WO2015170140A1 - Systèmes et procédés d'annulation de bruit tonal dans un système d'implant cochléaire - Google Patents

Systèmes et procédés d'annulation de bruit tonal dans un système d'implant cochléaire Download PDF

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Publication number
WO2015170140A1
WO2015170140A1 PCT/IB2014/061224 IB2014061224W WO2015170140A1 WO 2015170140 A1 WO2015170140 A1 WO 2015170140A1 IB 2014061224 W IB2014061224 W IB 2014061224W WO 2015170140 A1 WO2015170140 A1 WO 2015170140A1
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Prior art keywords
input signal
signal
sound processor
noise
cochlear implant
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PCT/IB2014/061224
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English (en)
Inventor
Udayan R. KANADE
Sanat D. GANU
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Advanced Bionics Ag
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Priority to PCT/IB2014/061224 priority Critical patent/WO2015170140A1/fr
Publication of WO2015170140A1 publication Critical patent/WO2015170140A1/fr

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Classifications

    • G—PHYSICS
    • G10—MUSICAL INSTRUMENTS; ACOUSTICS
    • G10L—SPEECH ANALYSIS OR SYNTHESIS; SPEECH RECOGNITION; SPEECH OR VOICE PROCESSING; SPEECH OR AUDIO CODING OR DECODING
    • G10L21/00—Processing of the speech or voice signal to produce another audible or non-audible signal, e.g. visual or tactile, in order to modify its quality or its intelligibility
    • G10L21/02—Speech enhancement, e.g. noise reduction or echo cancellation
    • G10L21/0208—Noise filtering
    • 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
    • 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
    • H04R25/43—Electronic input selection or mixing based on input signal analysis, e.g. mixing or selection between microphone and telecoil or between microphones with different directivity characteristics
    • G—PHYSICS
    • G10—MUSICAL INSTRUMENTS; ACOUSTICS
    • G10L—SPEECH ANALYSIS OR SYNTHESIS; SPEECH RECOGNITION; SPEECH OR VOICE PROCESSING; SPEECH OR AUDIO CODING OR DECODING
    • G10L21/00—Processing of the speech or voice signal to produce another audible or non-audible signal, e.g. visual or tactile, in order to modify its quality or its intelligibility
    • G10L21/02—Speech enhancement, e.g. noise reduction or echo cancellation
    • G10L21/0208—Noise filtering
    • G10L2021/02085—Periodic noise
    • G—PHYSICS
    • G10—MUSICAL INSTRUMENTS; ACOUSTICS
    • G10L—SPEECH ANALYSIS OR SYNTHESIS; SPEECH RECOGNITION; SPEECH OR VOICE PROCESSING; SPEECH OR AUDIO CODING OR DECODING
    • G10L21/00—Processing of the speech or voice signal to produce another audible or non-audible signal, e.g. visual or tactile, in order to modify its quality or its intelligibility
    • G10L21/02—Speech enhancement, e.g. noise reduction or echo cancellation
    • G10L21/0208—Noise filtering
    • G10L21/0216—Noise filtering characterised by the method used for estimating noise

Definitions

  • a telecoil which is configured to detect electromagnetic fields representative of audio content. Such electromagnetic fields may be generated by telephones, audio induction loops, and/or other types of assistive listening systems.
  • a telecoil may be used in place of (or in addition to) a microphone as the audio input source to a cochlear implant system, and, in some cases, may provide a cochlear implant user with a clearer, more accurate representation of sound than the microphone.
  • a telecoil can also detect electromagnetic fields produced by various sources associated with (e.g., internal to) a cochlear implant system.
  • a telecoil may detect tonal noise (i.e., discrete frequency noise) produced by a cochlear implant system's power supply.
  • tonal noise i.e., discrete frequency noise
  • the fundamental frequency of such tonal noise may change over time. For example, as the voltage level of a battery included in a cochlear implant system's power supply depletes over time, the frequency at which the power supply operates may change to
  • FIG. 1 illustrates an exemplary cochlear implant system according to principles described herein.
  • FIG. 2 illustrates a schematic structure of the human cochlea according to principles described herein.
  • FIG. 3 illustrates exemplary components of a sound processor according to principles described herein.
  • FIGS. 4-6 illustrate exemplary configurations of the sound processor of FIG. 3 according to principles described herein.
