auxiliary device is designed to charge the battery of the hearing aid in a charging operation.
  • the charging operation is generally carried out in particular in a connected state.
  • the wired data interface also serves as a charging interface for transmitting a charging current to the hearing aid.
  • a non-contact charging is suitable, for example by means of induction.
  • the hearing system is also worn by the user when loading.
  • An essential advantage of loading the hearing device via the additional device is in particular that it is possible to dispense with parts that are necessary for charging the hearing device and that it is preferably also dispensed with, so that the hearing device itself is particularly compact.
  • the auxiliary device itself has a corresponding charging connection for the purpose of supplying power to the hearing device and preferably also for charging a power source of the auxiliary device.
  • a charging connection is, for example, a USB connection or a non-contact charging connection as mentioned above, eg an inductive charging connection for charging via a charging station of suitable design.
  • the auxiliary device has an energy source, in particular a battery, and the hearing device is connectable to the energy supply by means of the energy source with the additional device.
  • the hearing aid is in this case battery-free, so has no own power supply, but is completely powered by the attachment.
  • the hearing aid has its own energy supply and is then additionally or alternatively supplied with energy by the auxiliary device, particularly in the connected state.
  • the attachment is designed as a charger for the hearing aid.
  • an energy source of the hearing device can advantageously be charged in a corresponding charging operation without the hearing device having to be connected to a special charger for this purpose.
  • a corresponding charging functionality is provided by the additional device.
  • the auxiliary device is designed such that in a loading operation for the hearing aid just that hearing aid via the wired (2009)stel- len by means of the auxiliary device is loaded.
  • the wired data interfaces thus have an advantageous dual functionality and serve on the one hand for data exchange, on the other hand also for charging the hearing device during charging operation.
  • the loading and the data exchange takes place either by means of the same conductor, by means of different conductors or both.
  • a separate charging connection on the hearing aid can then advantageously be dispensed with and is preferably also dispensed with.
  • the auxiliary device has a loading bay, into which the hearing device can be inserted, for loading the hearing device by means of the auxiliary device in a charging operation.
  • the loading bay is preferably a recess or bulge in the additional device, which is particularly adapted to a housing shape of the hearing device and in which the hearing aid can be used for loading.
  • the cargo bay expediently has a charging port, e.g. a coil, for inductive charging, or a connector for connecting to a complementary connector of the hearing aid.
  • the wireless interface is a Bluetooth interface or a WLAN interface.
  • the Bluetooth interface is for example a regular or a low energy (so-called low-energy) Bluetooth interface.
  • Such a wireless interface is particularly flexible, so that the additional device can be connected to a large number of different external data sources.
  • the additional device has one or more of the following components: a volume control for the hearing aid, a particular manually operable switch for initialization of a coupling with the external data source, an on / off switch, in particular for the entire hearing system or only for the attachment, a display element, in particular an LED, to indicate whether a coupling with an external data source is present or not.
  • the auxiliary device has at least one additional sensor, which is selected from a group of additional sensors, comprising: a microphone, a temperature sensor, a pulse sensor, an acceleration sensor.
  • additional sensors comprising: a microphone, a temperature sensor, a pulse sensor, an acceleration sensor.
  • Other sensors are conceivable and also suitable.
  • the at least one additional sensor is advantageously used for enriching those data which are transmitted by the additional device or to the additional device or which are transmitted between the additional device and the external data source or between the additional device and the hearing device.
  • the auxiliary device has at least one microphone and the additional device and the hearing device are designed such that in a headset operation sound signals from the environment are recorded by means of the microphone of the auxiliary device and output via the earpiece of the hearing device.
  • the additional device and the hearing device thus form a headset, with a microphone in the auxiliary device and a receiver in the hearing device.
  • the auxiliary device has a memory and is designed to store sound signals which are recorded by the microphone within a time window in the memory and to reproduce them at a later time.
  • the additional device is thus designed to store time-limited sections of the input signal in the memory and in particular to output at the request of the user.
  • the attachment therefore has a recording function up.
  • the recorded sound signals from the memory can also be transmitted to an external data source via the wireless interface.
  • the time window has, for example, a length of at least 1 s up to 1 h, more preferably a length in the range of 1 s to 1 min. But also other lengths are suitable.
