Tinnitus suppression by electric stimulation of the auditory nerve.

Electric stimulation of the auditory nerve via a cochlear implant (CI) has been observed to suppress tinnitus, but parameters of an effective electric stimulus remain unexplored. Here we used CI research processors to systematically vary pulse rate, electrode place, and current amplitude of electric stimuli, and measure their effects on tinnitus loudness and stimulus loudness as a function of stimulus duration. Thirteen tinnitus subjects who used CIs were tested, with nine (70%) being "Responders" who achieved greater than 30% tinnitus loudness reduction in response to at least one stimulation condition and the remaining four (30%) being "Non-Responders" who had less than 30% tinnitus loudness reduction in response to any stimulus condition tested. Despite large individual variability, several interesting observations were made between stimulation parameters, tinnitus characteristics, and tinnitus suppression. If a subject's tinnitus was suppressed by one stimulus, then it was more likely to be suppressed by another stimulus. If the tinnitus contained a "pulsating" component, then it would be more likely suppressed by a given combination of stimulus parameters than tinnitus without these components. There was also a disassociation between the subjects' clinical speech processor and our research processor in terms of their effectiveness in tinnitus suppression. Finally, an interesting dichotomy was observed between loudness adaptation to electric stimuli and their effects on tinnitus loudness, with the Responders exhibiting higher degrees of loudness adaptation than the Non-Responders. Although the mechanisms underlying these observations remain to be resolved, their clinical implications are clear. When using a CI to manage tinnitus, the clinical processor that is optimized for speech perception needs to be customized for optimal tinnitus suppression.

Introduction

Tinnitus is an auditory disorder known as “ringing of the ears or head” which affects 50 million Americans and an estimated 600 million worldwide, according to the American Tinnitus Association (ATA; www.ata.org). Its severity can range from being temporary and unobtrusive to debilitating and life-impairing. Tinnitus has steadily increased by 18% per year since 2001 in soldiers returning from the Global War on Terror, and is currently the number one cause of service-connected disability (ATA, 2011). Although management treatments and therapies are available, there currently exists no cure (Goodey, 2007).

While neural mechanisms causing tinnitus and hearing loss are not identical, the incidence of tinnitus is highly correlated with, and believed to be related to hearing loss (Axelsson and Ringdahl, 1989). A study by the National Study of Hearing showed that hearing impairment is the dominant factor in predicting the occurrence of prolonged spontaneous tinnitus (Coles et al., 1988; Tyler, 2000). Although not all individuals experiencing tinnitus have hearing loss, those who have a hearing loss experience an 83% higher risk of developing tinnitus over those who do not have a hearing loss (Nondahl et al., 2002). Interestingly, when these individuals are fit with hearing aids, approximately half of hearing aid users with tinnitus report that their amplification also provides either partial or total relief from their tinnitus (Surr et al., 1985).

Individuals with more severe hearing loss may receive a cochlear implant (CI) to help restore hearing (Zeng, 2004). While most individuals who have tinnitus are not profoundly deaf (Tyler, 2000), a reported 66–86% of CI users indeed experience tinnitus (Tyler and Kelsay, 1990; Hazell et al., 1995; Miyamoto et al., 1997; Quaranta et al., 2004; Bovo et al., 2010). Evidence of cochlear electrical stimulation has been noted to benefit tinnitus, and CIs have been suggested as a potential therapeutic since they became commercially available in the early 1980s (House and Brackmann, 1981). In recent years, the benefit of CI on tinnitus has been widely reported in many studies. Efficacy rates range from 34 to 93% (Tyler and Kelsay, 1990; Miyamoto et al., 1997; Pan et al., 2009; Bovo et al., 2010). On the other hand, a smaller percentage of 16.7–41.5% of CI users reports no effect of the CI on their tinnitus (Tyler and Kelsay, 1990; Miyamoto et al., 1997; Bovo et al., 2010).

Significantly, most studies investigating CI effects on tinnitus have used standard multichannel CIs using speech processors optimized for speech. Observational questionnaires comparing pre- and post-implantation tinnitus have found reduction in tinnitus intensity or loudness (Ito and Sakakihara, 1994; Miyamoto et al., 1997; Ruckenstein et al., 2001), decreased annoyance, and general reports that “the majority of patients thought that their CI was helpful in tinnitus suppression” (Souliere et al., 1992). Changes in tinnitus pitch and timber following implantation have also been noted (Souliere et al., 1992; Miyamoto et al., 1997). These effects have been attributed to surgical insertion of the intra-cochlear electrode (Baguley and Atlas, 2007) as well as plastic changes in the auditory system brought about by CI use (Quaranta et al., 2004; Baguley and Atlas, 2007). Of note, current candidacy requirements for CI implantation are strictly based on hearing capabilities, as measured by severe-to-profound sensorineural hearing loss that is not substantially improved by hearing aids, and speech recognition test scores in the United States, Canada, and the United Kingdom (UK Cochlear Implant Study Group, 2004; Balkany et al., 2007; Amoodi et al., 2012). Because clinical processors used in CIs are designed to improve speech perception (Wilson et al., 1991; Zeng et al., 2008), their effects on tinnitus are usually considered to be secondary.

