EP3448063B1 - Procédé de réglage d'un dispositif de correction auditive - Google Patents

Procédé de réglage d'un dispositif de correction auditive Download PDF

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Publication number
EP3448063B1
EP3448063B1 EP18186865.4A EP18186865A EP3448063B1 EP 3448063 B1 EP3448063 B1 EP 3448063B1 EP 18186865 A EP18186865 A EP 18186865A EP 3448063 B1 EP3448063 B1 EP 3448063B1
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EP
European Patent Office
Prior art keywords
individual
stored
sound transmission
amplification profile
transfer function
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EP18186865.4A
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German (de)
English (en)
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EP3448063A1 (fr
Inventor
Tom Männel
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Sivantos Pte Ltd
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Sivantos Pte Ltd
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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
    • H04R25/70—Adaptation of deaf aid to hearing loss, e.g. initial electronic fitting
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R25/00—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception
    • 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
    • H04R25/50—Customised settings for obtaining desired overall acoustical characteristics
    • H04R25/505—Customised settings for obtaining desired overall acoustical characteristics using digital signal processing
    • 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
    • H04R2225/021—Behind the ear [BTE] hearing aids
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R2225/00—Details of deaf aids covered by H04R25/00, not provided for in any of its subgroups
    • H04R2225/023—Completely in the canal [CIC] hearing aids
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R2225/00—Details of deaf aids covered by H04R25/00, not provided for in any of its subgroups
    • H04R2225/025—In the ear hearing aids [ITE] hearing aids
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R2225/00—Details of deaf aids covered by H04R25/00, not provided for in any of its subgroups
    • H04R2225/43—Signal processing in hearing aids to enhance the speech intelligibility
    • 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
    • H04R25/30—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
    • 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
    • H04R25/552—Binaural
    • 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

Definitions

  • the invention relates to a method for adapting a hearing device.
  • Hearing aids are portable hearing devices which are generally designed to output sound.
  • sound is generally understood to mean an acoustic signal, for example music and / or speech.
  • a hearing device is generally understood to mean any device that can be worn in or on the ear and produces a sound, for example a headset, headphones and the like.
  • Corresponding hearing devices are known in principle and, for example, in the US 2002/176 584 A1 or the WO 2013/075 255 A1 described.
  • Hearing aids are also specifically designed as hearing aids.
  • Hearing aid device is understood to mean a device for supplying a hearing-impaired or hearing-impaired person who wears the hearing aid device in particular continuously or for most of the time in order to compensate for a hearing deficit.
  • hearing aids such as behind-the-ear hearing aids (BTE), hearing aids with external receivers (RIC: receiver in the canal) and in-the-ear hearing aids (ITE), for example Concha hearing aids or canal hearing aids (ITE, CIC) provided.
  • BTE behind-the-ear hearing aids
  • RIC hearing aids with external receivers
  • ITE in-the-ear hearing aids
  • ITE Concha hearing aids or canal hearing aids
  • ITE Concha hearing aids or canal hearing aids
  • CIC Canal hearing aids
  • the hearing aids listed as examples are worn on the outer ear or in the auditory canal.
  • bone conduction hearing aids, implantable or vibrotactile hearing aids are also available on the market. The damaged hearing is stimulated either mechanically or electrically.
  • hearing aids have an input transducer, an amplifier and an output transducer as essential components.
  • the input transducer is usually a sound receiver, e.g. B. a microphone, and / or an electromagnetic receiver, e.g. B. an induction coil.
  • the output transducer is usually an electroacoustic transducer, e.g. B. miniature speakers, or as an electromechanical converter, e.g. B. bone conduction receiver realized.
  • the amplifier is usually integrated in a signal processing unit.
  • an IDO hearing device for example, often has a sound channel and an HDO device usually has a sound tube.
  • the sound is transmitted to the user's eardrum by means of the sound tube, which is fixed in the ear canal with an otoplastic, for example.
  • the sound channel similar to the sound tube in the HDO device, is used to transmit the sound from the listener to an output of the housing and thus in the direction of the user's eardrum.
  • the hearing deficit and / or the hearing impairment of the user is often not evenly pronounced over the entire frequency range of the user's auditory perception. This means that the user's hearing is only impaired in a certain frequency range, for example, or the hearing deficit and / or the hearing impairment of the user varies over the audible frequency spectrum (acoustic signals with a frequency in the range from 20Hz to 20kHz).
  • a setting of the hearing aid takes place, for example, by means of setting software, for example as part of a fitting session with an acoustician.
