EP0335542A2 - Prothèse auditive avec capacité de saisie de données - Google Patents

Prothèse auditive avec capacité de saisie de données Download PDF

Info

Publication number
EP0335542A2
EP0335542A2 EP89302689A EP89302689A EP0335542A2 EP 0335542 A2 EP0335542 A2 EP 0335542A2 EP 89302689 A EP89302689 A EP 89302689A EP 89302689 A EP89302689 A EP 89302689A EP 0335542 A2 EP0335542 A2 EP 0335542A2
Authority
EP
European Patent Office
Prior art keywords
datalogging
signal
control
programmable
auditory prosthesis
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.)
Granted
Application number
EP89302689A
Other languages
German (de)
English (en)
Other versions
EP0335542B1 (fr
EP0335542A3 (fr
Inventor
Stephan Eberhard Mangold
Rolf Christer Rising
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.)
GN Hearing Care Corp
Original Assignee
Diaphon Development AB
3M Hearing Health AB
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
Family has litigation
First worldwide family litigation filed litigation Critical https://patents.darts-ip.com/?family=22639486&utm_source=google_patent&utm_medium=platform_link&utm_campaign=public_patent_search&patent=EP0335542(A2) "Global patent litigation dataset” by Darts-ip is licensed under a Creative Commons Attribution 4.0 International License.
Application filed by Diaphon Development AB, 3M Hearing Health AB filed Critical Diaphon Development AB
Publication of EP0335542A2 publication Critical patent/EP0335542A2/fr
Publication of EP0335542A3 publication Critical patent/EP0335542A3/fr
Application granted granted Critical
Publication of EP0335542B1 publication Critical patent/EP0335542B1/fr
Anticipated expiration legal-status Critical
Expired - Lifetime legal-status Critical Current

Links

Images

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
    • 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
    • H04R29/00—Monitoring arrangements; Testing arrangements
    • H04R29/007—Monitoring arrangements; Testing arrangements for public address systems
    • 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
    • H04R2225/39—Aspects relating to automatic logging of sound environment parameters and the performance of the hearing aid during use, e.g. histogram logging, or of user selected programs or settings in the hearing aid, e.g. usage logging
    • 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
    • H04R25/35—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception using translation techniques
    • H04R25/356—Amplitude, e.g. amplitude shift or compression
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R25/00—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception
    • H04R25/60—Mounting or interconnection of hearing aid parts, e.g. inside tips, housings or to ossicles
    • H04R25/604—Mounting or interconnection of hearing aid parts, e.g. inside tips, housings or to ossicles of acoustic or vibrational transducers
    • H04R25/606—Mounting or interconnection of hearing aid parts, e.g. inside tips, housings or to ossicles of acoustic or vibrational transducers acting directly on the eardrum, the ossicles or the skull, e.g. mastoid, tooth, maxillary or mandibular bone, or mechanically stimulating the cochlea, e.g. at the oval window

