WO2003099179A1 - Production de stimuli electriques pour application a un implant cochleaire - Google Patents

Production de stimuli electriques pour application a un implant cochleaire Download PDF

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Publication number
WO2003099179A1
WO2003099179A1 PCT/AU2003/000639 AU0300639W WO03099179A1 WO 2003099179 A1 WO2003099179 A1 WO 2003099179A1 AU 0300639 W AU0300639 W AU 0300639W WO 03099179 A1 WO03099179 A1 WO 03099179A1
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WO
WIPO (PCT)
Prior art keywords
amplitude
spike
electrode
stimulation
spikes
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PCT/AU2003/000639
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English (en)
Inventor
David Bruce Grayden
Anthony Neville Burkitt
Owen Patrick Kenny
Janine Catherine Clarey
Antonio Giacomo Paolini
Peter Francis Duke
Graeme Milbourne Clark
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The Bionic Ear Institute
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Publication date
Application filed by The Bionic Ear Institute filed Critical The Bionic Ear Institute
Priority to JP2004506707A priority Critical patent/JP4763280B2/ja
Priority to AU2003229378A priority patent/AU2003229378B2/en
Priority to CA2487079A priority patent/CA2487079C/fr
Priority to EP03722073A priority patent/EP1555974A4/fr
Publication of WO2003099179A1 publication Critical patent/WO2003099179A1/fr
Priority to US10/996,758 priority patent/US7787956B2/en

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Classifications

    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R25/00—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception
    • H04R25/50—Customised settings for obtaining desired overall acoustical characteristics
    • H04R25/505—Customised settings for obtaining desired overall acoustical characteristics using digital signal processing
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N1/00—Electrotherapy; Circuits therefor
    • A61N1/18—Applying electric currents by contact electrodes
    • A61N1/32—Applying electric currents by contact electrodes alternating or intermittent currents
    • A61N1/36—Applying electric currents by contact electrodes alternating or intermittent currents for stimulation
    • A61N1/36036—Applying electric currents by contact electrodes alternating or intermittent currents for stimulation of the outer, middle or inner ear
    • A61N1/36038—Cochlear stimulation