  • FIG. 7 illustrates exemplary components of a filter system according to principles described herein.
  • FIG. 8 illustrates another exemplary configuration of the sound processor of FIG. 3 according to principles described herein.
  • FIG. 9 illustrates an exemplary method of cancelling tonal noise in a cochlear implant system according to principles described herein.
  • a sound processor included in a cochlear implant system associated with a patient may include a filter system that 1 ) receives an input signal that includes audio content representative of an audio signal presented to the patient and tonal noise introduced by a noise source within or outside the cochlear implant system, 2) tracks a fundamental frequency and a phase of the tonal noise within the input signal, 3) generates a reference noise signal based on the tracked frequency and the tracked phase, and 4) subtracts the reference noise signal from the input signal to generate a filtered version of the input signal.
  • tone noise refers to discrete frequency noise characterized by spectral tones that are pure tones in nature.
  • tonal noise generated by a particular noise source e.g., a power supply, a digital switching circuit, an electromagnetic source, etc.
  • a particular noise source e.g., a power supply, a digital switching circuit, an electromagnetic source, etc.
  • FIG. 1 illustrates an exemplary cochlear implant system 100.
  • cochlear implant system 100 may include various components configured to be located external to a patient including, but not limited to, a microphone 102, a sound processor 104, and a headpiece 106. Cochlear implant system 100 may further include various components configured to be implanted within the patient including, but not limited to, a cochlear implant 108 and a lead 1 10 (also referred to as an electrode array) with a plurality of electrodes 1 12 disposed thereon. As will be described in more detail below, additional or alternative components may be included within cochlear implant system 100 as may serve a particular implementation. The components shown in FIG. 1 will now be described in more detail.
  • Microphone 102 may be configured to detect audio signals presented to the patient.
  • Microphone 102 may be implemented in any suitable manner.
  • microphone 102 may include a microphone that is configured to be placed within the concha of the ear near the entrance to the ear canal, such as a T-MICTM microphone from Advanced Bionics. Such a microphone may be held within the concha of the ear near the entrance of the ear canal by a boom or stalk that is attached to an ear hook configured to be selectively attached to sound processor 104.
  • microphone 102 may be implemented by one or more microphones disposed within headpiece 106, one or more microphones disposed within sound processor 104, one or more beam-forming microphones, and/or any other suitable microphone as may serve a particular implementation.
  • Sound processor 104 may be configured to direct cochlear implant 108 to generate and apply electrical stimulation (also referred to herein as "stimulation current") representative of one or more audio signals (e.g., one or more audio signals detected by microphone 102, input by way of an auxiliary audio input port, etc.) to one or more stimulation sites associated with an auditory pathway (e.g., the auditory nerve) of the patient.
  • electrical stimulation also referred to herein as "stimulation current”
  • audio signals e.g., one or more audio signals detected by microphone 102, input by way of an auxiliary audio input port, etc.
  • Exemplary stimulation sites include, but are not limited to, one or more locations within the cochlea, the cochlear nucleus, the inferior colliculus, and/or any other nuclei in the auditory pathway.
  • sound processor 104 may process the one or more audio signals in accordance with a selected sound processing strategy or program to generate appropriate stimulation parameters for controlling cochlear implant 108.
  • Sound processor 104 may include or be implemented by a behind-the-ear (“BTE”) unit, a body worn device, and/or any other sound processing unit as may serve a particular implementation.
  • sound processor 104 may be implemented by an electro-acoustic stimulation (“EAS”) sound processor included in an EAS system configured to provide electrical and acoustic stimulation to a patient.
  • EAS electro-acoustic stimulation
  • sound processor 104 may wirelessly transmit stimulation parameters (e.g., in the form of data words included in a forward telemetry sequence) and/or power signals to cochlear implant 108 by way of a wireless communication link 1 14 between headpiece 106 and cochlear implant 108.
  • stimulation parameters e.g., in the form of data words included in a forward telemetry sequence
  • power signals to cochlear implant 108 by way of a wireless communication link 1 14 between headpiece 106 and cochlear implant 108.
  • communication link 1 14 may include a bi-directional communication link and/or one or more dedicated uni-directional communication links.
