Spatial distribution of electrically induced high frequency vibration on basilar membrane
Introduction
The outer hair cells (OHCs) of mammalian organ of Corti are able to convert electrical fluctuation of their transmembrane potential to cell length variation. This, the so-called OHC electromotility, has been demonstrated in isolated OHC experiments (Brownell et al., 1985, Kachar et al., 1986, Ashmore, 1987, Santos-Sacchi and Dilger, 1988, Frank et al., 1999). The motility is fast enough to follow changes in the membrane potential at auditory and ultrasonic frequencies (Dallos and Evans, 1995b, Frank et al., 1999). The OHC electromotility in vivo is considered to function within a cycle-by-cycle sound amplification mechanism by feeding back mechanical energy with the correct phase to the basilar membrane (BM) to enhance vibration or drive the BM. It has been shown in vivo that electrical stimulation applied into the cochlea can evoke otoacoustic emissions (Hubbard and Mountain, 1983, Nuttall and Ren, 1995, Ren et al., 1996, Nuttall et al., 2001) and induce BM motion (Xue et al., 1995, Nuttall et al., 2003, Grosh et al., 2004).
Based on the membrane resistance and capacitance of OHCs, a low-pass membrane filtering will occur, restricting the OHC electromotility force or stiffness change at high frequencies (Housley and Ashmore, 1992, Santos-Sacchi, 1992, Preyer and Gummer, 1996). Nevertheless, OHC electromotility was observed at least up to 79 kHz in an isolated OHCs experiment (Frank et al., 1999). Our previous in vivo studies have shown a high frequency BM motion above the best frequency (BF) extending to 100 kHz evoked with electrical stimulation at the round window (RW) or across the cochlear duct (Nuttall et al., 2003, Grosh et al., 2004). In these studies, the velocity magnitude spectrum above BF showed a low of BM velocity, called a “dip”, at a frequency around 50 kHz when the measurement was taken at a location about 14.9 mm from the apex (a BF location of 17 kHz). We defined the dip frequency (DF) as the frequency with the lowest magnitude and a rapid phase transition. A different pattern of BM motion evoked with electrical stimulation was also observed at the tunnel of Corti compared to the OHC region (Grosh et al., 2004).
These results showed that the OHC electromotility evoked with electrical stimulation has sufficient force to move the BM at such high frequencies (Nuttall et al., 2003, Grosh et al., 2004). The different radial pattern of the electrically evoked high frequency BM motion was assumed due to the asymmetrical mechanical properties of the organ of Corti and the involvement of the OHC electromotility, the test for which was by salicylate-induced reduction of the BM responses (Grosh et al., 2004).
Studies have revealed that the motility of OHC is based on a membrane protein motor that directly converts electrical energy to mechanical force (Zheng et al., 2000, Dallos and Faker, 2002). Conformational transitions of this membrane protein motor accompany charge transfer across the membrane resulting in mechanical displacement of membrane. The electrical and mechanical changes are coupled, analogous to piezoelectricity (Iwasa, 2001). Piezoelectric OHC models have been proposed for the lateral membrane motor of OHC (Mountain and Hubbard, 1994, Tolomeo and Steele, 1995, Weitzel et al., 2003). A recent equivalent circuit made for the OHC that includes piezoelectricity showed a greater mechanical admittance at high frequencies than one containing only the membrane resistance and capacitance (Weitzel et al., 2003). This model predicted resonance at ultrasonic frequencies that is inversely proportional to cell length (Weitzel et al., 2003).
We hypothesized that the longitudinal and radial patterns of high frequency vibration should depend on the mechanical properties of the cochlear partition. These mechanical properties will result from the variation of the length of OHCs, the width and stiffness of the BM and other cellular components. To test this hypothesis, we measured the BM vibration evoked by acoustic and electrical stimulation at three longitudinal locations of approximately 28.0, 21.3 and 17.0 kHz of the BFs. We also measured the BM vibration at different radial locations across the width of BM at the above longitudinal sites. This study extends our previous work (Nuttall et al., 2003, Grosh et al., 2004) with a more detailed investigation of the longitudinal and radial pattern of the electrically induced BM motion at the basal turn and hook areas.
Section snippets
Animal preparation
Young pigmented guinea pigs (n = 15) with normal hearing (strain 2, NCR, obtained from the Charles River Laboratory, weighing 250–350 g) were divided into three groups with five animals, each for the different longitudinal measurements. In general, the BM data were collected only from one longitudinal location per animal with a single exception as mentioned below. Surgical and experimental protocols used in animals were approved by the Institutional Animal Care and Use committee of Oregon Health
Results
BM velocity data from 15 animals (five animals at each of three longitudinal locations) are summarized in this report. Only one of these animals was used to record multiple longitudinal locations through one observation hole. In most cases, one longitudinal location was measured through an observation hole. The animals in this report had insensitive cochleae resulting from the surgical procedures for wide exposure of the BM. For most of animals in this report, the CAP thresholds at frequencies
Discussion
Our data confirm that the electrically evoked BM vibration near the BF is different from that at the frequency above the BF, which is consistent with previous results (Nuttall et al., 2003, Grosh et al., 2004). For frequencies near the BF, the vibration pattern was similar to that for acoustic simulation, i.e., there was a sharp peaked response and an increasing phase lag, typical for forward traveling waves. Thus, this BM vibration was considered as an electrically induced propagating
Conclusion
The electrically evoked high frequency BM motions were measured at different longitudinal and radial locations in the basal cochlear turn of guinea pigs in vivo in the present study. It was confirmed that OHC electromotility in vivo extends at least up to 100 kHz, and can vibrate the BM at such high frequencies. In addition, the BFs of BM motion to electrical stimulation was similar to that determined acoustically. The magnitude dip of the high frequency BM motion to electrical stimulation
Acknowledgements
This work was supported by NIDCD Grants DC00141, DC04554 and VA RR&D Center Grants.
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