EP2884772A1 - Prothèse auditive avec détermination de son positionnement dans l'oreille - Google Patents

Prothèse auditive avec détermination de son positionnement dans l'oreille Download PDF

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Publication number
EP2884772A1
EP2884772A1 EP14196099.7A EP14196099A EP2884772A1 EP 2884772 A1 EP2884772 A1 EP 2884772A1 EP 14196099 A EP14196099 A EP 14196099A EP 2884772 A1 EP2884772 A1 EP 2884772A1
Authority
EP
European Patent Office
Prior art keywords
signal
hearing aid
hearing
status signal
reference value
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Withdrawn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
EP14196099.7A
Other languages
German (de)
English (en)
Inventor
Eva Droste
Ulrich Giese
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Sivantos Pte Ltd
Original Assignee
Siemens Medical Instruments Pte Ltd
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by Siemens Medical Instruments Pte Ltd filed Critical Siemens Medical Instruments Pte Ltd
Publication of EP2884772A1 publication Critical patent/EP2884772A1/fr
Withdrawn legal-status Critical Current

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    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R25/00—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception
    • H04R25/30—Monitoring or testing of hearing aids, e.g. functioning, settings, battery power
    • 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
    • H04R25/30—Monitoring or testing of hearing aids, e.g. functioning, settings, battery power
    • H04R25/305—Self-monitoring or self-testing
    • 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
    • H04R2460/15—Determination of the acoustic seal of ear moulds or ear tips of 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
    • H04R25/558—Remote control, e.g. of amplification, frequency