Definitions

  • This invention relates generally to auditory pros­theses and more particularly the invention relates to auditory prostheses having datalogging capabilities.
  • Auditory prostheses of various types are known and commercially available. Such prostheses include hearing aids, cochlear implants, implantable hearing aids, and vibrotactile devices.
  • One such prosthesis is a program­mable hearing aid; see for example U.S. Patent No. 4,425,481.
  • Such devices have programmable memories for controlling a signal processor for different processing of audio signals.
  • the user can select one of several programs stored in memory for processing the signals by a manually-operated program control.
  • the conventional programmable hearing aid has a wide variety of signal-processing capabilities involving sig­nal amplification, automatic gain control, filtering, noise suppression and other characteristics.
  • a major problem lies in selecting the specific values or set of values of parameters to control the hearing aid for optimum use by each user. While one user might require a wide range of signal processing, another user will better utilize different programs in a more limited range of signal processing.
  • Other conventional hearing aids, while not programmable, are user-adjustable and have similar range adjustment limitations.
  • a datalogging capability is provided in a memory located in or associated with a programmable or manually adjustable auditory prosthesis.
  • the memory permits recording or logging of certain user-selected events, such as changes in settings, parameters, or algorithms, number of times agiven setting is selected, and duration for which a given setting is selected.
  • the memory may permit recording of environ­mentally selected events, such as selection of settings, parameters, or algorithms, where such selection is based on an automatic computation in response to the current sound environment of the wearer.
  • the method of determining the values for each of the data logs entails counting time in large segments, of the order of two minutes (128 seconds).
  • Duration of use of each setting is then stored in units of two minutes.
  • individual program settings are not recorded until after a given time period for each setting, thereby obviating the recording of many settings when the user is exploring settings for a desired re­sponse.
  • the control unit can be integral with the processing unit of the hearing aid or external to and coupled with the processing unit. However, in a preferred embodiment of a programmable hearing aid the control unit is remote from the hearing aid processing unit and has a transmit­ter (e.g. acoustical, electro-magnetic or infra-red) for transmitting control signals to the processing unit.
  • the datalog memory can be in the ear portion of the hearing aid or in the control unit. By using a remote control unit with the datalog memory therein, the ear portion can be smaller, lighter in weight, and less visible.
  • the user When the user returns the hearing aid to the dis­penser, it may be reprogrammed or readjusted as appro­priate in view of the data log information.
  • the dispen­ser will utilize an appropriate connection to the hearing aid to read out the data stored in the data log memory. Based on this information, a new set of operating para­meters can be programmed for the user. The selection of new programs is based upon interpreting the degree of use of the original programs by the user.
  • programs are intended one or more of: specific settings of a limited number of parameters; selection of a processing configu­ration of strategy; modification of a prosthesis control program; or setting of coefficients in a prosthesis program.
  • Fig. 1 is a functional block diagram of a multiple-­memory programmable hearing aid, shown generally at 2, such as described in U.S. Patent No. 4,425,481 which is hereby incorporated by reference.
  • the hearing aid 2 includes a microphone 10 for picking up sound and con­verting it to an electrical signal, a signal processor and associated slave memory 12 for operating on the elec­trical signal generated by microphone 10 in accordance with one of a plurality of signal-processing programs, and a speaker 14 for audibly transmitting the processed signals.
  • Other signal inputs can be provided such as a tele-coil.
  • a programmable memory with logic 16 stores a plurality of programs for controlling the signal proces­sor 12 in operating on signals from microphone 10.
  • a manual program control switch 18 is provided for the user of the device to select from among the several program­ming options stored in memory 16.
  • the conventional programmable hear­ing aid has a wide variety of signal-processing capabilities including signal amplification, automatic gain con­trol, filtering, and noise suppression.
  • signal-processing capabilities including signal amplification, automatic gain con­trol, filtering, and noise suppression.
  • a major problem lies in optimizing the programming of the hearing aid for use by each individual user.
  • Fig. 2 is a functional block diagram of a program­mable hearing aid shown generally at 4 and including datalogging capability in accordance with one embodiment of the invention.
  • the hearing aid includes a microphone 10, a signal processor with slave memory 12, and a speaker 14.
  • the programmable memory with logic further includes datalogging capability as shown at 20.
  • a pro­grammable decoder 22 is connected to the programmable memory 20. The decoder responds to a coded digital con­trol signal received by the microphone 10 and transmitted from a speaker in the remote control unit to be described in Fig. 3.
  • the carrier frequency of this control signal is in the upper part of the microphone bandwidth and will not be heard by the hearing-aid user.
  • Fig. 3 is a functional block diagram of the remote control unit 6 which can be placed in the user's pocket or on his wrist, for example.
  • the remote control unit 6 is equipped with a manual program control 24 and a logic block 26 to interface with a transmitter and coder 28.
  • the encoder as well as the decoder in the auditory pros­thesis are programmed for the same ID number contained in the control signal so as not to affect other similar auditory prosthesis.
  • the transmitter is connected to speaker 30 for transmitting the coded instructions to the hearing aid, cochlear implant, or implanted hearing aid of Figs. 2, 3 or 4.
  • An automatic program selector can be provided to automatically select a program in response to the ambient noise level as detected by micro­phone 32.
  • the APS will step through the programs in the programmable block 26, and it will stop in a program where the environmental sound level has been amplified above a certain predetermined (and manual­ly adjustable) level. This program number is then transmitted to the head-worn programmable prosthesis where the same program is entered.
  • the level and spectrum of the sound measured at the microphone 32 is used in a calcula­tion to determine specific values of each of the para­meters constituting a program, and these parameters are then loaded via coder 28 and speaker 30 to the prosthesis across the transmitting medium (acoustic, infra-red, electromagnetic, etc.).
  • the datalogging means records or logs the number of times that settings change, the number of times a given setting is selected, and the duration for which a given setting is selected.
  • a practical method for determining the values for each of the quantities is to count time in large segments, on the order of two minutes (128 seconds). Thus the duration is stored in units of two minutes. Additionally, settings are not recorded until after a given time segment for any given segment, thus obviating recording of settings when the settings are merely being explored by the user.
  • Fig. 4 and Fig. 5 are functional block diagrams of a hearing aid 8 and remote control unit 9, respectively, in accordance with an alternative embodiment of the inven­tion.
  • This embodiment is similar to the embodiment of Fig. 2 and Fig. 3, and like elements have the same reference numerals.
  • the major difference in the two embodiments is the removal of the programmable memory with logic and datalogging unit 20 from the hearing aid of Fig. 2, and placing the functions of unit 20 in the programmable APS with logic unit 26 in the remote control unit 9 of Fig. 5.
  • Relieving the hearing aid unit of the datalogging function reduces the size and weight of the hearing aid.
  • a more advanced programmable memory and datalogging can be implemented in the remote control unit with its larger size and greater battery power.
  • the manually-operated con­trol selection 29 is connected by wires 31 to the signal processor 33.
  • the datalogging unit 35 monitors the con­trol selection and includes memory means for recording the extent of use of the plurality of selections. Unit 35 is periodically read from the output 37.
  • the output 39 can be an acoustic speaker or a cochlear implant such as disclosed in U.S. Patent No. 4,357,497 or U.S. Patent No.
  • the invention can also be used in a prosthesis in which the mode or manner of operation is switched auto­matically.
  • the datalogging information is employed to monitor the suitability of the decision algorithm used to effect the automatic switching or adjustment.
  • programs refers to one or more of: specific settings of a limited number of parameters; selection of a prosthetic configuration or processing strategy in a prosthesis which is designed so that multiple modes of processing may be selected; selection of a particular algorithm or form of an algorithm microprocessor or set of micro­processor instructions; or modification of the constants or coefficients of a microprocessor-controlled set of instructions, such as changes in the number and value of filter coefficients in a digitally controlled or imple­mented filter (e.g. FIR or IIR filter).
  • a digitally controlled or imple­mented filter e.g. FIR or IIR filter
  • Figs. 7A, 7B and 7C are a more detailed functional block diagram of the programmable hearing aid 4 with datalogging, as shown in Fig. 2.
  • This embodiment has been built in two integrated circuits illustrated gen­erally at 36 and 38 wth circuit terminals denoted by square symbols.
  • Integrated circuit 36 (Fig. 7A) comprises a memory 42 which transfers portions of its stored information to the slave memory 82 in the analog signal processor in Fig. 7B via lines 41.