  • Headpiece 106 may be communicatively coupled to sound processor 104 and may include an external antenna (e.g., a coil and/or one or more wireless communication components) configured to facilitate selective wireless coupling of sound processor 104 to cochlear implant 108. Headpiece 106 may additionally or alternatively be used to selectively and wirelessly couple any other external device to cochlear implant 108. To this end, headpiece 106 may be configured to be affixed to the patient's head and positioned such that the external antenna housed within headpiece 106 is communicatively coupled to a corresponding implantable antenna (which may also be implemented by a coil and/or one or more wireless communication components) included within or otherwise associated with cochlear implant 108.
  • an external antenna e.g., a coil and/or one or more wireless communication components
  • stimulation parameters and/or power signals may be wirelessly transmitted between sound processor 104 and cochlear implant 108 via a communication link 1 14 (which may include a bi-directional communication link and/or one or more dedicated uni-directional communication links as may serve a particular implementation).
  • a communication link 1 14 which may include a bi-directional communication link and/or one or more dedicated uni-directional communication links as may serve a particular implementation.
  • Cochlear implant 108 may include any type of implantable stimulator that may be used in association with the systems and methods described herein.
  • cochlear implant 108 may be implemented by an implantable cochlear stimulator.
  • cochlear implant 108 may include a brainstem implant and/or any other type of active implant or auditory prosthesis that may be implanted within a patient and configured to apply stimulation to one or more stimulation sites located along an auditory pathway of a patient.
  • cochlear implant 108 may be configured to generate electrical stimulation representative of an audio signal processed by sound processor 104 (e.g., an audio signal detected by microphone 1 02) in accordance with one or more stimulation parameters transmitted thereto by sound processor 104. Cochlear implant 108 may be further configured to apply the electrical stimulation to one or more stimulation sites within the patient via one or more electrodes 1 12 disposed along lead 1 10 (e.g., by way of one or more stimulation channels formed by electrodes 1 12). In some examples, cochlear implant 108 may include a plurality of independent current sources each associated with a channel defined by one or more of electrodes 1 12. In this manner, different stimulation current levels may be applied to multiple stimulation sites simultaneously (also referred to as "concurrently") by way of multiple electrodes 1 12.
  • FIG. 2 illustrates a schematic structure of the human cochlea 200 into which lead 1 10 may be inserted.
  • the cochlea 200 is in the shape of a spiral beginning at a base 202 and ending at an apex 204.
  • auditory nerve tissue 206 Within the cochlea 200 resides auditory nerve tissue 206, which is denoted by Xs in FIG. 2.
  • the auditory nerve tissue 206 is organized within the cochlea 200 in a tonotopic manner.
  • Relatively low frequencies are encoded at or near the apex 204 of the cochlea 200 (referred to as an "apical region") while relatively high frequencies are encoded at or near the base 202 (referred to as a "basal region").
  • Cochlear implant system 100 may therefore be configured to apply electrical stimulation to different locations within the cochlea 200 (e.g., different locations along the auditory nerve tissue 206) to provide a sensation of hearing.
  • FIG. 3 illustrates exemplary components of sound processor 104. It will be recognized that the components shown in FIG. 3 are merely representative of the many different components that may be included in sound processor 104 and that sound processor 104 may include additional or alternative components as may serve a particular implementation.
  • sound processor 104 may include an analog-to-digital converter ("ADC") 302, a filter system 304, and processing circuitry 306.
  • ADC analog-to-digital converter
  • ADC 302 may receive an analog input signal and convert the analog input signal into a digital input signal, represented by "y" in FIG. 3.
  • the analog input signal may include both audio content representative of an audio signal presented to the patient and tonal noise introduced by a noise source associated with (e.g., included within or external to) the cochlear implant system 100.
  • both the analog input signal and its digital representation i.e., the signal represented by "y" may be referred to herein as a "corrupted input signal”.
  • the term "input signal” refers interchangeably to either the analog input signal supplied to ADC 302 or the digital representation of the analog input signal that is output by ADC 302.
  • the corrupted input signal may be provided by any suitable input source included within and/or otherwise associated with cochlear implant system 100.
  • FIG. 4 shows an exemplary configuration 400 in which the input signal may be provided by a telecoil 402 included in sound processor 104.
  • telecoil 402 may detect an audio signal (which, in this case, is encoded in the form of an
  • telecoil 402 may
  • the audio signal and the tonal noise combine to form the analog input signal generated by telecoil 402 and input into ADC 302.
