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EP2047713A1 - Procede de transmission de donnees sans fil entre une audioprothese et un appareil externe - Google Patents

Procede de transmission de donnees sans fil entre une audioprothese et un appareil externe

Info

Publication number
EP2047713A1
EP2047713A1 EP07787897A EP07787897A EP2047713A1 EP 2047713 A1 EP2047713 A1 EP 2047713A1 EP 07787897 A EP07787897 A EP 07787897A EP 07787897 A EP07787897 A EP 07787897A EP 2047713 A1 EP2047713 A1 EP 2047713A1
Authority
EP
European Patent Office
Prior art keywords
hearing aid
mode
external device
programming
data
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Withdrawn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
EP07787897A
Other languages
German (de)
English (en)
Inventor
Georg Gottschalk
Gottfried Rückerl
Gunter Sauer
Ulrich SCHÄTZLE
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 GmbH
Original Assignee
Siemens Audioligische Technik GmbH
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by Siemens Audioligische Technik GmbH filed Critical Siemens Audioligische Technik GmbH
Publication of EP2047713A1 publication Critical patent/EP2047713A1/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Withdrawn legal-status Critical Current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
    • H04R25/55—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
    • 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
    • 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
    • H04R25/70—Adaptation of deaf aid to hearing loss, e.g. initial electronic fitting

