Acute Endolymphatic Hydrops Generated by Exposure of the Ear to Nontraumatic Low-Frequency Tones
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Low-frequency sounds presented at high nontraumatizing levels induce temporary hyperacusis in humans and animals. One explanation of this finding is that the basilar membrane operating point may be disturbed by an endolymph volume change. This possibility was investigated using volume and flow markers iontophoresed into the endolymphatic space of guinea pigs. Marker concentrations were measured with ion-selective microelectrodes placed apically and basally to the iontophoresis site during exposure of the ear to low-frequency tones. Concentration changes were interpreted quantitatively using a finite-element model of the endolymphatic space that allowed changes of endolymph cross-sectional area and flow to be derived. Stimulation with a 200 Hz tone at 115 dB SPL for 3 min produced marker concentration changes consistent with the induction of transient endolymphatic hydrops and a basally directed displacement of endolymph. Endocochlear potentials were greater than normal after the exposure when hydrops was present. During identical tone exposures of animals without marker, we found that action potential (AP) threshold changes and endolymph potassium changes associated with the hydropic state were small. Marker concentration changes were compared with changes in endocochlear potential and AP thresholds for a range of exposure frequencies and levels. AP hypersensitivity occurred with 200 Hz exposure levels below those inducing endolymph volume disturbances. Endolymph volume changes are thought to be the result of, rather than the cause of, changes in operating point of the cochlear transducer. The observations that auditory threshold and endolymph potassium changes are minimal under conditions where substantial endolymphatic hydrops is present is relevant to our understanding of the hearing loss in patients with Ménière’s disease.
Keywordsendolymph volume Ménière’s disease
The ionic composition of endolymph is remarkably stable during most types of sound stimulation of the ear. Salt and Konishi (1979) reported that stimulation of guinea pigs with wideband noise at levels up to 115 dB produced only minor increases of endocochlear potential (EP) and endolymph K+, even though the 115 dB level produced a substantial impairment of cochlear sensitivity. Only when extremely high sound levels are delivered do substantial changes of endolymph K+ occur. Melichar and Syka (1980) showed that 142 dB octave band noise presented to guinea pigs caused dramatic reductions in both EP and endolymph K+, which recovered over a 20-day period. Salt and Konishi (1979) similarly found that wideband noise delivered at 125 dB SPL caused large reductions of EP and endolymph K+.
In contrast, low-frequency tones appear to produce unusual effects on the ear, causing a transient enhancement of hearing sensitivity immediately postexposure. This was initially reported in humans by Hirsh and Ward (1952), who called it the “two-minute bounce.” Kemp (1982) subsequently observed an increase in the amplitude of transient otoacoustic emissions following low-frequency tone exposures. The emission increase peaked at 1–1.5 min after the tone ended, which he also referred to as a “bounce.” The origins of the enhancements of auditory sensitivity and acoustic emissions after low-frequency tones were further investigated by Kirk and Patuzzi (1997) and Kirk et al. (1997). Using measurements of cochlear microphonics and otoacoustic emissions, Kirk and Patuzzi (1997) confirmed that the transient hypersensitivity seen approximately 1 min after low-frequency tone exposure was cochlear, rather than neural, in origin. Based on an analysis of the cochlear microphonic waveform from which the operating point of the cochlear transducer was derived, they suggested that the sensitivity changes were caused by a shift in the operating point of the cochlear transducer comparable to a displacement of the organ of Corti towards scala tympani (Kirk et al. 1997). One explanation put forward to account for this shift was through an osmotic mechanism, in which the low-frequency sound caused a transient “scala media bloating.” The concept that low-frequency tones influence the endolymphatic system was further supported by an in vitro study by Flock and Flock (2000). In that study, isolated cochleae were maintained by high-rate perilymphatic perfusion while tissue boundaries in the apical turn were visualized directly with a confocal microscope. Stimulation with 140 Hz tone bursts between 90 and 115 dB was found to produce substantial endolymphatic hydrops in the apical turn, which rapidly recovered to normal after cessation of the tone.