  • Integrated circuit 36 includes an analog block 40 containing a voltage doubler (charge pump) and an oscillator controlled by an external crystal at 32,768 Hz.
  • the minus pole of the supply battery is connected to ground and the oscillator starts with the help of a back-up battery.
  • the oscillator starts the voltage doubler which generates negative voltage VSS with the voltage doubler and a buffer capacitor.
  • a voltage level detector is activated and the back-up is connected again to secure the data in the RAM.
  • RAM 42 consists of a total of 896 bits organized in 112 X 8 bits.
  • the 112 groups of bits for each listening situation are divided into 64 bits for slave memory, 4 bits of tele-coil control, and 24 bits for datalogging.
  • a serial channel block 44 is utilized to program and/or read the RAM area by an external programming unit.
  • the data can be written to or read from the hearing aid via serial line connection 111.
  • Timing block 46 keeps track of timing for the different blocks and transfers data and generates clock pulses to the slave memory.
  • the input and test block 48 controls the activities of the external switches and the power reset pulse from the analog block.
  • the datalogging block 50 provides logic for RAM 42 which includes two datalog registers of 12 bits each for each program setting.
  • the first register is incremented whenever a listening situation has been used for more than two minutes.
  • the second register is incremented each fourth minute as long as the listening situation is used.
  • a separate register of 24 bits is incremented whenever a switch 90 has been actuated.
  • the signal processor 38 in Fig. 7B includes a microphone input 52, a tele-coil input 54 and an audio input 56.
  • the tele-coil and microphone inputs are passed through preamplifiers 58 and 60 and digitally controlled attenuators 59 and 61, respectively, and, together with the audio input signal, are summed in SUM unit 62.
  • the output from unit 62 is passed via line 63 to a filter 64 (Fig. 7C) which splits the signal into a low-pass signal and a high-pass signal.
  • the crossover frequency between the low- and high-pass channels can be varied digitally from 500 Hz to 4 KHz.
  • the circuits for the low-pass filter 65 and high-­pass filter 67 are identical and consist of automatic-­gain-controlled amplifiers.
  • the release time of the AGC can be controlled to effect soft clipping (i.e., zero release time), short, normal and long release times.
  • the low- and high-pass channel signals are summed together at 66 via digital attenuators 68 and 70.
  • An output amplifier 72 is provided for receiving the summed output at 66 and driving a transducer 74. Alternatively, an external output amplifier can be used to perform the driving function.
  • the digital portion of the chip 38 includes logic 80 and slave memory 82 (Fig. 7B).
  • the slave memory 82 is a 55-bit non-resettable shift register, where data is shifted into the register in series by each positive clock-transition.
  • the information in the slave memory controls the various functions in the analog circuits.
  • a 64-bit data word is loaded into the slave memory together with 64 clock pulses.
  • the datalogging logic performs three specific logic functions.
  • This logging function is referred to herein as Data-Log Sum (DLS).
  • the second function of the datalog­ging is to record the number of times a particular regis­ter is used for more than 128 seconds (2.13 minutes). There are 12 bits in each of the 8 registers used for this type of logging (4095 events).
  • This logging function is referred to herein as Data Log A (DLA).
  • DLA Data Log A
  • the third func­tion records the amount of time each particular register has been active. Each time count equals 256 seconds (4.27 minutes).
  • Figs. 8-13 are more specific details for the cir­cuitry in Fig. 7B for implementing the datalogging func­tion. While this implementation is hard-wired, it will be appreciated that the functions of the circuitry can be implemented with a programmed microprocessor, for example.
  • the datalogging record-keeping includes UP and DOWN buttons shown at 90 which cause the 8-bit counter 91 to count up and down, so that at any time, one and only one of the 8 outputs B0-B7 is active (high). When this output has changed to a new value and is stable, the DELTA () output generates a pulse, called Memory Select Load.
  • MSL Memory Select Load
  • the free-­running 32768 Hz crystal oscillator 96 causes the divider 93 to begin counting up.
  • divider 93 has counted 222 counts, its output goes high, being 128 seconds after the MSL pulse occurred.
  • the output of the 22-stage divider 93 gives a pulse which is ANDed at gate 97 with one of the selectively connected bits B0 - B7 of up-down counter 91 and the Q output of RS flip-flop 95 set by MSL. This produces an increment to the DLA register 98.
  • the change in the input to the DLA register is used to reset the RS flip-­flop 95, so that only one increment to the DLA register is accomplished per change of the 8-bit up/down counter, and due to the divider 93 this increment occurs only if the state of the counter has remained constant for over two minutes.
  • all registers may be provided with an RS flip-flop (identified by a prime number), which is set whenever the relevant register overflows. In this way, data read out of the hearing aid can be interpreted even with use times exceeding 256 x 212 sec.
  • the hearing aid communicates to the outside world through a serial interface 100 shown in Fig. 9.
  • This communication is managed by conventional logic, which detects appropriate instructions to load the hearing aid from the programmer, or to send information about the hearing aid setting or datalogging information back to the programmer.
  • an access code is checked on the input from the programmer to ensure that changes in the hearing aid program cannot be made inadvertently.
  • the data in the selected register 102 passes through a shift register 101.
  • the internal RAM on the digital circuit 36 is arranged into an XY matrix as shown in Fig. 10. Selecting a memory sets the Y value 0 through 7 in the RAM; specific functions, such as loading the memory into the analog circuit 38 or incrementing the datalogging registers 92, 98 or 99 (Fig. 8), select the X value (that is, the particular 16-bit cell of the matrix) used in the current operation.
  • the contents of the random access memory 104 (Fig. 11) is held by continuous application of a backup voltage 125. When the hearing aid is not in active use, this is the only voltage which is maintained.
  • the RAM 104 is effectively partitioned for each memory into a 64-bit parameter field 105 and a 48-bit field 106 used for datalogging.
  • the organization of the datalogging area is given more specifically in the RAM layout diagram (Fig. 11).
  • the heart of the logic functions to support the pro­grammable hearing aid is the 16-bit register 110 shown in Fig. 12, which serves as: a serial-in, parallel-out register for the incoming data; a parallel-in, serial-out register for programming the hearing aid or reading back the RAM to the host; and a parallel-out, parallel-in in­crementing register for datalogging recording.
  • the com­munications functions host programming, hearing aid pro­gramming, and data read-back) are controlled by a serial interface upon receipt of the appropriate codes.
  • the serial input/output control 116 resets the address coun­ter 112, and begins clocking the data in, 16 bits at a time, over the serial line 111. When each 16 bits accu­mulate, they are transferred to the RAM memory 104. This process continues until the whole memory is rewritten.
  • the serial input/output control 116 When the readout access code is received from the host, the serial input/output control 116 resets the address counter 112 and moves 16 bits into the shift register 110, and begins clocking them out the serial line 111. This process con­tinues until the contents of the whole memory 104 have been sent via the serial line 111.
  • the Y register 113 is changed to reflect the different memory selected.
  • the X register 112 is set at zero, and an operation begins in which four successive 16-bit words are loaded into the shift regis­ter 110 and shifted out to the analog circuit 38 via line 114. Thus, 64 bits of programming information are delivered to the analog chip 38.
  • the counting implemented is as follows: (a) DLSa (LSB) and DLSb (MSB) are incremented immediately upon each change from one memory to another; (b) DLA is incremented once after the first 128 seconds in the same memory; and (c) DLB is incremented every 256 seconds after the incrementation of DLA. Note that in this implementation means the first incrementation of DLB occurs 128 + 256 seconds after memories are changed.
  • This structure is implemented by using the positive-going transition at the output of the 23-bit counter 93 and 94, with the counter arranged in such a fashion that the first positive-going transition occurs at 128 seconds after a reset, but the period of the counter is actually 256 seconds between positive-going transitions.
  • the increment logic is part of the 16-bit shift register 110. Incrementation is implemented by attaching 12 half-adders to the 12 least significant bits of the shift register in incrementer 117. Carry output is latched in carry register 118. The output of carry regis­ter 118 is used in the DLS computation to generate a second increment cycle for DLSb if required.
  • the address generation for DLSa and DLSb in units 112 and 113 is facilitated by sensing exception condi­tions and temporarily redirecting the Y register 113 to that appropriate to memories 0 to 1, and the X register 112 to the last word in those registers.
  • the user returns the hearing aid to the dispenser.
  • the dispenser uses an appropriate connection to the hearing aid to read out the data stored in the datalogging information memory. Using this information, a new set of programs can be stored in memory for the user. Selection of the new programs is based on interpreting the degree to which the original programs are used.
  • the datalogging information can be used not only to revise a hearing prescription for an individual instru­ment; it can also be used for refining the initial pre­scriptions of future patients whose audiometric charac­teristics are similar to those of the user.