  • FIG. 5 illustrates an alternative configuration 500 in which the input signal is provided by a microphone 502.
  • Microphone 502 may include any of the microphones described herein.
  • microphone 502 may include a microphone that is configured to be placed within the concha of the ear near the entrance to the ear canal, a microphone disposed within headpiece 106, and/or any other microphone as may serve a particular implementation.
  • the signal detected by microphone 502 may include a combination of an audio signal presented to the patient and tonal noise generated by a noise source associated with cochlear implant system 100.
  • the input signal may include a mixture of a signal provided by a microphone included in cochlear implant system 100 and a telecoil included in sound processor 104.
  • FIG. 6 illustrates an exemplary configuration 600 in which the analog input signal input into ADC 302 is provided by a mixer 602. As shown, mixer 602 receives a first signal provided by microphone 502 and a second signal provided by telecoil 402. Mixer 602 may combine the first and second signals and provide the combined signal to ADC 302 in the form of the analog input signal. Alternatively, two ADCs may encode the two input analog signals separately, and the ensuing digital signals may be mixed together.
  • Filter system 304 may be configured to cancel the tonal noise from the input signal provided by ADC 302. As used herein, tonal noise may be "cancelled” by at least partially removing or filtering out the tonal noise from the input signal. Filter system 304 may output a filtered version of the input signal, which is represented by "r" in FIGS. 3-7 and has the tonal noise at least partially cancelled therefrom.
  • filter system 304 may track (e.g., in real time as the input signal is received) a fundamental frequency, a phase, and/or a magnitude of the tonal noise within the input signal, generate a reference noise signal based on the tracked attributes of the tonal noise, and subtract the reference noise signal from the input signal to generate a filtered version of the input signal.
  • the subtraction of the reference noise signal from the input signal at least partially cancels the tonal noise from the input signal.
  • FIG. 7 illustrates exemplary components of filter system 304.
  • filter system 304 may include additional or alternative components as may serve a particular implementation.
  • filter system 304 may include a resonant filter 702 that receives the input signal "y” and outputs an output signal "o", which is a signal that has the tracked frequency.
  • Filter system 304 may further include a normalizer 704, which normalizes the output signal "o" output by the resonant filter 702 to give a basis signal "b" (which is the reference noise signal).
  • Filter system 304 may further include an adaptive filter 706, which processes the basis signal "b” and the input signal "y” to output the filtered version of the input signal, which is represented by the signal "e”.
  • ⁇ is a scale factor and a is a complex number, chosen to be is equal to
  • is a real number constant on which the sharpness of the filter depends. The closer this constant is to 1 , the narrower the filter is.
  • An exemplary value of ⁇ is 1 .
  • Another exemplary value of ⁇ is (1 -a).
  • variable ⁇ is an angular resonant frequency given by 2 ⁇ / ⁇ ⁇ , where f is the center frequency of the resonant filter 702 and f s is the sampling frequency. This ⁇ is set to the expected angular frequency of the
  • ⁇ may be set to be equal to the expected fundamental angular frequency of the tonal noise output by a particular noise source included in cochlear implant system 100.
  • the output "o” is a complex signal whose phase is the same phase as the input complex sinusoidal of the tracked fundamental frequency, only if the frequency is being tracked accurately, i.e. only if ⁇ is the accurate angular frequency of the tonal noise being tracked. Otherwise, the phase difference between "o" and the complex sinusoidal being tracked quickly rushes to +/- ⁇ , even for a small frequency tracking error.
  • Normalizer 704 normalizes the output signal "o" of the resonant filter 702.
  • the normalized output of normalizer 704 is a basis signal "b".
  • This basis signal may also be referred to as a reference noise signal.
  • the reference noise signal is generated from the signal corrupted by noise itself (i.e., from the input signal "y") and is used by adaptive filter 706 to cancel the noise signal from the corrupted input signal.
  • the resonant filter 702 when normalized by normalizer 704, creates an output waveform of nearly a single complex frequency, i.e., "b" will be something very close to e j ⁇ 0 where ⁇ is the true frequency of the tonal noise present in the input signal "y”.
  • This basis is used to predict the noise corresponding to frequency ⁇ in input signal "y” and the best prediction is removed from the input to give a difference signal "e”.
