WO1994010820A1 - Simulateur electronique de traitement de signal cochleaire non lineaire actif - Google Patents

Simulateur electronique de traitement de signal cochleaire non lineaire actif Download PDF

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Publication number
WO1994010820A1
WO1994010820A1 PCT/US1993/010476 US9310476W WO9410820A1 WO 1994010820 A1 WO1994010820 A1 WO 1994010820A1 US 9310476 W US9310476 W US 9310476W WO 9410820 A1 WO9410820 A1 WO 9410820A1
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WIPO (PCT)
Prior art keywords
output
sound analyzer
sound
producing
analyzer
Prior art date
Application number
PCT/US1993/010476
Other languages
English (en)
Inventor
Julius L. Goldstein
Original Assignee
Goldstein Julius L
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
Priority claimed from US07/970,141 external-priority patent/US5402493A/en
Application filed by Goldstein Julius L filed Critical Goldstein Julius L
Priority to EP94900476A priority Critical patent/EP0748575A4/fr
Priority to AU55452/94A priority patent/AU5545294A/en
Priority to JP6511373A priority patent/JPH08505706A/ja
Publication of WO1994010820A1 publication Critical patent/WO1994010820A1/fr

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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
    • 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

  • the invention disclosed in the parent improved on this earlier model bringing it further in congruence with the known biophysical mechanisms of the ear, including most particularly the organ of Corti and basilar mem ⁇ brane, and in the process achieved simulation of the heretofore unexplained distortion product and otoacoustic emissions.
  • the inventor added bilateral signal processing to his prior model to more completely simulate the two signaling channels responsible for the "tips" and "tails" of Cochlear tuning curves.
  • the bila ⁇ teral processing potentiates extension of the model to other phenomena, including combination tones (distortion products) and otoacoustic emissions.
  • This intermediate step takes advantage of non-linear feedback while the full invention disclosed in the parent adds distributed amplification.
  • the distributed amplification provides for non-linear addition of many signals from tip sources which are believed to function similarly to the organ of Corti.
  • These organ of Corti filters, or tip sources are connected at different locations along a filter-bank spectrum analyzer (a corollary to the outer hair cells and adjoining structures) and are non-linearly added through a propagating medium (a corollary to the basilar membrane) to provide distributed amplification.
  • This model thus helps explain the non-linear input/output characteristic as observed by others in the basilar mem ⁇ brane mechanical response in the human ear.
  • the invention disclosed in the parent includes a pair of matched all pole lattices with a plurality of tip couplers tapped into each lattice and interconnecting them at chosen "center frequencies”.
  • a scaling factor, or alpha may be induced at any frequency to alter the response at that frequency and thereby match the model's output to any particular human ear output.
  • an efferent bias control which is ordinarily set to zero, may also be used to scale the throughput of any one or more tip couplers to simulate the brain's ability in humans to "tune out” undesirable sounds or simulate "li ⁇ stening without hearing” as experienced in humans. Choo- sing the number of tip couplers (and hence the length of the matched lattices), and the "center frequencies" of each of the tip couplers permits the model builder to focus on any one or more range of frequencies for mea ⁇ surement with the model.
  • the model accom- modates the use of 12,000 tip modules which corresponds to the full complement of outer hair cells believed to be contained and operative in the organ of Corti, to thereby provide a full representation and simulation of the fre ⁇ quency range of the human ear.
  • a fewer number of tip couplers may be used and may be focused over a chosen portion of the frequency range of hearing to thereby minimize cost and complexity of the model while still simulating with great accuracy the desired response frequencies.
  • a non-linear additive direc ⁇ tional wave amplification means (modeling the basilar membrane and space of Nuel) responds to two different signals, each of which corresponds to a physical mecha ⁇ nism.
  • One is a "global” signal to the organ of Corti filter model, which corresponds to the fast pressure wave within the inner ear cavity in response to stapes input.
  • the second is a "local" input signal to the organ of Corti filter model which corresponds to the classical slow-wave response to the pressure gradient across the basilar membrane in response to stapes input.
  • This model simulates the basilar membrane serving as a collector in the additive directional wave amplification of tuned responses by outer hair cells.
  • the collector uses stan ⁇ dard engineering principles (well-known in the art) for non-uniform transmission lines, with the added condition that dissipation is required to attenuate the amplified waves as they travel beyond their position of maximum build-up.