Definitions

  • the present invention relates generally to the generation of electrical stimuli for application to a cochlea via an auditory prosthesis electrode array.
  • the multi-channel cochlear implant was first implanted in 1978.
  • Early signal processing designs extracted the second formant (F2) and pitch (FO) to control electrode stimulation.
  • the frequency of F2 controlled the location of electrode stimulation, and FO controlled the rate of stimulation. Improvements were made by also extracting the first formant (FI) and adding a second stimulated electrode for each pitch period.
  • the MULTIPEAK stimulation strategy added stimulation of a number of fixed electrodes to better represent high-frequency information.
  • the next stages of development were the Spectral Maxima Sound Processor (SMSP) strategy, described in Australian Patent No. 657,959, and SPEAK strategy, described in US Patent No. 5,597,380.
  • SMSP Spectral Maxima Sound Processor
  • Kitazawa et al. (Kitazawa, S, Muramoto, K. and Ito, J. (1994) "Acoustic simulation of auditory model based speech processor for cochlear implant system", Proceedings of the International Conference on Spoken Language Processing, ICSLP'94, pp. 2043-2046) describes a strategy for the s ⁇ ectra/CI-22 system using an auditory model for choosing electrodes to stimulate and for extracting fundamental frequency to control rate of stimulation. This strategy was tested by simulation with normal hearing listeners. Stimulation was restricted to low rates and required explicit extraction of pitch information. Performance was reduced for word recognition compared to the Wearable Speech Processor (WSP) running MULTIPEAK.
  • WSP Wearable Speech Processor
  • SMSP Short-duration transient speech features
  • PCT/AU00/01310 International Publication Number WO 01/31632 Al
  • TAM Transient Emphasis Spectral Maxima Sound Processor
  • Multi-rate cochlear stimulation strategy and apparatus (PCT/AUOO/00838, International Publication Number WO 01/03622 Al) has been developed that does not use fixed stimulation rates.
  • the strategy determines rate of stimulation for each implant electrode by measuring average intervals between positive zero-crossings of the filtered signals for each band.
  • One aspect of the present invention provides a method for processing sound signals to generate electrical stimuli for an auditory prosthesis electrode array including a plurality of electrodes, the method including: deriving one or more filtered representations of an incoming audio signal; and generating a series of spikes from each filtered representation to directly control electrode stimulation, wherein each spike has a temporal position based upon an instant at which the filtered signal representation crosses a predetermined threshold in a positive direction.
  • the amplitude of each spike may be derived from the amplitude of a filtered signal representation peak following the threshold crossing.
  • Spike amplitude may be equal to the difference between the predetermined threshold and the amplitude of a filtered signal representation peak following the threshold crossing.
  • spike amplitude may equal to the amplitude of a filtered signal representation peak following the threshold crossing.
  • each spike may have a temporal position based upon an instant at which the filtered signal representation crosses a zero axis in a positive direction.
  • the amplitude of each spike may be derived from the amplitude of a filtered signal representation peak following the zero axis crossing.
  • Spike amplitude may be equal to the difference between a predetermined threshold and the amplitude of a filtered signal representation peak following the zero axis crossing.
  • spike amplitude may be equal to the amplitude of a filtered signal representation peak following the zero axis crossing.
  • the method may further include delaying the temporal position of each spike according to a travelling wave delay for a normally hearing person along the length of the electrode array.
  • the method may further include adapting the threshold based on long term average energy of the filtered signal representation.
  • the method may further include computing a neural adaptation variable from an integral of previous spikes in the spike series and from a decay function; and applying a gain derived rom the neural adaptation variable to the amplitude of each spike.
  • the method may further include limiting the number of spikes used to generate the electrical stimuli for each electrode so that the number of times a particular electrode is stimulated within a stimulation sequence window does not exceed a fixed maximum average rate.
  • the method may further include sorting spikes occurring within a stimulation sequence window in order of importance; and selecting a number of the sorted spikes in order of importance to derive an electrode stimulation sequence for generating electrical stimuli.
  • the spike importance may be determined by normalised amplitude.
  • the method may further include configuring normalisation coefficients for comparison and prioritisation of spikes in different frequency regions.
  • the method may further include obtaining the electrode stimulation sequence by progressively placing spikes occurring within the stimulation sequence window in stimulation time slots corresponding to the temporal positions of the spikes in decreasing order of importance from a sorted list of normalised amplitude spikes.
  • the method may further include mapping electrical stimuli to a current level for a particular user using a loudness growth function and stored threshold and comfort levels for that particular user, wherein the mapping uses a special comfort level for short duration transition events to provide increased stimulation levels during neural response adaptation.
  • the method may further include encoding the electrode stimulation sequence; and transmitting the encoded electrode stimulation sequence to the auditory prosthesis electrode array to enable stimulation of an auditory nerve or cochlea nucleus.