  • Adaptive filter 706 receives the reference noise signal “b” and subtracts the reference noise signal “b” multiplied by a complex number gain “a” from the input signal "y” to generate the filtered version of the input signal “e” (also referred to as the error signal “e”).
  • e(i) y(i) - a(i)b(i).
  • the output "e” will have the frequency ⁇ removed as much as possible.
  • the complex number "a” is a best predictor of the noise at frequency ⁇ from the basis signal "b".
  • the input signal "y” is a real signal, it would be constituted of complex
  • r(i) y(i) - 2 ( Re(a(i)) Re(b(i)) - lm(a(i)) lm(b(i)) ), where Re and Im respectively stand for the real and imaginary parts of a complex number.
  • a(i), a complex number for each time step i is the estimate of correlation between complex frequency ⁇ present in y(i) and b(i). This estimate is adapted in such a way that output "e” will have the frequency ⁇ removed as much as possible.
  • the real number ⁇ can be selected in many ways, depending on the normalization equation used to generate basis signal "b" and the equation used to adapt "a".
  • the angular frequency of tonal noise ⁇ can vary with time. Therefore, for more accurate and error free tracking, it is desirable to adapt ⁇ , the resonant angular frequency of the resonant filter 702, to ⁇ , the angular frequency of the noise to be tracked and removed i.e., it is desirable for ⁇ to be equal to ⁇ . To be able to achieve this, the systems and methods use a property of the resonant filter 702 itself, which is that the resonant filter output leads or lags the input depending upon whether the input noise frequency is lower or higher than the center frequency of the resonant filter.
  • feedback is given from the imaginary part of "a” to update the center frequency ⁇ .
  • the above algorithm uses two rate of adaptation parameters, ⁇ and ⁇ .
  • Frequency ( ⁇ ) as well as phase and gain (“a") adaptation works better under no-signal condition, i.e., when only noise is audible. Hence, the rate of adaptation is reduced as the input signal (sound) level "I” increases.
  • the level "I” is detected by averaging the half wave rectified version of the input signal over the past few samples.
  • l(i) max(
  • the maximum value between a constant ⁇ times the input signal level "I" and the absolute value of the instantaneous value of input signal "y” is selected as the estimate of input signal level "I” for the next time step.
  • decay parameter ⁇ dictates how quickly the the level signal follows the input. The larger the value of ⁇ , slower is the rate of change of the level signal. Thus ⁇ and ⁇ are chosen such that, the more the value of level signal T , the slower the adaption of phase and gain will be. Thus, both ⁇ and ⁇ , are chosen to be inversely related to T.
  • (') indicates complex conjugation
  • ⁇ is the adaptation parameter for "a”.
  • adaptation parameters ⁇ , ⁇ or ⁇ are chosen to be large, the amount with which the values of adapted parameters (namely, "a" and ⁇ ) change depends heavily on instantaneous signal values and would thus keep oscillating with a large variance about the optimal value. On the other hand, if the adaptation parameters are chosen to be too small, time to converge to the optimal values will be too large.
  • the algorithm directly uses filtered output signal "r” instead of adaptive filter output “e”, in order to adapt correlation "a” and tracked angular frequency ⁇ .
  • Both “e” and “r” are the filtered versions of input "y”.
  • “e” is generated by filtering out only the positive complex sinusoid from the input, while “r” is generated by filtering out both positive and negative complex sinusoids from the input.
  • filter system 304 may be used to cancel tonal noise.
  • the tonal noise may be
  • a switched mode power supply may induce a noise at the switching frequency, and possibly also harmonic frequencies.
  • An input source e.g., a telecoil
  • the filter system 304 may be provided (e.g., by a fitting system, by a clinician, and/or during a manufacturing process) with an estimated or expected value for the fundamental frequency of the tonal noise. Filter system 304 may then track variations in the fundamental frequency and/or phase of the tonal noise, and cancel the tonal noise from the input signal as described above.
  • the fundamental frequency of the tonal noise generated by the power supply may change over time. For example, as the voltage level of a battery included in the power supply depletes over time, the frequency at which the power supply operates may change to accommodate the drop in voltage. This, in turn, changes the fundamental frequency of the tonal noise. Filter system 304 may track this change and continuously remain locked to it, thereby allowing filter system 304 to accurately and effectively cancel the tonal noise from the input signal despite the variations in frequency.