  • the setting is used to set the hearing aid, in particular the signal processing of the signal processing unit, with regard to the hearing deficit and / or the hearing impairment of the user.
  • the sound tube often exerts an influence on a transmission behavior of the hearing aid.
  • under influence is understood a frequency-dependent damping and / or frequency-dependent amplification of the sound when the sound tube "passes" through to the eardrum.
  • This is taken into account when adapting the hearing aid, for example on the basis of a reference sound battle.
  • it is generally taken into account on the basis of the reference sound tube, ie not user-specific, whereby for example different lengths of sound tubes and in particular their influence on the transmission behavior are not or only insufficiently taken into account.
  • the invention is based on the object of specifying a method with the aid of which a hearing device can be adapted user-specifically with as little effort as possible.
  • hearing device is understood to mean, in particular, a hearing aid device of the type already mentioned.
  • a hearing device is generally understood to mean a device for generating and outputting sound, for example in the manner of headphones.
  • the hearing device has a signal processing unit for processing an electrical input signal into an electrical output signal.
  • the electrical input signal is processed on the basis of a transfer function.
  • the transfer function is usually a configurable and frequency-dependent reference transfer function.
  • the (reference) transfer function is generally understood to mean a mathematical function which describes the processing, for example a convolution and / or in particular a gain, of the electrical input signal.
  • configurable is specifically understood to mean an adjustability of parameters of the signal processing unit, via which an influence on the (reference) transfer function is obtained, especially taking into account a hearing deficit and / or a hearing impairment of the user.
  • the signal processing unit is special an individually tailored, in particular frequency-dependent, amplification of the electrical output signal can be set.
  • the hearing device also has a receiver for outputting an acoustic output signal based on the electrical output signal.
  • the receiver is preferably designed in the manner of an electroacoustic transducer of a known type.
  • the hearing device has an individual sound transmission element with a frequency-dependent individual amplification curve.
  • individual is understood to mean a user-dependency of the sound transmission element with regard to the length of the individual sound transmission element.
  • the length of the sound channel varies, for example due to an individual and thus different design of the housing of the IDO device, which can be traced back to an individual anatomy of the ear of a respective user.
  • the varying length of the sound channel often leads to unwanted frequency-dependent amplifications and / or frequency-dependent attenuations of the output signal transmitted by the earpiece.
  • the user's hearing is impaired, since the user perceives sound with a specific frequency or with a value in a frequency range either amplified or attenuated.
  • the unwanted amplification and / or attenuation of the sound within the sound channel is due, for example, to interference in the transmission of the output signal through the sound tube.
  • sound transmission elements that are individually adapted to the respective user are made with a length that is adapted to, for example, the ear canal of the user.
  • an individual gain curve is a particular understood as a function of the frequency of the signal to be amplified amplification due to the interferences occurring within the sound transmission element.
  • the different frequency-dependent gains can be represented graphically, for example, with the formation of a so-called "gain curve” which "shows" the gain curve.
  • HDO hearing devices also have a so-called otoplastic.
  • the otoplastic is an ear mold which is, for example, specially adapted to the ear canal of the user in order to guide the acoustic output signal transmitted by the sound transmission element to the eardrum of the user.
  • the otoplastic is typically arranged at the end of the sound transmission element, viewed in the direction of the user's eardrum.
  • the receiver and the individual amplifying element preferably form an individual transmission system for the acoustic output signal.
  • the individual transmission system takes into account, for example, individual receiver types, individual acoustic couplings of the listener to the (individual) sound transmission element and general acoustic tolerances of the listener and / or the individual sound transmission element. Such aforementioned aspects have an effect on the individual gain curve.
  • the individual gain curve is determined to adapt the hearing device and stored for a subsequent fitting process.
  • a fitting process is generally understood to mean an adaptation of the hearing aid, in particular the reference transmission function, to the individual user.
  • a user-dependent adaptation of the hearing device is achieved in order to compensate for a hearing deficit of the user as well as possible.
  • the individual amplification curve of the individual sound transmission element is measured on the basis of a particular predetermined and known reference transmission function.
  • An electrical input signal is fed in.
  • this is converted into the electrical output signal, which is then converted into the acoustic output signal by the listener and the individual sound transmission element. This is measured so that the individual amplification curve can be obtained or determined based on the measured acoustic output signal and is thus measured.
  • This reference transfer function corresponds in particular to a standard or reference presetting of the respective hearing aid before it is individually adapted to the respective hearing aid wearer.
