Larson VD, Williams DW, Henderson WG, Luethke LE, Beck LB, Noffsinger D, Wilson RH, Dobie RA, Haskell GB, Bratt GW, Shanks JE, Stelmachowicz P, Studebaker GA, Boysen AE, Donahue A, Canalis R, Fausti SA, Rappaport BZ, for the Participants of the NIDCD/VA Hearing Aid Clinical Trial Group . Efficacy of 3 Commonly Used Hearing Aid CircuitsA Crossover Trial. JAMA. 2000;284(14):1806-1813. doi:10.1001/jama.284.14.1806
Author Affiliations: Department of Veterans Affairs Medical Center, Washington, DC (Drs Larson, Beck, and Boysen); Hines VA Cooperative Studies Program Coordinating Center, Hines, Ill (Mr Williams and Dr Henderson); National Institute on Deafness and Other Communication Disorders, Bethesda, Md (Drs Luethke and Donahue); Greater Los Angeles VA Health Care System, Los Angeles, Calif (Dr Noffsinger); Department of Veterans Affairs Medical Center, Mountain Home, Tenn (Dr Wilson); University of Texas Health Sciences Center, San Antonio (Dr Dobie); Department of Veterans Affairs Medical Center, Iowa City, Iowa (Dr Haskell); Department of Veterans Affairs Medical Center, Nashville, Tenn (Dr Bratt); Department of Veterans Affairs Medical Center, Long Beach, Calif (Dr Shanks); Boys Town National Research Hospital, Omaha, Neb (Dr Stelmachowicz); University of Memphis, Memphis, Tenn (Dr Studebaker); Harborview/University of California, Los Angeles, Medical Center, Torrance (Dr Canalis); Department of Veterans Affairs Medical Center, Portland, Ore (Dr Fausti); and Department of Veterans Affairs Medical Center, Albuquerque, NM (Dr Rappaport).
Context Numerous studies have demonstrated that hearing aids provide significant
benefit for a wide range of sensorineural hearing loss, but no carefully controlled,
multicenter clinical trials comparing hearing aid efficacy have been conducted.
Objective To compare the benefits provided to patients with sensorineural hearing
loss by 3 commonly used hearing aid circuits.
Design Double-blind, 3-period, 3-treatment crossover trial conducted from May
1996 to February 1998.
Setting Eight audiology laboratories at Department of Veterans Affairs medical
centers across the United States.
Patients A sample of 360 patients with bilateral sensorineural hearing loss (mean
age, 67.2 years; 57% male; 78.6% white).
Intervention Patients were randomly assigned to 1 of 6 sequences of linear peak clipper
(PC), compression limiter (CL), and wide dynamic range compressor (WDRC) hearing
aid circuits. All patients wore each of the 3 hearing aids, which were installed
in identical casements, for 3 months.
Main Outcome Measures Results of tests of speech recognition, sound quality, and subjective
hearing aid benefit, administered at baseline and after each 3-month intervention
with and without a hearing aid. At the end of the experiment, patients ranked
the 3 hearing aid circuits.
Results Each circuit markedly improved speech recognition, with greater improvement
observed for soft and conversationally loud speech (all 52-dB and 62-dB conditions, P≤.001). All 3 circuits significantly reduced the frequency
of problems encountered in verbal communication. Some test results suggested
that CL and WDRC circuits provided a significantly better listening experience
than PC circuits in word recognition (P = .002),
loudness (P = .003), overall liking (P = .001), aversiveness of environmental sounds (P = .02), and distortion (P = .02). In the
rank-order ratings, patients preferred the CL hearing aid circuits more frequently
(41.6%) than the WDRC (29.8%) and the PC (28.6%) (P
= .001 for CL vs both WDRC and PC).
Conclusions Each circuit provided significant benefit in quiet and noisy listening
situations. The CL and WDRC circuits appeared to provide superior benefits
compared with the PC, although the differences between them were much less
than the differences between the aided vs unaided conditions.