  • the organ of Corti filters are simulated using hair-cell and electro-moti- lity models found in the prior art (Davis, H. "A model for transducer action in the cochlea.” Cold Spring Sym ⁇ posia on Quantitative Biology, vol. 30, 181-190 (1965); and Santos-Sacchi, J. "On the frequency limit and phase of outer hair cell motility: effects of the membrane filter.” J. Neurosci, vol. 12, 1906-1916 (1992)). Fol ⁇ lowing these models, the present invention simulates the organ of Corti filters using an operational amplifier, an inverse transducer and a compressive transducer.
  • the operational amplifier is used to implement the inverse transducer; however, the corresponding physical basis for this mechanism remains to be discovered. Further, the transducers are no longer memoryless, but include one or two integrations within the compressive transducer and an equal number of differentiations within the inverse transducer. (The electromotility function m(e) is de ⁇ fined by Santos-Sacchi, op. cit. )
  • Figure 1 is a schematic diagram representing the inventor's prior art model for simulating human ear re ⁇ sponse
  • Figure 2 is a first embodiment of the invention disclosed in the parent which includes bilateral signal processing in a model for simulating human ear response
  • Figure 3 is a schematic depicting the inventor's interpretation of the biological function of the cochlea as disclosed in the parent;
  • Figure 4 depicts a schematic representation of an idealized example of the invention disclosed in the par- ent based upon in-phase addition of apically propagating "tip" responses;
  • Figure 5 is a schematic of the invention disclosed in the parent detailing the non-linear cochlear simula ⁇ tor;
  • Figure 6 is a graph detailing the measured re ⁇ sponse of the invention disclosed in the parent;
  • Figures 7a and 7b are schematic diagrams detailing lattice construction as utilized in the invention dis ⁇ closed in the parent;
  • Figure 8 is a graph providing the relationship between tip coupler density and tip preamplifier gain as disclosed in the parent;
  • Figure 9 is a partial schematic of the model shown in Figure 5 and further detailing the interconnection between the tip line lattice and tail line lattice through the tip couplers disclosed in the parent;
  • Figure 10 is a schematic depicting the present invention which couples the bilateral signal processing model disclosed and claimed in the parent with an addi- tive directional wave amplifier incorporating analog electronic components for simulating human ear response;
  • Figures 11a and lib are schematic diagrams of the present invention depicting physical simulations of the organ of Corti filters.
  • the inventor herein has previously developed a model for explaining and simulat ⁇ ing the cochlear response of the human ear.
  • the model of Figure 1 is characterized by a unilateral non-linear signal processing of two signaling channels responsible for the "tips" and “tails” well demonstrated in the literature as being measured in cochlear frequency tuning curves.
  • cochlear spectrum analysis would be approximately simulated by a bank of independent non-linear filters, each tuned to a different audible frequency. Further details of the specific oper ⁇ ation and functional components of the model of Figure 1 are described in the inventor's prior article referenced above.
  • the non-linear amplification principle disclosed in the parent was extended to include a basilar membrane as a propagating medium which allows for the interaction between the sensed response of organ of Corti filters tuned to different frequencies.
  • a plurality of tip filters HI are each tuned to a different center frequency CF j which are then non-linearly coupled for bilateral processing to the basilar membrane.
  • the measured responses are thus the result of a distributed non-linear amplifying effect.
  • This bilateral signal processing is further exemplified by the double headed arrows connecting the cochlea (com ⁇ prising the organ of Corti and basilar membrane) with the middle ear and outer ear.
  • FIG. 5 A more physically realizable representation and embodiment for the invention disclosed in the parent is shown in Figure 5.
  • a pair of match ⁇ ed lattices comprising a tip line lattice and a tail line lattice are interconnected by a plurality of tip modules (as shown in Figure 2) to provide non-linear bilateral signal processing therebetween at different frequency points.
  • the tip line and tail line lattice are conven ⁇ tional all pole lattices as shown in Figure 7b.
  • a one pole lattice representing an ideal ⁇ ized section of a non-uniform acoustic tube has F ⁇ and B as its forward and backward waves.
  • a unit delay Z" 1 equals the transit time of the section.
  • K ⁇ is the reflec ⁇ tion coefficient that depends upon the ratio of cross- sectional areas of the idealized successive sections.
  • the forward delay is eliminated and the backward delay corresponds to twice the transit time.
  • the scaling fac ⁇ tor for each section is normalized to unity. Except for the scale factor and delay, the form of the frequency response is unchanged, as demonstrated therein. As shown in Figure 5, the responses interact along the tail line lattice much as is believed to be the case in the basilar membrane of the human ear.
  • the non-linearly coupled tip line lattice and differentiator D(Z) provide a phase-matched filter-bank sound analysis that is believed to simulate the action of the outer hair cells and adjoining structures comprising the organ of Corti.
  • the model as shown in Figure 5, has some correspondence to the physical properties of the cochlea and hence provide insight into the actual physical mecha ⁇ nisms at work in the cochlea.