  • Another aspect of the invention provides a system for stimulating an auditory prosthesis electrode array, including: a stimulator unit for selectively stimulating electrodes in the electrode array; and a processor for processing received sound signals and control of the operation of the stimulator unit by carrying out a method as previously described.
  • Yet another aspect of the invention provides a processor for use in a system for stimulating an auditory prosthesis electrode array, including a stimulator unit for selectively stimulating electrodes in the electrode array, the processor including digital signal processing means for processing received sound signals and controlling the operation of the stimulator unit by carrying out a method as previously described.
  • the strategy implemented by the present invention simulates the behaviour of the hair cells of the cochlea and of the auditory nerve to create a spike-based representation modelled on action potentials generated in the auditory neurons.
  • the cochlea is electrically stimulated using a sequence of electrical pulses that replicates this spike-based representation as closely as possible within device limitations.
  • the Spike-based Temporal Auditory Representation (STAR) strategy of the present invention improves speech perception ability in the presence of noise, including both pseudo-stationary random noise and multi-talker babble. This is achieved by providing an improved representation of fine-grained temporal information, especially phase locking to formants across multiple stimulation channels.
  • Adaptation effects improve detection of transient events, such as plosive onsets and formant transitions, and help to overcome pseudo- stationary background noise by a neural adaptation process similar to spectral subtraction.
  • the incoming acoustic signal may be passed through a filter bank in which the centre-frequencies are distributed according to an auditory/psychophysics-based distribution of frequencies.
  • the filters may have significant overlap based on equivalent rectangular bandwidth. Either linear or non-linear filters may be used.
  • a series of “spikes” are extracted from each filtered representation of the signal, each spike having a temporal position or “spike time” based upon the instance at which the signal crosses a threshold in a positive-going direction.
  • the amplitude of the spike may be determined by the difference between the threshold and the following maximum of the signal.
  • Neural adaptation effects may be incorporated to emphasise onsets of signals relative to the steady-state amplitudes as is observed in physiological studies.
  • a time-dependent integral may be computed from the series of spikes in each channel (the value of this integral decays in time if there are no subsequent spikes), and a gain applied to the amplitude of each spike by a measure related to this sum.
  • the value of the threshold may be adjusted based on signal history (i.e. threshold adaptation), in order to take account of differing listening conditions and levels of background noise.
  • the amplitudes of the spikes may also be adjusted based on the recent signal history, in order to model neural adaptation effects and allow increased responses at the onset of acoustical stimuli.
  • Electrodes may be stimulated at threshold crossing times (delayed across all electrodes by up to 10 msec to allow peak detection) using stimulus levels proportional to the adapted amplitudes. Owing to limitations in existing cochlear implants, a limited number of electrodes may be chosen for stimulation by selecting channels with the highest normalised average amplitude. Temporal contention (i.e. simultaneous spikes) may be accounted for by systematically shifting spikes to other times based on their importance, which are determined using normalised amplitudes. Average rate of stimulation may be limited on each electrode by ensuring that spikes in high frequency channels are not stimulated above a fixed maximum average rate.
  • the present invention builds upon a rich history of auditory modelling.
  • One of the most prominent such models is that developed by Allen & Ghitza (US Patent 4,905,285) in the context of developing improved strategies for automatic speech recognition based upon the human auditory system.
  • a similar system was developed by Kim et al. (Kim, D-S, Lee, S-Y and Rhee, M (1999) "Auditory processing of speech signals for robust speech recognition in real- world noisy environments", IEEE T-SAP 7(1), 55-69) that used a single zero- crossing measure to locate spikes and determined their amplitudes using the subsequent peak of the filtered signal.
  • the present invention uses a similar auditory model to Kitazawa et al. (1994) for the pre-processing of the incoming waveform, but uses a spike-train directly to control the electrode simulation rather than extract FO explicitly to control rate of stimulation across the electrode array.
  • Explicit extraction of pitch is not required to control the overall rate of stimulation but may be represented by the stimulation sequence of the more apical electrodes and by the amplitude modulation over the whole electrode array.
  • Direct extraction of spike trains with fine-grained temporal information also distinguishes this invention from the Multi-rate strategy.
  • the Travelling Wave Strategy is similar to the STAR strategy of the present invention in that it extracts precise timing information that is useful for higher levels of processing in the cochlear nucleus and other stages of the brainstem.
  • the Travelling Wave Strategy relies on specific basilar membrane properties that are not used in STAR, while STAR relies more on auditory nerve behaviour.
  • the model used by STAR allows various non-linear properties to be implemented such as neural response adaptation and threshold adaptation.