Definitions

  • the present invention relates to a hearing aid system which can be arranged completely or partially in the auditory canal. Moreover, the present invention relates to a method for determining the seated state of a hearing device or a hearing device component on or in an ear.
  • a hearing aid system is understood to mean any sound-emitting device that can be worn in or on the ear or on the head, such as a hearing aid, a headset, headphones and the like. Further, the term hearing aid system also includes additional elements such as a remote control for a hearing aid.
  • the seat or seated state of a hearing aid on the ear denotes wearing or using the hearing aid.
  • a sitting state may have different qualitative gradations.
  • a hearing aid can sit well and thus provide a good hearing result or on the other hand sit worse and deliver a not so good hearing result.
  • Another scenario would be, for example, that an inexperienced hearing aid user has his hearing aid via a sales channel how the internet relates. This can not be done individually by a hearing care professional. Consequently, in the absence of experience, it is possible for the user to not place the hearing aid properly seated on the ear. Thus, he is not the optimal performance of the hearing aid available. Basically, he does not know without help whether the hearing system is sitting correctly.
  • the publication EP 1 746 860 A2 shows a method for correct Wegak a hearing aid.
  • a first measurement is carried out to determine a first reference value.
  • a test signal is emitted from the listener and then received again by the microphone.
  • the proportion of the received signal is measured and stored as a first reference.
  • another such measurement is now performed.
  • the newly determined further value is compared with the first reference value of the first measurement. The result should provide information on the correct fit of the hearing aid.
  • the disadvantage here is that the hearing aid could possibly already have been incorrectly positioned in the ear during the reference measurement. Thus, the reference value would be useless. To avoid this error, the first measurement of the reference value would require the presence of specially trained personnel, such as an experienced hearing care professional, and appropriate instruments would be used to avoid erroneous reference measurement. This significantly restricts the freedom of use of the hearing aid wearer.
  • a microphone device for receiving the measurement signal in the auditory canal is required in the abovementioned document.
  • the microphone normally used in hearing aids must primarily receive sound from outside the ear canal. It is therefore addressed with its receiving characteristic to the outside, even if it is like a completely worn in the ear canal hearing aid is placed in the ear canal.
  • the measuring methods carried out in the abovementioned document function only in the area of the ear canal enclosed by the hearing aid or the earmold on the one hand and the eardrum on the other hand. Consequently, the method of the above-mentioned document implicitly requires an additional microphone directed into the ear canal. The seat is then determined based on the loss of the signal emitted by the listener into the ear canal and then reflected there again. Consequently, an additional, directed into the ear canal microphone must be installed for this purpose.
  • the object of the invention is to provide a hearing aid and a method for determining the seat of a hearing aid, in which the hearing aid wearer is not dependent on specially trained personnel and their instruments.
  • the test signal is, for example, a sinusoidal signal or a broadband signal.
  • the status signal is, for example, depending on the purpose and embodiment, an electronic signal or an acoustic signal. This will be explained in more detail in the embodiments below.
  • the fact that the reference value of the hearing aid wearer is fixed means that he / she can not freely choose or change this value on his own. It is permanently stored in a corresponding memory unit of the signal processing device. The reference value can thus only be changed by personnel with access to this memory unit, such as e.g. a hearing care professional.
  • the receiving device takes on two tasks in the form of a hearing device microphone.
  • the sound is recorded and fed to a signal processing unit, on the other hand, the signal is picked up from the ear, which passes to the hearing aid, or earmold as hearing aid component, passing to the outside.
  • a preset, fixed reference value of a reference criterion which is preferably preset at the factory and, for example due to design or coupling.
  • the factory preset reference value preferably depends on measurements on typical head and / or ear shapes (eg the KEMAR artificial head) or a suitable mean value from measurements on different subjects.
  • the receiving device prefferably located both inside and outside the ear canal and directed inwards or outwards.
  • the reference criterion is a reference signal and the reference value is a signal value. In another embodiment, the reference criterion by an attenuation and the reference value by an attenuation value.
  • the reference criterion or the reference value may also be the height of a predetermined deviation.
  • the reference criterion and / or reference value is preferably a statistically determined variable or a signal.
  • hearing aids are best adapted to the ear at several test persons and a feedback measurement (English: open-loop-gain measurement) carried out. In other words, it is the first measurement which has already been described above. Subsequently, for example, an average value is formed from the measurements with the test persons. This mean value serves as a reference value. This reference value in turn is stored in the hearing aid and is not changeable. Further feedback measurements as described above during the hearing aid operation are performed to detect the seat and compared to the fixed non-variable reference value. Instead of forming a mean value as a reference value, a median, maximum or minimum values, difference values or ratio values can also be used for this purpose.
  • This method is particularly suitable if the hearing aid was not traditionally purchased from a hearing care professional with a fitting process, but rather from alternative sales channels such as the Internet, where no customization is possible.