There is limited literature on optimizing electric stimulation for tinnitus suppression. Rubinstein et al. (1999) used high-rate stimulation to produce a pattern of spontaneous-like firing similar to that seen in the healthy auditory nerve, which is thought to represent the auditory “code for silence.” He tested the effectiveness of high-rate stimulation [4800 pulses per second (pps)] in three Cochlear CI users with tinnitus and found that one subject showed level-dependent tinnitus suppression with complete adaptation to the electric stimulus, one subject showed tinnitus suppression only in the presence of a stimulus percept, and one subject reported no change in tinnitus at her maximal comfort level of stimulation (Rubinstein et al., 2003). On the other hand, Dauman et al. (1993) explored low-rate bipolar stimulation in two Cochlear CI patients, finding that 125 pps stimuli was the most effective in that it required the lowest amount of current to achieve suppression, and that the effectiveness of stimulation could vary by place. A parametric study exploring various combinations of stimuli parameters also found low-rate stimuli effective at completely suppressing tinnitus in a single Advanced Bionics HiRes CI user (Zeng et al., 2011). In this study we sought to corroborate these findings in a larger subject size using various CI devices. The goal of the present study is twofold: (1) to use flexible research processors to systematically vary electric stimulation parameters and measure their effects on tinnitus suppression, and (2) to identify relationships between tinnitus characteristics and electric stimulation to tinnitus suppression.

Materials and methods

Subjects

Subjects who had chronic tinnitus and a CI were screened for the study. Prior to enrollment, subjects completed an online tinnitus survey, including a questionnaire about their hearing loss and tinnitus, the Beck Depression Inventory (BDI), Beck Anxiety Inventory, Tinnitus Handicap Index, and Tinnitus Severity Index. They also provided audiological records, which included their speech recognition scores as assessed by the standardized Hearing in Noise Test (HINT; Nilsson et al., 1994). Subjects who had not been evaluated by a physician for their tinnitus, had a treatable type of tinnitus, or were on medications or other treatments for their tinnitus were excluded from the study. All subjects perceived their tinnitus for a minimum of six months.

Thirteen CI users with chronic tinnitus, 11 female and two male of average age 60.8 ± 13.6 years (mean ± SD) participated in the study (Table 1). Etiology of hearing loss varied, and all subjects had severe to profound hearing loss in the non-implanted ear except for S11, who had sudden sensorineural hearing loss in one ear and normal hearing in the other. Average duration of hearing loss was 27.9 ± 11.7 years and subjects had an average CI use of 5.15 ± 3.8 years with at least one year of experience. Six subjects used Cochlear devices, four used Advanced Bionics, and three used Med-El. These CI users had sentence recognition ranged from 0 to 100%, and covered the full range from poor to good performers (Nilsson et al., 1994; Friesen et al., 2001).

Table 1

Patient demographics.

	Gender	Age	Hearing loss		Cochlear implant (CI)
			Etiology	Duration (years)	CI use (years)	CI side	HINT sentence (% correct)
S1	F	59	Otosclerosis	26	1	L	76
S2	F	67	Genetic	34	6	R	100
S3	F	74	Sensorineural	28	9	L	97
S4	F	77	Autoimmune	21	4	L	75
S5	F	50	Autoimmune	31	13	Both	96 (L)
							63 (R)
S6	F	61	Meniere's	29	2	L	96
S7	F	72	Idiopathic	15	9	Both	n.a. (L)
							87 (R)
S8	F	59	Sensorineural	43	8	L	44
S9	M	86	Noise-induced	39	3	R	8
S10	F	43	Radiation-induced	14	1	L	76
S11	M	50	Idiopathic	5	4	R	70
S12	F	45	Congenital rubella	45	6	L	0
S13	F	47	Genetic	33	1	R	100

n.a. = not available.