  • the stimulus times of STAR are based on threshold crossing times rather than at times of local maxima as specified for the Travelling Wave Sound Processor.
  • the TESM strategy contains an element similar to the neural adaptation effect that is part of the present invention.
  • the increasing of amplitude of short-duration amplitude transitions in the TESM strategy is based on a direct estimate of the slowly varying signal envelope and then rules are applied for applying a gain factor.
  • a consequence of the method used by TESM is that a delay of 30 ms is introduced in the signal.
  • the present invention applies the adaptation function continuously to the sequence of spikes and does not rely on examination of time periods to estimate gain as TESM does. Thus, not only is the technique different, but no extra time delay is introduced.
  • the following description refers in more detail to the various features of the method and system for generating electrical stimuli of the present invention. To facilitate an understanding of the invention, reference is made in the description to the accompanying drawings where the invention is illustrated in a preferred embodiment. It is to be understood however, that the invention is not limited to the preferred embodiment as shown in the drawings.
  • Figure 1 is a schematic diagram of one embodiment of a system for stimulating an electrode array implanted into a cochlea
  • Figure 2 is a schematic diagram showing the function blocks of a processor forming part of the electrode stimulation system of Figure 1;
  • Figure 3 is an exemplary filtered representation of an audio signal received by the electrode stimulation system of Figure 1.
  • FIG. 1 there is shown generally a system for stimulating an electrode array in accordance with a processed signal.
  • -An electrode array 1 implanted into a cochlea, connects via cable 2 to a receiver- stimulator unit (RSU) 3.
  • RSU receiver- stimulator unit
  • the implanted system receives control signals and power from an external speech processor unit, preferably via a tuned coil RF system 5, 6 as illustrated.
  • any alternative connection technique such as percutaneous connection may be employed.
  • the coil 6 carries a signal modulated by the processor 7 so as to cause the
  • the processor 7 receives electrical analog signals from a microphone 8 worn by the user.
  • the present invention is concerned with the operation of the processor and particularly the method of processing the incoming electrical signal.
  • FIG. 2 illustrates the various functional blocks of the processor 7, including a pre-filtering & ADC block 9, a filter bank 10, a spike generation block 11, a spike adaptation block 12, a stimulation selection & ordering block 13 and a loudness growth function block 14.
  • the pre-filtering & ADC block 9 may be implemented using known electronic circuitry and analog signal sampling techniques, whilst the functional blocks 10 to 14 may be implemented using known digital signal processing techniques.
  • Sound is recorded by the microphone 8, which may inherently apply pre- emphasis to the incoming signal.
  • This signal is low-pass filtered, to prevent aliasing during sampling, and is then sampled by an analog-to-digital converter in the pre-filtering and ADC block 9 .
  • the signal is sampled by the analog-to-digital converter at 14.4 kHz.
  • the digitally sampled audio signal is passed through the filter bank 10 spanning the region of approximately 200-7200 Hz.
  • the number of filters will depend on the cochlear implant device used and the number of electrodes available for a particular implant user, which is typically 22 channels in the Cochlear Ltd NucleusTM electrode array but varies across devices.
  • the centre- frequencies (CFs) of the filters are distributed using a psychophysical pitch scale, such as mel-scale or bark scale, in a similar way to standard frequency distributions for electrodes in commonly used cochlear implant frequency- electrode maps.
  • the filter bandwidth is proportional to the equivalent rectangular bandwidth obtained from the psychophysical critical band measurements.
  • the filter bank is designed along the lines of that designed by Kim et al. (1999, op cit) for automatic speech recognition, except that the number of filters is different and IIR filters may be used instead of FIR filters.
  • Spikes are generated in the spike generation block 11 from the filtered signal representation in a manner similar to that used by Kim et al. (1999, op cit) except that threshold-crossing times rather than zero-crossing times are used. This allows adaptation of the strategy to ambient long-term noise levels.
  • a spike is generated at time t ⁇ of a positive-going crossing of the threshold ⁇ .
  • An amplitude a s is assigned to the spike by subtracting the peak amplitude a p from the threshold ⁇ .
  • the peak amplitude is found by searching ahead in the channel for the maximum amplitude of the filtered signal representation before a following negative-going threshold crossing. The search is limited to 10 ms, or 1440 samples, to prevent significant processing time lag in the strategy.
  • the temporal position of each spike is delayed by a travelling wave delay that would exist for a normally hearing person along the length of the electrode array
  • C D the traveling wave delay coefficient
  • C L the length coefficient for the traveling wave delay
  • x(n) the propagation distance for electrode n .
  • x(n) is the distance of electrode n from the most basal electrode that is in use. In another implementation of the invention, x(n) is computed by determining the effective distance of electrode n from the round window based on the location in the normal cochlea of the centre frequency of the filter for that electrode using a frequency-place map function.
  • each spike has a temporal position based upon an instant at which the filtered signal representation crosses the threshold ⁇ in a positive direction.
  • the amplitude of each spike is derived from the amplitude a p of the filtered signal representation peak following the threshold crossing.