  • the reference transmission function is, for example, preinstalled on the hearing aid or stored in a setting unit (software).
  • the measurement of the individual gain profile of the individual sound transmission element takes place at the factory or by the manufacturer, for example as part of a final acceptance test at the manufacturer of the hearing aids.
  • the measured individual gain curve is also stored in order to make it available at a later point in time.
  • a later point in time is generally understood to mean all points in time after the measurement of the individual gain profile and specifically a fitting session with an acoustician in the context of handing over the hearing aid to the customer. This makes it possible to first determine an individual amplification curve of the individual sound transmission element at the factory and, for example, store it in a database so that it can be called up and make it available to an acoustician to adapt the hearing device during a fitting process, regardless of location.
  • the measured individual amplification curve is then compared with a reference amplification curve, which was preferably determined on the basis of the same (reference) transfer function.
  • the reference amplification curve describes the amplification behavior of a reference system (reference transmission system, in particular reference receiver and reference sound transmission element), which in particular has a reference sound transmission element with a predetermined reference length.
  • the measurement of the individual gain curve on the basis of the reference transfer function and, if necessary, the comparison with the reference gain curve are carried out at the factory.
  • the individual gain curves are measured and stored for a large number of individual transmission systems, if necessary together with the possibly determined differences to the reference gain curve.
  • the reference transfer function which describes the processing of the electrical input signal "within" the signal processing unit, is then set, in particular adapted, for example parameterized, as a function of a difference between the two amplification curves (individual amplification curve and reference amplification curve).
  • the reference transfer function is adapted and an (adapted) transfer function is obtained, with which the electrical input signal is then converted into the electrical output signal.
  • This adapted transfer function therefore takes into account the individual boundary conditions and is also referred to below as the individual transfer function. This therefore takes into account, in particular, the individual gain curve of the individual (user-specific) sound transmission element.
  • This adjustment is made by an acoustician during the fitting process.
  • the particular advantage is that the acoustician only needs to access the difference values determined and stored by the manufacturer.
  • the fitting process is therefore comparatively simple. That means it is only necessary to determine the individual transmission system, in particular, for example, only to retrieve the individual length of the sound transmission element and the data stored for this purpose and to import it into a fitting software.
  • a reference sound transmission element is generally understood to mean a sound transmission element with a known amplification curve, the reference amplification curve.
  • the reference reinforcement element is also part of the reference system, which has known parameters, for example based on empirical values.
  • parameters are generally understood to mean properties of the reference system, for example the reference gain curve of the reference sound transmission element and / or a predetermined and known length of the reference sound transmission element.
  • the reference system is to be understood as an, in particular, non-individual system and thus the reference sound transmission element and / or the reference sound transmission profile is to be understood as not individual.
  • the reference amplification curve serves as an in particular non-individual reference value for a comparison of the values of an actual amplification of the individual sound transmission element, the individual amplification curve with the reference amplification curve of the reference sound transmission element.
  • the reference amplification curve is thus the same for every comparison, the individual amplification curve of the individual sound transmission element varying from user to user.
  • the individual gain curve occurs if the individual sound transmission element is arranged on the hearing device, for example instead of the reference sound transmission element.
  • the individual sound transmission element has an individual amplification curve which - over the entire hearing spectrum of the user or over a certain frequency range - brings about an additional amplification of the acoustic output signal by, for example, 10 dB.
  • the user now takes the acoustic output signal - undesirable due to the additional amplification of 10 dB amplified true and a desired auditory impression is permanently disturbed.
  • the individual sound transmission element can also lead to an attenuation of the acoustic output signal due to the individual amplification curve.
  • the 10dB determined in the context of the comparison now serve as a difference and as an adjustment value of the reference transfer function to the effect that the electrical output signal of the signal processing unit is attenuated by 10dB in the affected frequency ranges by means of the adjusted reference transfer function.
  • This means that the acoustic output signal based on the electrical output signal is amplified to the acoustic output signal by the amplification of 10 dB occurring within the individual sound transmission element, so that the user perceives the desired hearing impression and the hearing device works without interference.
  • the adaptation does not take place exclusively for individual frequencies. Rather, by means of the method described, an adaptation with regard to a frequency-dependent individual gain curve of the individual sound transmission element is achieved. That is, due to different frequency-dependent additional amplifications of the acoustic output signal due to the individual amplification curve, the reference transfer function is preferably adapted with regard to the entire individual amplification curve.
  • the advantage is that by adapting the reference transmission function and thus the hearing device to an individual sound transmission element - in particular to its individual amplification curve - an adaptation of the transmission behavior of the hearing device is achieved.