In the present study, we have investigated the endolymph volume and functional changes produced by low-frequency tones. This was performed using ionic markers, iontophoresed into endolymph without volume disturbance and monitored with ion-selective electrodes during experimental manipulations. These markers have been used previously to quantify endolymph cross-sectional area and flow in normal ears (Salt et al. 1986), in ears with chronic endolymphatic hydrops (Salt et al. 1995), and in ears in which endolymph was manipulated acutely (Salt and DeMott 1997, 1998).
Pigmented NIH strain guinea pigs weighing 300–500 g were anesthetized with Inactin (sodium thiobutabarbital) at a dose of 100 mg/kg given intraperitoneally. The trachea was cannulated and the animal was mechanically ventilated, maintaining an end-tidal CO2 level of 4%–5%. Body temperature was maintained at 39°C with a thermistor-controlled heating pad. An intravenous line was placed in the external jugular vein for anesthetic supplements. The inner ear on the right side was exposed by a ventrolateral approach and the bulla was opened widely to gain access to the cochlea, leaving middle ear structures intact. Prior to recordings a muscle relaxant, pancuronium bromide (IV, to effect), was given to suppress movement artifacts and middle ear muscle effects. The results of this study are based on findings in 29 guinea pigs.
Sounds were delivered through a hollow ear bar inserted into the sectioned ear canal. One of two sound sources was used, according to the needs of the experiment. For those experiments requiring 8 kHz stimuli for threshold testing, an Etymotic ER-2 driver was used. In other experiments, such as those requiring levels up to 125 dB SPL at 200 Hz, a Sennheiser HD 580 driver coupled to the closed cavity was used. Sound stimuli were calibrated using a B&K 4135 microphone with a probe tube adaptor that terminated at the tip of the earbar. An automated routine was used to track a specified sound level (typically 75 dB SPL) in the ear canal as frequency was varied in 0.25 octave steps. All aspects of sound stimuli delivered (frequency, level, and timing) were computer controlled.
Evoked potentials were recorded from an Ag/AgCl ball electrode placed on the round window membrane, recorded differentially relative to a platinum needle inserted under the skin at the vertex. The signal was amplified 5000× and filtered below 30 Hz and above 30 kHz with a Princeton PAR113 amplifier. Waveforms were digitized and averaged using an Analogic D6000 under computer control. Cochlear action potential (AP) responses were collected by averaging responses to 10 condensation onset and 10 rarefaction onset (inverted) tone burst stimuli, thereby canceling the cochlear microphonic component. AP thresholds were established in an automated routine using an amplitude criterion of 10 μV, which was approximately 4 times greater than the recording noise level with no stimulus. Stimuli were increased in 5 dB steps until AP amplitude exceeded the criterion, and then decreased in 5 dB steps until the AP amplitude was below the criterion. The threshold value was established by interpolation between above- and below-threshold response amplitudes, at the point corresponding to 10 μV amplitude. In experiments where cochlear sensitivity was monitored during experimental treatments, AP thresholds at two frequencies were determined and the measurements repeated sequentially at 40 s intervals.
Analysis of marker changes used techniques that are described in detail elsewhere (Salt and DeMott 1995) and are presented briefly here. During the iontophoretic injection of volume marker, a concentration profile of the marker along the endolymphatic space is established, as shown schematically in Figure 1. Concentration is highest at the injection site and decreases with distance in both directions along the scala from the injection site as the marker spreads by diffusion. With this profile established, any longitudinal movement of endolymph will cause concentration at one ion-selective electrode to increase while the other decreases. For example, a basal movement of endolymph will cause concentration at the basal electrode to increase while the concentration at the apical electrode decreases. Thus, the ratio of concentrations detected by the two electrodes is a sensitive indicator of longitudinal endolymph flow. On the other hand, a cross-sectional area change, with fluid movement into or out of the compartment while the total amount of marker remains unchanged, will cause similar concentration changes at both electrodes. If fluid volume is lost and cross-sectional area decreases, then the marker concentration will increase. These relationships permit effects of flow and cross-sectional area change to be differentiated. Analysis of the marker concentration changes in those experiments using two ion-selective electrodes utilized our finite-element model of the cochlear fluid spaces that combines the effects of diffusion, longitudinal volume flow, and clearance of marker (Salt and DeMott 1995). A version of this program is available on the Internet at oto.wustl.edu/cochlea/. A custom version of this program (not available on the Internet) was used to simulate the spread of marker along the endolymphatic space for the two electrode