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|Year : 2005
: 7 | Issue : 29 | Page
|The benefit method: Fitting hearing aids in noise
I Svard1, KE Spens2, L Back1, BH Ahlner3, ML Barrenas4
1 BFM Support AB, Sweden
2 Department of Speech, Music and Hearing, Royal Institute of Technology, Stockholm, Sweden
3 Department of Audiology, Karolinska Hospital, Stockholm, Sweden
4 Department of Paediatrics, Queen Silvia Children's Hospital, Göteborg, Sweden
Click here for correspondence address
The most common complaint among individuals with hearing impairment is the inability to follow a conversation when several people are talking simultaneously, a noisy listening situation which is completely different from the quiet surrounding of the conventional pure tone audiometry used as basis for the hearing aid settings. The purpose of this report was to present important characteristics of the BeneFit Method (BFM), a procedure that fits the hearing aid under simulated conditions of competing speech and also a clinical pilot evaluation study comparing the BFM to the NAL-R recommendations and also to the Logic procedure, a GN resound proprietary fitting algorithm representing a modern digital hearing aid fitting procedure.
Speech recognition scores in noise (SRSN) using monosyllabic words presented under different background noise levels were evaluated on 21 randomly selected subjects with hearing impairment. The subjects were fitted with the same type of hearing aid Danalogic 163D according to the BFM procedure as well as the logic procedure, the latter developed and recommended by the manufacturer. A comparison of the SRSN when using the subjects' current hearing aid fitted according to the NAL-R procedure was also made.
Only the BFM procedure provided a significant SRSN improvement compared to the unaided condition (P< 0.01) in a signal/speech-noise level of 75/65 dB corresponding to a normal cocktail party condition. Moreover, patients performed significantly higher SRSN when fitted according to the BFM, than when fitted according the Logic or NAL-R procedures.
The BFM procedure, which is based on individual and functional detection of hearing thresholds in noise levels corresponding to a cocktail party condition, can improve SRSN significantly. Hearing aids should be fitted under conditions similar to those when the hearing disability is perceived the most, i.e., in an environment with background noise.
Keywords: Hearing aid fittings, noise, benefit, hearing loss
|How to cite this article:|
Svard I, Spens K E, Back L, Ahlner B H, Barrenas M L. The benefit method: Fitting hearing aids in noise. Noise Health 2005;7:12-23
| Introduction|| |
Despite considerable hearing aid technology improvements, such as digitalization, a wide range of adjustment options and tailored fitting procedures especially designed to take advantage of the characteristics of a particular hearing aid, the user's satisfaction was unchanged in year 2000 compared to 1990. , Still, the most common complaint is the inability to follow a conversation when several people are talking simultaneously, a noisy listening situation completely different from the quiet surrounding of the conventional pure tone audiometry used as basis for the hearing aid settings. So far, no current hearing aid fitting method is based on the assessment of detection thresholds in noise at normal and loud speech levels.  Moreover, when compared on coupler (IEC-136, 1961), the prescribed gain could differ by as much as ± 10 dB between prescriptive methods.  Finally, since the pure-tone audiogram only reflects a reduced sensitivity to sound, other important aspects associated with impaired hearing, such as distortion, masking and non-linearities might not be taken into account. For example, speech intelligibility in noise might depend on increased sensitivity to cochlear distortion.  The BeneFit Method (BFM), a procedure where the hearing aid is fitted under simulated conditions of competing speech, was developed bearing these concerns in mind.
The functional state of the BFM is now reached, bringing about good results at several Hearing Aid Centres in terms of satisfied hearing aid users and improved speech recognition score in noise (SRSN). The purpose of this report is to present important characteristics of the BFM and also a clinical pilot evaluation study comparing the BFM to the NAL-R recommendations and the Logic procedure (a GN resound proprietary fitting algorithm representing a modern digital hearing aid fitting procedure).