  • the adaptation is achieved with regard to at least one reduction in interference of the acoustic output signal that occurs within the individual sound transmission element.
  • a user-specific adaptation of the hearing device to user-specific, individual sound transmission elements is achieved above all.
  • acoustic superimpositions and / or resonances are understood in particular. Experimental measurements have shown that, for example, interference-related gains have a value of up to 5dB in a frequency range from 400Hz to 1300Hz and a value of up to 20dB in a frequency range from 4kHz to 6kHz.
  • an adaptation of an undesired attenuation of the acoustic output signal takes place by an additional amplification within the signal processing unit, provided that the individual sound transmission element effects the undesired attenuation of the acoustic output signal.
  • the reference transfer function is adapted by means of setting software.
  • the setting software is preferably stored or loaded onto a setting unit.
  • a setting unit is, for example, a computer set up to adjust and adjust the hearing device.
  • This setting unit is used for the fitting process, i.e. for adapting the reference transfer function, e.g. by the acoustician.
  • the reference transmission function is adapted, for example, by means of a wired or preferably wireless connection between the hearing device and the setting unit.
  • the setting software is set to a reference transfer function based on the reference gain curve.
  • the reference amplification curve is preferably implemented in the setting software within the framework of a factory presetting, for example within the framework of a final acceptance of the hearing aid.
  • the reference gain curve is stored in a database, for example.
  • the advantage is that the setting software enables simple implementation and adaptation of the reference transfer function. Furthermore, a reduction in the development effort is achieved, since the implementation of the reference gain curve is made possible, for example, in conventional standard adaptation software.
  • only extreme points and turning points are stored as data pairs for the individual gain curve. These are extracted from the individual gain curve, for example.
  • a data pair is specifically understood to mean a coordinate of the individual gain curve in a known manner, which has a frequency value on the one hand and an associated gain on the other. This prevents the storage space from being overloaded, since data pairs characteristic of the course of the individual gain course, for example the already mentioned local extreme values and turning points, are extracted for storage.
  • only a maximum of 20, preferably a maximum of 10 and in particular 8 data pairs are stored for a frequency spectrum audible by the user and for the individual gain curve.
  • the determination of the data pairs and their storage is done by the manufacturer.
  • each hearing device has, for example, a memory element on which the data pairs are stored.
  • the data pairs are coded and in particular stored as a graphic code. This is particularly accessible to the user, for example attached to a packaging of the hearing device or stored on an operating manual or the like assigned to the hearing device or, for example, can also be called up as a graphic code from a website Barcodes or a QR code.
  • the individual gain curve is reconstructed from the data pairs, so that the entire frequency-dependent individual gain curve is used for comparison by means of the setting software.
  • an electrical reference output signal is output by the signal processing unit.
  • the output reference output signal is then converted into an acoustic output signal by means of the receiver.
  • the acoustic output signal is then measured at the end of the individual sound transmission element arranged on the receiver.
  • the reference output signal is generated, for example, either on the basis of a given acoustic reference input signal being fed into the signal processing unit - for example by means of a tone generator that generates a signal that can be parameterized in terms of frequency and amplitude - or alternatively by the signal processing unit itself and / or a maximum output level from which the individual gain curve is generated.
  • an electrical reference output signal is understood to mean an electrical signal which, for example, has a specified, in particular constant, sound level over a specified frequency range.
  • the individual gain curve is reconstructed with the aid of the setting unit.
  • the reconstruction takes place as part of a fitting session with an acoustician. This enables the individual gain curve to be easily implemented in the setting software.
  • the individual gain curve is preferably determined without the user. In other words, the user does not wear the hearing device during the measurement.
  • the acoustician receives the data pairs necessary for the reconstruction either from the database and / or by decoding the, for example graphic codes printed on the packaging of the hearing aid.
  • the setting software compares the reference amplifier curve with the reconstructed individual gain curve. A difference between the two courses is then used to adapt the reference transfer function of the signal unit, which is also adapted and / or set by means of the setting software.
  • the adaptation of the reference transfer function takes place in the manner already mentioned, for example by "adding" the differential gain to the reference gain curve. In this way, in particular, an unadulterated hearing impression for the user is achieved even with an individual sound transmission element.
  • the setting software parameterises the signal processing on the basis of the adjusted reference transfer function.
  • the parameterization takes place, for example, by means of the wireless connection already described between the setting unit and the hearing device.
  • parameterization is specifically understood to mean a setting of the signal processing unit with the adapted reference transfer function.