Landscapes

  • Health & Medical Sciences (AREA)
  • General Health & Medical Sciences (AREA)
  • Otolaryngology (AREA)
  • Physics & Mathematics (AREA)
  • Engineering & Computer Science (AREA)
  • Acoustics & Sound (AREA)
  • Signal Processing (AREA)
  • Neurosurgery (AREA)
  • Prostheses (AREA)
  • Selective Calling Equipment (AREA)
EP89302689A 1988-03-30 1989-03-17 Prothèse auditive avec capacité de saisie de données Expired - Lifetime EP0335542B1 (fr)

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
US17523388A 1988-03-30 1988-03-30
US175233 1998-10-20

Publications (3)

Publication Number Publication Date
EP0335542A2 true EP0335542A2 (fr) 1989-10-04
EP0335542A3 EP0335542A3 (fr) 1991-09-11
EP0335542B1 EP0335542B1 (fr) 1994-12-21

Family

ID=22639486

Family Applications (1)

Application Number Title Priority Date Filing Date
EP89302689A Expired - Lifetime EP0335542B1 (fr) 1988-03-30 1989-03-17 Prothèse auditive avec capacité de saisie de données

Country Status (8)

Country Link
EP (1) EP0335542B1 (fr)
JP (1) JP2664466B2 (fr)
KR (1) KR890015634A (fr)
AU (1) AU610705B2 (fr)
CA (1) CA1317666C (fr)
DE (1) DE68920060T2 (fr)
DK (1) DK152389A (fr)
MY (1) MY103858A (fr)

