Share This


Bone conduction mechanisms and history of bone conduction aids

Bone conduction hearing devices work by stimulating hair cells via the bone conduction hearing pathways. These pathways are less well understood than the air conduction pathways, but recent research has shown that contributing factors include sound radiated to the external ear canal, inertia of middle ear ossicles and cochlear fluids, compression of the cochlear walls and transmission from the cerebrospinal fluid [1].

Bone conduction amplification has been in evidence as far back as the 16th Century when rod devices were used to transmit vibrations via the teeth. The development of the carbon microphone and magnetic receiver in the early 20th Century lead to the advent of the bone conduction vibrator [2]. This can be worn on a tight fitting headband placed against the mastoid or on a spectacle mount. Disadvantages of these conventional bone conduction devices include the unacceptable cosmetic appearance and discomfort associated with pressure. In addition, a significant amount of amplified sound energy is dispersed within the soft tissues of the scalp [3].

Percutaneous bone conduction devices and osseointegration

The challenges faced by traditional bone conduction aids lead to the idea of directly coupling the transducer to the skull. Branemark first developed the concept of osseointegration of a titanium metal screw in bone when he was doing research on blood flow in the rabbit. This involved using a titanium inspection chamber inserted into the rabbit tibia, but when it came to removing the chamber for reuse, he discovered that this was very difficult due to the osseointegration [4].

The first bone anchored hearing device (BAHD) was fitted by Tjellström in 1977 [5]. The design of the implant has changed over time in response to research determining the factors that influence osseointegration. Macroscopically, an increased diameter and modified threading are thought to have improved the implant stability and microscopically, a roughened surface provides a larger surface area for more direct contact with the bone [6]. Objective measurement of osseointegration (and by inference implant stability) has been a topic of discussion as this has implications in the early loading of implants. Currently, resonance frequency analysis (RFA) is being used to monitor stability changes over time and there is increasing evidence to support earlier loading of implants [7, 8]. Cone beam computed tomography (CT) has been used in the assessment of osseointegration of intra-oral implants as it exposes patients to a lower radiation dose compared with conventional CT. This may have applications in the temporal bone for the future [9].


Initially the concept of the percutaneous BAHD was introduced for those patients with bilateral acquired or congenital mixed or conductive hearing losses (CHL), who were for practical reasons unable to wear conventional air conduction aids. As the benefit of BAHD has been evaluated clinically, these indications have expanded over time and more recently evidence of the benefit to patients with unilateral hearing losses (of both a conductive and sensorineural nature) is emerging [10-12].

Challenges with percutaneous bone conduction aids Despite being more commonly accepted than the conventional bone conduction hearing devices, the BAHD does leave patients with a visible percutaneous abutment, which for some is cosmetically unacceptable. Additionally, the percutaneous abutments are associated with peri-abutment soft tissue reactions and fixture failures in a proportion of patients [13]. Recent years have seen different abutment shapes and lengths being advocated to minimise complications, and recent studies are now reporting that minimal or no soft tissue reduction with a longer abutment length has superior results [14]. Cochlear® have launched a hydroxyapatite coated abutment. Experimental studies have shown that the coated abutments promote enhanced dermal adherence and hence fewer skin problems [15].

Transcutaneous bone conduction devices

Concern surrounding the appearance of peri-abutment skin problems has lead to the development of transcutaneous bone conduction devices with similar indications to the skin penetrating or percutaneous devices. As there is no percutaneous abutment, there is reduced risk of skin reaction and trauma. However, the audiological candidacy criteria are more conservative when compared with the percutaneous devices.

Passive devices

  1. The Alpha 1 and 2 by Sophono™ is a semi implantable system that relies on magnetic coupling between implanted and external magnets. A recent study from Nijmegen confirms that the percutaneous BAHD has an output that is 10-15dB higher than that of the Sophono [16].
  2. The Baha® Attract is an implantable magnet that is attached to an osseointegrated titanium fixture. An external magnet is then coupled via the scalp. Clinical trials are currently ongoing, but there are no published human studies at the time of writing.

Active device

The Bonebridge™ system from Med-El is an intact skin device with an implantable floating mass transducer (FMT) that is retained in the mastoid temporal bone by two screws that do not rely on osseointegration. An external sound processor is coupled to internal magnets and the candidacy criteria are similar to the above transcutaneous devices. As the floating mass transducer is fairly large, pre operative CT imaging is recommended to establish sufficient bone depth and optimal placement. Case reports in the literature are encouraging [17].

Transcutaneous devices may be a relative contraindication in patients that require regular magnetic resonance imaging (MRI). A maximum of 3-Tesla scanners can be used with the Sophono™, and 1.5-Tesla scanners with the Baha® Attract and the Bonebridge™. If more detailed images are required then the magnet needs to be removed prior to imaging. As the devices are significantly larger than the percutaneous systems, a large artefact (up to 10 cm) can be seen on imaging.

Middle ear implant with round window application

The Vibrant Soundbridge (VSB) from Med-El was originally developed for patients with mild to moderate sensorineural hearing loss. It is a semi implantable active middle ear implant. The FMT is the active component of the internal vibrating ossicular prosthesis and was originally intended to be clipped to the incus in an intact ossicular chain. For the last ten years there have been reports of coupling the FMT to the round window (or ossicular chain remnants), expanding the audiological indications to include conductive and mixed hearing losses. The round window technique (VSB-RW) involves placing the FMT onto the round window membrane after cutting off the titanium clip and widening the round window niche. Challenges include damage to the inner ear with resultant sensorineural hearing loss and loss of the coupling resulting in reduced amplification [18].

