Brain voice processing with bilateral cochlear implants: a positron emission tomography study
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Transcript of Brain voice processing with bilateral cochlear implants: a positron emission tomography study
OTOLOGY
Brain voice processing with bilateral cochlear implants: a positronemission tomography study
Arnaud Coez • Monica Zilbovicius • Evelyne Ferrary • Didier Bouccara •
Isabelle Mosnier • Emmanuele Ambert-Dahan • Eric Bizaguet •
Jean-Luc Martinot • Yves Samson • Olivier Sterkers
Received: 9 September 2013 / Accepted: 3 November 2013
� Springer-Verlag Berlin Heidelberg 2013
Abstract Most cochlear implantations are unilateral. To
explore the benefits of a binaural cochlear implant, we used
water-labelled oxygen-15 positron emission tomography.
Relative cerebral blood flow was measured in a binaural
implant group (n = 11), while the subjects were passively
listening to human voice sounds, environmental sounds
non-voice or silence. Binaural auditory stimulation in the
cochlear implant group bilaterally activated the temporal
voice areas, whereas monaural cochlear implant stimula-
tion only activated the left temporal voice area. Direct
comparison of the binaural and the monaural cochlear
implant stimulation condition revealed an additional right
temporal activation during voice processing in the binaural
condition and the activation of a right fronto-parietal cor-
tical network during sound processing that has been
implicated in attention. These findings provide evidence
that a bilateral cochlear implant stimulation enhanced the
spectral cues associated with sound perception and
improved brain processing of voice stimuli in the right
temporal region when compared to a monaural cochlear
implant stimulation. Moreover, the recruitment of sensory
attention resources in a right fronto-parietal network
allowed patients with bilateral cochlear implant stimulation
to enhance their sound discrimination, whereas the same
patients with only one cochlear implant stimulation had
more auditory perception difficulties.
Keywords Binaural hearing � Brain imaging �
Cochlear implant � Deafness � Positron emission
tomography � Temporal voice area
Introduction
Hearing loss is an auditory perception disorder that induces
deficits in oral communication due to an ability to perceive
A. Coez � M. Zilbovicius � J.-L. Martinot
CEA-Inserm U1000 Neuroimaging and Psychiatry, Service
Hospitalier Frederic Joliot, IFR49, 91401 Orsay, France
A. Coez � M. Zilbovicius � J.-L. Martinot � Y. Samson
CEA, DRM, DSV, Service Hospitalier Frederic-Joliot,
91401 Orsay, France
A. Coez (&) � E. Bizaguet
Laboratoire de Correction Auditive, Eric Bizaguet,
20, rue Therese, 75001 Paris, France
e-mail: [email protected]
E. Ferrary � D. Bouccara � I. Mosnier � O. Sterkers
UMR-S 867, Inserm, 75018 Paris, France
E. Ferrary � D. Bouccara � E. Ambert-Dahan � O. Sterkers
Service d’ORL et de Chirurgie Cervico-Faciale, AP-HP,
Hopital Beaujon, 92110 Clichy, France
E. Ferrary � D. Bouccara � I. Mosnier � O. Sterkers
Universite Paris, 7 Denis Diderot, Paris, France
E. Ferrary � D. Bouccara � I. Mosnier � O. Sterkers
Institut Federatif de Recherche Claude Bernard Physiologie et
Pathologie, IFR02, 75018 Paris, France
I. Mosnier � O. Sterkers
Service d’ORL et de Chirurgie Cervico-Faciale, AP-HP,
Hopital Louis Mourier, 92700 Colombes, France
Y. Samson
Service Urgences Cerebro-Vasculaires, AP-HP,
Hopital Pitie-Salpetriere, 75013 Paris, France
Y. Samson
Universite Paris, 6 Pierre et Marie Curie, Paris, France
123
Eur Arch Otorhinolaryngol
DOI 10.1007/s00405-013-2810-8
acoustical cues important for speech production and
understanding. Patients with hearing loss have difficulty in
distinguishing speech and voices from other sounds such as
environmental noises. Individuals with hearing loss may
benefit from cochlear implantation to improve voice and
speech cue transduction. Most current cochlear implants
(CI) are multichannel devices that provide intra-cochlear
stimulation, exploiting the tonotopic organisation of the
cochlea and the central auditory pathways. Psychophysical
experiments have demonstrated that stimulating different
cochlear electrodes elicits auditory perception of different
pitches and that the identification of consonants, vowels
and words significantly improved as the number of bands
increased [1]. The functional results ranged from the res-
toration of sound perception to full speech intelligibility
and voice recognition [2]. The outcome of implantation
depended on the implant signal, its coupling to the central
auditory system and the ability of the auditory system and
other related brain systems to learn how to most efficiently
obtain information from the signal [3].