Tinnitus characteristics

Patient tinnitus characteristics are shown in Table 2. Prior to testing, patients were asked if “their tinnitus has improved since cochlear implantation.” Seven (54%) patients reported “Yes” or “sometimes,” while five subjects (38%) reported “No” and one subject was unsure. All patients had experienced tinnitus for a minimum of one year, ranging from 1 to 49 years with an average of 20.5 ± 15.3 years. Tinnitus Handicap Inventory (THI) scores showed 38% of subjects (5 of 13) with moderate handicap, 31% (4 of 13) with mild handicap, and 31% (4 of 13) with slight or no tinnitus handicap. Ninety-two percent (12 of 13) of patients had minimal depression (the lowest grade possible) based on the BDI, and one subject experienced mild depression.

Table 2

Patient tinnitus characteristics.

	CI benefit (self-report)	Duration (years)	Tinnitus Handicap Inventory (THI)		Beck Depression Inventory
			THI	THI score	BDI	BDI score
S1a	No	1	20	Mild (Grade 2)	1	Minimal
S2	Sometimes	14	18	Mild (Grade 2)	5	Minimal
S3b	Sometimes	Unsure	6	Slight or None (Grade 1)	10	Minimal
S4	Sometimes	21	22	Mild (Grade 2)	6	Minimal
S5b	No	32	40	Moderate (Grade 3)	8	Minimal
S6b	No	20	40	Moderate (Grade 3)	9	Minimal
S7	Yes	14	14	Slight or None (Grade 1)	4	Minimal
S8b	Yes	44	14	Slight or None (Grade 1)	2	Minimal
S9	Sometimes	49	22	Mild (Grade 2)	13	Minimal
S10	Unsure	12	0	Slight or None (Grade 1)	0	Minimal
S11	No	5	52	Moderate (Grade 3)	15	Mild
S12	No	5	52	Moderate (Grade 3)	4	Minimal
S13	Sometimes	29	48	Moderate (Grade 3)	6	Minimal

Onset of tinnitus after implantation.

Experienced bilateral tinnitus, with distinct sounds reported by ear.

Average baseline loudness rating (LR) of their tinnitus was 4.4 ± 1.9 on a numeric scale from 0–10 (Table 3). Subjects reported a variety of different sounds descriptive of their tinnitus. The most common sound perceived was humming (85%, 11 subjects), followed by ringing and roaring (both 77%, 10 subjects each), then buzzing and the “inside of a seashell” (both 69%, nine subjects each). Two subjects reported hearing music alongside their tinnitus.

Table 3

Tinnitus characteristics.

	Baseline loudness	Buzz	Hum	Ring	Blow	Hiss	Roar	Whistling	Pulsating	Constant high pitches	Constant low pitches	Running water	Inside of a seashell	Sizzle	Other
S1	4.0										X				X
S2	3.2	X	X	X		X	X	X	X			X	X	X	Xa
S3	1.0 (L)	X	X	X		X	X	X		X	X		X	X
	5.0 (R)
S4	6.7	X	X	X	X		X	X		X	X		X		Xa
S5	8.3 (L)	X	X	X			X			X	X		X		X
	7.3 (R)
S6	4.5 (L)	X	X	X			X		X				X		X
	4.9 (R)
S7	2.4	X	X			X							X
S8	1.6 (L)		X		X	X	X	X	X	X	X		X
	4.0 (R)
S9	3.6	X	X	X			X			X		X
S10	3.4			X											X
S11	5.2	X	X	X		X	X	X	X	X	X	X	X	X	X
S12	3.9		X	X			X				X	X
S13	6.0	X	X	X		X	X		X	X		X	X		X
#	4.4 ± 1.9	9	11	10	2	6	10	5	5	7	7	5	9	3	8
%		69	85	77	15	46	77	38	38	54	54	38	69	23	62

S2 and S4 reported hearing music.

Stimuli and procedure

All stimuli were delivered to the subject's CI using a research processor, controlled by a customizable research interface connected to a computer. Use of the customizable research interfaces allowed fixed pulse trains to be continuously delivered to only a single electrode at a given stimulation rate, place, or level, as distinct from commercial speech processors. Stimuli were fixed, charge-balanced, biphasic anodic-first pulse trains, delivered with a given stimulation rate (low: 100 or 200 pps and high: 5000 pps), stimulation place (apical, middle, or basal electrode) and stimulation level (corresponding to soft, medium, and loud) for a total combination of 18 stimuli conditions. Stimulated electrodes were selected as the apical- and basal-most electrodes, as well as the electrode in the middle of the array. Apical, middle, and basal electrodes were selected, respectively as electrodes 22, 11, and 1 for Cochlear devices; 1, 8, 16 for Advanced Bionics; and 1, 6, and 12 for Med-El (see Figure 1). Loudness levels were determined via subject feedback, using a LR numeric scale from 0 to 10 (0 = no sound, 10 = very uncomfortable) as a guide. On this scale, LR 3 corresponded to “soft,” LR 5 to “medium,” and LR 7 to “loud but comfortable.”