  • spike amplitude is equal to the difference between the threshold ⁇ and the amplitude a p .
  • spike amplitude may alternatively be equal to the amplitude a itself.
  • the threshold may be the zero axis and each spike may have a temporal position based upon an instant at which the filtered signal representation crosses the zero axis (referenced 0 in Figure 3) in a positive direction.
  • the amplitude of each spike may be derived from the amplitude a p of a filtered signal representation peak following the zero axis crossing.
  • Spike amplitude may be equal to the difference between the threshold ⁇ and the amplitude a p .
  • spike amplitude may be equal to the amplitude a p itself.
  • Adaptation effects modelled on neural adaptation are applied to each generated spike by the spike adaptation block 12 based on the previous history of the spike train in each channel.
  • the adaptation is controlled by a variable obtained by integrating over all previous spikes with an appropriate decay function.
  • a gain derived from the adaptation variable is applied to the spike amplitude (a s ) to obtain an adapted version (af) that may be greater than the original amplitude when the integral is small. With sustained activity, the integral will increase thus making af reduce back to a s .
  • the equation for this complete operation is
  • C A is the maximum value permissible for an adapted spike
  • C s is the maximum sustained amplitude permissible for a spike sequence
  • ⁇ A is a normalising term to control rate of adaptation
  • ⁇ A is a time constant controlling rate of decay of previous spike train influence on the current spike
  • t s is the time of the current spike
  • t s represents the times of the previous spikes
  • a s represents the amplitudes of the previous spikes.
  • the spike adaptation block 12 also acts to adapt the value of the threshold based on the long-term average energy of the filtered signal representation.
  • the threshold, ⁇ is adjusted by the previous sequence of generated spikes for each filter.
  • An equation of the form ⁇ , ⁇ s _ ⁇ e- t °- ⁇ l ⁇ » + C n a s
  • ⁇ s is the new threshold computed after the generation of the current spike s at time t s , based on the previous threshold ⁇ s _ ⁇ that was computed at the previous spike time t s _ x .
  • the time constant ⁇ n is set for each filter based on the centre frequency of that filter to control the rate of decay of the threshold.
  • the value a s is the amplitude of the current spike, which was computed using the threshold established for the previous spike, and C n is a constant for each filter to control the rate of growth of the threshold.
  • the maximum pulse rate delivered to a single cochlear implant electrode may be limited to a fixed maximum average rate. This may be usually controlled by limiting the maximum average stimulation rate per electrode, for example, to 2000 pulses per second (pps).
  • the cochlear implant has a maximum possible total rate of stimulation. For example, in the Cochlear CI-24M device, this is 14,400 pps.
  • Stimulation of multiple electrodes should be non-simultaneous to avoid current interactions within the cochlea. Therefore, there should be a means of arbitrating contention between spikes with simultaneous arrival times.
  • T and C should be established for each user and for each electrode.
  • T and C levels should be established for each user and for each electrode.
  • Overall adjustments of T and C levels may often be made, usually downward, after fitting the map to account for loudness summation across multiple electrodes when the device is actually being used with sound input.
  • a loudness growth function (LGF) should be applied to transform spike height to current level.
  • the minimum time between successive stimuli on a single electrode should be, on average, greater than or equal to 0.5 ms.
  • a maximum total stimulation rate for an implant of 14,400 Hz provides about 0.07 ms per stimulus.
  • T E 7.2 stimulation intervals.
  • the spikes from each channel that occur with the window T w are then considered for selection as electrode stimuli.
  • the spikes may be combined across channels and are ordered by normalised amplitude.
  • the normalisation is determined from configuration of the entire prosthesis, particularly the characteristics of the microphone 8 and the filter bank 10, as well as the properties of speech, so that the priority of spikes in different frequency regions can be incorporated into the sorting procedure.
  • the list of sorted normalised amplitude spikes is progressively examined to obtain a stimulation sequence for the window T w .
  • the top candidate is selected (i.e. the candidate with the largest normalised amplitude) and a stimulation pulse is placed in a stimulation time slot corresponding to the closest time to the spike time t s .
  • the process continues until all time slots within T w have been filled. If a stimulation pulse is to be placed in a slot that is already filled, then neighbouring slots are examined in the following order: [-1 +1 -2 +2 -3 +3 ...] where -1 indicates the previous slot, +1 is the next slot, -2 is the slot before the previous one, etc. Only slots within window T w may be examined in this way.
  • the stimuli are mapped to current levels using the standard loudness growth function (LGF) and the stored map (T and C levels) for the user by the loudness growth function block 14.
  • LGF is a logarithmic function relating stimulus level to loudness to obtain an appropriate increase in subjective loudness.
  • the stored map specifies the minimum and maximum current levels permitted for a user.
  • a special C level may be specified for short duration transient events to allow increased levels during an adaptation step.
  • the stimulus sequence is then transmitted to the receiver-stimulus unit 3 that interfaces with the cochlear implant and encodes the electrode selection and current level information to the device.

