Abstract:We present the first simultaneous sound pressure measurements in scala vestibuli and scala tympani of the cochlea in human cadaveric temporal bones. The technique we employ, which exploits microscale fiberoptic pressure sensors, enables the study of differential sound pressure at the cochlear base. This differential pressure is the input to the cochlear partition, driving cochlear waves and auditory transduction. In our results, the sound pressure in scala vestibuli (P SV ) was much greater than scala tympani … Show more
“…The model results were compared with the experimental data measured in human temporal bones by several groups. Middle-ear sound pressure gain reached the maximum value at frequencies of 1 -2 kHz predicted by the FE model and measured in temporal bones by Aibara et al (2001), Nakajima et al (2009) and Puria and Allen (1991). The good agreement between the model-predicted middle-ear transfer function and that measured in human temporal bones in acoustic pressure transmission is shown in Figure 6.…”
Section: Comparison Of Model With Published Datasupporting
confidence: 57%
“…As shown in Figure 6(A), the pressure gain from the TM to the SV has a maximum magnitude of approximately 23 dB. The FE model well predicted the middle-ear pressure gain over frequencies of 0.2-8 kHz compared to the results measured from human cadaver ears by Aibara et al and Puria et al The magnitude curve of model was about 4 dB higher than the results reported by Nakajima et al (2009) above 1 kHz.…”
Section: Model Validationsupporting
confidence: 45%
“…Figure 6 shows the FE model-derived middle-ear pressure gain (solid line), which is defined as the ratio of SV pressure near the OW to the ear canal sound pressure at the surface of the TM. The modelling results were also compared with published data by Aibara et al (2001), Nakajima et al (2009) and Puria and Allen (1991). As shown in Figure 6(A), the pressure gain from the TM to the SV has a maximum magnitude of approximately 23 dB.…”
A three-dimensional finite element model is developed for the simulation of the sound transmission through the human auditory periphery consisting of the external ear canal, middle ear and cochlea. The cochlea is modelled as a straight duct divided into two fluid-filled scalae by the basilar membrane (BM) having an orthotropic material property with dimensional variation along its length. In particular, an active feed-forward mechanism is added into the passive cochlear model to represent the activity of the outer hair cells (OHCs). An iterative procedure is proposed for calculating the nonlinear response resulting from the active cochlea in the frequency domain. Results on the middle-ear transfer function, BM steady-state frequency response and intracochlear pressure are derived. A good match of the model predictions with experimental data from the literatures demonstrates the validity of the ear model for simulating sound pressure gain of middle ear, frequency to place map, cochlear sensitivity and compressive output for large intensity input. The current model featuring an active cochlea is able to correlate directly the sound stimulus in the ear canal with the vibration of BM and provides a tool to explore the mechanisms by which sound pressure in the ear canal is converted to a stimulus for the OHCs.
“…The model results were compared with the experimental data measured in human temporal bones by several groups. Middle-ear sound pressure gain reached the maximum value at frequencies of 1 -2 kHz predicted by the FE model and measured in temporal bones by Aibara et al (2001), Nakajima et al (2009) and Puria and Allen (1991). The good agreement between the model-predicted middle-ear transfer function and that measured in human temporal bones in acoustic pressure transmission is shown in Figure 6.…”
Section: Comparison Of Model With Published Datasupporting
confidence: 57%
“…As shown in Figure 6(A), the pressure gain from the TM to the SV has a maximum magnitude of approximately 23 dB. The FE model well predicted the middle-ear pressure gain over frequencies of 0.2-8 kHz compared to the results measured from human cadaver ears by Aibara et al and Puria et al The magnitude curve of model was about 4 dB higher than the results reported by Nakajima et al (2009) above 1 kHz.…”
Section: Model Validationsupporting
confidence: 45%
“…Figure 6 shows the FE model-derived middle-ear pressure gain (solid line), which is defined as the ratio of SV pressure near the OW to the ear canal sound pressure at the surface of the TM. The modelling results were also compared with published data by Aibara et al (2001), Nakajima et al (2009) and Puria and Allen (1991). As shown in Figure 6(A), the pressure gain from the TM to the SV has a maximum magnitude of approximately 23 dB.…”
A three-dimensional finite element model is developed for the simulation of the sound transmission through the human auditory periphery consisting of the external ear canal, middle ear and cochlea. The cochlea is modelled as a straight duct divided into two fluid-filled scalae by the basilar membrane (BM) having an orthotropic material property with dimensional variation along its length. In particular, an active feed-forward mechanism is added into the passive cochlear model to represent the activity of the outer hair cells (OHCs). An iterative procedure is proposed for calculating the nonlinear response resulting from the active cochlea in the frequency domain. Results on the middle-ear transfer function, BM steady-state frequency response and intracochlear pressure are derived. A good match of the model predictions with experimental data from the literatures demonstrates the validity of the ear model for simulating sound pressure gain of middle ear, frequency to place map, cochlear sensitivity and compressive output for large intensity input. The current model featuring an active cochlea is able to correlate directly the sound stimulus in the ear canal with the vibration of BM and provides a tool to explore the mechanisms by which sound pressure in the ear canal is converted to a stimulus for the OHCs.