  • the correlation between the model of the invention disclosed in the parent and the cochlea itself leads to adjustments in the model which may be used to simulate responses measured in the human ear.
  • the filter responses of the tip line lattice must be normalized to the "center frequency" of each tip filter or tip module.
  • losses in sensitivity of each of these tip filters or modules may be simulated by choosing a scaling factor alpha such that 0 ⁇ __ ⁇ ** ⁇ __ 1. This scaling factor may be used to adjust the output at the "center frequency", corresponding to the response, as would be the case in the response of a dam ⁇ aged cochlea.
  • efferent neural control of the tip sensitivity can be simulated by providing a quiescent bias control at each of the tip modules, as shown.
  • This efferent neural control is representative of the brain's ability to suppress the response of the ear to undesir ⁇ able sounds and to also simulate the results of inatten- tiveness, as when a person is listening but not hearing.
  • Coupling of the backward propagation to the tip line from the tail line can be controlled by choosing beta such that 0 ⁇ _ ⁇ _ ⁇ 1.
  • the tip preamplifier G may have its gain adjusted -fco correspond to the number of tip couplers used in implementing the simulator.
  • FIG 8 This is shown in Figure 8 which allows that number to be as large as the 12,000 outer hair cells of the organ of Corti.
  • 600 represents the normal number of hair cells in a five percent section of the cochlea.
  • the figure specifies the increase in gain required (G in Figure 5) to simulate normal sensitivity when the number of tip filters is reduced below 600 per five percent section.
  • G gain required
  • the present invention utilizes empirical data from the study of tonotopically organized mechano-motility responses from isolated outer hair cells (See Brundin, L. & Russell, I., Sound-Induced Movements and Frequency Tuning in Outer Hair Cells Isolated from the Guinea Pig Cochlea; Symposium Reprints: Biophysics Of Hair Cell Sensory Systems, Duifhuis, H. et al., Eds., Groningen, June 28, 1993 - July 2, 1993, pp. 121-127) to implement principals of cochlear system operation disclosed in the parent with analog electronic technology in closer agree- ment with cellular biophysics of the human ear.
  • the source delay line of the inven ⁇ tion disclosed in the parent is replaced with the dif ⁇ ferential delays within the passbands of the bilateral signal processors (which model tonotopically organized organ of Corti filters).
  • the present invention utilizes a non-linear additive directional wave amplifi ⁇ cation means, which responds to two different signals, each of which corresponds to a physical mechanism.
  • One is a "global" signal to the organ of Corti filter model which corresponds to the tonotopically-tuned phasic mechano-motility responses by the outer hair cells to the fast pressure wave within the inner ear in response to stapes input.
  • the second is a "local" input signal to the organ of Corti filter which corresponds to a clas ⁇ sically defined slow-wave response to the pressure gradi- ent across the basilar membrane in response to stapes input.
  • Tuned phasic length-modulation responses of outer hair cells inject phasic signals into the space of Nuel by modulating the separation between the reticular lamina and the basilar membrane. Being bound by the basilar membrane, the space of Nuel supports traveling waves similar to the classical slow-wave response to the pres ⁇ sure gradient across the membrane.
  • the amplification principles in the present inven ⁇ tion require dissipation means to attenuate the amplified waves as they travel beyond their position of maximum build-up. Dissipation is introduced in the model with the shunt capacitors C t and can be added in parallel with the series inductors 1 .
  • the invention simulates the basilar membrane serving as a collector in the additive directional wave amplification of tuned responses by outer hair cells.
  • the collector uses standard engineer ⁇ ing principles (well-known in the art) for non-uniform transmission lines.
  • the present invention further simulates the biophysical implementa ⁇ tion of organ of Corti filters using the hair-cell and electro-motility models found in the prior art (Davis, H. "A model for transducer action in the cochlea.” Cold Spring Symposia on Quantitative Biology, vol. 30, 181-190 (1965); and Santos-Sacchi, J. "On the frequency limit and phase of outer hair cell motility: effects of the mem ⁇ brane filter.” J. Neurosci, vol. 12, 1906-1916 (1992)).
  • the left side thereof corresponds to the compressive transducer f and the right side there- of corresponds to the inverse transducer f -1 as shown in the schematic in Figure 11a.
  • an operat- ional amplifier is used to implement the inverse trans ⁇ ducer.
  • the transducers are no longer memoryless, but include one or two integrations within the compressive transducer and an equal number of differentiations within the inverse transducer.
  • the electromotility function m(e) is defined by Santos- Sacchi, op. cit. )
  • VLSI simula- tion technology The invention was demonstrated using VLSI simula- tion technology.
  • the preferred embodiment is the rec ⁇ ommended implementation.
  • VLSI simulation required a powerful general purpose computer, while the inventor considers DSP technology more practical.