Sensorineural hearing loss is one of the most prevalent disabling conditions
reported in the United States, affecting some 20 million to 26 million people.1- 3 Hearing loss is present
in 35% to 42% of individuals older than 65 years.4- 6
It adversely affects physical, cognitive, behavioral, and social function,
as well as the general quality of life,7 and
has been linked to depression and dementia.8- 10
While hearing aids are the main form of treatment, only about 20% of
those who could benefit from hearing aids wear them.2,3,11
Moreover, surveys have suggested that about 50% of hearing aid users are dissatisfied
with their instruments.12 A recent survey,
however, suggested that because of improved technology, approximately 65%
of hearing aid users are satisfied with their devices.13
A vast array of hearing aid technologies is available, ranging from
simple and relatively inexpensive analog circuits to complex and expensive
digital devices that require sophisticated fitting procedures. Whereas numerous
studies have demonstrated that hearing aids provide significant benefit compared
with unaided listening for persons with hearing losses ranging from mild to
carefully controlled, multicenter clinical trials of the relative benefit
provided by different types of hearing aids have not been conducted. Laboratory
studies and small-scale field studies have been designed in ways that make
them difficult to compare and have failed to show consistent superiority for
any type of signal processing.18,19
Choices among available hearing aids must be made without the benefit
of data from well-designed clinical trials. This report presents the results
of a double-blind, multicenter clinical trial to compare the efficacy of 3
different hearing aid circuits. Efficacy was measured in a variety of listening
situations using tests of speech understanding, sound quality, and patient
rank-order ratings. The 3 hearing aid circuits jointly account for 70% of
the US hearing aid market.
The clinical trial compared 3 commonly used hearing aid circuits: the
linear peak clipper (PC), the compression limiter (CL), and the wide dynamic
range compressor (WDRC). The PC and CL circuits amplify input sounds linearly
up to a predetermined level (usually set relative to loudness discomfort levels).
Above that level, the output is limited using 2 different electronic methods. Figure 1 illustrates the major difference
among the 3 circuits. For the PC, as the input signal level increases by 10
dB, so does the output level up to its maximum output capabilities when the
instrument is said to be in "saturation." The CL operates similarly in that
the output increases linearly up to a certain point. After that, however,
the output is reduced by circuitry that automatically turns down the gain
of the hearing aid by a fixed ratio. In this instance, the output is allowed
to increase by 1 dB for each 10-dB increase in the input sound level. Finally,
the WDRC behaves similarly to the CL circuit except that the automatic gain
function begins at lower input sound levels and allows, in this instance,
the output to increase 1 dB for each 2 dB increase in input sound level up
to its point of maximum output.
The PC removes the positive and/or negative peaks of the amplified signal,
whereas the CL uses automatic volume control circuitry. A disadvantage of
PC circuitry is that some acoustic distortion results when the output limit
is exceeded.20,21 Far less distortion
is created by CL circuitry.22 The WDRC circuit
allows input signals that vary in level over a wide range to be amplified
as a narrower range of output signals,23,24
which is associated with the reduced dynamic range found in the majority of
sensorineural hearing loss. Although theoretically beneficial to listener
comfort and speech understanding, a disadvantage of compression circuits (eg,
CL and WDRC) is that they alter the temporal characteristics of signals in
a way that can be apparent to the listener.25,26
Eight audiology laboratories located within Department of Veterans Affairs
(VA) medical centers participated. The experimental design was a 3-period,
3-treatment crossover design. Baseline measurements were made using a battery
of tests in the unaided condition (no hearing aids). Patients were then stratified
by center and randomized to 1 of 6 sequences of the 3 hearing aid circuits.
Six sequences were used so that each hearing aid circuit had approximately
an equal number of patients who used the circuit first, second, and third.
Each block of 6 consecutive patients within each center was balanced so that
each sequence was represented once. The actual frequencies for the 6 sequences
in the trial ranged from 59 to 61. In each of the 3 periods, the patients
were fit binaurally and used 1 circuit (aided condition) for 3 months. At
the end of each period, the battery of outcome tests was repeated in both
the unaided and aided conditions. The protocol was conducted in double-blind
fashion. Neither the audiologist who administered the tests nor the patient
could identify the circuit being worn because all 3 hearing aid circuits resided
in the same casement and because a different audiologist programmed the device.
The protocol was approved by the National Institute on Deafness and
Other Communication Disorders (NIDCD) Hearing Aid Advisory Committee, the
Hines VA Cooperative Studies Program Coordinating Center's Human Rights Committee,
and by the institutional review board of each participating center. All patients
provided informed consent, were fluent speakers of English, and had bilaterally
symmetrical sensorineural losses with no evidence of retrocochlear pathology.