Definitions

  • the invention relates to a method for transmitting data via a wireless connection between a hearing aid and an external programming device.
  • the hearing device In addition to a reception mode, the hearing device also has a standby mode in which the energy consumption of the hearing device is significantly reduced.
  • modern hearing aids In addition to an interface for a wired connection to an external control device, modern hearing aids also have a transmitting / receiving device in order to wirelessly connect the hearing device to the external control device.
  • Radio link the hearing aid in the context of wireless programming and programming data from an external programmer receive. Furthermore, this also makes possible a wireless binaural coupling of hearing aids in which two hearing aids are coupled to one another in such a way that they function as an integrated unit and functions such as volume or program selection are synchronized between the two hearing aids.
  • a hearing aid with an integrated receiving device for wireless reception with increased power consumption can be expected. Since the hearing aid usually has only its internal power supply available, the wireless data transmission inevitably leads to a reduced operating time and thus more frequent battery replacement. For this reason, it is desirable to have the additional caused by the receiving device
  • the receiving device Since in known systems designed for wireless binaural coupling, the receiving device is permanent is activated, but which leads to a relatively high power consumption of the hearing aid, conventional hearing aids are currently still programmed via a cable connection.
  • the object of the invention is, starting from this prior art, to provide a method for wireless data transmission between a hearing device and another device, by means of which the energy consumption of the hearing device during operation can be reduced. This object is achieved by a method having the features of claim 1. Further advantageous embodiments of the invention are specified in the subordinate claims.
  • a method for wireless data transmission between a hearing device and an external device in which the hearing device receives data by means of an internal receiving device, which are transmitted by the external device via a wireless connection. It is envisaged that the hearing device will switch to a reception mode as soon as data is sent from the external device via the wireless connection, the reception device being permanently switched on in the reception mode for the reception of data. Furthermore, the hearing device switches to a standby mode when no data is transmitted from the external device via the wireless connection. In this standby mode, the receiving device is alternately turned on and off to detect an incipient data transfer of the external device. Since the receiving device is operated only temporarily in the standby mode, the power consumption of the hearing aid can be significantly reduced by the use of the standby mode.
  • the hearing device changes to the receive mode as soon as the receiving device detects an incipient data transmission of the external device via the wireless connection during a switch-on phase of the standby mode. Since the hearing aid in standby mode, so to speak, again and again in the transmission channel snoops into it, it can detect a beginning data transmission relatively quickly and switch without much delay in the receiving mode.
  • a further advantageous embodiment of the invention provides that the hearing device changes to the standby mode as soon as the receiving device registers no data transmission of the external device via the wireless connection in the receive mode for a predetermined time. This measure can ensure that the hearing aid does not remain in receive mode for an unnecessarily long time. This allows the hearing aid to save more energy.
  • a further advantageous embodiment of the invention provides that the receiving device is switched on and off periodically in the standby mode, wherein the duration of the switch-on and switch-off is selected so that an incipient data transmission of the external device can be detected.
  • the duration of the switch-on and switch-off phases determines the duty cycle with which the hearing device scans the transmission channel for the purpose of monitoring. By determining the duration of this time, the duty cycle and thus the energy savings can be adapted to the respective requirements.
  • the external device sends an activation signal to the hearing aid via the wireless connection in order to indicate to the hearing aid the beginning of a new data transmission.
  • an actual data transmission upstream activation signal can be ensured that the hearing aid is already activated when the actual data transfer begins. Since the hearing aid in this case can receive all data and no data must be repeated, this measure leads to an increased data transfer rate.
  • a further advantageous embodiment of the invention provides that the duration of the activation signal is selected such that it exceeds the duration of a switch-off phase of the receiving device 11 in the standby mode of the hearing device. This ensures that the activation signal at least partially coincides in time with a switch-on. This has the advantage that this increases the probability of the activation signal being recognized by the hearing device.
  • the activation signal comprises an activation message and a redundant preamble.
  • the duration of the redundant preamble is selected such that the total duration of the activation signal exceeds the duration of a switch-off phase of the receiving device in the standby mode of the hearing device. This ensures that the hearing device can receive at least a part of the activation signal in a switch-on phase. Since the preamble is sent before the actual activation message, that can
  • Hearing aid suppress the following off phases until it has received the actual activation message.
  • the activation message in the activation signal can be repeated until the total duration of the activation signal exceeds the duration of the switch-off phase of the receiving device in the standby mode of the hearing aid. This alternative also increases the likelihood that the hearing aid will receive the actual activation message correctly.
  • a particularly advantageous embodiment of the invention provides that the external device uses a specific modulation method to indicate the beginning of a new data transmission.
  • the hearing aid switches to the receive mode as soon as it detects that the external device transmits its data signals by means of the specific modulation method.
  • the advantage here is that a specific modulation method can be detected much faster than a corresponding activation message that may need to be fully received. Also, the risk of accidental change to the receive mode can be reduced if the special modulation method is used only for data transmission. It is advantageous if the hearing device changes into the reception mode as soon as the hearing device detects that the external device transmits data signals by means of a specific phase or frequency modulation method.
  • the data transmission takes place in the context of a wireless hearing device programming, wherein the hearing aid in a special programming mode programming data wirelessly from a than
  • Controller device receiving external device. It is provided that the hearing aid changes to the programming mode as soon as it receives a special command from the control unit via the wireless connection. Programming data that the controller transmits to the hearing aid via the wireless connection outside the programming mode is ignored by the hearing aid. It is provided that the hearing aid in the programming mode prohibits the change to the standby mode. This has the advantage that the connection does not always have to be reactivated, which would lead to delays and thus to lower data rates. Furthermore, this also ensures that the hearing aid receives all programming data correctly. However, it is also advantageous if, in the programming mode, the hearing device automatically changes to the reception mode or the standby mode after a predetermined time has elapsed.
  • the hearing device can prevent the automatic change from the programming mode to the reception mode or the standby mode if a renewed programming access takes place via the wireless connection within the predetermined time. This is advantageous because it prevents unnecessary interruptions in programming.
  • the hearing device in the programming mode the hearing device resets the time for the automatic operating mode change when a renewed programming access takes place or when the hearing device receives an audio data stream. Even with this measure can be prevented that the programming of the hearing aid is interrupted unnecessarily.
  • Fig. 1 shows schematically a hearing aid and an external device, which are connected to each other via a wireless transmission path.
  • FIG. 2 schematically shows the time waveform during the change between the different operating modes.
  • FIG. 1 shows a typical hearing aid 10 which, in addition to other circuits 12, also has an interface 11, 11 1 for wireless data transmission.
  • This interface 11, 11 has a receiving device 11 and an antenna 111 connected to the receiving device 11.
  • the receiving device 11 is preferably used as a transmitting
  • the hearing aid 10 is designed for both the wireless reception as well as for the wireless transmission of data.
  • the optional separate transmission circuit is not shown here in detail for reasons of clarity. If bidirectional communication is supported, works the antenna 111 then preferably in the transmitting and receiving directions.
  • the hearing aid 10 shown in FIG. 1 is connected to an external device 20 via a wireless transmission link 30 in order to receive data from this device 20.
  • the external device 20 also has a corresponding antenna 211 and a corresponding transmitting and receiving device 21.