  • multiple filter systems 304 may be included in sound processor 104 in order to track and remove tonal noise originating from multiple different noise sources.
  • multiple noise sources may include multiple power supplies, or circuits or algorithms working at different rates of operation.
  • the noise from each noise source can include a fundamental frequency and harmonics of that fundamental frequency ( frequencies at an integer multiple of the fundamental frequency).
  • the noise from various noise sources can also intermodulate (usually because of the presence of sum non-linearity), and produce cross harmonics.
  • a cross harmonic of various fundamental frequencies is at a frequency which is the numerical sum of some integer multiple of each of the fundamental frequencies.
  • processing circuitry 306 may include any suitable processing components configured to generate control data used to direct cochlear implant 108 to generate and apply electrical stimulation representative of the filtered version of the filtered input signal "e" to the patient (i.e., to one or more stimulation sites within the cochlea of the patient).
  • FIG. 8 shows an exemplary configuration 800 in which sound processor 104 includes a mixer circuit 802 configured to mix the filtered version of the input signal "e" with a signal output by a microphone 804 included within cochlear implant system 100.
  • Microphone 804 may include any of the microphones described herein.
  • Configuration 800 may be used in scenarios in which it is desirable to combine audio content detected by a microphone and by a different input source (e.g., a telecoil).
  • tonal noise may be cancelled in the frequency domain.
  • sound processor 104 may take a "snapshot" of the system noise (i.e., tonal noise generated by each noise source within the cochlear implant system 100). This may be performed in any suitable manner. For example, while no audio is being presented to the user, sound processor 104 may process an input signal provided by an input source (e.g., a microphone, a telecoil, and/or any other input source) for a predetermined amount of time and then compute the average of the FFT output. This snapshot may be representative of the system noise, and may be stored and then subtracted from frequency domain representations of input signals provided by the input source during normal operation of the cochlear implant system 100 (i.e,. while audio is being presented to the patient).
  • an input source e.g., a microphone, a telecoil, and/or any other input source
  • FIG. 9 illustrates an exemplary method 900 of cancelling tonal noise in a cochlear implant system. While FIG. 9 illustrates exemplary steps according to one embodiment, other embodiments may omit, add to, reorder, and/or modify any of the steps shown in FIG. 9. One or more of the steps shown in FIG. 9 may be performed by filter system 304 and/or any implementation thereof.
  • a filter system included in a sound processor that is a part of a cochlear implant system associated with a patient receives an input signal that includes audio content representative of an audio signal presented to the patient and tonal noise introduced by a noise source associated with the cochlear implant system.
  • Step 902 may be performed in any of the ways described herein.
  • step 904 the filter system tracks a fundamental frequency and a phase of the tonal noise within the input signal.
  • Step 904 may be performed in any of the ways described herein.
  • step 906 the filter system generates a reference noise signal based on the tracked frequency and the tracked phase.
  • the reference noise signal could have a frequency nearly equal to the fundamental frequency or its harmonics.
  • Step 906 may be performed in any of the ways described herein.
  • step 908 the filter system subtracts the reference noise signal from the input signal to generate a filtered version of the input signal.
  • Step 908 may be performed in any of the ways described herein.

Abstract

L'invention concerne un processeur audio à titre d'exemple, compris dans un système d'implant cochléaire associé à un patient, qui peut comprendre un système de filtre qui 1) reçoit un signal d'entrée qui comprend un contenu audio représentant un signal audio présenté au patient et le bruit tonal introduit par une source de bruit à l'intérieur du système d'implant cochléaire, 2) suit une fréquence fondamentale et une phase du bruit tonal dans le signal d'entrée, 3) génère un signal de bruit de référence sur la base de la fréquence suivie et de la phase suivie, et 4) soustrait le signal de bruit de référence à partir du signal d'entrée pour générer une version filtrée du signal d'entrée. L'invention concerne également des systèmes et des procédés correspondants.
PCT/IB2014/061224 2014-05-06 2014-05-06 Systèmes et procédés d'annulation de bruit tonal dans un système d'implant cochléaire WO2015170140A1 (fr)

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US10595134B1 (en) 2017-03-24 2020-03-17 Advanced Bionics Ag Systems and methods for detecting and reacting to system noise generated by a cochlear implant system

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