Cited By (26)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
EP0341995A2 (fr) * 1988-05-10 1989-11-15 Minnesota Mining And Manufacturing Company Dispositif de calibrage et prothèse auditive comportant des informations de calibrage
WO1990008448A1 (fr) * 1989-01-11 1990-07-26 Tøpholm & Westermann APS Systeme programmable a telecommande pour appareils de correction auditive
WO1991008654A1 (fr) * 1989-11-30 1991-06-13 Nha As Prothese auditive
EP0448764A1 (fr) * 1990-03-30 1991-10-02 Siemens Audiologische Technik GmbH Prothèse auditive électrique programmable
EP0468131A1 (fr) * 1990-06-25 1992-01-29 Robert Bosch Gmbh Elément de mémoire
EP0557847A1 (fr) * 1992-02-27 1993-09-01 Siemens Audiologische Technik GmbH Appareils portatif à tête pour sourds
EP0794687A1 (fr) * 1996-03-04 1997-09-10 Siemens Audiologische Technik GmbH Procédé et dispositif pour déterminer la fonction et la caractéristique de transfer de prothèses auditives
WO1998016086A1 (fr) * 1996-10-10 1998-04-16 Alexandrescu Eugene Instrument auditif programmable ameliore et son procede de programmation
WO2000044198A1 (fr) * 1999-01-25 2000-07-27 Tøpholm & Westermann APS Systeme de correction auditive et appareil de correction auditive destine a etre assemble in situ
WO2001026419A1 (fr) * 1999-09-02 2001-04-12 Beltone Netherlands B.V. Appareil de correction auditive et unite externe pouvant communiquer mutuellement
EP1239269A1 (fr) * 2000-08-29 2002-09-11 Japan as represented by Director-General of National Istitute of Advanced Industrial Science and Technology, Ministry of Econo Procede de mesure sonore et dispositif prenant en compte des caracteristiques de l'audition
EP1320282A2 (fr) * 2003-03-25 2003-06-18 Phonak Ag Procédé d'enregistrement d'information dans une prothèse auditive et une telle prothèse auditive
EP1367857A1 (fr) * 2002-05-30 2003-12-03 GN ReSound as Procédé d'acquisition de données pour prothèses auditives
EP1414271A2 (fr) * 2003-03-25 2004-04-28 Phonak Ag Procédé d'enregistrement d'information dans une prothèse auditive et une telle prothèse auditive
EP1696701A2 (fr) * 2005-02-23 2006-08-30 Siemens Audiologische Technik GmbH Dispositif d'écoute et procédé pour la surveillance de la capacité auditive pour malentendants
EP1708543A1 (fr) * 2005-03-29 2006-10-04 Oticon A/S Prothèse auditive pour l'enregistrement de données et pour l'apprentissage a partir de ces données
WO2007045276A1 (fr) * 2005-10-18 2007-04-26 Widex A/S Prothese auditive comprenant un enregistreur de donnees et mode d'utilisation de cette prothese
WO2007059185A1 (fr) * 2005-11-14 2007-05-24 Audiofusion, Inc. Appareils, systemes et procedes permettant d'attenuer l'acouphene, l'hyperacousie et/ou le deficit auditif
EP1898672A1 (fr) * 2006-09-07 2008-03-12 Siemens Audiologische Technik GmbH Procédé d'adaptation d'un appareil auditif en utilisant une caractéristique morphométrique du porteur de l'appareil auditif
US7349549B2 (en) 2003-03-25 2008-03-25 Phonak Ag Method to log data in a hearing device as well as a hearing device
US8077889B2 (en) 2004-01-27 2011-12-13 Phonak Ag Method to log data in a hearing device as well as a hearing device
US8111851B2 (en) 2006-03-31 2012-02-07 Siemens Audiologische Technik Gmbh Hearing aid with adaptive start values for apparatus
US8588442B2 (en) 2008-11-25 2013-11-19 Phonak Ag Method for adjusting a hearing device
US8644535B2 (en) 2008-10-28 2014-02-04 Siemens Medical Instruments Pte. Ltd. Method for adjusting a hearing device and corresponding hearing device
WO2016162758A1 (fr) * 2015-04-10 2016-10-13 Marcus Andersson Systèmes et procédé d'ajustement des réglages de prothèses auditives
US10499169B2 (en) 2017-02-22 2019-12-03 Sonova Ag Automatically determined user experience value for hearing aid fitting

Families Citing this family (19)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP2970498B2 (ja) * 1995-10-26 1999-11-02 日本電気株式会社 ディジタル補聴器
DE10152197B4 (de) * 2001-10-23 2009-07-09 Siemens Audiologische Technik Gmbh Verfahren zum Programmieren eines Hörgerätes, Programmiergerät sowie Fernbedienung für das Hörgerät
US7650004B2 (en) 2001-11-15 2010-01-19 Starkey Laboratories, Inc. Hearing aids and methods and apparatus for audio fitting thereof
DE10347211A1 (de) 2003-10-10 2005-05-25 Siemens Audiologische Technik Gmbh Verfahren zum Nachtrainieren und Betreiben eines Hörgeräts und entsprechendes Hörgerät
DE102005009530B3 (de) 2005-03-02 2006-08-31 Siemens Audiologische Technik Gmbh Hörhilfevorrichtung mit automatischer Klangspeicherung und entsprechendes Verfahren
US8494193B2 (en) 2006-03-14 2013-07-23 Starkey Laboratories, Inc. Environment detection and adaptation in hearing assistance devices
US8068627B2 (en) 2006-03-14 2011-11-29 Starkey Laboratories, Inc. System for automatic reception enhancement of hearing assistance devices
US7986790B2 (en) * 2006-03-14 2011-07-26 Starkey Laboratories, Inc. System for evaluating hearing assistance device settings using detected sound environment
US8681999B2 (en) 2006-10-23 2014-03-25 Starkey Laboratories, Inc. Entrainment avoidance with an auto regressive filter
CN101711485B (zh) * 2007-04-25 2013-06-12 丹尼尔·R·舒梅尔 用户可编程听力辅助装置
US8718288B2 (en) 2007-12-14 2014-05-06 Starkey Laboratories, Inc. System for customizing hearing assistance devices
US8571244B2 (en) 2008-03-25 2013-10-29 Starkey Laboratories, Inc. Apparatus and method for dynamic detection and attenuation of periodic acoustic feedback
JP5037435B2 (ja) * 2008-06-16 2012-09-26 リオン株式会社 補聴器の調整方法
US9729976B2 (en) 2009-12-22 2017-08-08 Starkey Laboratories, Inc. Acoustic feedback event monitoring system for hearing assistance devices
US8737654B2 (en) 2010-04-12 2014-05-27 Starkey Laboratories, Inc. Methods and apparatus for improved noise reduction for hearing assistance devices
US9654885B2 (en) 2010-04-13 2017-05-16 Starkey Laboratories, Inc. Methods and apparatus for allocating feedback cancellation resources for hearing assistance devices
WO2011132403A1 (fr) * 2010-04-19 2011-10-27 パナソニック株式会社 Dispositif d'installation d'aide auditive
CN103270779A (zh) * 2011-02-10 2013-08-28 松下电器产业株式会社 脑电波记录装置、助听器、脑电波记录方法以及其程序
US8958586B2 (en) 2012-12-21 2015-02-17 Starkey Laboratories, Inc. Sound environment classification by coordinated sensing using hearing assistance devices