locations specific to each experiment. The diffusion coefficients used were 1.34 × 10−9 m2 /s for TMA+ and 1.30 × 10−9 m2 /s for AsF 6 − . For TMA+ a clearance half-time of 30 min was used (Salt and DeMott 1995). After each 10 s period of simulation, the program compared the concentrations at the locations in the model corresponding to the recording locations, with the concentrations measured experimentally. First, the ratio of the concentrations between the two sites in the model was adjusted by longitudinal movements of marker, with an algorithm simulating longitudinal endolymph flow. If the basal/apical ratio in the model was lower than that observed experimentally, then a basal movement of marker was performed as required to obtain the exact ratio measured. The amount of longitudinal movement (i.e., longitudinal flow) necessary to keep the ratio of concentrations in the model identical to the measured ratio of concentrations was established. Then, the cross-sectional area of the compartment was adjusted in the model until the concentrations at the two locations in the model were identical to those for the experimental data. If the concentration in the model was too high, then cross-sectional area was decreased proportionately. In this manner, the simulation established a pair of concentration time courses identical to the measured data and provided sequential values for the longitudinal movements and cross-sectional area changes required to fit the measured data. Between each adjustment interval, corresponding to the 10 s data sampling intervals, the program simulated marker injection by iontophoresis and marker diffusion. In the case of TMA+ simulations, TMA+ clearance from the endolymphatic space was also included. This analysis makes the assumption that flow and area changes are similar at the two recording electrode locations. Since the two sites are only approximately 1 mm apart (the distances are highly exaggerated in Fig. 1), this assumption appears reasonable.
The Animal Studies Committee of Washington University approved the experimental procedures used in this study under protocol numbers 91062 and 19990029.
Our results show that low-frequency tones, presented at high but nondamaging levels, cause an acute endolymphatic hydrops in the second turn of the guinea pig cochlea. This confirms the observation by Flock and Flock (2000) of low-frequency sound-induced hydrops in the apical turn of isolated, perfused cochleae. The further observation of near-normal AP thresholds at a time when endolymphatic hydrops is present in the cochlea suggests that this type of hydrops is not a pathologic state, but is part of the normal repertoire of cochlear responses to stimulation. Recovery from the hydropic state takes place rapidly, apparently dominated by local homeostatic mechanisms. Although a small basally directed flow was observed during the 3 min exposure period, the flow rate is small relative to the area increase and the rate falls after exposure. The recovery back toward normal cross-sectional area therefore cannot be accounted for by longitudinal flow mechanisms. The basally directed flow during 200 Hz exposure is consistent with prior studies in which basally directed flow was demonstrated following acute endolymphatic injections (Salt and DeMott 1997) and from pressure studies that suggest that the saccule may form a compliant structure so that flow may be directed toward it (Wit et al. 2000). However, such an explanation based on “passive” mechanical properties of the endolymphatic space is not consistent with coexistence of apically directed displacement and endolymphatic hydrops induced by 50 Hz stimulation. This suggests that more complex relationships, possibly involving compliance changes of the boundary tissues, may exist. Indeed, the observation that marker changes were minimal in the basal turn also suggests that the hydrops induced in the second turns [and, based on Flock and Flock (2000), also assumed to be present in higher turns] does not spread down the cochlea to the saccule as endolymph injection experiments have suggested (Salt and DeMott 1997, Wit et al. 2000). This may be the result of the nonlinear relationship between endolymph pressure and volume increase (Wit et al. 2000), in which the endolymphatic boundaries appear to be highly compliant for small volume disturbances.
The magnitude and rate of endolymph volume change induced by 200 Hz exposure is larger than we thought possible, based on steady-state kinetic data. The observation that endolymph volume can increase by more than 30% within 3 min, with almost no reduction in endolymph K+ concentration (approximately 0.6% decrease), indicates that electrolytes must be added to the endolymphatic space during the exposure and subsequently removed during the recovery period. The rate of these changes (half-time 2.5 min for the increase, 3.2 min for the recovery; based on fitted exponential curves) is much faster than the endolymph turnover rates measured by radiotracer under steady-state conditions. In guinea pigs the turnover half-time for endolymph K+ was 55 min and for Cl− it was 69 min (Konishi et al. 1978; Konishi and Hamrick 1978). The rate of ionic change with low-frequency stimulation is thus larger than that expected based on steady-state endolymph turnover rates.