  • the sound transmission element is designed as a sound channel.
  • Such sound channels are often arranged on hearing devices for the transmission of an acoustic signal.
  • the individual length of the sound transmission element has a value in the range between 2 mm and 20 mm, depending on the user. This results in an individual and user-dependent production of the sound transmission element for the user.
  • the hearing device is designed as a hearing aid device, in particular as an IDO hearing aid device.
  • IDO hearing aid devices are available on the market either as so-called wireless devices or as non-wireless devices.
  • a wireless device is understood to mean a hearing aid device that has two hearing aid sub-devices (one hearing aid sub-device for each ear of the user), which preferably has wireless connections, for example to an adjustment unit or alternatively between the hearing aid sub-devices, for example for generating binaural signals.
  • a non-wireless device is understood analogously to be a hearing aid device which, in particular, is not designed for communication by means of a wireless connection.
  • the described method can also be transmitted in an analog manner, in particular, with regard to wireless and non-wireless devices.
  • This transmission is based on the consideration that wireless devices, in particular wireless IDO devices ex works, for example, have a longer sound transmission element than, for example, non-wireless IDO devices.
  • the longer sound transmission element in wireless devices results, for example, from an antenna element which is arranged on the wireless device and which is arranged around the sound transmission element in the manner of a coil antenna.
  • the sound transmission elements of the wireless devices and the non-wireless devices also have differences in length, which in particular each show a different frequency-dependent gain curve.
  • the method already described can be used in order to at least reduce deviations of the type already described that occur.
  • the method described can be applied to all hearing aid variants which, for example, differ due to their design Have lengths of the individual sound transmission element. In this way, an advantage in terms of simplified development is achieved in particular.
  • IDO hearing aid is understood to mean a hearing aid which is at least partially, in particular completely, arranged in the auditory canal of a user.
  • the IDO hearing aid has a hearing aid housing 1, a microphone 2 for recording and converting an acoustic input signal into an electrical input signal, and a signal processing unit 3.
  • the signal processing unit 3 is used to convert, in particular amplify, the electrical input signal into an electrical output signal.
  • the IDO hearing aid has a battery 5 for electrical supply.
  • the IDO hearing aid has a receiver 4 for converting the electrical output signal into an acoustic output signal S and outputting the acoustic output signal.
  • a sound transmission element 6 for example a sound tube of a known type, is arranged at the end of the receiver 4.
  • the sound transmission element 6 is used to transmit the acoustic output signal from the earphone 4 to the eardrum 10 of the user.
  • the receiver 4 is usually not arranged directly on the hearing aid housing 1. Due to a hearing aid housing 1 that is individually adapted to the ear of the user, a position of the earphone 4 within the hearing aid housing 1 varies the sound transmission element 6 is arranged.
  • the sound transmission element 6 has, for example, a user-specific length with a value in the range from 2 mm to 20 mm. Analogously show this Sound transmission elements 6 of different lengths also each have different amplification curves of the acoustic output signal transmitted through them.
  • the receiver 4 and the individual sound transmission element 6 form an individual sound transmission system.
  • Fig. 2 two such gain curves 12, 14 as a function of the frequency f are shown sketched.
  • the frequency f is plotted logarithmically on the axis X of the abscissa.
  • the gain in decibels acoustically (dBa) is indicated on the y-axis of the ordinate.
  • a reference amplification curve 12 (amplification of an acoustic output signal when transmitted using a reference sound transmission element) and, on the other hand, an individual amplification curve 14 (amplification of an acoustic output signal when transmitted using an individual, user-specific sound transmission element) are plotted as a function of the frequency f .
  • the curves 12, 14 shown serve to illustrate and explain a frequency difference for adapting a reference transfer function of the signal processing unit 3.
  • FIG Fig. 2 the course of a reference signal S R fed into the signal processing unit on the input side is shown.
  • the fed-in reference signal S R has a constant sound level over the entire frequency spectrum. Frequency-dependent differences, for example between the reference signal S R and the individual gain profile 14, are used to determine the individual gain profile 14 in the manner already explained.
  • the individual gain profile 14 has a first gain difference ⁇ 1 from the reference gain profile 12 at a first frequency f 1.
  • the individual gain curve 14 has a gain difference ⁇ 2 that is second from the reference gain curve 12.
  • the two gain differences differ here ⁇ 1, ⁇ 2 in terms of their gain.