“…methods used to measure ear-canal pressure and velocities (e.g., stapes, round window, promontory, etc.) have been described in earlier publications [1,3]. The cartilaginous ear canal was removed in our preparation, thus the contribution of ear canal compression (occusion effect) of BC that would have occurred was presumably reduced in these experiments.…”
Section: Introductionmentioning
confidence: 99%
“…Because the highest voltage before significant distortion occurred was approximately 71 mV RMS , an input voltage of about 40 mV RMS across all frequencies was used. Intracochlear pressure measurements were made using 150-160 m diameter fiberoptic pressure sensors developed by Olson [1]. Cochleostomies (~200 m in diameter) were drilled by hand under fluid to prevent entrance of air into the cochlea.…”
Effect of middle-ear pathology on high-frequency ear-canal reflectance measurements in the frequency and time domains AIP Conference Proceedings 1703, 060003 (2015) Abstract. The mechanisms of bone conduction (BC) hearing, which is important in diagnosis and treatment of hearing loss, are poorly understood, thus limiting use of BC. Recently, information gained by intracochlear pressure measurements has revealed that the mechanisms of sound transmission that drive pressure differences across the cochlear partition are different for air conduction (AC) than for round-window stimulation. Presently we are utilizing these pressure measurement techniques in fresh human cadaveric preparations to improve our understanding of sound transmission during BC. We have modified our technique of intracochlear pressure measurements for the special requirements of studying BC, as bone vibration poses challenges for making these measurements. Fiberoptic pressure sensors were inserted through cochleostomies in both scalae at the base of the cochlea. The cochleostomies were then tightly sealed with the sensors in place to prevent air and fluid leaks, and the sensors were firmly secured to ensure uniform vibrations of the sensors and surrounding bone of the cochlea. The velocity of the stapes, round window and cochlear promontory were each measured with laser Doppler vibrometry simultaneous to the intracochlear pressure measurements. To understand the contribution of middle-ear inertia, the incudo-stapedial joint was severed. Subsequently, the stapes footplate was fixed (similar to the consequence of otosclerosis) to determine the effect of removing the mobility of the oval window. BC stimulation resulted in pressure in scala vestibuli that was significantly higher than in scala tympani, such that the differential pressure across the partition -the cochlear drive input -was similar to scala vestibuli pressure (and overall, similar to the relationship found during AC but different than during round-window stimulation). After removing the inertial mass of the middle ear, with only the stapes attached to the flexible oval window, all pressures dropped similarly (10 dB). Fixing the oval window resulted in further drop of all pressures (10 dB more). These decreases in pressure occurred around 1-4 kHz, consistent with clinical observations of Carhart's notch.
A vestibular third window in the posterior semicircular canal decreases the sensitivity to air-conducted sound stimuli, raising the air-conduction threshold. There is no change in the bone-conduction threshold. These findings agree with the theoretical model and clinical findings.
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