Citations (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO1986001671A1 (fr) * 1984-08-28 1986-03-13 Central Institute For The Deaf Systeme et methode pour la compensation de defauts de l'ouie
EP0175909A1 (fr) * 1984-08-28 1986-04-02 Siemens Audiologische Technik GmbH Appareil auditif
DE3642828A1 (de) * 1986-02-03 1987-08-13 Toepholm & Westermann Programmierbares hoergeraet

Family Cites Families (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4435481A (en) * 1979-03-30 1984-03-06 Alloy Surfaces Company, Inc. Pyrophoric foil and article, and pyrophoric technique
SE428167B (sv) * 1981-04-16 1983-06-06 Mangold Stephan Programmerbar signalbehandlingsanordning, huvudsakligen avsedd for personer med nedsatt horsel
US4947432B1 (en) * 1986-02-03 1993-03-09 Programmable hearing aid

Patent Citations (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO1986001671A1 (fr) * 1984-08-28 1986-03-13 Central Institute For The Deaf Systeme et methode pour la compensation de defauts de l'ouie
EP0175909A1 (fr) * 1984-08-28 1986-04-02 Siemens Audiologische Technik GmbH Appareil auditif
DE3642828A1 (de) * 1986-02-03 1987-08-13 Toepholm & Westermann Programmierbares hoergeraet

Cited By (44)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
EP0341995A2 (fr) * 1988-05-10 1989-11-15 Minnesota Mining And Manufacturing Company Dispositif de calibrage et prothèse auditive comportant des informations de calibrage
EP0341995A3 (fr) * 1988-05-10 1991-05-22 Minnesota Mining And Manufacturing Company Dispositif de calibrage et prothèse auditive comportant des informations de calibrage
WO1990008448A1 (fr) * 1989-01-11 1990-07-26 Tøpholm & Westermann APS Systeme programmable a telecommande pour appareils de correction auditive
US5202927A (en) * 1989-01-11 1993-04-13 Topholm & Westermann Aps Remote-controllable, programmable, hearing aid system
WO1991008654A1 (fr) * 1989-11-30 1991-06-13 Nha As Prothese auditive
EP0448764A1 (fr) * 1990-03-30 1991-10-02 Siemens Audiologische Technik GmbH Prothèse auditive électrique programmable
EP0468131A1 (fr) * 1990-06-25 1992-01-29 Robert Bosch Gmbh Elément de mémoire
EP0557847A1 (fr) * 1992-02-27 1993-09-01 Siemens Audiologische Technik GmbH Appareils portatif à tête pour sourds
US5524150A (en) * 1992-02-27 1996-06-04 Siemens Audiologische Technik Gmbh Hearing aid providing an information output signal upon selection of an electronically set transmission parameter
EP0794687A1 (fr) * 1996-03-04 1997-09-10 Siemens Audiologische Technik GmbH Procédé et dispositif pour déterminer la fonction et la caractéristique de transfer de prothèses auditives
WO1998016086A1 (fr) * 1996-10-10 1998-04-16 Alexandrescu Eugene Instrument auditif programmable ameliore et son procede de programmation
US5909497A (en) * 1996-10-10 1999-06-01 Alexandrescu; Eugene Programmable hearing aid instrument and programming method thereof
WO2000044198A1 (fr) * 1999-01-25 2000-07-27 Tøpholm & Westermann APS Systeme de correction auditive et appareil de correction auditive destine a etre assemble in situ
AU751154B2 (en) * 1999-01-25 2002-08-08 Widex A/S Hearing aid system and hearing aid for in-situ fitting
US7239711B1 (en) 1999-01-25 2007-07-03 Widex A/S Hearing aid system and hearing aid for in-situ fitting
WO2001026419A1 (fr) * 1999-09-02 2001-04-12 Beltone Netherlands B.V. Appareil de correction auditive et unite externe pouvant communiquer mutuellement
EP1239269A1 (fr) * 2000-08-29 2002-09-11 Japan as represented by Director-General of National Istitute of Advanced Industrial Science and Technology, Ministry of Econo Procede de mesure sonore et dispositif prenant en compte des caracteristiques de l'audition
EP1239269A4 (fr) * 2000-08-29 2007-12-19 Nat Inst Of Advanced Ind Scien Procede de mesure sonore et dispositif prenant en compte des caracteristiques de l'audition
US7242777B2 (en) 2002-05-30 2007-07-10 Gn Resound A/S Data logging method for hearing prosthesis
EP1367857A1 (fr) * 2002-05-30 2003-12-03 GN ReSound as Procédé d'acquisition de données pour prothèses auditives
EP1320282A2 (fr) * 2003-03-25 2003-06-18 Phonak Ag Procédé d'enregistrement d'information dans une prothèse auditive et une telle prothèse auditive
EP1414271A3 (fr) * 2003-03-25 2009-03-04 Phonak Ag Procédé d'enregistrement d'information dans une prothèse auditive et une telle prothèse auditive
US7349549B2 (en) 2003-03-25 2008-03-25 Phonak Ag Method to log data in a hearing device as well as a hearing device
EP1414271A2 (fr) * 2003-03-25 2004-04-28 Phonak Ag Procédé d'enregistrement d'information dans une prothèse auditive et une telle prothèse auditive
EP1320282A3 (fr) * 2003-03-25 2004-01-07 Phonak Ag Procédé d'enregistrement d'information dans une prothèse auditive et une telle prothèse auditive
US8077889B2 (en) 2004-01-27 2011-12-13 Phonak Ag Method to log data in a hearing device as well as a hearing device
EP1696701A3 (fr) * 2005-02-23 2007-04-25 Siemens Audiologische Technik GmbH Dispositif d'écoute et procédé pour la surveillance de la capacité auditive pour malentendants
EP1696701A2 (fr) * 2005-02-23 2006-08-30 Siemens Audiologische Technik GmbH Dispositif d'écoute et procédé pour la surveillance de la capacité auditive pour malentendants
US8085961B2 (en) 2005-02-23 2011-12-27 Siemens Audiologische Technik Gmbh Hearing device and method for monitoring the hearing ability of a person with impaired hearing
EP2986033A1 (fr) * 2005-03-29 2016-02-17 Oticon A/s Prothèse auditive permettant d'enregistrer des données et apprentissage à partir de celle-ci
US7738667B2 (en) 2005-03-29 2010-06-15 Oticon A/S Hearing aid for recording data and learning therefrom
EP1708543A1 (fr) * 2005-03-29 2006-10-04 Oticon A/S Prothèse auditive pour l'enregistrement de données et pour l'apprentissage a partir de ces données
US8406440B2 (en) 2005-10-18 2013-03-26 Widex A/S Hearing aid and method of operating a hearing aid
WO2007045276A1 (fr) * 2005-10-18 2007-04-26 Widex A/S Prothese auditive comprenant un enregistreur de donnees et mode d'utilisation de cette prothese
WO2007059185A1 (fr) * 2005-11-14 2007-05-24 Audiofusion, Inc. Appareils, systemes et procedes permettant d'attenuer l'acouphene, l'hyperacousie et/ou le deficit auditif
US8306248B2 (en) 2005-11-14 2012-11-06 Digiovanni Jeffrey J Apparatus, systems and methods for relieving tinnitus, hyperacusis and/or hearing loss
US8111851B2 (en) 2006-03-31 2012-02-07 Siemens Audiologische Technik Gmbh Hearing aid with adaptive start values for apparatus
EP1898672A1 (fr) * 2006-09-07 2008-03-12 Siemens Audiologische Technik GmbH Procédé d'adaptation d'un appareil auditif en utilisant une caractéristique morphométrique du porteur de l'appareil auditif
US8644535B2 (en) 2008-10-28 2014-02-04 Siemens Medical Instruments Pte. Ltd. Method for adjusting a hearing device and corresponding hearing device
US8588442B2 (en) 2008-11-25 2013-11-19 Phonak Ag Method for adjusting a hearing device
WO2016162758A1 (fr) * 2015-04-10 2016-10-13 Marcus Andersson Systèmes et procédé d'ajustement des réglages de prothèses auditives
US10477325B2 (en) 2015-04-10 2019-11-12 Cochlear Limited Systems and method for adjusting auditory prostheses settings
US11904166B2 (en) 2015-04-10 2024-02-20 Cochlear Limited Systems and method for adjusting auditory prostheses settings
US10499169B2 (en) 2017-02-22 2019-12-03 Sonova Ag Automatically determined user experience value for hearing aid fitting