The volume changes we observed must arise from an accumulation of both anions and cations within the endolymphatic space, as we see only minor changes in endolymph K+ concentration during 200 Hz exposures at 115 dB SPL. Perilymphatic manipulations with osmotically altered media indicate that water equilibration is rapid between the endolymphatic and the perilymphatic spaces (Salt and DeMott 1995). The equilibration half-time was estimated to be approximately 8 min, so that an increase in total electrolytes in the endolymph would result in a volume increase. In order for electrolytes to accumulate there must be a reduction in K+ efflux from the endolymphatic space during the tone exposure. Based on measurements of transducer operating point during low-frequency simulation, Kirk and Patuzzi (1997) suggested that there is a movement of the organ of Corti toward scala tympani as a result of high level, low-frequency tone stimulation. Such a movement would reduce current through the organ of Corti, a current that is predominantly carried by K+ as the hair cell transducer channels are cation-specific (Kros 1996). The second factor is how the increase of endolymph anion content could arise. Zidanic and Brownell (1992) demonstrated that, during individual stimulus cycles as current through the organ of Corti was modulated, current efflux through Reissner’s membrane was modulated in a reciprocal manner. Current through Reissner’s membrane was shown to increase when current through the organ of Corti was reduced. They interpreted this as indicating that the stria vascularis maintained a constant current during acoustic stimulation and that Reissner’s membrane acted as a current shunt, compensating for current changes through the organ of Corti. They also noted that, in the absence of stimulation, voltage gradients in the fluids of scala vestibuli were larger than those in scala tympani (Zidanic and Brownell 1990), indicating higher current magnitudes in scala vestibuli. While part of this apparently sizable current through Reissner’s membrane may be carried by K+, there is considerable evidence that Cl− movements across Reissner’s membrane also occur. In a series of studies, evidence was found for the presence of cAMP-activated Cl− channels in Reissner’s membrane that, when activated by forskolin, produced increases in endolymph Cl− concentration (Doi et al. 1992; Kitano et al. 1993, 1995). Chloride channels have also been demonstrated in the apical membranes of Reissner’s membrane epithelial cells (Yeh et al. 1997) If a substantial part of the outwardly directed current observed by Zidanic and Brownell (1990) was carried by Cl− entering the endolymphatic space, then the situation could arise in which a reduction in K+ current across the organ of Corti would result in an increase in Cl− current across Reissner’s membrane. This would result in both K+ and Cl− accumulating in the endolymphatic space. There could also be a degree of positive feedback in this process since volume enlargement would displace the organ of Corti even further toward scala tympani. Although the mechanisms of endolymph Cl− homeostasis are not well established, it is notable that the radiotracer studies cited above show that the rate of endolymph Cl− turnover (69 min half-time) is almost as fast as that of K+ (55 min half-time), so the contribution of Cl− movements to the currents circulating through endolymph must be considerable even in this undisturbed state. However, the above explanation is obviously speculative to some degree and should not be regarded either as complete or as the sole explanation. The possible contributions of other tissues and cell types and other cations, such as HCO−3, cannot be excluded. Other plausible mechanisms involved in the volume increase may also exist.
The nature of the operating point shift occurring with low-frequency tones is of considerable interest. Kirk and Patuzzi (1997) suggested that either “an osmotic imbalance in the fluids of the organ of Corti” or a “bloating of scala media” could be the cause of the operating point shift. While the acute endolymphatic hydrops we observe could certainly contribute to an operating point shift (tending to displace the organ of Corti toward scala tympani and reducing current through the organ of Corti), it appears that operating point shifts occur at stimulus levels well below those causing endolymph volume disturbances. It remains likely that the operating point shift at the level of the hair cells is a major factor in the cause of the endolymph volume disturbance, but it appears less likely that the operating point shift occurs as a result of endolymph volume disturbance. It is not possible to draw a strong conclusion regarding cause and effect from the present data as the organ of Corti may be more sensitive to small volume disturbances than is our marker measurement system. Localized ionic changes in the organ of Corti may precede disturbances of endolymph volume. This may also account for why threshold changes to high-frequency stimulation (8 kHz) are observed under conditions where endolymph volume in the basal turn is apparently unaffected.