  • the auxiliary device has a translation unit and is designed, in the case of a sound signal containing a voice component in a first language, to translate the voice component from the first language into another second language and output it to the user.
  • the additional device thus has a translation function, so that incomprehensible languages, in particular, are automatically translated to the user and thus become understandable.
  • the auxiliary device has a speech detection unit, which is designed on the one hand to detect the presence of a speech component and, on the other hand, to recognize the language of the speech component.
  • the additional device is designed to transmit data of a digital assistant, which is provided by the external data source, to the hearing device.
  • a digital assistant is understood in particular to be a voice control which recognizes voice commands of the user and, depending on the voice command, can execute and also execute various functions or actions.
  • the digital assistant is in particular designed for speech recognition, for speech analysis, for searching for information or for processing simple tasks or a combination thereof.
  • the digital assistant forms an interface between the user and another device, in particular the external data source.
  • the digital assistant outputs data intended for the user, in particular in the form of speech. This data, ie an output of the digital assistant and especially a voice output of the digital assistant, is then transmitted to the hearing aid via the additional device for output to the user.
  • the external data source is special here, but also generally preferably the cloud.
  • the attachment is designed to play a soothing music again.
  • the attachment generally has preferably a music playback function.
  • the music is preferably obtained via the wireless interface from an external data source or alternatively or additionally from a memory of the auxiliary device.
  • the soothing music is, for example, yoga music or a recording of the sounds of a river, a forest or a beach.
  • the object is also achieved by a method for operating a hearing system as described above and by the respective use of a hearing device or additional device in a hearing system as described above.
  • Advantageous embodiments will be apparent from the above.
  • FIG. 1 shows a single device of a hearing aid
  • Fig. 2 shows a hearing system with two individual devices as in Fig. 1 and with a
  • a hearing aid 2 is shown, which is exemplified as a BTE hearing aid. Alternatively, other types of hearing aid 2 are suitable.
  • the hearing device 2 is used to supply a hearing-impaired user N.
  • the hearing device 2 is designed to pick up sound signals from the surroundings and to output them to the user N.
  • the hearing device 2 comprises at least one, in FIG. 1, two microphones 4 and a receiver 6.
  • the microphones 4 receive sound signals from the environment during operation of the hearing device 2 and convert these into an electrical input signal E, from which a signal processing tion 8 then generates an electrical output signal A, which is then output via the handset 6.
  • the signal processing 8 is a part of the hearing device 2.
  • the signal processing which provides the said functionality of the hearing aid 2, no part of the hearing aid, but with respect to this externally arranged.
  • the microphones 4 and the signal processing 8 are accommodated in a housing 10 of the hearing device 2.
  • a battery 12 is accommodated in the housing 10 for the power supply of the hearing device 2.
  • the battery 12 is seated in a battery compartment 14, which is closed by a cover 16 of the housing 10.
  • the energy supply can be done alternatively or additionally by other means.
  • the handset 6 is connected via an unspecified supply line to the housing 10.
  • the housing 10 is formed so that it can be worn by the user N as shown in Fig. 2 at the head and in the vicinity of the ear.
  • a single device 18 is shown, in the arrangement in FIG. 2, on the other hand, a binaural hearing device 2 with two individual devices 18 is shown, which are each supported on different sides of the head. Accordingly, the hearing device 2 in FIG. 2 also has two receivers 6 and at least one microphone 4 per individual device 18.
  • the hearing device 2 is designed only for wired data exchange and free of a wireless interface. In order nevertheless to be able to receive data, ie signals, from an external data source 20 and to be able to transfer them to the hearing device 2, the hearing device 2 is combined together with an additional device 22 in a hearing system 24. Such is illustrated in an exemplary embodiment in FIG.
  • the auxiliary device 16 has a wireless interface 26, which can be coupled to a corresponding wireless interface 28 of the external data source 20 in order to realize a wireless connection.
  • the wireless interfaces 26, 28 are eg Bluetooth interfaces.
  • the external data source 20 is also referred to as an external device and is merely a smart phone in FIG. 2.
  • an external data source 20 are a multiplicity of other devices, in particular multimedia devices, eg a television, a telephone or a computer.
  • the data which are transmitted by means of the wireless interfaces 26, 28 between the auxiliary device 22 and the external data source 20 are, for example, audio signals or alternatively or additionally control data for the hearing device 2.
  • the hearing aid 2 and the auxiliary device 22 each have a wired data interface 30, 32, via which the hearing device 2 can be connected to the auxiliary device 22 for wired data exchange and is also connected during operation.