  • an external device 20 is eg another hearing aid in question, which is binaurally coupled to the first hearing aid 10 via the wireless connection.
  • the external device 20 can also be used as a control or
  • the hearing aid 10 also has further circuits 12, such as e.g. Control circuits and signal processing circuits. Since these circuits for the understanding of the invention have no relevance, they are shown schematically in the figure 1.
  • the external device 20 also has a transmission
  • Receiving device 21 and an antenna 211 typically further circuit parts 22, which are also shown schematically summarized in Figure 1.
  • the hearing aid 10 is used during operation usually only its internal battery as a power supply. Due to its small dimensions, the housing of the hearing aid 10 can only accommodate a relatively small battery. Due to the relatively small battery, the operating time of the hearing aid is already severely restricted during normal operation. Due to the wireless data reception, the power supply of the hearing aid 10 is additionally heavily loaded. With the concept according to the invention, a significant power saving in the hearing aid 10 is to be achieved.
  • the first slide gram a) shows the time course of the on and off times of the receiving device 11 of the hearing aid 10 when switching from the reception mode to the standby mode.
  • the on and off times are represented by a binary signal, with the value "high” for a switch-on time and the value "low” for a switch-off time.
  • the receiving device 11 is constantly turned on in the receiving mode to receive the data sent from the external device 20 via the wireless link without delay.
  • the time profile of the data received from the hearing aid 10 of the external device 20 is shown in the associated diagram b), wherein the hearing aid 10 receives data only via the wireless connection at the beginning.
  • the hearing aid 10 is to switch to the standby mode when it no longer receives data from the external device 20. As shown in the diagram a) of Figure 2, this operating mode change takes place at time t2.
  • the hearing aid 10 has received data from the external device 20 up to a previous time ti. After a predetermined period of time .DELTA.t, in which it has received no more data, it now automatically switches to standby mode.
  • the receiving device 11 is preferably switched on and off periodically. This sniffs the hearing aid 10 in this designated as sniff mode operating mode practically always back into the transmission channel to the beginning of a new
  • the duty cycle selected in standby mode in the present example ie the duration of a switch-on phase in relation to the duration of a switch-off phase, is 2/3.
  • this duty cycle can be shifted to extreme values in standby mode by shortening the switch-on times and / or extending the switch-off times.
  • the on and off times should be chosen so that an incipient data transfer of the external device 20 is detected in any case, as this can lead to undesirable delays. It therefore makes sense to include the input and output switching times and the duration of the activation signal to one another.
  • the period of time ⁇ t after which the hearing aid 10 switches to the standby mode, if it no longer receives any further data, should be selected such that short transmission pauses, which typically can occur during the communication between the hearing aid 10 and the external device 20, are not already lead to a change of operating modes. Because too frequent operating mode changes and the associated reactivation procedures of the receiving device can lead to delays in the data transmission and thus to an undesirable reduction of the data rate.
  • the hearing aid 10 should switch back to the receive mode as soon as it has registered in the standby mode an incipient data transfer.
  • a mode change is shown in the two associated diagrams c) and d) of Figure 2.
  • the hearing aid 10 in the standby mode scans the transmission channel by periodically switching its receiving device 11 on and off. Before the external device 20 sends data to the hearing device 10, it announces this to the hearing aid 10 preferably. This is preferably done with the aid of a specific activation signal, which is sent to the hearing device 10 via the wireless transmission link 30 in advance of a data transmission. This activation signal is indicated in diagram d) by a hatched data block.
  • the switch-on and switch-off phases of the receiver 11 and the activation signal must be coordinated, it being particularly necessary for the duration of the activation signal to be the duration exceeds a switch-off phase.
  • the switch-on phase must be selected to be sufficiently long so that the part of the activation signal necessary for unambiguous identification can be received during the switch-on phase.
  • the activation signal in the present example lasts more than twice as long as the turn-off time of the receiving device 11 in the standby mode.
  • the hearing aid 10 can therefore clearly detect the beginning of a data transmission by the external device 20 in a switch-on phase. Therefore, at time t3, the hearing aid 10 changes to the receiving mode to receive the actual data transmitted from the external device 20.
  • the external device 20 can in principle begin with the data transmission without waiting for the reactivation of the hearing device 10. Once the hearing aid 10 has changed to receive mode, the external device 20 re-transmits the data already sent to the hearing aid 10 to ensure that all data from the hearing aid 10 is properly received. Such multiple transmissions are also used inter alia to avoid errors in disturbed data transmissions, especially when a return channel is missing. However, there is the danger in this procedure that the hearing device 10 can not clearly identify whether the currently received data is already the actual data that it is intended to utilize, or whether these data still serve to activate the receive mode and subsequently on the actual data transfer again be sent.
  • a misinterpretation of the data by the hearing aid 10 could in principle lead to reception errors. It is therefore advantageous if the external device 20 uses a special activation signal to activate the reception mode of the hearing device 10.
  • This activation signal can contain a special activation message and, in addition, redundant parts, such as a preamble preceding the activation message. It is advantageous to use a preamble preceding the activation message, since the hearing aid 10 can already recognize when receiving such a preamble that a data transmission is imminent. Thus, it can suppress the switch-off phases in the standby mode until it has received the activation message and thus possibly also the information in which operating mode it should change. This may speed up the operating mode change under certain circumstances.
  • the length of the activation signal should exceed the duration of the switch-off phases in standby mode. This can be achieved by repeatedly repeating the activation message in the activation signal until this condition is met. Furthermore, it is also possible to extend the length of the activation signal by means of the redundant parts until it exceeds the duration of a switch-off phase.
  • the hearing aid 10 can detect the beginning of a new data transmission on the basis of the modulation method with which the external device 20 transmits its data.
  • certain phase or frequency modulation methods eg frequency shift keying (FSK) or phase shift keying (PSK) are suitable.
  • the external device 20 can always use the special modulation method only at the beginning of a new data transmission, in order to then transmit the actual data by means of a different modulation method.
  • the external device 20 may use a different modulation method for each new data transmission.
  • the programming mode is preferably an independent operating mode and not a special receive mode.
  • the programming mode should have some important features that are not necessary in regular receive mode. Unlike the regular receive mode, switching to programming mode should not be automatic to avoid unintentional programming.
  • the hearing aid 10 is first put into the programming mode via special commands of the external device 20.
  • programming of the hearing device 10 requires higher data rates than, for example, the coupling of the hearing device 10 with the external device 20, which may be designed as another hearing device or as a remote control. Therefore, it makes sense to increase the data rate in programming mode.
  • the programming mode is initiated by a command transmitted at the lower data rate of normal operation. Then the standby mode is deactivated and the programming mode started, is now working in the higher data rate.
  • the automatic mode switch to standby mode typical of regular receive mode is similar to the ones mentioned above Reasons in the programming mode is undesirable, it may be advantageous if the hearing aid 10 remains only for a preset programming time .DELTA.t P in the programming mode and automatically returns to the normal operating mode after this time. By changing to a safe operating mode, it can be ensured that no unintentional modification of the programming takes place. Furthermore, the internal power supply of the hearing aid 10 is relieved by a change to the standby mode.
  • the period of time ⁇ t P after which the hearing device 10 changes from the programming mode to a normal operating mode typically lags significantly longer than the time period ⁇ t after which the hearing aid 10 changes from the reception mode to the standby mode. This can be seen in FIG. 2 by comparing the two diagrams a), b) with the two diagrams e) and f), the representation not being true to scale.
  • the predetermined programming time ⁇ t P can also be reset and restarted in the programming mode by a successful programming access. Similarly, a received audio stream may reset this time ⁇ t P as long as the system supports the transmission of audio streams during programming.

