Issue: 2007 International

Although not a new concept, open-fitting devices have enjoyed a renaissance in popularity during the past several years. For example, the introduction of “mini” and “micro” behind-the-ear (BTE) devices has reversed a decades-long trend of growth in the custom in-the-ear (ITE) devices in the United States.1 In 2005, most major manufacturers began offering several devices that were either specifically developed for open fitting or were modified from existing product lines.

In order to be effective, open-fitting strategies should provide:

David A. Fabry, PhD, is vice president of professional relations and education at Phonak Hearing Systems, located near Chicago.
  • Minimal occlusion via a narrow (0.8 mm) tube fitting or large (greater than 3.0 mm) vented earmold or shell;
  • Feedback phase cancellation system;
  • Minimal signal processing group delays (less than 15 ms);
  • Precise frequency compensation with steep filter slopes; and
  • Directional microphones to improve speech recognition in noise.

The last factor, directional microphones, has repeatedly been proven to be the single factor most related to patient satisfaction and benefit with hearing aids. Conventional wisdom, however, has suggested that open fitting and directional microphones are mutually exclusive; this is due primarily to the misconception that the acoustic properties of venting act to attenuate low-frequency gain in the frequency regions where directional microphones are most effective, rendering them useless.

This article will address the issue, as well as several other “urban myths” related to selecting and fitting open-fit devices.

Myth Directional mics are incompatible with open-fit aids.

Directional microphones have proven to be one of the most significant factors related to self-perceived benefit and satisfaction with digital hearing aids.2 Consequently, the percentage of hearing instruments with directional microphones has grown steadily.

Based on recent success, it stands to reason that directional microphone technology should extend to open-fit hearing aids. The fact that directional microphones and venting both impact low-frequency gain has led many clinicians to conclude, however, that the benefits of directional microphones are negligible for patients with high-frequency hearing loss. Ricketts3 showed that high-level environmental noise may pass through the vent, rather than the directional microphone array, in open-fit devices.

In reality, although the magnitude of benefit for open-fit hearing aids is less than that for occluded earmolds/shells, modern directional microphones do provide improved speech recognition in noise with open fittings. Despite digital technology innovations, much of the background evidence in support of using directional microphones with large vents was provided by research conducted decades ago when BTEs were a much larger part of the market. In other words, “past is prologue.”

FIGURE 1. Vent parameters for different parallel vent diameters and for an open “tube” fitting with no canal occlusion. Based on Lybarger.4
Click on image for larger version.

Venting effects. In 1985, Sam Lybarger4 conducted a series of measurements of various acoustic coupling strategies to investigate the impact on hearing aid frequency response. His results, summarized in Figure 1, illustrate the following:

  • 1 mm, 2 mm, and 3 mm parallel vents attenuate hearing aid gain below 750 Hz, when compared to the unvented response;
  • Nonoccluding “tube-style” fits that do not seal the ear canal via a dome tip attenuate frequencies below 1500 Hz, compared to the unvented response.

These findings suggest that, to be effective with open-fit devices, directional microphones need to provide benefits for spatially separated noises above 750 Hz for vented earmolds or 1500 Hz for nonoccluding earmolds.

FIGURE 2. Polar pattern results for a prototype directional microphone system that uses a 5 mm port separation, rather than the conventional 12 mm separation distance. Click on image for larger version.

Directional Microphones. For a dual-microphone directional microphone system, the process of signal subtraction of energy received at the two microphones adds the power from the two microphones, which increases the internal noise relative to an omnidirectional microphone system. Closer microphone spacing increases internal noise, but it also improves high-frequency directionality, which is critical for open fittings for high-frequency hearing losses. The industry standard port separation between microphones is 12 mm, which provides a reasonable compromise between high-frequency directionality (with benefits up to 4000 Hz) and low internal noise that is not audible to users with mild-to-moderate low-frequency hearing loss.

Phonak’s directional microphone system uses a port separation of 5 to 8 mm, designed to improve high-frequency directional benefits through 6350 Hz (Figure 2). Directivity indices (DIs) as a function of frequency for an unvented acoustic coupling system (Figure 3) reveal DIs in excess of 6 dB across the entire hearing instrument bandwidth. Obviously, reducing the low-frequency gain below 750 Hz or 1500 Hz will impact low-frequency DIs—and ultimately speech recognition in noise. However, significant benefits remain for systems that provide directionality between 1500 and 6350 Hz for patients with high-frequency sensorineural hearing loss.

FIGURE 3. DI measurements as a function of frequency for an occluded acoustic coupler for a prototype directional microphone system with 5 mm microphone spacing between microphone ports. Click on image for larger version.