Figure 1

Electrode stimulation site by condition and CI manufacturer. Diagrammatic representations of electrode arrays are presented by CI manufacturer, with the stimulated electrode number listed above the appropriate electrode (shaded in black) for apical (left), middle (center), and basal (right) stimulation conditions.

For Cochlear users, electric stimuli were delivered through a programmable SPEAR3 Speech Processor (Hearworks, Pty, Melbourne, Australia) and controlled via the Woomera software (Cochlear Ltd., Sydney, Australia); source code was written in Motorola DSP563xx assembly language. Subjects adjusted the volume to the appropriate loudness using a dial on the speech processor.

For Advanced Bionics users, electric stimuli were delivered via a research interface provided by Advanced Bionics Corporation and controlled via the BionicEar Data Collection System software (Advanced Bionics LLC; Sylmar, CA, USA).

For Med-El users, electric stimuli were delivered via the Diagnostic Interface Box connected to the CIS-PRO + processor and controlled using the CI.Studio+ 2.0 software (Med-El Corporation, Innsbruck, Austria). The clinical mapping software was used to turn off all but one electrode, which was set at the appropriate stimulation rate. A steady state sound was then delivered directly through the processor via an audio input cable to activate that given electrode.

Prior to each trial, baseline tinnitus was assessed as the LR of the tinnitus prior to delivery of the test stimulus. Fixed, unmodulated pulse trains were then delivered to a single electrode at a fixed stimulation level for 6 min. LRs of the tinnitus and the electric stimuli were each reported by the subject every 30 s for the duration of the stimuli. Tinnitus was allowed to return to baseline prior to the next testing condition. S10 had a dead region in the basal region of her cochlea secondary to radiation for a cerebellar tumor (Moore et al., 2000); S3, S6, S7, and S9 did not complete testing conditions. Testing conditions were presented in a randomized order. Due to thorough evaluation of stimulation conditions and time required between trials, total testing time could span two full days for each subject.

All patients gave informed, written consent and protocols were approved by the Institutional Review Board at the University of California Irvine.

Analysis

LRs for tinnitus and electric stimuli were reported as loudness adaptation percentages, calculated as such: where L is LR at time t and L0 is the initial LR at time t = 0. A value of −100% means that the tinnitus or sound is inaudible (L = 0), while 0% means that the tinnitus or sound is unchanged from the baseline (L = L0). The adaptation data were fitted using the following equation: where s represents the plateaued adaptation percentage, calculated as the average of the final five loudness estimates in terms of percentage of the original loudness at the onset of stimulation. τ represents the time constant at which the loudness percept adapted. For cases where no adaptation occurred, both s (plateaued adaptation percentage) and τ (time constant) were set to 0.

Subjects were also classified based on their responses to the tested stimuli. Tinnitus suppression outcome were based on a 30% cutoff; a tinnitus suppression of 30% or more was considered “successful” while suppression of less than 30% was considered as “no suppression.” Thus, subjects tested in this paradigm fit into one of two categories: “Responder” subjects, whose tinnitus adapted to at least one condition by 30% or more, or “Non-Responder” subjects, whose tinnitus remained uninfluenced by electric stimulation.

Statistical analyses were performed for all subjects. Data were analyzed using Generalized Estimating Equations to control for repeated measures, using a linear scale response outcome of the minimum tinnitus adaptation percentage, or plateaued adaptation and time constant of the curve-fit variables for adaptation of the electric stimulus (SPSS/PASW Statistics 18; Somers, NY, USA).

Another Generalized Estimating Equations model using binary logistic regression was used to evaluate effects of stimulation parameters on tinnitus suppression outcome of greater or less than −30%. All regression models were built using rate, place and level as main effects; two-way interactions were consequently assessed. The statistical significance of each regression coefficient was determined using Wald Chi-square analyses, and the model was reduced by backward elimination. Variables of clinical interest were evaluated in the final model, and post-hoc analyses were performed based on pairwise contrasts.

Results

Tinnitus suppression

Figure 2 shows representative data from three subjects (S1, S2, and S5) at a high rate (5000 pps) and an apical electrode, with the loudness of the electric stimuli at soft, medium and loud levels represented in columns. Subjects S1 and S2 (in the first two rows) show loudness adaptation of both the tinnitus (filled circles) and the electric stimuli (open triangles). Note in the first panel S1 particularly—-both the tinnitus and electric stimulus adapted from a soft level (LR: 3) to a barely audible sensation (LR: 1) for a total adaptation of −66.7%. Subject S2 also showed loudness adaptation to both her tinnitus and the electric stimuli, with her tinnitus percept adapting completely to −100% (LR: 0) in the medium and loud conditions. Subject S5 is a bilateral user who showed no loudness adaptation to the tinnitus in either ear (right ear: filled circles; left ear: X's) or the electric stimuli (open triangles).