Also Published As

Publication number Publication date
KR890015634A (ko) 1989-10-30
DK152389A (da) 1989-10-01
CA1317666C (fr) 1993-05-11
MY103858A (en) 1993-09-30
JPH0243900A (ja) 1990-02-14
EP0335542B1 (fr) 1994-12-21
DK152389D0 (da) 1989-03-29
DE68920060D1 (de) 1995-02-02
JP2664466B2 (ja) 1997-10-15
AU610705B2 (en) 1991-05-23
AU3142089A (en) 1989-10-05
EP0335542A3 (fr) 1991-09-11
DE68920060T2 (de) 1995-09-14

Similar Documents

Publication Publication Date Title
EP0335542B1 (fr) Prothèse auditive avec capacité de saisie de données
US4972487A (en) Auditory prosthesis with datalogging capability
US4187413A (en) Hearing aid with digital processing for: correlation of signals from plural microphones, dynamic range control, or filtering using an erasable memory
US6829363B2 (en) Hearing aid with time-varying performance
US20040190737A1 (en) Method for recording information in a hearing device as well as a hearing device
JP3113661B2 (ja) 校正装置および校正情報を持つ人工耳
US5604812A (en) Programmable hearing aid with automatic adaption to auditory conditions
EP0341903B1 (fr) Interface et méthode de programmation pour prothèse auditive
AU579890B2 (en) Hearing aids, signal supplying apparatus, systems for compensating hearing deficiencies, and methods
EP2667640B1 (fr) Dispositif auditif pouvant être programmé par un utilisateur
JP2782475B2 (ja) 遠隔制御可能、特にプログラム可能な補聴器系
JPH0683517B2 (ja) プログラム可能な補聴器
EP0341997B1 (fr) Ajustage de prothèses auditives en utilisant des vecteurs
US8396237B2 (en) Preprogrammed hearing assistance device with program selection using a multipurpose control device
US6240194B1 (en) Hearing aid with external frequency control
EP2140725B1 (fr) Dispositif auditif pouvant être programmé par un utilisateur
GB2184629A (en) Compensation of hearing
US6130950A (en) Hearing aid which allows non-computerized individual adjustment of signal processing stages
McDermott A programmable sound processor for advanced hearing aid research
US7031481B2 (en) Hearing aid with delayed activation
EP1310138A1 (fr) Prothese auditive dotee d'une activation retardee
JP2529432B2 (ja) 補聴器
AU2009222611B2 (en) Preprogrammed hearing assistance device with program selection using a multipurpose control device
AU2004218723A1 (en) External speech processor unit for an auditory prosthesis