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  • Health & Medical Sciences (AREA)
  • Otolaryngology (AREA)
  • Engineering & Computer Science (AREA)
  • General Health & Medical Sciences (AREA)
  • Nuclear Medicine, Radiotherapy & Molecular Imaging (AREA)
  • Radiology & Medical Imaging (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Animal Behavior & Ethology (AREA)
  • Biomedical Technology (AREA)
  • Public Health (AREA)
  • Veterinary Medicine (AREA)
  • Neurosurgery (AREA)
  • Physics & Mathematics (AREA)
  • Acoustics & Sound (AREA)
  • Signal Processing (AREA)
  • Prostheses (AREA)
  • Electrotherapy Devices (AREA)

Abstract

L'invention concerne un procédé de traitement de signaux sonores destiné à produire des stimuli électriques pour un réseau d'électrodes de prothèse auditive comprenant une pluralité d'électrodes. Ce procédé comprend les étapes consistant: à distribuer (10) une ou plusieurs représentations filtrées (voir figure) d'un signal audio entrant; et à produire (11) une série de variations à partir de chaque représentation filtrée de signal afin de commander directement la stimulation des électrodes. Chaque variation présente une position temporale fondée sur un instant auquel la représentation filtrée de signal dépasse un seuil prédéterminé (?;0) dans un sens positif.
PCT/AU2003/000639 2002-05-27 2003-05-26 Production de stimuli electriques pour application a un implant cochleaire WO2003099179A1 (fr)

Priority Applications (5)