Figure 2

Representative data from three subjects at a high rate (5000 pps), apical electrode. Plots show tinnitus and electric stimulus loudness percepts across time at three different loudness levels for three representative subjects. Loudness levels are shown in columns; subjects S1, S2, and S5 are displayed in rows. For S1 and S2, plots show LRs (scale: 0–10) of tinnitus (filled circles) and electric stimuli (open triangles). S5 is a user who reported bilateral tinnitus; tinnitus from her right ear (filled circles) is shown alongside tinnitus from her left ear (filled X's), and electric stimuli (open triangles).

Figure 3 shows the spread of suppression across tinnitus subjects, with each circle representing a single trial condition. Of 227 trials tested, 37% (83 of 227) were successful conditions that elicited a tinnitus suppression of 30% or more, represented by the dotted line in Figure 3. Of these, 49% (41/83) of the successful conditions yielded complete tinnitus suppression, where the tinnitus percept dropped to be completely imperceptible (LR: 0). Sixty-nine percent (9 of 13) of subjects responded to at least one condition tested: S1, S2, S3, S6, S8, S9, S10, S11, and S13. For subjects with bilateral tinnitus, ears responded uniformly: both ears responded to stimuli for S3, S6, and S8; neither ear responded for S5.

Figure 3

Spread of suppression, by subject. The spread of variability in tinnitus suppression percentage across all conditions is shown for each subject. Subjects are listed across the x-axis and grouped as Responders (left) or Non-Responders (right). Each open circle represents the maximal tinnitus suppression for a given condition. Bilateral tinnitus percepts for subjects S3, S5, S6, and S8 are listed by ear. Symbols at −100% suppression (complete adaptation) were shifted by up to 5% for visualization purposes. A dotted line is shown at −30% suppression to indicate the cutoff for successful suppression.

The large individual variability produced no significant effect of stimulation rate, place of stimulation, or loudness level of the electric stimulus on tinnitus suppression outcome. However, subjects who responded to one stimulus were much more likely to respond a second stimuli (χ2 = 93.5, df = 1, p < 0.001, likelihood ratio Chi-square test). Subjects who responded to at least one stimuli responded to a minimum of 27% of conditions tested (S9) and up to 78% conditions tested (S1) for an average of 50% of successful conditions.

Figure 4 shows the percentage of successful suppression conditions based on the total number of conditions tested, with low rate stimuli represented as open bars and high rate stimuli as filled bars. A binary logistic regression model found a significant effect of loudness level on tinnitus suppression (p = 0.049, Wald Chi-square analysis), along with a significant rate-level interaction (p = 0.030). Only loud sounds were significantly more effective than soft sounds (p = 0.027). The significant rate-level interaction showed additionally that, for high rate sounds, medium sounds were more effective than soft sounds (p = 0.043) and loud sounds (p = 0.008). No other significant effects or interactions were found.

Figure 4

Percentage of successful suppression conditions, by condition. Percentage of successful conditions (achieving tinnitus suppression of −30% or greater) of conditions tested are reported by stimulus condition. Open bars denote low rate stimuli; filled bars denote high rate stimuli. Electrodes for an apical, middle and basal place are grouped in clusters, and loudness levels are shown for each electrode (S = soft; M = medium; L = loud).

Responder versus non-responder subjects

We sought to evaluate adaptation differences to external sounds (electric stimulus) as compared to internal ones (tinnitus) under the same stimulation conditions. Figure 5 (top panel) shows a distinctive pattern of tinnitus adaptation between Responder (filled circles) and Non-Responder (open circles) subjects averaged over all conditions. No significant effects of stimulation rate, place or level were found on the overall degree of tinnitus adaptation in these subjects.

Figure 5

Adaptation of tinnitus and electric stimuli, Responders versus Non-Responders. Tinnitus adaptation is shown across time in the top panel, averaged across Responder (filled circles) and Non-Responder subjects (open circles). Electric stimuli adaptation is shown across time in the bottom panel, averaged across Responder (filled triangles) and Non-Responder subjects (open triangles). Error bars indicate SEM.