Average audiometric thresholds for 500, 1000, 2000, 3000, and 4000 Hz were
no better than 25-dB hearing level in either ear, with no threshold from 500
to 2000 Hz exceeding 70-dB hearing level. Figure 2 shows the mean (±1 SD) audiogram. To ensure that
the sample included patients who were typical of the majority of adult hearing
aid users, monaural word recognition scores on a recorded version of the Central
Institute for the Deaf W-22 test27 were required
to be at least 28%, with a difference no greater than 26% between ears.
Each participant was fit binaurally with single channel, programmable,
full-concha in-the-ear hearing aids (Dyna P2, Phonak, Stäfa, Switzerland)
that contained all 3 circuit options. The National Institute of Standards
and Technology evaluated prototypes to ensure that characteristics of the
hearing aid conformed to the manufacturer's specifications.
The 3 programmable options were PC, CL, and WDRC. The CL had an 8:1
compression ratio (above compression threshold, an 8-dB increase in the input
level resulted in only a 1-dB increase in the output) and duration-dependent
release time capability. The WDRC had a fixed-compression threshold (approximately
52-dB input sound pressure level [SPL]), a compression ratio that ranged from
1.1:1 to 2.7:1 and a short, fixed release time (50 milliseconds). The maximum
output levels of the 3 circuits were programmable over approximately the same
range of SPLs.
Electroacoustic measurements28 were made
at each visit to ensure that hearing aid characteristics remained stable.
Acoustic gain targets were established using the NAL-R method,29
and probe microphone procedures were used to verify that targets had been
achieved. Maximum output targets were obtained using loudness discomfort levels30 and were subsequently held constant across visits
and circuit types.
All testing was carried out in audiometric test rooms using identical
equipment for test presentation and data collection at each site. Three categories
of outcome measures were used: speech recognition tests, category ratings
of perceived sound quality, and self-assessed subjective ratings of hearing
Two tests of speech recognition were used. A recorded version of a monosyllabic
word-recognition test, the NU-6,27 was presented
using a single loudspeaker (positioned at 0°; ie, patients faced the loudspeaker)
at an SPL of 62 dB (conversational speech level). Each of the 4 NU-6 lists
contains 50 scoreable items with each item having a value of 2%. At conversational
speech levels, listeners with normal hearing obtain perfect monosyllabic word
recognition scores. The second test, a recorded version of the Connected Speech
Test (CST),31,32 consists of 48
passages with 8 to 10 sentences that approximate everyday, connected discourse.
Because it was unlikely that a single laboratory condition could represent
the range of possible listening conditions, we conducted this test in a variety
of presentation and background-noise levels. The CST was presented via the
loudspeaker (located at 0° azimuth) at a level of 74-dB SPL (loud speech)
in quiet and then again at 74 dB in 3 background noise conditions. For SPLs
of 52 dB (soft) and 62 dB (conversational loudness), the speech materials
were presented in 3 conditions of background noise.
The background noise used was an uncorrelated multitalker babble,31 which was delivered from loudspeakers located at
azimuths 45° left and right at nominal signal-to-babble (S/B) ratios of −3
dB, 0 dB, and 3 dB. The S/B ratio refers to the relationship of the SPL of
the speech to the SPL of the background babble. The nominal 0-dB S/B condition
was estimated during the baseline visit prior to conducting tests for each
patient by presenting CST practice materials at 62-dB SPL in the "unaided"
condition using a bracketing procedure in which the binaural babble level
was varied for each subject to produce 50% intelligibility. (The mean [SD]
level of the babble was 55 [5.4] dB.) This relationship for each subject was
designated as the 0-dB condition. The same S/B ratio for each subject was
used for the −3-dB and 3-dB conditions, and for all tests conducted
over the 9-month protocol, the same ratios were used. Normal listeners typically
receive perfect scores at loud and conversational levels in a quiet background,
but their performance at softer levels and in the presence of background noise
varies as a function of the difficulty of the listening situation.
The Quality Rating Test, was used to assess 3 aspects of patients' perception
of sound quality: loudness, noise interference, and overall liking of the
listening experience. The patients rated each dimension on a 10-point scale.
On the loudness scale, 1 was too soft; 10, too loud; and 5, comfortably loud.
For overall liking, 1 was very poor or terrible and 10 was excellent. In this
task, the patients were instructed to ignore the loudness of the speech and
consider only the overall sound quality. For noise interference, they assigned
a 1 if noisiness completely interfered with quality and understanding of the
speaker and 10 if noisiness did not interfere. Intermediate integer ratings
could be assigned for all tests. Sentences designated as practice sentences
of the CST31 served as the stimuli for the
Quality Rating Test. Patients were presented 5 different sentences and provided
a rating after each presentation, which were were then averaged. The sentences
were presented at an SPL of 52 dB, 62 dB, and 74 dB in a quiet background
and then in the multitalker babble (S/B ratio, 10 dB).