| The BFM|| |
According to the BFM, the main key to optimize speech intelligibility under competing speech conditions is to find a hearing aid setting that offers a good balance between the gain in the high and low frequency ranges. Therefore, not only is the BFM based upon individually assessed measurements of the signal detection threshold in noise (SDTN). It also focuses at optimizing listening under adverse conditions (cocktail noise) by bringing the aided SDTNs at several noise levels and frequencies into the range of that for people with normal hearing [Table - 1]. Since an expanded high frequency range improves both listening comfort and speech audibility , and especially in background noise,  it is assumed that detection of speech sounds up to 6 kHz is optimized, when the aided SDTNs at noise levels ranging from 45 dB SPL and up to 75 dB SPL (corresponding to quiet and loud competing speech, respectively) are within that for the normative SDTNs. The selection of SDTN assessments is considered a feasible simulation of the most common adverse listening conditions. Accordingly, no prescriptive formula based on the hearing thresholds can be provided for the BFM. For all other present fitting procedures, on the other hand, a certain algorithm is used when setting the gain in the available frequency bands, which depends on the characteristics of that particular hearing aid. Usually, such settings give a too low amplification of the high frequencies relative to the low and middle frequencies. This constitutes a risk that the hearing aid user will not receive the high frequency information, which might be drowned by distortion products created from the lower frequency ranges of the cochlea. These differences between conventional methods and the BFM are probably crucial.
Test stimuli, speech-weighted noise and calibration
Computer-generated sequences ad modum Victoreen  [Figure - 1] were chosen as test stimuli, because the Victoreen signal is easily recognized in SWN and it shares certain characteristics with speech. The resemblance between stimulus and the building blocks in human speech with regard to onset and duration probably constitutes an important prerequisite to good perception of similar speech elements, since both the Victoreen stimulus and a glottal pulse from a typical vowel sound are built up of a fast click onset and a tonal decay as shown in [Figure - 1],[Figure - 2]. Vowels and other voiced sounds are repetitive glottal pulses or clicks, which activate the resonance in the mouth cavity as illustrated by an "a" and "k" in [Figure - 1]. In the high-frequency range, the Victoreen stimuli resemble the single click found in stops such as the p, t, k and b, d, g sounds. This similarity becomes evident, when looking at the time domain or listening to the stimuli. The broad spectral information of the fast click onset (as illustrated by the click during the first millisecond in [Figure - 2]) is very important and should be perceived as precise as possible. This is a task for all intact sensory cells in the cochlea.
To simulate masking competing speech when assessing both unaided and aided SDTNs and SRSN, the BFM uses a speech weighted noise (SWN). Its spectral configuration resembles that of an average long-term speech spectrum. , In [Figure - 3], the noise spectrum is shown as long-term root-mean-square (rms) 1/3-octave band levels of 35, 45, 55, 65 and 75 dB SPL, respectively. When presented at a fixed overall level of 45 dB SPL, the SWN corresponds to quiet competing speech. At the 55, 65 and 75 dB SPL it corresponds to subdued, normal and loud speech masking levels, respectively. All levels correspond to the assessed values obtained in the position between the subjects' ears. A computerized audiometer of the fixed Bιkιsy type (PortaRem, Digital 2000, Rastronics, Copenhagen, Denmark) generates both the test signal and the SWN, which both are routed from the audiometer to the respective signal and noise loudspeakers [Figure - 4]. The repetition frequency of the stimulus is 3 Hz. Within the stimulus, each period has 10% lower amplitude than the preceding one meaning that its effective duration is dependent on the frequency [Figure - 1], left. Due to the short decay of the Victoreen stimulus when compared to the sinusoidal stimuli, the standing wave problem is small.
All measurements were carried out in a soundproof booth having a reverberation time of <0.1s. A B and K 2230N sound level meter with a filter type 1625 (Brüel and Kjaer, Copenhagen, Denmark) calibrates the levels of the stimuli in order to eliminate possible disturbances from the outside. Four symmetrically located loudspeakers emit identical noise signals, creating a sound field varying < ± 2 dB(C) within 20 cm from the test subject. The test subject is placed centrally, 1 m from the signal loudspeaker with an azimuth of 45° relative to the test ear, i.e., the aided ear [Figure - 4]. At the 45° angle, the level is most stable, therefore slight movements of the head during testing will not affect the results.  Moreover, when measuring in a sound field it is easy to separate the ears with a 45°-approach angle from the signal loudspeaker.  A headrest, small enough to avoid any influence from baffle effects, is used to ensure correct positioning of the subject's head.
| Sdtn|| |
The SDTNs indicate the minimum level that the stimulus must attain in order to be detected. It is designated by the dB SPL peak equivalent value and is determined for the 0.5, 1, 2, 4, 6 and 8 kHz frequency. The measured values apply to a point in the middle of the booth at a 1 m distance from the signal loudspeaker, which correspond to an ordinary conversation distance. This point also corresponds to the centre of the head of the hearing aid wearer and not to the eardrum of the assessed individual.
