A digital heterodyne laser interferometer for studying cochlear mechanics
Introduction
The ear is a remarkably sensitive detector of minute pressure fluctuations. Such pressure fluctuations, sound, cause vibration of the detector cells, the inner and outer hair cells (OHCs). The hair cells convert the sound-evoked vibration into electric potentials that can be relayed to the brain through the auditory nerve.
The sensory cells are not merely passive detectors. The outer hair cells boost the vibration of the cochlear partition by supplying energy to counteract the viscous damping caused by the fluids surrounding the hearing organ (reviewed by Ulfendahl, 1997, Robles and Ruggero, 2001). The underlying mechanisms are controversial, but are believed to depend on the electrochemical gradient between outer hair cells and scala media, the endocochlear potential. To study this process, it is necessary to make precise measurements of vibrations from structures with very low optical reflectivity (Khanna et al., 1989a) that are highly sensitive to various forms of trauma. Furthermore, monitoring the electrochemical as well as electrophysiological parameters is important for understanding the function of the outer hair cells.
Previous studies showed that the vibration pattern of the hearing organ is complex. The main axis of vibration may differ for the various anatomical structures (Tomo et al., 2007, Fridberger et al., 2004). Therefore the angle of incidence of the laser beam must be precisely determined, since the interferometer will only detect the projection of the motion on the optical axis of the objective lens. A second important issue is the localization of the point from where vibration measurements are taken in the organ of Corti. Structures close by may have the same motion amplitude but a completely different phase response (Nowotny and Gummer, 2006). These factors may make interpretation of the results difficult.
The laser interferometer described here was designed to tackle the problems mentioned above. Hence the current system has novel components not found in its predecessors (Cooper, 1999, Willemin et al., 1989, Nuttall et al., 1991). To ameliorate common problems in analog electronics and to reduce overall system cost, we chose not to use conventional analog demodulation, but rather to use digital signal processing techniques based on direct sampling of the carrier waveform. To permit concurrent morphological studies and to allow precise control of the measurement location and angle, the interferometer is integrated with a laser scanning confocal microscope. Furthermore, up to two microelectrodes can monitor or modify electrochemical parameters.
Section snippets
General design
The presented setup (Fig. 1, Fig. 2) is based on a standard heterodyne detection schema. Following this schema an interference signal between two light beams of slightly different frequencies is detected. The interference consists of a high and a low frequency part. The later one, the so-called beating signal, is detected whereas the high frequency part is equal to the frequency of light, and therefore impossible to detect.
The interferometric beam path can be divided in three major parts: a
Confocality
Confocality is a measure of the size of the focus spot. It usually refers to the size of the focus spot along the optical axis of the lens. As the focus spot size decreases fewer structures will be illuminated and hence fewer structures will contribute to the motion measurements. Therefore a very small focus spot is desirable, since it will yield very localized measurements (Dalhoff et al., 2001, Ren and Nuttall, 2001). On the other hand as the focus spot size decreases, the light intensity
Discussion
The presently implemented system has several new features including the use of digital displacement decoding, the usage of a third interferometer arm generating a reference interference signal and the integration with a laser scanning confocal microscope, as described above.
The presented setup was developed to tackle problems occurring particular in interferometric measurements in the apical turn of the inner ear. While in basal measurements it is possible to use hundreds to thousands of
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