Monaural or binaural cochlear implantation
Although binaural perception is important for normal
hearing, recent clinical studies have demonstrated that
bilateral perception improves speech intelligibility and
sound localisation in complex, noisy environments [4]. The
majority of the 120,000 patients [2] who have benefited
from cochlear implantation only have one cochlear implant.
Binaural information (interaural time and level differences)
and the spectral shaping of sounds by the pinna are used for
sound source localisation and to increase the ability to
distinguish background noise [5]. The overall increase in
sound quality is attributed to the head shadow effect, the
squelch effect and the diotic summation effect [6]. It is still
unknown whether two CI compared to one CI could
enhance voice and speech perception and whether their
response properties differ in the two brain hemispheres.
Cochlear implants and neuroimaging
Functional neuroimaging studies provide an insight into the
cortical changes that take place in patients with cochlear
implant (see review [7]), and especially in bilateral
cochlear implant users [8, 9]. Recent (H215O) positron
emission tomography (PET) activation studies [10, 11]
have suggested that PET is an effective method to explore
the benefit of cochlear implants and that improvements in
speech intelligibility can be linked to the activation of the
temporal voice area (TVA), which is located bilaterally
along the upper bank of the superior temporal sulcus (STS).
In adults, the cerebral processing of vocal sounds is known
to engage TVAs that are primarily located along the middle
and anterior parts of the STS. Functional magnetic reso-
nance imaging (fMRI) studies have shown increased
activity in the TVA in response to voices (speech and non-
speech vocalisations, such as laughs and coughs) when
compared to natural non-vocal sounds (environmental and
musical sounds) or to amplitude- or frequency-matched
acoustical control sounds [12]. A previous study [12]
examined how the activation of voice-sensitive areas and
the subjects’ performance on voice-perception tasks are
affected by modifying the spectral structure of the stimuli.
Sets of vocal and non-vocal sounds were presented during
scanning, and spectral filtering removed either the high or
low frequencies. The mean activity in the TVA was
enhanced by vocal stimuli in comparison to non-vocal
stimuli, but the activity was significantly decreased by
spectral filtering. A CI was used as one method of spectral
filtering [1]. To measure the benefit of two independent
sites of cochlear stimulation provided by a bilateral CI, we
used PET (H215O) to study TVA activation. We hypothe-
sised that an improvement in spectral cue transmission
by bilateral CI stimulation would produce stronger
TVA activation when compared to a unilateral implant
stimulation.
Materials and methods
Subjects
Eleven male patients with bilateral cochlear implants and
an average age of 56 years ± 9 (mean ± SD, n = 11)
were studied during binaural or monaural stimulation.
Written informed consent was obtained from all subjects.
The Xavier-Bichat Hospital Ethics Committee approved
the protocol. Patients had bilateral progressive (n = 8),
otosclerosis (n = 2), or meningitis (n = 1) post-lingual
deafness. They were bilaterally implanted between 2003
and 2006 with Opus 2 cochlear implants containing 12
active electrodes (Medel Inc, Innsbruck, Austria), and they
had 3 years ± 1 (mean ± SD, n = 11) of cochlear implant
experience. The CI was used more than 8 h a day. The
mean auditory threshold (average of auditory thresholds at
500 Hz, 1, 2 and 4 kHz) measured in the free field with
warble tones was 23 dB ± 7 (mean ± SD, n = 11). The
average intelligibility score on the Lafon monosyllabic task
at 65 dB in the free field of the binaural condition was
75 % ± 23, which was higher than in the monaural con-
dition (54 ± 28 %, p\ 0.05).