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  • Health & Medical Sciences (AREA)
  • General Health & Medical Sciences (AREA)
  • Neurosurgery (AREA)
  • Otolaryngology (AREA)
  • Physics & Mathematics (AREA)
  • Engineering & Computer Science (AREA)
  • Acoustics & Sound (AREA)
  • Signal Processing (AREA)
  • Prostheses (AREA)
  • Testing, Inspecting, Measuring Of Stereoscopic Televisions And Televisions (AREA)
  • Amplifiers (AREA)
  • Measurement Of Mechanical Vibrations Or Ultrasonic Waves (AREA)

Abstract

On décrit un modèle qui simule une analyse spectrale cochléaire (Fig. 3) et comporte une paire de réseaux coordonnés entièrement à base de lignes interconnectées par plusieurs coupleurs d'extrémités et donnant un traitement de signal bilatéral réparti non linéaire. L'un des réseaux ainsi que les coupleurs d'extrémités correspondent à l'organe de Corti qu'on trouve dans la cochlée et le deuxième réseau correspond à la membrane basilaire également placée dans la cochlée, de manière que ce modèle offre une ressemblance frappante en matière de structure avec les propriétés physiques de la cochlée elle-même. Avec un tel modèle, on simule des produits de distorsion et des émissions oto-acoustiques. On décrit aussi un modèle intermédiaire (Fig. 10) qui donne un traitement de signal bilatéral non linéaire et une amplification complémentaire d'onde directionnelle. L'invention met en ÷uvre ce modèle cochléaire à l'aide d'une technologie à électronique analogique qui s'accorde mieux avec la biophysique cellulaire de l'oreille humaine.
PCT/US1993/010476 1992-11-02 1993-11-01 Simulateur electronique de traitement de signal cochleaire non lineaire actif WO1994010820A1 (fr)

Priority Applications (3)

Application Number Priority Date Filing Date Title
EP94900476A EP0748575A4 (fr) 1992-11-02 1993-11-01 Simulateur electronique de traitement de signal cochleaire non lineaire actif
AU55452/94A AU5545294A (en) 1992-11-02 1993-11-01 Electronic simulator of non-linear and active cochlear signal processing
JP6511373A JPH08505706A (ja) 1992-11-02 1993-11-01 非線形能動的蝸牛信号処理の電子シミュレータ

Applications Claiming Priority (4)

Application Number Priority Date Filing Date Title
US07/970,141 1992-11-02
US07/970,141 US5402493A (en) 1992-11-02 1992-11-02 Electronic simulator of non-linear and active cochlear spectrum analysis
US13438293A 1993-10-12 1993-10-12
US08/134,382 1993-10-12

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WO1994010820A1 true WO1994010820A1 (fr) 1994-05-11

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JP (1) JPH08505706A (fr)
AU (1) AU5545294A (fr)
CA (1) CA2148453A1 (fr)
WO (1) WO1994010820A1 (fr)

Cited By (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO1997043871A1 (fr) * 1996-05-16 1997-11-20 The University Of Melbourne Calcul des attributions de frequence d'electrode dans un implant cochleaire

Families Citing this family (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP6094844B1 (ja) * 2016-03-14 2017-03-15 合同会社ディメンションワークス 音響再生装置、音響再生方法、及びプログラム

Citations (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US3989904A (en) * 1974-12-30 1976-11-02 John L. Holmes Method and apparatus for setting an aural prosthesis to provide specific auditory deficiency corrections
US4536844A (en) * 1983-04-26 1985-08-20 Fairchild Camera And Instrument Corporation Method and apparatus for simulating aural response information

Patent Citations (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US3989904A (en) * 1974-12-30 1976-11-02 John L. Holmes Method and apparatus for setting an aural prosthesis to provide specific auditory deficiency corrections
US4536844A (en) * 1983-04-26 1985-08-20 Fairchild Camera And Instrument Corporation Method and apparatus for simulating aural response information

Non-Patent Citations (1)

* Cited by examiner, † Cited by third party
Title
See also references of EP0748575A4 *

Cited By (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO1997043871A1 (fr) * 1996-05-16 1997-11-20 The University Of Melbourne Calcul des attributions de frequence d'electrode dans un implant cochleaire

Also Published As

Publication number Publication date
AU5545294A (en) 1994-05-24
EP0748575A4 (fr) 1997-04-02
JPH08505706A (ja) 1996-06-18
CA2148453A1 (fr) 1994-05-11
EP0748575A1 (fr) 1996-12-18

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