The possible effect of EP changes on the cochlear sensitivity and on endolymph volume changes remains uncertain. EP changes are known to strongly influence auditory sensitivity, with thresholds elevated by approximately 1 dB for each 1 mV of EP decrease (Sewell 1984). It is therefore possible that the poststimulus EP increase could contribute to threshold improvements after sound. However, the time course of AP threshold changes is slower than that of the EP (Fig. 9). In addition, Kirk and Patuzzi (1997) pointed out that EP changes would also be a direct consequence of operating point shifts of the organ of Corti. A displacement of the organ of Corti toward scala tympani would reduce current through the hair cells and cause a rise in EP. Their analysis indicated that the sensitivity changes of cochlear responses were more consistent with operating point shifts at the level of the hair cells being the primary cause, with EP changes arising as a secondary phenomenon. Our present data remain consistent with this interpretation. Similarly, while substantial ionic movements must be associated with endolymph volume changes and their recovery, the EP changes are only a few mV in magnitude and follow time courses dissimilar to those of the volume changes. Since the potential changes cannot be accounted for simply by modulation of K+ currents at the hair cells or stria vascularis, additional data will be required to understand how such large ionic movements can occur with only modest influence on the EP.
The physiologic effects of acute hydrops seen in the present study are considerably different from those associated with the chronic hydrops that develops over a period of weeks after ablation of the endolymphatic sac. Associated with the acute hydrops in the present study is an increase in the postexposure EP, while EP in the chronic hydrops model is typically decreased by 5–30 mV (Cohen and Morizono 1984; Salt et al. 1995). The observation that the thresholds at 8, 4, and 2 kHz are within 5 dB of normal in animals in which endolymph volume has increased by over 30% clearly demonstrates that hydrops itself is not the cause of substantial hearing loss. Threshold shifts in animals with chronic hydrops are generally greater and increase with time (reviewed by Horner 1993). However, a number of studies have reported normal thresholds or only slight threshold elevations in animals with confirmed endolymphatic hydrops (van Deelen et al. 1987; Klis and Smoorenburg 1988). It seems likely that the substantial hearing loss seen in the later stages of chronic hydrops involves factors other than the endolymph volume increase. This may include the EP decrease, which is known to elevate cochlear sensitivity (Sewell l984), endolymph Ca2+ elevation (Ninoyu and Meyer zum Gottesberge 1986; Salt and DeMott 1994), or other pathological changes known to be occurring in the cochlea, such as stereociliary abnormalities (Horner et al. 1988). In addition, our observations showing that acute endolymphatic hydrops is rapidly corrected in the normal cochlea, apparently by local ion transport mechanisms, raises the intriguing question of why such a rapid correction does not occur in the cochleae of animals after endolymphatic sac ablation. Understanding the mechanisms contributing to local volume recovery, specifically what factors block or stimulate recovery from volume disturbance, would seem to be of prime importance for understanding chronic hydrops and Ménière’s disease.
I would like to dedicate this article to the memory of Des Kirk and Graeme Yates, both outstanding physiologists who pioneered work in this area. Their contributions to the field will be missed. This study was supported by research grant RO1 DC01368 from the National Institute on Deafness and Other Communication Disorders (NIDCD), National Institutes of Health. The technical contributions of John DeMott and Shane Hale, who performed the experimental work reported here, are also acknowledged.
- 4.Greenwood, DD 1990A cochlear frequency–position function for several species—29 years later.J. Acoust. Soc. Am.8725922605Google Scholar
- 5.Hirsh, IJ, Ward, WD 1952Recovery of the auditory threshold after strong acoustic stimulation.J. Acoust. Soc. Am.24131141Google Scholar
- 13.Kros, CJ 1996
Physiology of mammalian cochlear hair cells.Dallos, PPopper, ANFay, RR eds. The Cochlea.SpringerNew York318385Google Scholar
- 15.Konishi, T, Hamrick, PE, Walsh, PJ 1978Ion transport in the guinea pig cochlea I. Potassium and sodium transport.Acta Otolaryngol.1862234Google Scholar