Guidelines for the selection of mechanical bone conduction hearing devices in adults

Since BAHDs were first introduced in the 1970s, there have been numerous developments to percutaneous devices. In addition, there are several other devices available on the market making device selection challenging (if funding is available). Below is a summary of choices available for patients that we use in Birmingham:

  • If patient requires regular MRI scans – percutaneous BAHD
  • If considering Bonebridge – pre operative CT imaging required, (if previous mastoid surgery may not be suitable bone thickness).


Single sided deafness (SSD) (Ave BC 0.5,1,2,3 contralateral side)
BC<20 dBHL Percutaneous BAHD or Transcutaneous device
CHL and mixed loss unilateral or bilateral (Ave BC 0.5,1,2,3)
BC <20 dBHL Percutaneous BAHD or transcutaneous device
BC 20-40 dBHL Percutaneous BAHD, transcutaneous device, VSB-RW
BC 40-55 dBHL BAHD or VSB-RW
BC 55-65 dBHL Trial of Baha® Cordelle


The development of these newer transcutaneous devices provides clinicians and patients with new treatment choices, however the longer term results from larger studies are not yet available. These devices are more expensive when compared to the traditional percutaneous BAHD and hence funding may become difficult in the current financial climate.



1. Stenfelt S, Goode RL. Bone-conducted sound: physiological and clinical aspects. Otol Neurotol 2005;26(6):1245-61.
2. Berger KW. Early bone conduction hearing aid devices. Arch Otolaryngol 1976;102:315-8.
3. Mylanus E, Snik A, Cremers C. Patients’ opinions of bone anchored vs conventional hearing aids. Arch Otolaryngol 1995;121:421-5.
4. Branemark P, Hansson B, Adell R, Breine U, Lindstrom J, Hallen O. Osseointegrated implants in the treatment of the edentulous jaw. Scand J Plast Recons 1977;11:104-19.
5. Tjellström A, Lindstrom J, Hallen O, Albrektsson T, Branemark P. Osseointegrated titanium implants in the temporal bone. Am J Otolaryng 1981;2:304-10.
6. Marsella P, Scorpecci A, D’Eredita R, Della Volpe A, Malerba P. Stability of osseointegrated bone conduction systems in children: a pilot study. Otol Neurotol 2012;33(5):797-803.
7. Faber HT, Dun CA, Nelissen RC, Mylanus EA, Cremers CW, Hol MK. Bone-anchored hearing implant loading at 3 weeks: stability and tolerability after 6 months. Otol Neurotol 2013;34(1):104-10.
8. McLarnon CM, Johnson I, Davison T, et al. Evidence for early loading of osseointegrated implants for bone conduction at 4 weeks. Otol Neurotol 2012;33(9):1578-82.
9. Granstrom G, Grondahl HG. Imaging of osseointegrated implants in the temporal bone by accuitomo 3-dimensional cone beam computed tomography. Otol Neurotol 2011;32(2):199-203.
10. de Wolf M HK, Mylanus E, Snik A, Cremers C. Benefit and Quality of Life After bone-Anchored Hearing Aid Fitting in Children With Unilateral or Bilateral Hearing Impairment. Arch Otolaryngol 2011;137(2):130-8.
11. Grantham DW, Ashmead DH, Haynes DS, Hornsby BW, Labadie RF, Ricketts TA. Horizontal plane localization in single-sided deaf adults fitted with a bone-anchored hearing aid (Baha). Ear Hear 2012;33(5):595-603.
12. Pai I, Kelleher C, Nunn T, et al. Outcome of bone-anchored hearing aids for single-sided deafness: a prospective study. Acta Otolaryngol 2012;132(7):751-5.
13. Pelosi S, Chandrasekhar SS. Soft tissue overgrowth in bone-anchored hearing aid patients: use of 8.5 mm abutment. J Laryngol Otol 2011;125(6):576-9.
14. Hultcrantz M. Outcome of the bone-anchored hearing aid procedure without skin thinning: a prospective clinical trial. Otol Neurotol 2011;32(7):1134-9.
15. Larsson A, Wigren S, Andersson M, Ekeroth G, Flynn M, Nannmark U. Histologic evaluation of soft tissue integration of experimental abutments for bone anchored hearing implants using surgery without soft tissue reduction. Otol Neurotol 2012;33(8):1445-51.
16. Hol MK, Nelissen RC, Agterberg MJ, Cremers CW, Snik AF. Comparison Between a New Implantable Transcutaneous Bone Conductor and Percutaneous Bone-Conduction Hearing Implant. Otol Neurotol 2013;34(6):1071-5.
17. Manrique M, Sanhueza I, Manrique R, de Abajo J. A new bone conduction implant: surgical technique and results. Otol Neurotol 2014;35(2):216-20.
18. Luers JC, Huttenbrink KB, Zahnert T, Bornitz M, Beutner D. Vibroplasty for mixed and conductive hearing loss. Otol Neurotol 2013;34(6):1005-12.

Declaration of Competing Interests: RB has been reimbursed by Oticon and Cochlear, manufacturers of bone conduction devices, towards the costs of her PhD thesis.

Share This
Rupan Banga

University Hospitals Birmingham NHS Foundation Trust, Queen Elizabeth Hospital ,Birmingham, UK.

View Full Profile