In order to define normative reference values of the SDTNs at all SWN levels and frequencies, SDTNs were determined for 240 normal hearing subjects. The normative SDTN35, SDTN45, SDTN55, SDTN65 and SDTN75 means for each frequency [Table - 1] were then defined as zero for the corresponding level. All assessed SDTN values will refer to the corresponding normative reference, i.e. the SDTN is set at zero dB if it equals the normative SDTN value. It should be noted that when the SWN is increased by 10 dB(C), then the mean SDTN threshold is also increased by about 10 dB (SPL peak eq) except for the lowest level and highest frequency [Figure - 3] and [Table - 1].
| Srsn|| |
The SRSN-test is performed monaurally without ear protectors using lists of 50 monosyllabic phonetically balanced-words  in a SWN at a fixed speech-to-noise ratio of 75/65 dB, a condition simulating listening to speech masked by a speech noise level of normal group conversation. The level of the speech signal is defined as the equivalent of the rms of 1 kHz sinusoid with the same level as the average dB peak equivalent levels of the speech. The level of the SWN is measured in dB(C). According to Thornton and Raffin  binomial confidence intervals cannot be used to determine whether two individual scores are significantly different or not. Therefore, an individual improvement better than 10% when comparing the unaided and aided SRSN (S/N=75/65 dB) is regarded as a significant improvement of the speech perception ability under adverse listening conditions. This 10% limit was based on a SRSN test-retest (n=30; sd for the difference = 5.09; t0,05 = 2,042; variation limits = 5.09 x 2,042 = 10%, i.e. 5 words).
Test-retest-reliability of normative SDTNs and SRSN
A test-retest study was carried out on 30 subjects with hearing impairments ranging from slight to severe. The average SDTN difference between tests was 0.3 dB, the inter-individual standard deviation (SD) of the difference was 1.7 dB and the intra-individual SD was 1.2 dB. If a 90% confidence interval (CI) is chosen, a change larger than 3.0 dB between two tests will be regarded as a significant difference (90% CI SDTN difference = 0.3 ± 2.7 dB). This means that even a worsening by 3 dB in SDTN should result in some kind of action from the audiologist, such as a new setting of the hearing aid or the selection of another aid. If a 95% confidence interval is chosen, then a 4 dB change in SDTN should render the audiologist to act.
3 SD are considered to cover the normal variation (i.e. about ± 10 dB, [Table - 1]) and a ± 3 dB range to cover measurement errors. Thus, a ± 13 dB range around the normative SDTN value when set at zero is used when deciding whether an individual SDTN should be regarded as within the range of people who have normal hearing or not (see BFM procedure). The average SRSN difference between the tests was 0.9%, the inter-individual SD of the difference 5.1% and the intra-individual SD was 3.6%. If a 95% CI is chosen, a difference larger than 10% dB between two tests will be regarded as a significant difference (95% CI = ± (3.6 * 1.96 * o2).
| The BFM procedure|| |
The STDN assessments take place monaurally in a sound field. An ear protector is used in order to avoid interference from the non-tested ear. The aided STDNs are assessed in SWN at the standard frequencies 0.5-8 kHz, using the fixed frequency Bιkιsy technique. On the screen, each SDTN value is presented as the stimulus level above the corresponding normative SDTN value (reference). This means that the threshold of each masking noise level is zero if it equals the reference value. The audiologist follows the test procedure on the screen and manages the situation with possible out-liers. The effect of each new hearing aid setting is continuously monitored in order to ensure that the outcome converges positively i.e., that the functional gain makes the aided SDTN for all frequency bands and noise levels move into the corresponding normative SDTN range. Compression is used if necessary.
The assessments should continue until the normative SDTN values are reached in the high frequency range at the high noise level also. Then the target is reached. In order not to lose detection in other frequency ranges, all previous results must be checked, too. This is essential, because due to probable masking effects, there is often interference between the threshold gain settings at different frequencies. These paths are, with necessity, individual and could never rely on a prescriptive fitting formula based on hearing thresholds in a silent environment. The amount of efforts necessary to reach the target also gives further diagnostic information on how well the subject will recognize speech with the hearing aid.