Task and stimuli
The subjects were scanned while passively listening to
voice sounds (30 % speech sounds, 70 % non-speech vocal
Eur Arch Otorhinolaryngol
123
sounds) or to only non-voice stimuli (19 % nature, 24 %
animals, 47 % modern human environment, and 10 %
musical instruments). The same stimuli were used in the
original fMRI study [12]. Twelve PET (ECAT-EXACT-
HR?; Siemens AG, Erlangen, Germany) acquisitions after
an intravenous bolus of (H215O) (333 MBq per injection)
were obtained at 10-min intervals during passive listening:
four measurements occurred during passive listening to the
voice condition (two during a binaural stimulation, two
during a monaural stimulation), four occurred during pas-
sive listening to a non-voice condition (two during a bin-
aural stimulation, two during a monaural stimulation), and
four occurred during passive listening in silence. The lis-
tening blocks were presented to the patient in random order
at a mean sound pressure level of 65 dB through KOSS
electrostatic headphones. Patients were asked to listen
carefully to the sounds with their eyes closed and while
awake, which was systematically checked during the exam.
At the end of the PET exam, the patients were asked to
report what they had heard.
PET acquisition
The rCBF was determined from the distribution of radio-
activity measured with the PET (ECAT-EXACT-HR?,
Siemens AG, Erlangen, Germany) after intravenous H215O
bolus injections [13]. Listeners received 12 H215O injections
(333 MBq per injection) corresponding to the 12 rCBF
measurements that were performed at 10-min intervals.
The first scan corresponded to a silent condition. There was
a fixed period of 30 s between the bolus infusion and the
presentation of the stimuli. The attenuation-corrected data
were reconstructed into 63 axial slices (2.25 mm thick)
with a resulting resolution of 4.5 mm full width at half
maximum after reconstruction [14].
Data analyses
The rCBF images were analysed using statistical para-
metric mapping software (SPM99) that was used for image
realignment, transformation into standard stereotaxic ana-
tomical space [15], smoothing (12 mm) and statistical
analyses [16]. The state-dependent differences in global
flow were covaried using proportional scaling. Compari-
sons across conditions were made using a t test that was
subsequently transformed into normally distributed z sta-
tistics using a multi-study design. The resulting z map
threshold was at p\ 0.001.
Three statistical analyses of activation were performed
in the monaural and binaural conditions: a comparison of
activation for listening to voice and non-voice sounds
versus the silent condition (p = 0.001; corrected for mul-
tiple comparisons to p = 0.05) and a comparison between
voice stimuli and non-voice stimuli (p = 0.00005). These
analyses were then examined by a between-condition
comparison relative to the results obtained in the CI
monaural and binaural stimulation conditions for the voice
and non-voice stimuli (p = 0.001) and for the voice and
non-voice conditions compared to the silent condition
(p = 0.0001).
Results
Comparing voice to non-voice stimuli during monaural
and binaural conditions
Activation was observed bilaterally in the TVA in the
binaural CI stimulation condition. In contrast, in the
monaural condition, patients only showed left TVA acti-
vation without right TVA activation (Fig. 1, left upper
panel; Table 1).
When comparing the binaural condition to the monaural
condition, the CI showed a significantly greater right
activation along the upper bank of the right STS in the
former condition than in the latter one (Fig. 1, left lower
panel; Table 2). When comparing the monaural condition
to the binaural one, no activation was found.
Comparing the whole sound stimuli to silence
during the monaural and binaural conditions
When comparing the listening condition (pooled voice and
non-voice conditions) to the silence condition, binaural and
monaural stimulations by the CI led to a bilateral temporal
pattern of activation (Fig. 1, right upper panel; Table 3).
Activation peaks were similarly located in both right and
left STS, during the binaural and monaural stimulations.
Activation of a right fronto-parietal network was
observed in the binaural condition when compared to the
monaural one (Fig. 1, right lower panel; Table 4). No
additional temporal activation was found in the binaural
condition as compared to the monaural one.
Discussion
Bilateral cochlear implant and TVA activation
Listening to the voice stimuli compared to listening to non-
voice stimuli, a bilateral TVA activation was found during
bilateral CI stimulation. Only the left TVA was activated
during unilateral CI stimulation. When compared to mon-
aural stimulation, binaurally stimulated patients had an
additional right temporal activation with their CI. Patients
also had a better intelligibility score with two cochlear
Eur Arch Otorhinolaryngol
123
implants. As shown in previous studies [10, 11], we found
that the subjects’ rCBF response to the stimuli paralleled
their intelligibility score performance. With a different
PET paradigm design, using word stimuli, binaural stim-
ulation through cochlear implants appeared also advanta-
geous when compared with the monaural at the
neurofunctional level because the pattern of brain activa-
tion was closer to the normal one [9]. The paradigm of the
present study allowed a direct comparison of a binaural
stimulation to a monaural one by cochlear implants.