Application Number Priority Date Filing Date Title
JP2004506707A JP4763280B2 (ja) 2002-05-27 2003-05-26 蝸牛に加える電気刺激の発生
AU2003229378A AU2003229378B2 (en) 2002-05-27 2003-05-26 Generation of electrical stimuli for application to a cochlea
CA2487079A CA2487079C (fr) 2002-05-27 2003-05-26 Production de stimuli electriques pour application a un implant cochleaire
EP03722073A EP1555974A4 (fr) 2002-05-27 2003-05-26 Production de stimuli electriques pour application a un implant cochleaire
US10/996,758 US7787956B2 (en) 2002-05-27 2004-11-24 Generation of electrical stimuli for application to a cochlea

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AUPS2590A AUPS259002A0 (en) 2002-05-27 2002-05-27 Generation of electrical stimuli for application to a cochlea
AUPS2590 2002-05-27

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WO2005057983A1 (fr) * 2003-12-10 2005-06-23 The Bionic Ear Institute Stimulation retardee dans des protheses auditives
WO2007028123A2 (fr) 2005-09-01 2007-03-08 Alfred E. Mann Institute For Biomedical Engineering At The University Of Southern California Pose d'implant cochleaire
US7495998B1 (en) * 2005-04-29 2009-02-24 Trustees Of Boston University Biomimetic acoustic detection and localization system
EP3499914A1 (fr) * 2017-12-13 2019-06-19 Oticon A/s Système d'aide auditive
CN115174032A (zh) * 2021-03-19 2022-10-11 托多克有限公司 线圈之间数据传递装置及数据读取方法

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WO2002032501A1 (fr) * 2000-10-19 2002-04-25 Universite De Sherbrooke Neurostimulateur programmable

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WO1991003913A1 (fr) * 1989-09-08 1991-03-21 Cochlear Pty. Limited Processeur de la parole multicrete
US5749912A (en) * 1994-10-24 1998-05-12 House Ear Institute Low-cost, four-channel cochlear implant
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WO2002032501A1 (fr) * 2000-10-19 2002-04-25 Universite De Sherbrooke Neurostimulateur programmable

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Cited By (13)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US8065016B2 (en) 2003-12-10 2011-11-22 The Bionic Ear Institute Delayed stimulation in auditory prostheses
JP2007521855A (ja) * 2003-12-10 2007-08-09 ザ バイオニック イヤ インスティテュート 聴覚人工器官内における遅延した刺激
WO2005057983A1 (fr) * 2003-12-10 2005-06-23 The Bionic Ear Institute Stimulation retardee dans des protheses auditives
US7495998B1 (en) * 2005-04-29 2009-02-24 Trustees Of Boston University Biomimetic acoustic detection and localization system
US7885714B2 (en) 2005-09-01 2011-02-08 University Of Southern California Cochlear implant fitting
EP1931415A4 (fr) * 2005-09-01 2009-11-11 Univ Southern California Pose d'implant cochleaire
EP1931415A2 (fr) * 2005-09-01 2008-06-18 Alfred E. Mann Institute for Biomedical Engineering at the University of Southern California Pose d'implant cochleaire
WO2007028123A2 (fr) 2005-09-01 2007-03-08 Alfred E. Mann Institute For Biomedical Engineering At The University Of Southern California Pose d'implant cochleaire
EP3499914A1 (fr) * 2017-12-13 2019-06-19 Oticon A/s Système d'aide auditive
CN110062318A (zh) * 2017-12-13 2019-07-26 奥迪康有限公司 助听器系统
US10542355B2 (en) 2017-12-13 2020-01-21 Oticon A/S Hearing aid system
CN110062318B (zh) * 2017-12-13 2022-03-04 奥迪康有限公司 助听器系统
CN115174032A (zh) * 2021-03-19 2022-10-11 托多克有限公司 线圈之间数据传递装置及数据读取方法

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EP1555974A1 (fr) 2005-07-27
CA2487079C (fr) 2011-09-06
JP4763280B2 (ja) 2011-08-31
CA2487079A1 (fr) 2003-12-04
EP1555974A4 (fr) 2007-06-20
JP2006520613A (ja) 2006-09-14

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