  • the acoustic output signal is amplified by the value ⁇ 1 during transmission through the individual sound transmission element 6, provided it is fed into the individual sound transmission element 6 at the frequency f1 (compared to the transmission by means of the reference sound transmission element).
  • the acoustic output signal if it is fed into the individual sound transmission element 6 at the frequency f 2 , is attenuated by the value ⁇ 2 (compared to the transmission by means of the reference sound transmission element).
  • One and the same acoustic output signal is fed into both sound transmission elements (reference sound transmission element and individual sound transmission element) by the signal processing unit, so that the gain differences occur exclusively due to, for example, the differences in length of the sound transmission elements.
  • the two sound transmission elements also differ, for example, in terms of material, shape and / or cross section.
  • Such gain differences .DELTA.1, .DELTA.2 lead, in the event of a non-adaptation within the transfer function of the signal unit, to undesired interferences in the acoustic output signal which are disturbing for the user.
  • FIG. 3 The basic idea of the method 15 in the exemplary embodiment was discussed once again by means of a roughly sketched block diagram of the method steps.
  • the reference amplification curve 12 is determined as part of the development, for example on the basis of empirical values with regard to, for example, an expected average value for the length of the individual sound transmission elements 6 manufactured for the hearing device H.
  • a reference sound transmission element which, for example, has such a mean value length has used.
  • the reference gain curve 12 is then stored in a database, for example.
  • the individual gain curve 14 is determined, for example, in the context of a final acceptance after production of the hearing device H 16.
  • a predetermined electrical input signal for example the reference signal S R
  • the individual amplification curve 14 of the acoustic output signal output at the end of the individual sound transmission element 6 is then recorded.
  • this is checked for measurement inaccuracies or disturbances. For example, when determining the individual gain curve 14, disturbances and / or deviations often occur due to, for example, incorrect positioning of the hearing device H within a measuring chamber.
  • data pairs of the recorded individual gain curve are determined, for example by extracting relevant data pairs 20 Understood minima or turning points.
  • a maximum of 20 in particular a maximum of 8 data pairs are extracted in the present case.
  • the extracted data pairs are then stored 24.
  • the storage takes place, for example, in a database.
  • the database is set up as a cloud storage, so that a location-independent and / or time-independent access to the data pairs is guaranteed.
  • the data pairs are stored, for example, by means of an internal storage element within the hearing aid or, for example, printed on the packaging of the hearing apparatus H by means of graphic coding.
  • graphic coding is understood to mean, for example, a bar code in a known manner or a QR code.
  • the reference transfer function on the basis of which the signal processing unit 3 processes the electrical input signals into electrical output signals is set up in the exemplary embodiment on the basis of the data pairs of the reference amplification signal stored as part of the development (as already mentioned).
  • the described method steps 16, 18, 20, 22, 24 take place in the exemplary embodiment in particular at the factory. This means that the recording of the individual amplification curve and the extraction and storage of the data pairs take place, for example, as part of the final acceptance of the hearing aid during manufacture.
  • An adaptation of the reference transmission function of the signal processing unit 3 to an individual gain curve 14 of an individual sound transmission element 6 takes place, for example, as part of a fitting session at the acoustician.
  • the hearing aid is initially read in by means of an adjustment unit 25, for example a computer, with a view to checking whether data pairs are stored for the hearing device H and in particular for the individual sound transmission element 6 26.
  • an adjustment unit 25 for example a computer
  • the stored data pairs are read out 30 from the database.
  • the data pairs are determined by decoding the graphic code on the packaging of the hearing device H.
  • the reference transmission function of the signal processing unit is not adjusted with regard to an individual gain curve 14, but the setting unit 25 takes over the data pairs of the reference gain curve 12 for the device the reference transfer function 32.
  • a reconstruction 34 of the individual gain curve 14 takes place by means of the stored data pairs on the part of the setting unit, for example by means of setting software 36.
  • the two determined or reconstructed courses 12, 14 are now compared 38 with regard to a difference in the gain behavior.
  • the setting software 36 determines by comparing the two courses 12, 14 to what extent the individual gain course deviates from the reference gain course 12 in terms of gain.
  • this difference is determined, for example, for a frequency band in the audible range of humans (20 Hz to 20 kHz), so that, for example, a difference between the two curves 12, 14 is determined for each audible frequency.
  • the difference over a specific frequency band is used to adapt the reference transfer function.
  • the background to this determination is that the difference in the gain of the two curves 12, 14 changes in particular as a function of the frequency.
  • the previously determined difference is "added" to the reference transfer function by means of the setting software 36.