Although, some studies suggested a dissociation in the
dynamic of functional recuperation of speech and voice
processing [17], binaural cochlear users had in this study an
immediate degradation of speech intelligibility when using
only one cochlear implant and they had concomitantly a
different pattern of brain networks when listening to voi-
ces. Moreover, in adults, the TVAs are sensitive to voices
and highly selective. The enhanced responses to voice
stimuli as compared to a range of control sounds, even after
spectral filtering of voice and non-voice stimuli [12],
allowed showing that the TVA’s preference is driven by
low-level acoustical parameters.
Bilateral cochlear implant and perception of spectral
acoustical cues
A weaker brain response with increased spectral filtering
was found in a group of normal hearing adults [12, 18]. In
vocoding, a process that mimics the effects of a cochlear
implant processor, global temporal information is pre-
served, while the fine spectral structure is degraded (1).
The difference between monaural and binaural CI stimu-
lation reflects the impact of a reduced number of inde-
pendent peripheral sites of stimulation in the cochlea
obtained with a single CI when compared to a strict bin-
aural effect with two cochlear implants. Actually, no more
than 4–8 independent sites are available in the speech-
processor context using the present electrode designs due
to substantial overlap in the electric fields from adjacent
electrodes [19]. The use of two CI allowed for an increase
in the number of independent ear stimulation sites and
improved the ability to discriminate the features of two
different sounds that could allow the patient to have a
stronger discrimination of voice sounds as compared to
other sounds.
Fig. 1 Localisation of activation peaks. Left upper panel voice versus
non-voice group analysis. The location of activation peaks to compare
‘voice’ versus ‘non-voice’ in each condition (binaural and monaural
condition with bilateral CI at p = 0.00005) shown in a lateral view of
both hemispheres. Right upper panel voice and non-voice versus
silence group analysis. The location of activation peaks comparing the
‘voice ? non-voice’ versus ‘silence’ conditions [binaural and mon-
aural conditions with bilateral CI at p\ 0.001 and then corrected for
multiple comparisons (p = 0.05)] are shown in a lateral view of both
hemispheres. Lower panel direct comparison of a monaural and a
binaural stimulation using a CI. The localisation of the activation
peaks are shown in a glass brain view. Left lower panel voice versus
non-voice (at p = 0.001). The location of activation peaks comparing
the ‘voice’ versus ‘non-voice’ in the binaural versus the monaural
stimulation (upper panel) is shown. Right lower panel voice and non-
voice versus silence (at p = 0.0001). The location of activation peaks
comparing the ‘voice ? non-voice’ versus ‘silence’ in the binaural
versus the monaural stimulation is shown. CI cochlear implant
Eur Arch Otorhinolaryngol
123
Specifically, several studies have examined the spectral
and temporal acoustical cues present in the stimuli, which
were shown to be important factors for determining the
recruitment of the left and/or right auditory cortex [20].
Many PET and fMRI experiments [21, 22] have shown an
enhanced sensitivity to temporal rate by the left auditory
cortex and to pitch by the right auditory cortex. In general,
damage to the right superior temporal cortex, but not to the
left primary auditory areas, affects a variety of other tonal
or spectral processing tasks [23, 24]. In this study, patients
had no cerebral lesions, and the supplementary right tem-
poral activation should reflect stronger bottom-up sound
perception from spectral cues when two cochlear implants
were functioning.
Bilateral cochlear implant and brain sound
discrimination networks
rCBF increases in the right temporal lobe have been pre-
viously correlated with subjects’ performance in a speaker
identification task [25] or with their ability to direct
attention to vocal identity [26, 27]. By comparing the
binaural to monaural conditions when listening to voice
and non-voice stimuli versus silence, we observed the
activation of a supplementary right fronto-parietal network
in the binaural CI stimulation condition. This right fronto-
parietal network activation has been found in other studies
on selective or sustained attention to sound intensity dis-
crimination [28] or to sound duration [29]. In these two
Table 1 Coordinates, size and Z score of areas activated by voice
compared to non-voice conditions in the CI group
Area Voice versus non-voice
x y z Z t Cluster
size
Binaural CI stimulation
STS, anterior (BA21) 66 -2 -6 4.38 4.48 27
STS, middle (BA22) 68 -14 4 4.06 4.14 15
STS, middle (BA21) -60 -10 -4 4.10 4.18 66
STS, posterior (BA22) -64 -22 4 4.17 4.25
Monaural CI stimulation
STS, middle (BA21) -58 -12 0 5.66 5.87 517
STS, posterior (BA22) -64 -22 2 4.98 5.12
Approximate Brodmann numbers (BA) associated with anatomical
regions of the superior temporal sulcus (STS) are given in paren-
theses. Coordinates (in standard stereotaxic space [15]) of voxels
correspond to local maxima of Z value, above Z = 4.0 (p = 0.00005)
within each focus of activation. x: distance (mm) to right (?) or left
(-) of the midsagittal line; y: distance anterior (?) or posterior (-) to
vertical plane through the anterior commissure; z: distance above (?)