Two measures were used to elicit expressions of the quality of hearing
aid performance from the patients. One was the Profile of Hearing Aid Performance/Profile
of Hearing Aid Benefit (PHAP/PHAB), which quantifies 2 major aspects of hearing
aid performance: speech communication in a variety of daily life situations
and reactions to the loudness and quality of environmental sound.33 For the PHAP/PHAB, 7 subscale scores were derived
from the 66 items of the inventory that were completed by the patient in written
format. The scales quantify problems in communication in favorable and unfavorable
listening conditions as well as the aversiveness and distortion of a variety
of sounds. The 7 subscales include communication with familiar talkers, ease
of communication, reverberation, reduced cues, background noise, aversiveness
of sound, and distortion of sound. At the end of each of the 3 trial periods,
the patients completed the PHAP/PHAB inventory in the unaided and aided conditions
using a 7-point scale that ranged from always to never. The PHAP scores quantify
the scale scores in terms of aided performance, while PHAB scores quantify
the scale scores in terms of benefit (ie, the difference between the aided
scores and unaided scores). Hence, in the PHAP, scores for all subscales are
reported in terms of percentage of time a problem is experienced and scores
for the PHAB are reported in terms of the change in percentage of time a problem
The second subjective assessment procedure was used at the final visit
only. After having completed each of the 3 treatments, the patients provided,
from memory, a rank-order rating of the 3.
A crossover design was chosen for this study instead of the more traditional
randomized, parallel group design because it required fewer patients, eliminated
between-patient variation, and it increased power for other objectives of
the trial (eg, to determine which patient characteristics predict success
with the different hearing aid circuits). In addition, some of the known disadvantages
of the crossover design (eg, large dropout rate, instability of the patient's
condition, and a large carryover effect) were not expected in this study.
The 3 circuits were compared using aided scores and aided minus unaided scores
(benefit scores) with a repeated measures analysis.
The sample of 360 patients provided at least 80% power to detect a small-to-medium
effect size for the patients' rank-order rating among the 3 circuits. This
sample size also provided greater than 95% power to detect a 7.2% difference
in the NU-6 test, greater than 95% power to detect a 3.6% difference in the
CST, greater than 90% power to detect a 20% difference in the Quality Rating
Test, and 90% power to detect a 16.6% difference in the PHAB.
A mixed, repeated measures model was used to compare the 3 hearing aid
circuits for the individual outcome variables. If the overall test was statistically
significant, then pairwise comparisons were made between the groups using
the Bonferroni procedure to adjust the α level for multiple tests. No
adjustment was made for multiple outcomes. For this reason, P values close to .05 should be interpreted with caution. Sample sizes
reported for specific tests and conditions departed somewhat from 360 because
some patients did not complete the study, some were unable to perform the
task, or, occasionally, the examiner was unable to follow the study's protocol.
Four hundred forty-six patients were screened for inclusion in the trial
and 360 (80.7%) were randomized. Of the patients who were not randomized,
15 were excluded on the basis of a single criterion, but most failed to meet
2 or more of the inclusion criteria. The main reasons included: air conduction
thresholds exceeded 70 dB in either ear (20); a difference in pure tone averages
between ears of more than 10 dB (17); mean air-bone gap exceeded 5 dB in either
ear (13); or routine otoscopy did not reveal clear ear canals (13). In 7 instances,
the audiologist did not feel that the patient was capable of performing the
tasks required by the trial.
Of the 360 patients enrolled, 69.7% were military veterans. The mean
age of the group was 67.2 years (range, 29-91 years). The racial/ethnic distribution
approximated that of the US population: 78.6% were white; 12.2% black; 6.1%
Hispanic; 1.9% Asian; and 1.1% Native American. Fifty-seven percent were men;
women were mainly nonveteran patients who were authorized to be treated at
VA medical centers for the purposes of this trial because the study grant
funded the cost of the hearing aids and the time of the treating and evaluating
audiologists. The most common self-reported causes of the patient's hearing
loss were noise exposure and aging. About half (46.7%) had never used a hearing
The number of patients from each center was nearly equal (range, 44-46).