Landscapes

  • 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)
  • Selective Calling Equipment (AREA)

Abstract

On décrit un procédé de transmission de données sans fil entre une audioprothèse (10) et un appareil externe (20), dans lequel, à l'aide d'un dispositif de réception interne (11), l'audioprothèse (10) reçoit des données qui sont émises par l'appareil externe (20) par une liaison sans fil. Quand des données sont émises par l'appareil externe (20) par la liaison sans fil, l'audioprothèse (10) se commute dans un mode de réception, le dispositif de réception (11) étant alors connecté en permanence pour la réception des données. En outre, quand aucune donnée n'est émise par l'appareil externe (20) par la liaison sans fil, l'audioprothèse (10) se commute dans un mode d'attente, le dispositif de réception (11) étant alors connecté et déconnecté alternativement pour détecter un début de transfert de données de l'appareil externe (20).
EP07787897A 2006-07-28 2007-07-25 Procede de transmission de donnees sans fil entre une audioprothese et un appareil externe Withdrawn EP2047713A1 (fr)

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
DE102006035126 2006-07-28
PCT/EP2007/057670 WO2008012327A1 (fr) 2006-07-28 2007-07-25 Procédé de transmission de données sans fil entre une audioprothèse et un appareil externe

Publications (1)

Publication Number Publication Date
EP2047713A1 true EP2047713A1 (fr) 2009-04-15

Family

ID=38512423

Family Applications (1)

Application Number Title Priority Date Filing Date
EP07787897A Withdrawn EP2047713A1 (fr) 2006-07-28 2007-07-25 Procede de transmission de donnees sans fil entre une audioprothese et un appareil externe

Country Status (3)

Country Link
US (1) US8165330B2 (fr)
EP (1) EP2047713A1 (fr)
WO (1) WO2008012327A1 (fr)

Families Citing this family (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
SG184255A1 (en) * 2010-05-21 2012-11-29 Widex As Automatic power-off of hearing aid
EP2424274B1 (fr) * 2010-08-25 2018-08-01 Nxp B.V. Dispositif de radiodiffusion, récepteur pour recevoir les données radiodiffusées et procédé pour initier la radiodiffusion
US10379573B2 (en) 2014-02-10 2019-08-13 Samsung Electronics Co., Ltd. User terminal device and displaying method thereof
EP3157270B1 (fr) * 2015-10-14 2021-03-31 Sonion Nederland B.V. Dispositif auditif doté d'un transducteur sensible aux vibrations

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JPH09331577A (ja) * 1996-06-10 1997-12-22 Hitachi Ltd 携帯電話装置および／またはその着信報知装置
US5909497A (en) * 1996-10-10 1999-06-01 Alexandrescu; Eugene Programmable hearing aid instrument and programming method thereof
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Also Published As

Publication number Publication date
WO2008012327A1 (fr) 2008-01-31
US8165330B2 (en) 2012-04-24
US20100008527A1 (en) 2010-01-14

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