  • the functionality of the wireless data exchange is thus decoupled from the hearing device 2 and transmitted to the additional device 22, by which the greatest possible functionality and the highest possible connectivity of the hearing device 2 are realized despite the compact nature of the hearing device 2.
  • the hearing device 2 communicates with external data sources 20 exclusively via the additional device 22, which accordingly mediates between an external data source 20 and the hearing device 2.
  • the wired data interface 30 of the auxiliary device 22 has at least one here two connections 34, which are each connectable to the hearing aid 2.
  • the hearing device has a correspondingly complementary connection, which here corresponds to the wired data interface 32, but is separately formed in a variant which is not shown.
  • a line is omitted on the hearing aid 2 and such is rather attached as part of the terminals 34 on the auxiliary device 22.
  • the connections 34 on the additional device 22 and the connections on the hearing device 2 are designed, for example, as a plug connection with plug and socket, as a bayonet connection, as a screw connection or as an audio shoe.
  • the connections 34 are designed for the magnetic connection to the hearing device 2.
  • the cover 16 on the battery compartment 14 serves as a connection to the hearing aid 2.
  • the attachment 22 is designed as a neck band, which is worn by the user N in the neck and around the neck.
  • the attachment 22 is U-shaped and placed around the neck around the neck, so that then two legs 36 of the attachment 22 are correspondingly guided over the shoulders to the front and in the direction of the breast.
  • the two legs 36 are closed on the front side.
  • the hearing device 2 is also in a single operation due to the independent energy supply by the battery 12, and ne the attachment 22 operable.
  • the hearing aid 2 since the hearing aid 2 lacks the possibility of a wireless transmission, the hearing aid 2 in individual operation may have a limited range of functions. In return, the hearing aid is very compact.
  • at least one basic function without the additional device 22 is executable, namely the output of amplified or at least modified sound signals from the environment such that a hearing damage of the user is compensated. This is possible in the present case above all by the own signal processing 8 of the hearing device 2.
  • the hearing aid 2 has no battery 12 or no signal processing 8 or neither the one nor the other and the corresponding functionality, ie energy supply or signal processing solely via the attachment 22 relates.
  • the auxiliary device 22 generally has a signal processing 38, which is also presently designed to modify the sound signals picked up by the microphones 4 and to forward them to the listeners 6 for output.
  • the input signals E which originate from the A respective microphone 4 of the hearing device 2 are generated, are thus transmitted via the wired data interface 30, 32 to the signal processing 38 of the auxiliary device 22, processed there, eg modified or amplified and then sent in the reverse direction via the wired data interface 30, 32 to the respective handset 6 of the hearing 2 for output.
  • the basic function of the hearing device 2 is thus transferred in whole or in part to the additional device 22, so that the hearing device 2 saves energy accordingly.
  • signal processing 8 is completely dispensed with in the hearing device 2.
  • the auxiliary device 22 is designed for beamforming for the hearing aid 2 and for kontralateralen redirecting Schallsig signals.
  • the auxiliary device 22 has an unspecified beamformer, which is part of the signal processing 38.
  • the attachment 22 has no closer designated CROS unit, which in the present case is also part of the signal processing 38.
  • the wired data interface 30, 32 simultaneously serves as a charging interface for transmitting a charging current to the hearing device 2, more precisely to its battery 12.
  • non-contact charging is possible in a variant, not shown, for example by means of induction.
  • the auxiliary device 22 has a corresponding charging port 42 for supplying power to the hearing aid and preferably also for charging a power source 40 of the auxiliary device 22 itself, for example for supplying energy. already mentioned a USB port or a non-contact charging port.
  • the additional device 22 further components, namely a volume control for the hearing aid 2, a switch for initializing a coupling with the external data source 20, an on / off switch for the entire hearing system 24 or only for the additional advises 22, a display element, in particular an LED, to indicate whether a coupling with an external data source 20 is present or not.
  • the above-mentioned components are not shown explicitly in FIG. 2 for the sake of clarity and are arranged, for example, in or on the legs 36.
  • the auxiliary device 22 has a memory as part of the signal processing 38 and is designed to store sound signals, which are picked up by the hearing device 2, in the memory within a time window and to reproduce them at a later time.
  • the attachment 22 thus has a recording function.
  • a translation unit is integrated in the signal processing 38, which translates the speech component from the first language into another, second language and outputs it via the hearing device 2 to the user N in the case of a sound signal containing a speech component in a first language ,
  • the attachment 22 thus has a translation function.
  • the shown auxiliary device 22 is adapted to play a calming music repeatedly, generally having a music reproduction function, which in the present case is also realized as a part of the signal processing 38 is. All or some of the aforementioned functions are not accommodated in the signal processing 38 in a variant, but separately thereto.