None of the groups representing the 6 randomized orders were statistically
different in terms of age, age at onset of hearing loss, sex, race, previous
hearing aid usage, and degree of hearing loss (P≥.11
for all comparisons). Twenty-nine of the 360 patients did not complete the
trial due to illness, relocation of residence, or other reasons (eg, withdrawal
of patient consent, illness unrelated to hearing, death, sudden change in
hearing). Three hundred thirty-seven patients completed the 90-day trial with
the PC circuit, 338 with the CL, and 333 with the WDRC. The average reported
hearing aid use time for the 3 circuits did not differ significantly and averaged
about 9.8 (SD, 4) hours per day.
Figure 3 provides a summary
of the mean percentage correct results for the unaided and aided conditions
for the NU-6 test for each of the 3 circuits together with the benefit scores
(aided minus unaided). For statistical testing, percentage correct scores
for the NU-6 test were arcsine transformed to stabilize the error variance.34 Comparison of the unaided means with the aided means
showed that each of the 3 circuits improved the mean word recognition score
by a substantial amount (approximately 29% in absolute score differences; P<.001). The overall statistical test comparing the
3 circuits was significant (P = .002 for the aided
scores and P = .002 for the benefit scores). Pairwise
comparison tests showed that the WDRC circuit was superior to the other 2
circuits for the aided scores and superior to the PC circuit for the benefit
Figure 4 summarizes the findings
for the aided and unaided CST results. Percentage correct scores were arcsine
transformed to stabilize the error variance.34
As expected, there were no differences among unaided means. However, significantly
higher CST scores (P<.001) were achieved for all
aided conditions relative to the unaided conditions. The overall statistical
test comparing the 3 circuits for aided CST scores was significant for 1 condition
(62/0; P = .006). Pairwise comparisons showed that
the WDRC circuit was inferior to the CL and PC circuits.
The mean CST benefit scores (aided minus unaided) are shown in Figure 5. Comparison of the 3 circuits showed
significant differences for the 62/0 (P = .04) and
74/0 conditions (P = .02). Pairwise comparison tests
showed that for the 62/0 condition, the WDRC circuit was inferior to the CL
circuit; and for the 74/0 condition, the WDRC circuit was superior to the
The data presented in Figure 4
and Figure 5 also show that the
3 circuits provided similar amounts of improvement in test scores, but all
showed successively less benefit as a function of signal level when background
noise was present. A marked decrease in CST benefit scores from about 26%
for the 52-dB conditions to approximately 6% for the 74-dB conditions was
observed, suggesting that the hearing aids were less helpful at higher than
at lower and moderate input levels. Furthermore, the Figures show that all
3 circuits provide measurable benefit in noisy conditions.
The Quality Rating Test was administered at 3 signal levels in quiet
(designated as 52Q, 62Q, 74Q) and elicited ratings of loudness, noise interference,
and overall liking. It was also administered at the same signal levels with
an absolute S/B ratio of 10 dB (designated as 52N, 62N, and 74N), which means
that the level of the speech was 10 dB greater than the level of the multitalker
Table 1 shows no differences
in the loudness ratings between the unaided means for each condition. Significant
differences were observed, however, for the aided condition across the 3 circuits
for both the quiet and background noise conditions for the lowest (52-dB SPL)
and for the highest signal levels (74-dB SPL) (P<.001).
The WDRC circuit was rated as being more comfortably loud (ie, a rating closer
to 5) than the other 2 circuits for the 52-dB SPL conditions (P = .003) and 74-dB SPL conditions (P = .003).
The CL circuit was more comfortably loud compared with the PC circuit for
the 74-dB SPL condition.
A summary of data for the noise interference task is shown in Table 2. Analysis of the mean unaided data
revealed no differences. For the aided data, the analysis also showed no significant
differences among circuit types, except for the 62N condition (P = .01). Pairwise comparison revealed that the PC circuit scored higher
(less noise interference) than the WDRC circuit.
A summary of data for the overall liking task is shown in Table 3. There were no significant differences between the unaided
means at each condition. The analyses of the data among circuit types for
the aided condition showed significance for the 74Q condition (P = .001). Pairwise comparisons across circuits showed that the PC
was less liked than both the CL and the WDRC.
Finally, for each circuit, significant improvement in overall liking
was observed for soft and conversational speech levels (P≤.05). For the loud conditions (74Q, 74N), however, negative average
benefit ratings were observed (P≤.01) except for
the 74N condition for the WDRC (P = .39), suggesting
that the aided experience was rated as being less liked than the unaided experience
for loud sounds.