Similarly, Figure 5 (bottom panel) shows a distinctive pattern of loudness adaptation to the external electric stimulus between Responder (filled triangles) and Non-Responder (open triangles) subjects. Responders exhibited a significantly greater degree of plateaued stimulus adaptation (−29%) than Non-Responders (−22%), but a similar rate of loudness adaptation τ= 0.03 (Responders) versus τ= 0.02 (Non-Responders). Effects of loudness adaptation were significant at T(225) = 1.686, p = 0.030. The similar patterns between Responders and Non-Responders suggest that mechanisms of tinnitus adaptation may be related to loudness adaptation to external stimuli.

Discussion

Comparison to previous studies

Our findings are in line with published results reporting effectiveness of electrical stimulation of the auditory nerve via a CI to suppress tinnitus. In our study, a fixed pulse train delivered to a single electrode of the CI effectively suppressed tinnitus for 69% of our subjects, while published efficacy rates of the CI range from 46 to 93% (reviewed by Pan et al., 2009). Two recent studies reported 80–95% of their subjects to respond positively to the CI (van de Heyning et al., 2008; Arndt et al., 2011). While our efficacy rates are not as high, our study populations are also different. These two studies focus on individuals with incapacitating unilateral tinnitus and deafness, implanted primarily for their tinnitus, while our subjects are individuals with bilateral hearing loss treated by cochlear implantation who have coincident tinnitus. By nature of our study design and patient selection, our subjects are also those whose tinnitus was resistant to complete suppression by the CI (hence seeking relief in our study). Furthermore, we found additional tinnitus benefit in four subjects who did not initially report tinnitus benefit with their own speech processor.

Characterizing differences between responder and non-responder subjects

We evaluated demographics, hearing loss, and tinnitus profiles, and past medical histories of the two groups of subjects to identify any characteristic differences of the two groups. However, no significant differences were found between the Responder and Non-Responder groups with regard to gender, age, duration of hearing loss, duration of CI use, CI ear implant, CI device type (manufacturer), tinnitus duration, tinnitus severity (TSI), tinnitus handicap (THI), anxiety levels (BAI), or depression status (BDI). No differences were found in patient self-report of if their CI was beneficial to their tinnitus or not. No significant differences were found in general health status between the two groups either, based on self-reported past medical history of: endolymphatic shunt, vestibular neurectomy, chronic upper respiratory infection, noise exposure, sudden hearing loss, vertigo, Meniere's disease, chronic ear infections, abnormal bone growth, otorrhea, balance problems, hypertension, hypothyroidism, anemia, head tumor, autoimmune disorder(s), genetic disorder, heavy smoking, excessive caffeine use, chronic pain, insomnia, anxiety, depression, allergies, sinus congestion, or chronic infection. Interestingly, all four subjects with reported previous history of motor vehicle collision (MVC; S3, S8, S11, and S13) were Responders while none of the four Non-Responders reported having been involved in a MVC [T(8) = 2.530, p = 0.035].

Lastly, only one of the tinnitus sound component qualities was seen more highly associated with Responder subjects: Responders were significantly more likely than Non-Responders to have pulsatile-type tinnitus, T(8) = 3.162, p = 0.013. No significant differences were noted for individuals with tinnitus components of: buzzing, humming, ringing, blowing, hissing, roaring, whistling, constant high pitches, constant low pitches, water-like, seashell sounds, sizzling, or any other reported sounds. Furthermore, no differences were seen between the groups either in baseline levels of tinnitus, or in the overall standard deviation (or variability) of baseline tinnitus for each subject.

Effectiveness of sound stimuli by tinnitus quality

We also ran an analysis comparing effectiveness of each of the eighteen stimuli by the sound components of tinnitus (Table 4). No stimuli were significantly more or less effective for tinnitus with buzzing, humming, blowing, constant high pitches, constant low pitches, water-like, seashell sounds, or any “other” reported sound components. However, for several sounds, particular stimuli were found to be significantly more effective for subjects reporting that given tinnitus sound component, than for subjects who did not report that sound. For example, individuals reporting tinnitus with a “roaring” component achieved a significantly greater amount of tinnitus suppression with a low rate, soft stimuli to an apical electrode as compared to subjects without a roaring tinnitus component, T(14.140) = 2.853, p = 0.013; T-values are reported in Table 4. Ringing was the only sound that was predictive of negative predictability; namely, individuals with ringing tinnitus were less likely to respond to high rate stimuli of a soft-loudness level to either middle or basal electrodes. Tinnitus with a pulsatile component was easily suppressed with any of the six loud sound conditions except to an apical electrode with a low stimulation rate.

Table 4

Effectiveness of sound stimuli by tinnitus quality.