To test this idea, a recent field study was conducted using 20 adult subjects with moderate-to-severe high-frequency sensorineural hearing loss (Figure 4). Subjects were fitted binaurally with hearing instruments utilizing the smaller microphone port spacing (MicroSavia). Subsequently, an adaptive speech recognition threshold (SRT) in noise metric was used to evaluate the 50% recognition threshold for speech originating from 0° azimuth, with four “noise jammers” originating from 45°, 135°, 225°, and 315° relative to the midline. The average SRT in noise improvement for the aid in directional mode was 2.3 dB, versus the omnidirectional condition, translating
into approximately 20 to 30% improvement for conversational speech.

Although the magnitude of benefit is less than what a patient might receive from occluded earmolds, directional microphones are compatible and beneficial with open-fit hearing aids.

FIGURE 4. Average SRT in noise measurements for 20 subjects with sloping high-frequency sensorineural hearing loss for unaided conditions and with MicroSavia in omni and directional microphone mode. Click on image for larger version.

Fact Appropriate manual/automatic program selection improves benefit with open-fit hearing aids.

As stated above, the concession for improved high-frequency directivity is increased internal noise, which may be audible to patients with normal low-frequency hearing sensitivity. So it is important that hearing aids—especially those with reduced directional microphone port spacing—have a mechanism for switching between directional and omnidirectional mode.

Cord, Surr, Walden, and Olson5 reported that patients whose instruments had manual “mode” switches used directional microphones approximately 25% of the time—partly due to confusion over when omni- and directional microphone modes would benefit. The authors report that patients who persist in using the directional microphone mode eventually determine when it is beneficial and set their hearing aids in that mode when appropriate. But the study also suggests that the use of automatic program switching between microphone modes may minimize the impact of increased circuit noise by engaging the directional microphones only when noise is present.

The issue of automatic versus manual control depends on patient preference, but the bottom line is that increased internal noise is a moot point if the patient cannot hear it. This is especially critical for patients with sloping high-frequency hearing losses and normal low-frequency hearing sensitivity.

Myth Open-fit hearing aids with omnidirectional microphones provide improved speech recognition in noise by providing improved audibility.

Studies have reported that, for subjects with moderate-to- severe hearing loss, speech recognition in noise performance may be predicted based on long-term average speech levels, audiometric thresholds, and noise spectrum levels.6,7 For patients with more significant hearing losses, hearing aid gain compensates for elevated audiometric thresholds by providing improved speech audibility and speech recognition scores, both in quiet and in noise. For open fittings, however, this advantage is less clear, because processed and unprocessed sound enter the ear canal through the hearing aid microphone and vent path, respectively.

Further, with BTE open fittings, pinna and concha bowl resonances are lost for over-the-ear microphone placements, so there is evidence speech recognition in noise performance with open-fit omnidirectional microphones is not statistically significant from unaided performance.8

Similarly, Figure 4 suggests worse performance for the omnidirectional microphone condition than with no hearing aid at all! Interestingly, when pinna and concha resonances were partially restored using a special algorithm (Real Ear Sound), measured SRT in noise in the same patients improved to their unaided performance levels. Increasing empirical evidence suggests that, at best, speech recognition in noise with omnidirectional microphone open-fit devices is equivalent to unaided performance.

Myth Feedback phase inversion completely eliminates feedback issues with open-fit hearing aids.

Recently, digital hearing aids with feedback phase inversion have become widely available and are a primary reason for the resurgence of open-fit devices. It is a popular misconception, however, that feedback cancellation algorithms eliminate the presence of feedback. Rather, feedback cancellation allows high-frequency gain to be preserved or increased when vent size is increased in an effort to minimize occlusion.9

Yet there are still theoretical limitations on the high-frequency gain that may be provided for various vent configurations.10 Although additional research is required, it is probably safe to conclude that a practical limitation resides in the range of 30 dB maximum stable high-frequency gain for unoccluded earmolds used with open-fit devices.

Fact Real-ear measurements (REM) are possible with open-fit devices.

Lybarger11 says reduced internal tubing diameter affects the aid’s acoustic coupling response. To compensate, the real-ear-to-coupler difference (REAR) of a “slim tube” hearing aid should be adjusted in the software to reflect the change in resonance properties from standard (#13) tubing.

A more accurate performance measure is obtained via real-ear measurements with open-fit devices. But conventional use of insertion gain is complicated by the fact that the difference between aided and unaided measurements is corrupted by sound entering through the vent path. So the best way to accurately verify open-ear fittings is through measuring and displaying the real-ear aided response on the “SPL-o-gram.”12

FIGURE 5. REAR responses for soft speech (green), moderate speech (magenta), and MPO sweep (red) using an AudioScan Verifit real-ear measurement system. Click on image for larger version.