  • the reference transfer function is adapted by means of the setting software in such a way that it depends on the Frequency generates an electrical output signal which differs by the value and sign of the difference from the preset electrical output signal.
  • the signal processing unit 3 deliberately outputs an electrical output signal that is, for example, overly amplified or too weakly amplified, and an acoustic output signal S after conversion in the listener, which, however, is amplified or attenuated due to the individual amplification curve 14 of the individual sound transmission element 6 in such a way that the user hears the desired output signal.

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  • Health & Medical Sciences (AREA)
  • General Health & Medical Sciences (AREA)
  • Neurosurgery (AREA)
  • Otolaryngology (AREA)
  • Physics & Mathematics (AREA)
  • Engineering & Computer Science (AREA)
  • Acoustics & Sound (AREA)
  • Signal Processing (AREA)
  • Measurement Of The Respiration, Hearing Ability, Form, And Blood Characteristics Of Living Organisms (AREA)
  • Circuit For Audible Band Transducer (AREA)

Claims (14)

  1. Procédé (15) d'adaptation d'un dispositif auditif (H), dans lequel le dispositif auditif (H) comprend :
    - une unité de traitement de signal (3) pour traiter un signal électrique d'entrée en un signal électrique de sortie sur la base d'une fonction de transfert,
    - un récepteur (4) pour émettre un signal acoustique de sortie (S) sur la base du signal électrique de sortie, et
    - un élément de transmission sonore individuel (6) relié au récepteur (4), la longueur individuelle de l'élément de transmission sonore (6) ayant une valeur de 2 mm à 20 mm en fonction de l'utilisateur, et le récepteur (4) et l'élément de transmission sonore individuel (6) formant un système de transmission individuel avec un profil d'amplification individuel (14) dépendant de la fréquence pour le signal de sortie acoustique (S),
    dans lequel le profil d'amplification individuel (14) est déterminé et stocké pour un processus d'adaption ultérieur et dans lequel
    a) les profils d'amplification individuelles (14) sont mesurés par le fabricant pour une multiplicité de systèmes de transmission individuels,
    b) les valeurs extrêmes locales et les points d'inflexion sont extraits de ces profils d'amplifications individuels (14) en tant que paires de données caractérisant le profil, et les paires de données sont stockées dans une base de données,
    c) au cours d'un processus de raccord chez un acousticien, la longueur individuelle de l'élément individuel de transmission sonore (6) destiné à un porteur d'appareil auditif respectif est déterminée,
    d) pour le système de transmission individuel, les paires de données stockées dans la base de données à cet effet sont récupérées,
    e) le profil d'amplification individuel associé (14) mesuré par le fabricant est reconstruit à partir des paires de données stockées à cet effet,
    f) le profil d'amplification individuel (14) est comparé au moyen d'une unité d'adaption (25) à un profil d'amplification de référence mémorisé (12) et des différences (Δ1, Δ2) sont déterminées,
    g) une fonction de transfert de référence de l'unité de traitement de signal (3) est adaptée en fonction des différences (Δ1, Δ2), de sorte qu'une fonction de transfert individuelle est obtenue, qui prend en compte le comportement individuel de transmission sonore de l'élément individuel de transmission sonore (6) et avec laquelle le traitement du signal électrique d'entrée est ensuite effectué.
  2. Procédé (15) selon la revendication précédente,
    dans lequel
    - le profil d'amplification individuel est mesuré sur la base de la fonction de transfert de référence,
    - le profil d'amplification individuel (14) est comparé au profil d'amplification de référence (12),
    - la fonction de transfert de référence est adaptée en fonction des différences (Δ1, Δ2) entre le profil d'amplification individuel (14) et le profil d'amplification de référence (12) afin d'obtenir la fonction de transfert individuelle.
  3. Procédé (15) selon l'une des deux revendications précédentes,
    dans lequel l'adaption est effectuée à l'aide d'un logiciel de réglage (36) stocké sur l'unité de réglage (25), ledit logiciel de réglage (36) étant réglé par défaut sur la fonction de transfert de référence basée sur le profil d'amplification de référence (12).
  4. Procédé (15) selon l'une des revendications précédentes,
    dans lequel seuls les points extrêmes et les points d'inflexion du profil d'amplification individuel (14) sont stockés comme paires de données.
  5. Procédé (15) selon la revendication précédente,
    dans lequel pour un spectre de fréquences audibles et pour le profil d'amplification individuel (14), seulement un maximum de 20, de préférence un maximum de 10 paires de données sont stockées.