After some three months of hearing aid use, the unaided and aided SRSN are assessed in order to verify the performance after adaptation, a time span necessary for the learning of how to decode the new sound of the hearing aid.  The comparison between the unaided and aided SRSN (S/N=75/65 dB) is also used as a quality assurance estimate. Under adverse listening conditions, an individual speech perception improvement is regarded as significant when better than 10%. After three months of adaptation, most of our patients have accepted the new sound (see pilot study below) and often the increase in clarity is appreciated. More important however is that the subject learns to benefit from the now available new information carried by the expanded bandwidth and dynamic range, which most patients have not been able to detect for many years. Easier tasks, such as listening to close and distant sources with no background noise, are also checked.
| The Clinical Pilot Evaluation Study|| |
The study sample comprised randomly selected cases from the waiting list at the Department of Audiology, Karolinska Hospital, who during standard audiological evaluation procedures were regarded to be in need of a hearing aid and who seven years previously were fitted with a Danavox Aura according to the NAL-R procedure. From this group all available subjects born 1920 or later were chosen. The study group comprised 13 men and 8 women (age range 69-84 years, mean 78 years). [Figure - 5] illustrates mean pure-tone thresholds and standard deviations.
Experiment procedures, study design and statistics
Each subject attended a 2 hr appointment twice. The same audiologist pursued all measurements at both sessions and the equipment had the same calibration for all corresponding measurements. At the first visit, the ear canals were checked and the pure tone audiometry performed. Then, unaided and aided SDTN65, SDTN75 and SRSN (65/55 and 75/65) were measured for the old Danavox/Aura hearing aid, which had been fitted according to the NAL-R procedure 7 years earlier. When assessing the SRSN performances with the Danavox Aura, the subjects controlled the volume wheel themselves. The subjects were then fitted monaurally according to the Logic procedure with the digital six-channel BTE hearing aid Danavox/Danalogic163D hearing aid. "Logic" is a proprietary prescriptive fitting procedure, based on the conventional pure tone audiogram and developed by the manufacturer Danavox by revising their older S2000R rule for their hearing aid Danalogic 163D. Aided SDTN45, SDTN65 and SDTN75 were assessed as well as unaided and aided SRSN as above. All ear moulds had a Bakke-horn as tube connection, a 2.5 mm sound channel with a horn shaped opening. The insert had a ventilation channel 0.8-1 mm in diameter.
At the second visit, the subjects were again fitted with the same Danalogic 163D hearing aid, however now according to the BFM. The assessments of SDTN and SRSN were repeated as described above. All SRSN values for the Danalogic/163D were obtained without any adaptation. The non-parametric Wilcoxon signed-rank test was used for comparisons of SRSN between fitting procedures and also the aided versus unaided SRSN. Correlation analyses were performed according to Pearson.
In order to explore the perceived sound quality when using BFM, 60 patients were asked to fill in a questionnaire with 2 queries having a 5 response format ranging between "no" (1) and "much" (5) discomfort about the amount of discomfort perceived when first fitted according to the BFM and after 6 months of usage.
| Results|| |
In [Figure - 6], the individual aided SRSN results are presented as a function of the unaided SRSN for the masking condition corresponding to normal speech noise (S/N=75/65 dB).
Observations above the diagonal line indicate benefit of the hearing aid. In some cases the hearing aid was a disadvantage under this masking condition (observations below the vertical diagonal). Only the BFM gave a significant benefit, i.e. significantly better aided than unaided SRSN ( P <0.01; Wilcoxon signed-rank test). No significant improvement in SRSN was observed when using the NAL-R or Logic procedures. Moreover, the BFM gave a significantly higher benefit than both the Logic and NAL methods ( P <0.02 and 0.01, respectively).
The mean aided improvement in SRSN for two S/N conditions (65/55 and 75/65 dB) with the three different HA fitting conditions are shown in [Figure - 7]. At the 65/55 level, the mean benefit using the Danalogic 163D improved from 10% to 18% compared to the old Aura HA when fitted according to the NAL-R method. For the low competing speech condition the improvement was independent of the fitting procedure used for the Danalogic 163D, 18% for both procedures. At the higher noise level (S/N=75/65) the BFM improved the SRSN significantly more than both the Logic method and NAL-R, 13% compared to 3% and 4%, respectively. The Danalogic 163D offered no improvement compared to the old Aura/NAL-R when fitted according to the logic procedure, (a 1% difference, not statistically significant) but a 9% better improvement when using the BFM. It should be mentioned that in the Aura/NAL condition, the patient controlled the volume while under the two other conditions the gain was set according to the logic algorithm and BFM procedures, respectively.