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  • Engineering & Computer Science (AREA)
  • Computer Networks & Wireless Communication (AREA)
  • Health & Medical Sciences (AREA)
  • General Health & Medical Sciences (AREA)
  • Neurosurgery (AREA)
  • Otolaryngology (AREA)
  • Physics & Mathematics (AREA)
  • Acoustics & Sound (AREA)
  • Signal Processing (AREA)
  • Circuit For Audible Band Transducer (AREA)

Abstract

L'invention concerne un système auditif (24), lequel comporte un appareil acoustique (2), et un appareil auxiliaire (22), l'appareil acoustique (2) servant à recevoir des signaux sonores de l'environnement et à les transmettre à un utilisateur (N) de l'appareil acoustique (2), et comportant à cet effet au moins un microphone (4) ainsi qu'au moins un écouteur (6), l'appareil acoustique (2) servant à l'échange de données filaire, l'appareil auxiliaire (22) comportant une interface sans fil (26) pour l'échange de données avec une source de données externe (20), l'appareil acoustique (2) et l'appareil auxiliaire (22) comportant chacun une interface de données filaire (30, 32) par le biais de laquelle l'appareil acoustique (2) peut être connecté à l'appareil auxiliaire (22) pour l'échange de données filaire l'un avec l'autre. Il est par conséquent possible de réaliser l'appareil acoustique (2) de manière particulièrement compacte et de le faire fonctionner de manière particulièrement économe en énergie. L'invention concerne en outre un appareil auxiliaire (22) correspondant.
PCT/EP2019/058323 2018-04-03 2019-04-02 Système auditif et appareil auxiliaire pour un tel système Ceased WO2019193017A1 (fr)

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DE102018204950.5 2018-04-03
DE102018204950.5A DE102018204950A1 (de) 2018-04-03 2018-04-03 Hörsystem sowie Zusatzgerät für ein solches

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Cited By (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20240242704A1 (en) * 2023-01-17 2024-07-18 Sonova Ag Systems and Methods for Optimizing Voice Notifications Provided by Way of a Hearing Device

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EP0814634A1 (fr) 1996-06-21 1997-12-29 Siemens Audiologische Technik GmbH Prothèse acoustique programmable et procédé pour déterminer une série de paramètres optimisés dans une prothèse acoustique
DE102005006404B3 (de) * 2005-02-11 2006-08-17 Siemens Audiologische Technik Gmbh Modulares Hörgerätesystem
WO2010081915A2 (fr) 2010-04-23 2010-07-22 Phonak Ag Dispositif de programmation d'un dispositif auditif et d'alimentation en énergie d'un dispositif auditif
US20130101128A1 (en) 2011-10-14 2013-04-25 Oticon A/S Automatic real-time hearing aid fitting based on auditory evoked potentials
US20140003636A1 (en) 2012-06-14 2014-01-02 Oticon A/S Binaural listening system with automatic mode switching
US20160021446A1 (en) 2014-07-18 2016-01-21 Bose Corporation Acoustic Device
WO2017013937A1 (fr) * 2015-07-22 2017-01-26 ソニー株式会社 Dispositif de traitement d'informations, procédé de traitement d'informations, et programme
US20170064469A1 (en) 2015-08-31 2017-03-02 Oticon A/S Hearing device
EP3179743A1 (fr) * 2015-12-08 2017-06-14 Sivantos Pte. Ltd. Appareil auditif comprenant un appareil de communication vocale
DE102016104598A1 (de) * 2016-03-14 2017-09-14 Sonova Ag Demonstrationsvorrichtung für Hörgeräte

Patent Citations (10)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
EP0814634A1 (fr) 1996-06-21 1997-12-29 Siemens Audiologische Technik GmbH Prothèse acoustique programmable et procédé pour déterminer une série de paramètres optimisés dans une prothèse acoustique
DE102005006404B3 (de) * 2005-02-11 2006-08-17 Siemens Audiologische Technik Gmbh Modulares Hörgerätesystem
WO2010081915A2 (fr) 2010-04-23 2010-07-22 Phonak Ag Dispositif de programmation d'un dispositif auditif et d'alimentation en énergie d'un dispositif auditif
US20130101128A1 (en) 2011-10-14 2013-04-25 Oticon A/S Automatic real-time hearing aid fitting based on auditory evoked potentials
US20140003636A1 (en) 2012-06-14 2014-01-02 Oticon A/S Binaural listening system with automatic mode switching
US20160021446A1 (en) 2014-07-18 2016-01-21 Bose Corporation Acoustic Device
WO2017013937A1 (fr) * 2015-07-22 2017-01-26 ソニー株式会社 Dispositif de traitement d'informations, procédé de traitement d'informations, et programme
US20170064469A1 (en) 2015-08-31 2017-03-02 Oticon A/S Hearing device
EP3179743A1 (fr) * 2015-12-08 2017-06-14 Sivantos Pte. Ltd. Appareil auditif comprenant un appareil de communication vocale
DE102016104598A1 (de) * 2016-03-14 2017-09-14 Sonova Ag Demonstrationsvorrichtung für Hörgeräte

Cited By (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20240242704A1 (en) * 2023-01-17 2024-07-18 Sonova Ag Systems and Methods for Optimizing Voice Notifications Provided by Way of a Hearing Device

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