LOW RATE
Apical	Soft	Roaring: T(14.140) = 2.853, p = 0.013
Middle	Loud	Pulsating: T(12) = 2.509, p = 0.027
Basal	Loud	Sizzling: T(11) = 2.279, p = 0.044
		Pulsating: T(7.633) = 3.601, p = 0.008
HIGH RATE
Apical	Loud	Hissing: T(9) = 2.415, p = 0.039
		Pulsating: T(9) = 2.415, p = 0.039
Middle	Loud	Hissing: T(4.890) = 3.365, p = 0.021
		Pulsating: T(4.890) = 3.365, p = 0.021
	Soft	(Ringing: T(11) = −2.589, p = 0.025)
Basal	Loud	Hissing: T(9) = 4.492, p = 0.002
		Whistling: T(9) = 2.600, p = 0.029
		Pulsating: T(9) = 4.492, p = 0.002
	Medium	Pulsating: T(11) = 2.383, p = 0.036
	Soft	(Ringing: T(9) = −8.435, p = 0.000)

Tinnitus and electric stimulus adaptation: insights into underlying mechanisms

Loudness adaptation to externally presented electric stimuli in these subjects, as compared to simultaneous tinnitus adaptation, may also be insightful to mechanisms of tinnitus production. Despite a large variability in tinnitus response between subjects, a significant level-dependence was observed for tinnitus adaptation, with loud sounds achieving more tinnitus adaptation than soft sounds. While this may be partially attributed to a masking effect of electric stimuli on the tinnitus percept (Vernon, 2000; Vernon and Meikle, 2000), simple masking may not fully explain the observed results.

First, a large variability in tinnitus suppression results may indicate a heterogeneous population of tinnitus subjects. Where a final common pathway has been implicated for the perception of tinnitus (Shulman et al., 2009), evidence of tinnitus-related activity has been observed from the peripheral auditory system, through the brainstem and up to the cortex (Muhlnickel et al., 1998; Eggermont and Roberts, 2004; Roberts et al., 2010; Kaltenbach, 2011). Variability in both tinnitus characteristics described and responses to the stimuli tested here may indicate tinnitus manifesting from different sources.

Next, patterns of adaptation to electric stimuli are different from those to tinnitus adaptation. Loudness adaptation to electric stimuli showed significant effects of stimulation rate (p = 0.011), stimulation place (p = 0.000), and stimulation level (p = 0.020) (similar results were found in Tang et al., 2006), while tinnitus suppression is unaffected by these same parameters. This suggests that neural mechanisms underlying loudness adaptation to electric stimuli are likely distinct from those underlying tinnitus adaptation.

Despite these differences, electric stimuli are able to elicit tinnitus suppression in a subset of this heterogeneous group of tinnitus subjects. Responder individuals who experienced tinnitus suppression here also exhibited a higher degree of adaptation to the electric stimuli, while Non-Responders achieved a lesser degree of adaptation to both their tinnitus and the electric stimulation percepts. This result supports the auditory gain hypothesis, in which increased central gain in response to reduced input from the periphery results in tinnitus (Salvi et al., 2000; Norena, 2011). If physiological mechanisms underlying loudness growth are mediated by cochlear and central non-linearities (Zeng and Shannon, 1994; Moore, 2004) and loudness adaptation may be mediated by a central feedback loop dependent on peripheral nerve activity (Tang et al., 2006), then our observation here of increased stimulus adaptation in Responder individuals may indicate that their tinnitus is such that the external stimulus, applied at the auditory periphery, can induce adaptation to the tinnitus as well. Accordingly, Non-Responders who exhibit less adaptation to both the stimulus and their tinnitus may have tinnitus which originates more centrally within the auditory system, making their tinnitus less susceptible to adaptation via peripheral stimulation.

Clinical implications

We also compared an individual's tinnitus suppression outcome using our testing paradigm to their self-reported answer to the question “Has your tinnitus improved since cochlear implantation?” In Table 5, we see the patient's self-reported answer as “Helpful” or “Not Helpful” in rows, with any actual, validated effectiveness using the sounds in our study reported in columns as “Effective” or “Not Effective.” Nearly half (6 of 13 subjects; 46.2%) of the subjects inaccurately predicted actual effectiveness with our testing paradigm. Of these, two subjects predicted that their CI was helpful towards their tinnitus while not actually finding any effective sounds, while four subjects reported no benefit of their CI, but found relief with our testing stimuli.

Table 5

Expected versus actual effectiveness of tinnitus suppression through the CI.