When comparing the average BFM SDTNs to the logic SDTNs [Figure - 8], it was shown that both the BFM and the Logic succeeded in bringing the SDTNs for the 0.5-4 kHz range into that of the "normal" area at all three noise levels. At the 65 and 75 dB noise level however, only the BFM but not the logic procedure reached the normative SDTN also at 6 kHz. Moreover, at the 75 dB noise level, the logic produced poorer normalized SDTN at 4-8 kHz than at the 65 dB noise level. In [Figure - 9], a comparison was made between all aided as well as the unaided condition for the 75 dB (C) SPL level. Only the BFM produced better SDTNs compared to the corresponding unaided condition, which might explain why many hearing aids are kept in drawers. Our suggestion that too high gain in the low and middle frequency ranges might interfere with the high frequency information, if the high frequency range is not sufficiently amplified, was supported by the average insertion gain for the Logic and BFM, as shown in [Figure - 10].
The questionnaire data concerning sound discomfort reported with BFM fitting are plotted in [Figure - 11], showing that the proportion of patients reporting minor or no discomfort at start compared with 6 months later had increased from 38% to 70%, while patients reporting great discomfort at start compared with 6 months later had declined from 13% to 10%.
| Discussion|| |
In the adverse listening conditions (S/N=75/65), the Danalogic 163D using the BFM procedure showed better SRSN improvement than did the Aura/NAL-R and the Danalogic 163D using the logic procedures. The most likely explanation was that the BFM offered a better balance between the high frequency gain and that of the low and mid frequencies as BFM was based on the subject's own psycho-acoustically measured hearing thresholds in noise (i.e., SDTNs), while the other procedures were based upon conventional threshold assessments in a quiet surrounding and standard prescriptions. If the time of adaptation is to play an important role, then with time both the BFM and Logic results might improve even further compared to the Aura/NAL-R condition, which included many years of adaptation.
For the low noise level condition (S/N=65/55 dB SPL, [Figure - 7]) the average SRSN improvements with the Danalogic 163D hearing aid were independent of fitting procedure. However, for the high noise level condition (S/N=75/65 dB SPL) the BFM procedure was superior to both the logic and NAL-R/Aura procedures. An 8% better average improvement of the SRSN was indicated for the BFM procedure compared to logic, which in turn was only 1% (not significant) better than the old NAL-R/Aura condition. These results correlated well with the average SDTN75 values in [Figure - 9] showing that all the signal detection thresholds obtained for the BFM procedure were within or almost within the range of that for people with normal hearing (framed area). The logic procedure indicated only a minor improvement compared to the old NAL-R/Aura condition and exhibited normalized SDTNs only for the frequency range 0.5 - 4 kHz, a result which offered no benefit compared to the unaided condition [Figure - 9]. The STDN graphs in [Figure - 8],[Figure - 9] could be looked upon as an audiogram with different stimuli and a specified masking noise level different from zero as in conventional audiograms. However, they suffer from the fact that some of the subjects could not produce a true response at some frequencies. If so, then the data points correspond to an average of the true detection levels and the max output values of the equipment [Table - 2]. The BFM produced far more true responses, i.e., higher detection rate, than did the other two fitting procedures and especially so in the high frequency range [Table - 2].
It could be argued, that the NAL-R/Aura comparisons should not have been included in this study, because the fitting done 7 years earlier might have been altered and also because a different hearing aid was used. Since the NAL or NAL-like fitting strategies are used world-wide, the comparisons are relevant. Moreover, the out come with the NAL-R Aura hearing aid was on average quite similar to that from the Danalogic 163D using the logic fitting, which is also very much based upon the NAL recommendations.
Two individual examples
Subjects 1 and 19 were chosen to exemplify that, despite having similar conventional pure tone hearing thresholds [Figure - 12], the results may end up in sub optimizations and that an individual assessment was one way to assure a high quality fitting. When fitted by the Logic procedure [Figure - 13], the SDTN75 results deviated substantially between subjects as well as from the norm-SDTN75. Arrows at the 4, 6 and 8 kHz frequencies indicate that true thresholds were not reached and were hence replaced by the max output values of the equipment [Table - 2]. When fitted according to the BFM [Figure - 14], the SDTN75 assessments were very similar to or within the normal range (framed area) for both patients.