Legal Events

Date Code Title Description
PUAI Public reference made under article 153(3) epc to a published international application that has entered the european phase

Free format text: ORIGINAL CODE: 0009012

AK Designated contracting states

Kind code of ref document: A2

Designated state(s): CH DE FR GB LI NL SE

PUAL Search report despatched

Free format text: ORIGINAL CODE: 0009013

AK Designated contracting states

Kind code of ref document: A3

Designated state(s): CH DE FR GB LI NL SE

17P Request for examination filed

Effective date: 19920204

17Q First examination report despatched

Effective date: 19930727

GRAA (expected) grant

Free format text: ORIGINAL CODE: 0009210

AK Designated contracting states

Kind code of ref document: B1

Designated state(s): CH DE FR GB LI NL SE

EAL Se: european patent in force in sweden

Ref document number: 89302689.8

REF Corresponds to:

Ref document number: 68920060

Country of ref document: DE

Date of ref document: 19950202

RAP2 Party data changed (patent owner data changed or rights of a patent transferred)

Owner name: 3M HEARING HEALTH AKTIEBOLAG

REG Reference to a national code

Ref country code: CH

Ref legal event code: PUE

Owner name: 3M HEARING HEALTH AKTIEBOLAG

ET Fr: translation filed
PLBI Opposition filed

Free format text: ORIGINAL CODE: 0009260

26 Opposition filed

Opponent name: TOPHOLM & WESTERMANN APS

Effective date: 19950628

NLR1 Nl: opposition has been filed with the epo

Opponent name: TOPHOLM & WESTERMANN APS

PLBF Reply of patent proprietor to notice(s) of opposition

Free format text: ORIGINAL CODE: EPIDOS OBSO

PLBF Reply of patent proprietor to notice(s) of opposition

Free format text: ORIGINAL CODE: EPIDOS OBSO

REG Reference to a national code

Ref country code: CH

Ref legal event code: PL

REG Reference to a national code

Ref country code: CH

Ref legal event code: AEN

Free format text: DAS PATENT IST AUFGRUND DES WEITERBEHANDLUNGSANTRAGS VOM28.11.1996 WIEDER AKTIVIERT WORDEN.

PLBL Opposition procedure terminated

Free format text: ORIGINAL CODE: EPIDOS OPPC

PLBM Termination of opposition procedure: date of legal effect published

Free format text: ORIGINAL CODE: 0009276

STAA Information on the status of an ep patent application or granted ep patent

Free format text: STATUS: OPPOSITION PROCEDURE CLOSED

REG Reference to a national code

Ref country code: CH

Ref legal event code: PUE

Owner name: 3M HEARING HEALTH AKTIEBOLAG TRANSFER- RESOUND COR

27C Opposition proceedings terminated

Effective date: 19970331

NLR2 Nl: decision of opposition
NLS Nl: assignments of ep-patents

Owner name: K/S HIMPP;RESOUND CORPORATION

REG Reference to a national code

Ref country code: FR

Ref legal event code: TP

PGFP Annual fee paid to national office [announced via postgrant information from national office to epo]

Ref country code: SE

Payment date: 19980219

Year of fee payment: 10

REG Reference to a national code

Ref country code: GB

Ref legal event code: 732E

PG25 Lapsed in a contracting state [announced via postgrant information from national office to epo]

Ref country code: SE

Free format text: LAPSE BECAUSE OF NON-PAYMENT OF DUE FEES

Effective date: 19990318

EUG Se: european patent has lapsed

Ref document number: 89302689.8

EUG Se: european patent has lapsed

Ref document number: 89302689.8

REG Reference to a national code

Ref country code: GB

Ref legal event code: IF02

PGFP Annual fee paid to national office [announced via postgrant information from national office to epo]

Ref country code: NL

Payment date: 20030305

Year of fee payment: 15

PGFP Annual fee paid to national office [announced via postgrant information from national office to epo]

Ref country code: CH

Payment date: 20030306

Year of fee payment: 15

PG25 Lapsed in a contracting state [announced via postgrant information from national office to epo]

Ref country code: LI

Free format text: LAPSE BECAUSE OF NON-PAYMENT OF DUE FEES

Effective date: 20040331

Ref country code: CH

Free format text: LAPSE BECAUSE OF NON-PAYMENT OF DUE FEES

Effective date: 20040331

PG25 Lapsed in a contracting state [announced via postgrant information from national office to epo]

Ref country code: NL

Free format text: LAPSE BECAUSE OF NON-PAYMENT OF DUE FEES

Effective date: 20041001

REG Reference to a national code

Ref country code: CH

Ref legal event code: PL

NLV4 Nl: lapsed or anulled due to non-payment of the annual fee

Effective date: 20041001

PGFP Annual fee paid to national office [announced via postgrant information from national office to epo]

Ref country code: GB

Payment date: 20080327

Year of fee payment: 20

PGFP Annual fee paid to national office [announced via postgrant information from national office to epo]

Ref country code: DE

Payment date: 20080430

Year of fee payment: 20

Ref country code: FR

Payment date: 20080317

Year of fee payment: 20

REG Reference to a national code

Ref country code: GB

Ref legal event code: PE20

Expiry date: 20090316

PG25 Lapsed in a contracting state [announced via postgrant information from national office to epo]

Ref country code: GB

Free format text: LAPSE BECAUSE OF EXPIRATION OF PROTECTION

Effective date: 20090316