However, Fabry13 describes a more comprehensive method to verify open-fit devices: Using a broadband live or recorded speech (or speech-like) stimulus, REAR is measured for three presentation levels—50 dB SPL, 65 dB SPL, and 85 dB SPL—to ensure that soft speech is soft, moderate speech is comfortable, and loud speech and other sounds do not exceed the loudness discomfort level (LDL) (Figure 5). For open-fit devices, the criterion for “matching” target values should be as follows:

1) Ensure that REAR peaks and minima are audible across as broad a frequency range as possible for average speech levels (65 dB SPL).

2) Match median speech levels to the patient’s unaided thresholds for soft speech levels (50-55 dB SPL). (Exception: If median soft speech levels are above patient’s unaided thresholds, do not reduce gain.)

3) Adjust hearing aid maximum power output (MPO) for loud speech (85 dB SPL) or MPO “sweep” stimulus (85 to 90 dB SPL) to ensure that MPO approaches, but does not exceed, the patient’s LDL.

This method will ensure that compression ratios remain as low as possible, while preserving maximum use of the patient’s residual auditory area. The use of REM verifies that the hearing aids are “acoustically matched” to individual ears, and that they provide audible speech information over as broad a frequency range as possible. Most importantly, however, this approach stresses that REMs are a starting point—not a “gold standard”—and should be used in combination with follow-up tools (eg, datalogging).

Modern hearing aids that use datalogging to monitor volume control adjustments made by the patient after the i
nitial fitting help optimize the initial settings to meet individual patient needs. The bottom line is that real-ear measurements can—and should—be used with open-fit devices.


The popularity of open-fit hearing aids has increased dramatically, in large part due to digital capabilities in combination with feedback phase-inversion systems that may be used to dynamically cancel hearing aid feedback. In addition, mini- and microsized BTE devices offer improved cosmetics while providing minimal occlusion through the use of large acoustic vents. Although there is slightly less of a “wow” factor than with occluded shells or earmolds, open-fit devices equipped with directional microphones provide improved speech recognition in noise compared with unaided or omnidirectional conditions.


  1. Hearing Industries Association (HIA). Special survey results on BTEs, directional, and telecoil use. Alexandria, Va: HIA; Feb 22, 2006.
  2. Kochkin S. Customer satisfaction with single and multiple microphone digital hearing aids. The Hearing Review. 2000; 7(11), direct mail sales:24-29.
  3. Ricketts T. Impact of noise source configuration on directional hearing aid benefit and performance. Ear Hear. 2000; 21:194-205.
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  5. Cord MT, Surr RK, Walden BE, Olson L. Performance of directional microphone hearing aids in everyday life. J Am Acad Audiol. 2002; 13: 295-307.
  6. Plomp R. A signal-to-noise ratio for the speech reception threshold of the hearing impaired. J Speech Hear Res. 1986; 29(2):146-154.
  7. Fabry DA, Van Tasell DJ. Evaluation of an articulation-index based model for predicting the effects of adaptive frequency response hearing aids. J Speech Hear Res. 1990; 33(4):676-89.
  8. Kuk F, Keenan D, Ludvigsen C. Efficacy of an open-fitting hearing aid. The Hearing Review. 2005;12(2):26-32.
  9. Hellgren J, LunnerT , Arlinger S. Variations in the feedback of hearing aids. J Acoust Soc Am. 1999; 106 (5): 2821-2833.
  10. Greenberg JE, Zurek PM, Brantley M. Evaluation of feedback-reduction algorithms for hearing aids. J Acoust Society Am. 2000;108(5):2366-2376.
  11. Lybarger S. Earmold venting as an acoustic control factor. In: GA Studebaker, Hochberg I, eds. Acoustic Factors Affecting Hearing Performance. Baltimore: University Park Press; 1980:197-217.
  12. Pascoe D. An approach to hearing aid selection. Hear Instrum. June 1978;12-16, 36.
  13. Fabry DA. Nonlinear hearing aids and verification of fitting targets. Trends Amplif. 2003; 7(3):99-115.
  14. Kochkin S. MarkeTrak VI: The VA and direct mail sales spark growth in hearing aid market. The Hearing Review. 2001; 8(12):16-24,63-65.

This article was adapted from an article of the same title that appeared in the May 2006 HR, available in the HR Archives. Correspondence may be addressed to David Fabry at .