When comparing the SRSN assessed in subject 1, the logic procedure improved the SRSN by only 1% under the low (S/N=65/55 dB) and 2% under the high (S/N=75/65 dB) masking level condition compared to unaided SRSN. The corresponding improvement for the BFM procedure was 8% and 6%, respectively. For subject 19, the Logic fit improved the SRSN by as much as 30% in the low level condition, but only 8% the high level condition. Using the BFM, the SRSN was improved by 14% in the S/N=65/55 dB condition and by 13% for the high level S/N=75/65 dB condition. Note that the SRSN results corresponded well with the SDTN75 data in [Figure - 13],[Figure - 14], which were below the normative SDTN range for the Logic fit (framed areas), but within the norm-SDTN range for most frequencies when the HA was fitted according to the BFM procedure.
The assessments of subjects 1 and 19 also illustrated how different the SDTN characteristics can be for two hearing-impaired subjects with similar conventional audiograms. This is something we see quite often. One reason may be individual differences in internal cochlear masking. The comparison between the two subjects also elucidated the importance to pursue the fitting to include also high noise levels and not to be misled to conclude the fitting procedure after obtaining good SDTN values at levels corresponding only to subdued or normal levels of competing speech.
Another indication that patients prefer a fitting procedure based upon psycho-acoustical detection thresholds was reported by Lennart,  who found the BFM to be superior to the NAL-Non-Linear, version l procedures. The subjective reason for choosing the BFM procedure was in most cases an unacceptable high gain when fitted according to the NAL procedure. Accordingly, a too high gain at lower levels may reduce the speech reception ability when the level is raised, as was the case for subject 19 when fitted according to the logic procedure. However, the SDTN values for subject 19 when fitted with the BFM [Figure - 14] were all within the normative SDTN range (0-13 dB) and the overall quality of listening comfort was better than that of the Logic procedure [Figure - 13]. Usually, subjects reaching the normative SDTN values will almost directly after the fitting procedure arrive at a reasonable good listening comfort also under quite adverse acoustical conditions. It was also shown from the questionnaire data [Figure - 11] that most patients will adapt to high frequency amplification, even though some patients at first may find the sound somewhat sharp.
In our opinion, the conventional fitting procedures are too much focused on the immediate listening comfort in a silent environment instead of the speech intelligibility in noise, which requires the clarity achieved by proper high frequency amplification. It may even be that hearing impaired subjects will not get improved speech reception ability in noise unless the aided SDTN values are detected within the normative SDTN range under corresponding noise conditions. This possibility is supported by the correlation between SRSN and SDTNs at different frequencies for the 55 and 65 dB noise conditions [Table - 3], indicating that the higher the level and frequency, the stronger the correlation. This in turn is a further indication that the information carried by the high frequency range at high noise levels is important.
| Conclusions|| |
The present pilot study indicated that the BFM procedure, even without a subsequent adaptation period, arrived at a significantly better hearing ability under adverse conditions than did the manufacturer's procedure Logic and the old conventional NAL-R procedures. The specific correlates to the optimal settings of the BFM procedure are not yet fully understood, but it is suggested that the main reason for the good results was that the BFM offered a better balance between the high frequency gain and that of the low and mid frequencies by using an individual "close-to-reality" procedure based on psycho acoustically assessed thresholds in noise. Moreover, BFM is designed to establish aided detection thresholds in more "natural" masking noise for more "natural" stimuli, which are within the detection range of that for people with normal hearing for the speech frequencies at speech levels varying from subdued to loud. Finally, the Victoreen stimulus is regarded as more "natural" compared to conventional sinusoidal stimuli in the sense that it has a structure resembling that of the building stones of speech rather than having. Both the time domain and the spectral domain of the hearing ability will then be addressed in a more "natural" way. The SDTN values correlated well with the respective SRSN values at loud speech levels, which mean that it is not necessary to confirm the settings by a time consuming SRSN assessment [Table - 3].