  • reference criterion and reference value can also be interpreted and represented as a curve and associated values.
  • reference criterion can also be regarded as a reference signal or as a reference curve.
  • the output of the status signal is effected by means of the output device.
  • the output device is preferably a sound transducer and the status signal is thus an acoustic status signal.
  • the output device is preferably a so-called listener, a hearing aid loudspeaker. The hearing aid wearer can thus be notified, for example by means of voice output or a specific sound signal, whether his hearing aid is seated correctly.
  • the status signal is sent to an external transmitting and receiving unit.
  • the status signal can be sent by means of a wireless connection to a remote control or a mobile telephone or a smartphone.
  • wireless connections for example, radio links or magnetically induced compounds come into question.
  • the status signal can then be output on a screen, by voice output, by means of a colored light-emitting diode, etc.
  • the status signal is a positive signal if the reception test signal deviates from the reference value only within predefined limits. Conversely, the status signal is a negative signal if the reception test signal deviates more than the reference value within predefined limits. Under positive or negative signal is understood here a status message regarding a good or bad fit of the hearing aid in the ear.
  • the status signal is re-determined in presettable time intervals.
  • regular time intervals are adjustable in which the process is repeated.
  • a correct fit of the hearing aid can be checked at these regular intervals and corrected if necessary.
  • These intervals can be set by either a hearing aid wearer and / or a hearing care professional, depending on the design.
  • the status signal is redetermined after switching on and / or inserting the hearing device in the ear.
  • the hearing aid is switched off and on again several times. Frequently, the hearing aid is removed from the ear and then used again.
  • the procedure for correct seat detection in the ear should be repeated.
  • the hearing aid is first turned on and then placed in or on the ear. In this case, a measurement only makes sense, as soon as the device has been used on the ear. For example, this is only 30 seconds after switching on the case.
  • a delay of the first process run can be set to, for example, 40 seconds after power-on.
  • the method is started immediately or with a time delay after switching on the hearing aid and repeated so many times until a correct or acceptable seat is recognized in your. This is communicated to the user by means of the status signal and the method is carried out from this point in time only at greater intervals. For example every 5 minutes. Alternatively, the method can then be stopped again after the correct seat determination, so that it is no longer performed.
  • the receiving device is directed towards an outside area outside the ear canal of a user.
  • the same microphone as Recording device can be used for the method, which also receives the sound from outside the ear canal.
  • the receiving device is directed towards an interior area within the ear canal of a user.
  • a hearing device or a hearing aid system having a recording device for recording sound and converting it into a signal, a signal processing device for processing the signal, and an output device for converting the processed signal into a sound signal and for outputting the sound signal.
  • the signal processing device is suitable for comparing a test signal with at least one reference value of a reference criterion and, as a result, generating a status signal.
  • the status signal contains information about the seating state of the hearing device.
  • the output device is suitable for outputting test signals.
  • the recording device is suitable for recording sound and recording at least part of the test signal.
  • the at least one reference value is a preset value that can not be changed by a hearing aid wearer.
  • the recording device is preferably the microphone of the hearing aid system.
  • hearing aids are equipped with one or two microphones.
  • the output device is the handset, the loudspeaker of the hearing aid system.
  • the microphone or microphones are preferably directed to the outside of an ear canal. They are mainly intended to pick up the sound.
  • a microphone as here but also as a receiving device for test signals can be used. Thus, no additional microphone for such Test signals are placed on the hearing aid and this is thus cheaper to produce.
  • an additional, directed into the ear canal receiving device is possible.
  • This recording device which is usually designed as a microphone, has the advantage that the measuring accuracy is higher when it is used to receive the test signal.
  • the status signal is newly determined by means of a triggering function of an external transmitting and / or receiving unit.
  • the status signal can be forwarded, for example, to a remote control with a reception function.
  • This could output the status signal acoustically or visually, for example.
  • the remote control has a transmitting functionality. As a result, it could trigger a measurement of the status signal by means of a tripping radio signal.
  • the signal processing device is arranged in an external transmitting and / or receiving unit.
  • the status signal is then generated there in the external transmitting and receiving unit.
  • a hearing device 2 with output device 4, receiving device 6 and signal processing unit 8 is shown.
  • the hearing device 2 is an in-the-ear hearing device (IdO), which sits in the ear canal 10 of the ear 12 of a user.
  • IdO in-the-ear hearing device
  • the propagation of a test signal 14 is shown.
  • air gaps 16 between the hearing aid 2 and a wall of the ear canal 10 are present.
  • the smaller the dimensions of the air gaps 16 the better the correct fit of a hearing device 2.
  • the reason is that with larger air gaps 16 more damping occurs. As it were, part of the sound is "lost".
  • the seat of the hearing aid 2 is in the Fig. 1 only sketched, the size of an air gap 16 therefore nothing to scale.
  • an output device 4 directed into the ear canal 10 outputs a test signal 14.
  • a portion of this test signal 14 is directed to an eardrum 18, another or a part reflected by the eardrum 18 passes through the air gaps 16 to an outside area 20 outside the ear canal 10.
