Human middle-ear sound transfer function and cochlear input impedance

Aibara, Ryuichi; Welsh, Joseph T.; Puria, Sunil; Goode, Richard L.

doi:10.1016/s0378-5955(00)00240-9

Cited by 261 publications

(233 citation statements)

References 16 publications

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“…Convolution of the latter with input waveforms representing sound pressure at the tympanic membrane yielded fluid pressure in scala vestibuli near the stapes, or the BM base (vestibular pressure). To link vestibular pressure and stapes acceleration, which was used as input to the inner ear model, we considered that cochlear acoustic impedance Z c (vestibular pressure divided by stapes footplate area times stapes velocity) appears approximately independent of frequency in the relevant range for OAEs (Z c ' 21 GX; Aibara et al 2001), implying approximate proportionality between pressure and velocity. Accordingly, stapes acceleration was computed as a quantity proportional to the time derivative of sound pressure at the eardrum convolved with the middleear forward impulse response (Fig.…”

Section: Connecting Middle and Inner Earmentioning

confidence: 99%

“…The mutual cancellation of the acceleration terms makes vestibular pressure essentially a function of fluid velocity alone. This explains why the acoustic impedance of the cochlea is resistive over a wide frequency range (Aibara et al 2001). In our model, the acoustic impedance of the passive and the active cochlea are the same and close to 21 GX in a frequency range of 0.5-6 kHz.…”

Section: Acoustic Impedance Of the Cochlea Modelmentioning

confidence: 99%

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Otoacoustic Emissions from Residual Oscillations of the Cochlear Basilar Membrane in a Human Ear Model

Nobili

Vetešník

Turicchia

et al. 2003

JARO

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Sounds originating from within the inner ear, known as otoacoustic emissions (OAEs), are widely exploited in clinical practice but the mechanisms underlying their generation are not entirely clear. Here we present simulation results and theoretical considerations based on a hydrodynamic model of the human inner ear. Simulations show that, if the cochlear amplifier (CA) gain is a smooth function of position within the active cochlea, filtering performed by a middle ear with an irregular, i.e., nonsmooth, forward transfer function suffices to produce irregular and long-lasting residual oscillations of cochlear basilar membrane (BM) at selected frequencies. Feeding back to the middle ear through hydrodynamic coupling afforded by the cochlear fluid, these oscillations are detected as transient evoked OAEs in the ear canal. If, in addition, the CA gain profile is affected by irregularities, residual BM oscillations are even more irregular and tend to evolve towards self-sustaining oscillations at the loci of gain irregularities. Correspondingly, the spectrum of transient evoked OAEs exhibits sharp peaks. If both the CA gain and the middle-ear forward transfer function are smooth, residual BM oscillations have regular waveforms and extinguish rapidly. In this case no emissions are produced. Finally, and paradoxically albeit consistent with observations, simulating localized damage to the CA results in self-sustaining BM oscillations at the characteristic frequencies (CFs) of the sites adjacent to the damage region, accompanied by generation of spontaneous OAEs. Under these conditions, stimulusfrequency OAEs, with typical modulation patterns, are also observed for inputs near hearing threshold. This approach can be exploited to provide novel diagnostic tools and a better understanding of key phenomena relevant for hearing science.

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Section: Connecting Middle and Inner Earmentioning

confidence: 99%

Section: Acoustic Impedance Of the Cochlea Modelmentioning

confidence: 99%

Otoacoustic Emissions from Residual Oscillations of the Cochlear Basilar Membrane in a Human Ear Model

Nobili

Vetešník

Turicchia

et al. 2003

JARO

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show abstract

“…As for Kringlebotn (1988), parameters for the model were obtained by fitting the model to data from human temporal bones. O'Connor and Puria (2008) modeled the cochlear input impedance as resistive, consistent with Zwislocki's suggestion that the cochlear input impedance is predominantly resistive, although there is a compliant reactance element (Aibara et al 2001). Kringlebotn (1988) included compliant reactance and mass reactance terms for the cochlea in his model.…”

Section: Introductionmentioning

confidence: 57%

An Analysis of the Acoustic Input Impedance of the Ear

Withnell

Gowdy

2013

JARO

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Ear canal acoustics was examined using a onedimensional lossy transmission line with a distributed load impedance to model the ear. The acoustic input impedance of the ear was derived from sound pressure measurements in the ear canal of healthy human ears. A nonlinear least squares fit of the model to data generated estimates for ear canal radius, ear canal length, and quantified the resistance that would produce transmission losses. Derivation of ear canal radius has application to quantifying the impedance mismatch at the eardrum between the ear canal and the middle ear. The length of the ear canal was found, in general, to be longer than the length derived from the one-quarter wavelength standing wave frequency, consistent with the middle ear being mass-controlled at the standing wave frequency. Viscothermal losses in the ear canal, in some cases, may exceed that attributable to a smooth rigid wall. Resistance in the middle ear was found to contribute significantly to the total resistance. In effect, this analysis "reverse engineers" physical parameters of the ear from sound pressure measurements in the ear canal.

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“…2012), the functional lengths of the malleus and incus and the stapes footplate area are important physiological variables in modeling audition (Rosowski. 1996;Aibara et al. 2001;Martinez et al.…”

Section: Auditory Implicationsmentioning

confidence: 99%