  6. Procédé (15) selon l'une des deux revendications précédentes,
    dans lequel les paires de données sont stockées dans la base de données.
  7. Procédé selon l'une des revendications 4 à 6,
    dans lequel les paires de données sont stockées dans un stockage sur la base d'un serveur, en particulier dans un nuage.
  8. Procédé (15) selon l'une des revendications 4 ou 5,
    dans lequel les paires de données sont codées, en particulier stockées sous forme de code graphique.
  9. Procédé selon l'une des revendications 4 à 5,
    dans lequel, avant de comparer le profil d'amplification individuel (14) avec le profil d'amplification de référence mémorisé (12), le profil d'amplification individuel (14) est reconstruit à partir des paires de données.
  10. Procédé (15) selon la revendication 3,
    dans lequel le profil d'amplification individuel (14) est reconstruit à l'aide de l'unité de réglage (25).
  11. Procédé (15) selon la revendication 2 et selon la revendication 3,
    dans lequel le logiciel de réglage (36) adapte la fonction de transfert de référence en fonction de la différence (Δ1, Δ2).
  12. Procédé (15) selon la revendication précédente,
    dans lequel le logiciel de réglage (36) paramètre l'unité de traitement de signal (3) sur la base de la fonction de transfert de référence ajustée.
  13. Procédé (15) selon l'une des revendications précédentes,
    dans lequel l'élément de transmission sonore (6) est conçu comme un canal sonore.
  14. Procédé (15) selon l'une des revendications précédentes,
    dans lequel l'appareil auditif est conçu comme un appareil d'aide auditive, en particulier un appareil d'aide auditive IDO.
EP18186865.4A 2017-08-25 2018-08-01 Procédé de réglage d'un dispositif de correction auditive Active EP3448063B1 (fr)

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DE102017214942.6A DE102017214942A1 (de) 2017-08-25 2017-08-25 Verfahren zum Anpassen einer Hörvorrichtung

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DK (1) DK3448063T3 (fr)

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US11257510B2 (en) 2019-12-02 2022-02-22 International Business Machines Corporation Participant-tuned filtering using deep neural network dynamic spectral masking for conversation isolation and security in noisy environments
CN111669682A (zh) * 2020-05-29 2020-09-15 安克创新科技股份有限公司 扬声设备音质的优化方法

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Publication number Priority date Publication date Assignee Title
US4677675A (en) * 1985-09-17 1987-06-30 Killion Mead C Response-modifying acoustic couplers for hearing aids
US5303306A (en) * 1989-06-06 1994-04-12 Audioscience, Inc. Hearing aid with programmable remote and method of deriving settings for configuring the hearing aid
US7058182B2 (en) * 1999-10-06 2006-06-06 Gn Resound A/S Apparatus and methods for hearing aid performance measurement, fitting, and initialization
DE102004025122A1 (de) 2004-05-21 2005-12-22 Siemens Audiologische Technik Gmbh Hörgerät mit abgespeichertem, individuellem Frequenzgang und entsprechendes Anpassverfahren
US7564979B2 (en) * 2005-01-08 2009-07-21 Robert Swartz Listener specific audio reproduction system
DE102007035174B4 (de) * 2007-07-27 2014-12-04 Siemens Medical Instruments Pte. Ltd. Hörvorrichtung gesteuert durch ein perzeptives Modell und entsprechendes Verfahren
EP2378792A1 (fr) 2010-04-14 2011-10-19 GN Resound A/S Appareil d'aide auditive avec tube acoustique
EP2521377A1 (fr) * 2011-05-06 2012-11-07 Jacoti BVBA Dispositif de communication personnel doté d'un support auditif et procédé pour sa fourniture
US9271666B2 (en) 2011-11-22 2016-03-01 Sonova Ag Method of processing a signal in a hearing instrument, and hearing instrument
EP3211917B1 (fr) * 2014-10-24 2020-02-26 Sony Corporation Écouteur
CN107005775B (zh) 2014-12-17 2020-04-10 唯听助听器公司 操作助听器系统的方法以及助听器系统
CN104661168B (zh) * 2015-01-13 2017-02-08 欧仕达听力科技（厦门）有限公司 一种基于子带宽动态范围压缩的最佳验配方法与系统

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US20190069099A1 (en) 2019-02-28
DE102017214942A1 (de) 2019-02-28
DK3448063T3 (da) 2021-12-20
US10841715B2 (en) 2020-11-17
EP3448063A1 (fr) 2019-02-27
CN109429161B (zh) 2021-07-06

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