		Research processor
		Effective	Not effective	Total
Own speech processor (self-report)	Helpful	5	2	7
	Not helpful	4	2	6
	Total	9	4	13

While this result could be explained by inaccurate reporting by the subjects of actual helpfulness of their CI, it seems less likely that subjects would be oblivious to a significant change to a bothersome percept and more likely that tinnitus suppression achieved using a CI with stimulation parameters ideal for speech understanding may be different from that using a CI optimized for tinnitus suppression. This effect is further clarified in Figure 6, which shows this relationship between speech recognition (using their own clinical speech processors) and tinnitus suppression (using research processors) for each subject, with Non-Responders in open diamonds and Responders in filled diamonds. The lack of correlation shown here (R2 = 0.02, p = 0.68, Pearson correlation) suggests that optimal stimulation patterns may indeed be distinct for speech understanding and tinnitus suppression needs. Thus, in order to use a CI to manage tinnitus, the clinical speech processor should be programmed not only for speech perception but also by using stimulus parameters optimal for achieving tinnitus suppression in that particular patient.

Figure 6

Correlation of speech recognition with tinnitus suppression. The relationship between tinnitus suppression (x-axis) and speech recognition scores (y-axis) is shown for Responders (filled diamonds) and Non-Responders (open diamonds).

Furthermore, the two subjects (S4 and S5) who reported that their CI was helpful but did not find relief with our stimuli did find relief from stimulation of the CI, albeit outside the context of our research stimuli. S4 found no relief with any of our 18 stimuli, but reported a “relaxing” and calming effect from the afternoon she got home from our testing until she woke up the next morning. The tinnitus in her implanted ear had disappeared from a “roar into a slight whistle,” and the patient felt calm and relaxed with an “unexpected and unusual relief from tinnitus.” She had experienced unrelenting tinnitus for 21 years. This was only the third time and by far the longest relief she had ever experienced from her tinnitus; the previous times had lasted only for minutes. This anecdotal report suggests a possible long-term effect of electric stimulation on tinnitus that needs to be explored in the future.

S5 also experienced profound relief of her tinnitus with use of her CI, although her relief is immediate with activation of her implant. With her CIs inactivated, her tinnitus is regularly at a LR 7–8 (“loud but comfortable” to “maximal comfort”) loudness. Activation of her CIs (she is a bilateral user) brings her tinnitus down nearly instantaneously to a LR 0, or complete imperceptibility in environments with ambient noise. With CIs activated, her tinnitus does not exceed a LR 2 (“very soft”) level even in a sound-attenuating booth; tinnitus suppression via electric cochlear stimulation is clearly effective for this patient. Some subjects may require multiple electrodes to be activated and/or dynamic stimulation to successfully achieve tinnitus suppression, as compared to our single-electrode, fixed stimulation tested here. Of note, 13% (30 of 227) of trials resulting in exacerbation of tinnitus were noted in the conditions tested here. This is consistent with exacerbation of tinnitus associated with CI use that has been noted in a small but notable number of patients (10%) in other studies (Quaranta et al., 2004).

Lastly, we wanted to draw attention to any link between tinnitus and musical hallucinations in acquired deafness, with absence of evidence to suggest epilepsy or psychosis. One individual contacted us with tinnitus, but complaining especially of musical hallucinations. She was not enrolled in the study for unrelated reasons, but upon questioning, two enrolled subjects (one responder and one non-responder) reported musical hallucinations. Reported sounds varied from old Elvis songs to marching band and church bells; interestingly, no individual reported any lyrics or verbal hallucinations. Non-psychotic auditory hallucinations appear to be an underreported phenomenon associated with acquired deafness and especially in the elderly (Griffiths, 2000; Auffarth and Kropp, 2009).

Conclusion

Tinnitus suppression is possible via electrical stimulation of the cochlea in a subset of “Responder” subjects. A large variability between subjects, as well as the lack of a “most-effective” stimulus type (with respect to stimuli parameters: rate, place, or level), is indicative of the heterogeneity of the underlying tinnitus pathophysiology and individualized percept. These findings elucidate differences between two populations of individuals with tinnitus, Responders and Non-Responders, who not only respond to their tinnitus differently, but also exhibit different patterns of loudness adaptation to externally presented electric stimuli. These findings support the auditory gain hypothesis of tinnitus and suggest there may be characteristic differences in tinnitus generation between Responder and Non-Responder groups. It should be noted that while this study is to our knowledge the largest of its kind, the study size may nevertheless be relatively small given the grand diversity of tinnitus. Tinnitus suppression appears to be possible, but parameters of effective stimuli for tinnitus suppression may need to be customized for the individual.

Conflict of interest statement

The authors declare that the research was conducted in the absence of any commercial or financial relationships that could be construed as a potential conflict of interest.