  • the test signal 14 is at least partially received by the receiving device 6.
  • the output device 4 is a listener and the recording device 6 is a microphone. Consequently, the test signal 14 is a sound signal. Specifically, it is the received test signal 14 only a part of the originally transmitted test signal 14, which arrives at the receiving device 6.
  • the resumed part of the test signal 14 is now compared in the signal processing unit 8 with at least one reference value of a reference criterion.
  • the reference value is a suitable value which can be compared with previously determined values of the test signal 14.
  • the reference criterion may be, for example, an attenuation or a signal. Accordingly, the reference value is an attenuation value or a signal value.
  • the reference value is already stored in the delivery state of the hearing device 2. For example, these data are stored in a memory area of the signal processing unit 8. Hearing aids have been adapted as best as possible to specialists by several specialists, generally hearing healthcare professionals. Subsequently, a feedback measurement was performed on the hearing aids. As a result, a statistical average of all test results was calculated. As a result, the data referred to herein as reference criteria or reference values were obtained. These references can thus be considered as an approximation for an ideal fit of the hearing aid 2 in the ear canal 10. Instead of forming a mean value as a reference value, a median, maxima or minima values, difference values or ratio values may also be used.
  • a result of the comparison between the received test signal 14 and the reference value can be, for example, the magnitude of a deviation of the test signal 14 from the reference value.
  • a good fit increases the effectiveness of the hearing aid 4.
  • test method This explained measurement, the comparison of the test signal with the associated reference values, is referred to below as the test method.
  • a status signal can be output for this purpose.
  • a status signal can be output, for example, as a synthetic speech signal by means of the output device 4.
  • the hearing aid tells the user whether he is sitting well or not.
  • Another possibility is to send the status signal by means of a wireless radio link to a terminal such as a hearing aid remote control.
  • An insertion and fitting operation of the hearing aid 2 proceeds as described below.
  • a user pushes the hearing aid 2 into the ear canal 10.
  • the test procedure already described above, so to speak, tests the fit of the hearing device 2 in the ear canal 10. If the fit of the hearing aid is in need of improvement, then the test procedure will determine this and it will For example, output the status signal "bad seat” by means of the output device 4. The user hears this output artificial sound signal and thereby recognizes that he should change the seat.
  • the test procedure is executed again. If now the seat of the hearing aid 2 is judged to be good on the basis of the result of the test procedure, then the status signal "good fit" is output. The user now knows that he no longer needs to change the seat of the hearing aid 2.
  • the trigger of the test procedure could be various activities or automatisms. For example, it can be triggered by switching on the hearing device 2. It is also possible a delayed start of the test procedure after switching on to give the user time for insertion into the ear canal 10. Also, an automatic interval at regular intervals, the test procedure could be restarted and so the user also regularly on the correctness of the Inform hearing aid seat. In this variant, it makes sense to output the status signal only in case of a bad seat. For a good fit, the user must at least not be informed regularly. Preferably, this interval can be set by the user himself. For example, this could be done by means of a hearing aid remote control.
  • hearing aids instead of the in-the-ear device used in this embodiment, other types of hearing aids can be used. For example, behind-the-ear devices or so-called receiver-in-canal devices.
  • the status signal may be sent to an external transmitting and / or receiving device 28.
  • the external transmitting and / or receiving device 28 is also suitable for triggering the determination of the status signal by means of a triggering function.
  • the external transmitting and / or receiving device 28 may be, for example, a remote control with transmitting and / or receiving function.
  • Fig. 2 and Fig. 3 the measurement of different curves is shown graphically.
  • the x-axis specifies a logarithmic frequency range of approximately 125 hertz to approximately 12,000 hertz.
  • the y-axis shows an attenuation or gain in the logarithmic unit decibel.
  • the gain curve 22 represents the maximum possible gain of a hearing aid.
  • the test curves 24 and 26 are determined by performing the test procedure.
  • the test curve 24 indicates a good fit of a hearing aid in the ear.
  • test curves 24 and 26 different gains occur in different frequency ranges.
  • the test curve 26 when measured by the test method for the frequency value 1 kHz has given the gain value of about 25 dB.
  • test curve 24 measured a value of about 30 dB.
  • Frequency ranges are the values of the test curve 24 higher than the test curve 26. But not all.
  • important frequency ranges are initially selected. These are then assigned a threshold value. These different thresholds for the different frequency ranges can be considered as reference values.
  • a measurement is performed by the test method. After the measurement, a test curve is obtained, such as the test curves 24 or 26. It can then be compared whether and how often the reference values were exceeded or undershot on the basis of the measurement. Based on the number of overruns or underruns can be assumed then from a good or bad fit of the hearing aid. In addition, this procedure can be weighted more heavily as important frequency ranges considered or corresponding threshold values. Thus, in the method for determining the fit of the hearing aid in the ear certain frequencies can be prioritized.
  • a threshold value of at least 30 dB can be set for the frequencies 1 kHz and 7 kHz.
  • the test curve 24 exceeds these values, the test curve 26, however, does not reach these thresholds.
  • a "good fit” and in the test curve 26 a "poor fit” of the hearing aid can be given.