No differences were observed among the unaided means for the PHAP. For
the aided means, the analysis showed statistical significance (P<.001) for 2 of the 7 scales: distortion of sounds and aversiveness
of environmental sounds. Pairwise comparisons showed that the scores for the
PC were significantly different (ie, higher frequency of problems) than both
the CL and WDRC circuits on the aversion and distortion scales (P≤.02). The mean values for the PC circuit were 4% to 5% higher
(ie, higher frequency of problems) for aversion and were 2% to 3% higher for
The PHAB scores also showed that each circuit significantly reduced
the frequency of problems reported on 6 of the 7 scales (P<.001). For aversion, however, all circuits produced a significantly
higher frequency of problems (P<.001) than in
the unaided condition. In the analysis comparing circuit types, significant
differences were observed for aversion (P<.001)
and distortion (P = .02). Pairwise comparisons for
aversion showed that the PC circuit was more aversive than both of the other
circuits (P = .003) with the mean frequency of problems
being 4% to 5% higher. The PHAB scores also showed that the PC score was significantly
higher than the WDRC for distortion (P = .02) with
the mean difference between PC and WDRC being 3%.
Finally, on completion of the study, the patients provided, from memory,
a ranking of the 3 hearing aid circuits. The CL circuit received the highest
percentage of first rankings (41.6%), followed by the WDRC (29.8%), and the
PC (28.6%). In addition, the CL circuit was ranked third by the lowest percentage
of patients (25.4% for the CL vs 36.2% for the PC and 38.4% for the WDRC).
Statistical analysis using the Friedman test showed a significant overall
difference among the rankings (P = .002). Subsequent
analyses using the Wilcoxon test showed that, overall, the CL was preferred
more frequently than the PC (P = .001) and the WDRC
(P = .001) and that there were no significant differences
between the rankings for the PC and the WDRC (P =
Each of the 3 hearing aid circuits provides substantial benefit over
unaided listening. Benefit was observed for measures of speech recognition
and ratings of speech quality in a variety of noisy and quiet conditions as
well as for subjective measures. Each circuit improved monosyllabic word recognition
scores in a quiet background at conversational levels by an average of 29%
(absolute score improvement). Speech recognition ability, as shown by the
CST, in noise was improved by each circuit by amounts ranging from 10% to
30% (absolute score improvement), with greater improvement observed for speech
at soft and conversational levels. Loudness rating data suggested that all
3 circuits amplified soft and conversationally loud speech to comfortable
levels. The noise interference ratings showed that none of the circuits had
a deleterious effect. For soft and conversational speech levels, each circuit
improved the overall quality of the listening experience. For loud speech,
the overall quality of listening was not significantly degraded. The results
of 6 of the 7 subscales of the subjective measure of hearing aid benefit (PHAB)
showed a significant reduction in the frequency of problems associated with
communication in everyday environments.
Statistically significant differences (small in comparison with the
benefits seen with each of the circuits) were noted among the circuits on
several components of the outcome measures. The results of the loudness rating
suggest that the WDRC circuit was more comfortably loud than the other 2 circuits
for soft and for loud speech input conditions. Because of its operating characteristics,
the WDRC was expected to produce a more comfortable listening experience for
the soft and loud input levels. Differences in scores on the PHAP/PHAB for
2 subscales were statistically significant among circuits, with the PC rated
as 4.5% more aversive than the other 2 circuits and producing an average of
3% more problems for distortion of sounds compared with the WDRC circuit.
The preference rankings provided at the end of the trial favored the CL circuit.
Because the differences between the hearing aid circuits were small in most
cases, dispensing decisions should take into account cost vs benefit considerations
for individual patients. In this regard, many programmable hearing aids (such
as the one used in this trial) may be configured to function as a PC, CL,
or WDRC and, as such, there are no cost differences between circuit options;
however, for conventional, nonprogrammable devices, compression circuitry
(either CL or WDRC) adds significantly to the single-unit price of the device.
Because concerted efforts were made to recruit patients into the study
from both sexes and all racial groups, the study sample was a good representation
of US adults who are candidates for hearing aids. We believe, therefore, that
the study results are generalizable to the US population with sensorineural
hearing loss. One limitation of the trial is that it did not measure other
domains, such as affect and cognition, which are influenced by hearing loss.