The evaluation of the BFM procedure and the comparisons with other procedures has indicated results favouring the BFM. The importance of high frequency information was clearly indicated, putting high demands that modern "good" hearing aids must convey enough high frequency gain. Achieving a successful low-level assessment only is too easy and not enough. Also, the BFM assessments at high levels of masking noise are important considering the current demands on quality assurance. In Sweden, the introduction of the BFM procedure has already contributed to an improved quality of audiological rehabilitation. Further evaluation and refinement of the BFM procedure is already in progress and hopefully enough data will be collected for modelling a computerized BFM fitting strategy.
| References|| |
|1.||Hjortzby B, Edιn M. H φr vi bδttre med ny teknik? Audionytt, ISSN: 0347-6308, (Swedish) 2002;4:21-2. |
|2.||Rosenhall U, Arlinger S, Brorsson B, Lagerbring C, Leijon A, Scherstιn T. Hearing aids for adults - benefits and costs. The Swedish Council on Technology Assessment in Health Care (SBU). Report 164. 2003. ISBN: 91-87890-85-2. Available from: http:/www.sbu.se. |
|3.||Kiessling J. Hearing aid fitting procedures - State-of-the-art and current issues. Paper presented at the 4 th European Conference on Audiology - EFAS: Finland; 1999. |
|4.||Smeds K, Leijon A. Threshold-based fitting methods for non-linear (WDRC) hearing instruments - comparison of acoustical characteristics. Scand Audiol 2001;30:213-22. |
|5.||Houtgast T. Psychoacoustics and speech recognition of the hearing impaired. In: Proceedings of the European Conference on Audiology. Noordwijkerhout: the Netherlands; 1995. p. 165-9. |
|6.||Byrne D, Dillon H. The National Acoustic Laboratories' (NAL) new procedure for selecting the gain and frequency response of a hearing aid. Ear Hear 1986;7:257-65. |
|7.||Hornsby BW, Ricketts TA. The effects of hearing loss on the contribution of high- and low-frequency speech information to speech understanding. J Acoust Soc Am 2003;113:1706-17. |
|8.||Mackersie CL, Crocker TL, David RA. Limiting high-frequency hearing aid gain in listeners with and without suspected cochlear dead regions. J Am Acad Audiol 2004;15:498-507. |
|9.||Barrenδs ML, Wikstr φm I. The influence of hearing and age on speech recognition scores in noise in audiological patients and in the general population. Ear Heart 2000;21:569-77. |
|10.||Victoreen JA. Equal loudness pressures determined with a decaying oscillatory waveform. J Acoust Soc Am 1974;55:309-12. |
|11.||Tarnoczy T. Das durchschnittliche Energi-Spektrum der Sprache (für sechs Sprachen). Acoustica 1971;24:57-74. |
|12.||Cox RM, Moore JN. Composite speech spectrum for hearing aid gain prescriptions. J Speech Hear Res 1988;31:102-7. |
|13.||Killion MC, Revit LJ. Insertion gain repeatability versus loudspeaker location. Ear Heart 1987;8:68S-73S. |
|14.||Nordlund B, Fritzell B. The influence of azimuth on speech signals. Acta Otolaryngol (Stockh) 1963;56:632-42. |
|15.||Lidιn G. Speech audiometry. An experimental and clinical study with Swedish language material. Speech audiometry. Acta Otolaryngol Suppl (Stockh) 1954;114. |
|16.||Thornton AR, Raffin MJ. Speech-discrimination scores modeled as a binomial variable. J Speech Hear Res 1978;21:507-18. |
|17.||Gatehouse S. The time course and magnitude of perceptual acclimatization to frequency responses: Evidence from monaural fitting of hearing aids. J Acoust Soc Am 1992;92:1358-68. |
|18.||Lennart I. Utvδrdering av programmeringsmetoder f φr h φrapparater. Essay in Swedish at the Medical Faculty, Lund University, Dept of Logopedics and Phoniatrics. 2001. Available from: http://www.logopedi.lu.se/audmag0il.htm. |
M L Barrenas
Institute of Health of Women and Children, Department of Paediatrics, Queen Silvia Children's Hospital, SE 41685 Göteborg
Source of Support: None, Conflict of Interest: None
[Figure - 1], [Figure - 2], [Figure - 3], [Figure - 4], [Figure - 5], [Figure - 6], [Figure - 7], [Figure - 8], [Figure - 9], [Figure - 10], [Figure - 11], [Figure - 12], [Figure - 13], [Figure - 14]
[Table - 1], [Table - 2], [Table - 3]
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