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  • Health & Medical Sciences (AREA)
  • General Health & Medical Sciences (AREA)
  • Otolaryngology (AREA)
  • Neurosurgery (AREA)
  • Physics & Mathematics (AREA)
  • Engineering & Computer Science (AREA)
  • Acoustics & Sound (AREA)
  • Signal Processing (AREA)
  • Measurement Of The Respiration, Hearing Ability, Form, And Blood Characteristics Of Living Organisms (AREA)
EP14196099.7A 2013-12-12 2014-12-03 Prothèse auditive avec détermination de son positionnement dans l'oreille Withdrawn EP2884772A1 (fr)

Applications Claiming Priority (1)

Application Number Priority Date Filing Date Title
DE102013225760.0A DE102013225760A1 (de) 2013-12-12 2013-12-12 Hörgerät mit Sitzerkennung

Publications (1)

Publication Number Publication Date
EP2884772A1 true EP2884772A1 (fr) 2015-06-17

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EP14196099.7A Withdrawn EP2884772A1 (fr) 2013-12-12 2014-12-03 Prothèse auditive avec détermination de son positionnement dans l'oreille

Country Status (5)

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US (1) US20150172829A1 (fr)
EP (1) EP2884772A1 (fr)
CN (1) CN104717592A (fr)
AU (1) AU2014268158A1 (fr)
DE (1) DE102013225760A1 (fr)

Cited By (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
EP3113519A1 (fr) * 2015-07-02 2017-01-04 Oticon A/s Procédés et dispositifs pour placement correct et sûr d'un dispositif de communication intra-auriculaire dans le canal auditif d'un utilisateur

Families Citing this family (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
DE102016212879B3 (de) * 2016-07-14 2017-12-21 Sivantos Pte. Ltd. Verfahren zur Funktions- und/oder Sitzüberprüfung eines Hörgerätes
EP3343952A1 (fr) * 2016-12-30 2018-07-04 GN Hearing A/S Instrument auditif modulaire comprenant des paramètres d'étalonnage électroacoustique
DE102019218616A1 (de) * 2019-11-29 2021-06-02 Sivantos Pte. Ltd. Verfahren zum Betrieb eines Hörsystems, Hörsystem und Computerprogrammprodukt
DE102021204939A1 (de) 2021-05-17 2022-11-17 Robert Bosch Gesellschaft mit beschränkter Haftung Verfahren und Vorrichtung zur Erkennung der Passgenauigkeit von Kopfhörern

Citations (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
EP1746860A2 (fr) 2005-07-22 2007-01-24 Siemens Audiologische Technik GmbH Prothèse auditive avec détermination automatique de son positionnement dans l'oreille et procédé correspondant
EP1938658A1 (fr) * 2005-10-17 2008-07-02 Widex A/S Procede et systeme de reglage d'une prothese auditive
WO2010049543A2 (fr) * 2010-02-19 2010-05-06 Phonak Ag Procédé pour le contrôle d’un ajustement d’une prothèse auditive et prothèse auditive
WO2012107100A1 (fr) * 2011-02-11 2012-08-16 Widex A/S Appareil auditif comportant des moyens permettant d'évaluer l'adaptation de l'embout intra-auriculaire
EP2613566A1 (fr) * 2012-01-03 2013-07-10 Oticon A/S Dispositif d'écoute et procédé de surveillance de la fixation d'un embout auriculaire de dispositif d'écoute

Family Cites Families (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
DE102010031619B4 (de) * 2010-07-21 2024-08-22 Sennheiser Electronic Se & Co. Kg In-Ohr-Hörer

Patent Citations (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
EP1746860A2 (fr) 2005-07-22 2007-01-24 Siemens Audiologische Technik GmbH Prothèse auditive avec détermination automatique de son positionnement dans l'oreille et procédé correspondant
EP1938658A1 (fr) * 2005-10-17 2008-07-02 Widex A/S Procede et systeme de reglage d'une prothese auditive
WO2010049543A2 (fr) * 2010-02-19 2010-05-06 Phonak Ag Procédé pour le contrôle d’un ajustement d’une prothèse auditive et prothèse auditive
WO2012107100A1 (fr) * 2011-02-11 2012-08-16 Widex A/S Appareil auditif comportant des moyens permettant d'évaluer l'adaptation de l'embout intra-auriculaire
EP2613566A1 (fr) * 2012-01-03 2013-07-10 Oticon A/S Dispositif d'écoute et procédé de surveillance de la fixation d'un embout auriculaire de dispositif d'écoute

Cited By (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
EP3113519A1 (fr) * 2015-07-02 2017-01-04 Oticon A/s Procédés et dispositifs pour placement correct et sûr d'un dispositif de communication intra-auriculaire dans le canal auditif d'un utilisateur
US10448177B2 (en) 2015-07-02 2019-10-15 Oticon A/S Methods and devices for correct and safe placement of an in-ear communication device in the ear canal of a user

Also Published As

Publication number Publication date
CN104717592A (zh) 2015-06-17
US20150172829A1 (en) 2015-06-18
DE102013225760A1 (de) 2015-06-18
AU2014268158A1 (en) 2015-07-02

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