or below (-) the intercommissural (AC-PC) line. The cluster size
refers to the number (k) of voxels in a given cluster (voxel size, in
mm: 2 9 2 9 2); for statistical parametric mapping, SPM(Z) maps
were thresholded at t = 3.96 (p\ 0.00005, uncorrected)
Table 2 Monaural and binaural CI stimulation comparison
Area Voice versus non-voice
x y z Z t Cluster
size
Binaural versus monaural CI stimulation
STS, middle (BA42) 72 -14 12 3.24 3.28 4
Monaural CI stimulation No significant differences
Coordinates, size and Z score of areas activated by voice compared to
non-voice conditions
Approximate Brodmann numbers (BA) associated with anatomical
regions of the superior temporal sulcus (STS) are given in paren-
theses. Coordinates (in standard stereotaxic space [15]) of voxels
correspond to local maxima of Z value, above Z = 3.0 (p = 0.001)
within each focus of activation. x: distance (mm) to right (?) or left
(-) of the midsagittal line; y: distance anterior (?) or posterior (-) to
vertical plane through the anterior commissure; z: distance above (?)
or below (-) the intercommissural (AC-PC) line. The cluster size
refers to the number (k) of voxels in a given cluster (voxel size, in
mm: 2 9 2 9 2); for statistical parametric mapping, SPM(Z) maps
were thresholded at t = 3.13 (p = 0.001, uncorrected)
Table 3 Coordinates, size and Z score of areas activated by voice
and non-voice conditions compared to silent conditions in the CI
groups in the monaural and the binaural condition at p\ 0.001 cor-
rected for multiple comparison (p = 0.05)
Area Voice ? non-voice versus silence
x y z Z t Cluster
size
Binaural CI stimulation
STS, posterior (BA22) 62 -24 6 [10 16.76 5,455
STS anterior (BA21) 64 -6 -6 [10 14.50
STS posterior (BA 22) -60 -22 6 [10 11.48 3,280
STS posterior (BA42) -46 -24 6 [10 10.74
Monaural CI stimulation
STS, posterior (BA22) 66 -22 4 [10 18.12 4,811
STS, anterior (BA21) 62 -4 -4 [10 12.28
STS, posterior (BA22) -58 -30 8 [10 12.37 4,250
STS, middle (BA21) -48 -12 -4 [10 10.99
Approximate Brodmann numbers (BA) associated with anatomical
regions of the superior temporal sulcus (STS) are given in paren-
theses. Coordinates (in standard stereotaxic space [15]) of voxels
correspond to local maxima of Z value, above Z[ 10 (p\ 0.001)
within each focus of activation. x: distance (mm) to right (?) or left
(-) of the midsagittal line; y: distance anterior (?) or posterior (-) to
vertical plane through the anterior commissure; z: distance above (?)
or below (-) the intercommissural (AC-PC) line. The cluster size
refers to the number (k) of voxels in a given cluster (voxel size, in
mm: 2 9 2 9 2); for statistical parametric mapping, SPM(Z) maps
were thresholded at t = 4.65 (p\ 0.001, uncorrected) and then cor-
rected for multiple comparisons (p = 0.05)
STS superior temporal sulcus
Eur Arch Otorhinolaryngol
123
studies, comparable peaks (mean location: x, y, z) of acti-
vation [(48, 0, 48), (44, -48, 50) and (42, 28, 4)] were
found. This non-specific cortical network is associated with
sound discrimination ability. This neuro-functioning
observation supports the conclusion that with two CI,
patients have better sound discrimination abilities and they
have to pay less attention because of a lack of auditory
perception when compared to one CI.
We could speculate that while the involvement of
auditory areas reflected the processing of acoustic con-
tributors to voice sounds activity in frontal regions reflec-
ted the overall perceived attractiveness of sounds despite
their lack of linguistic content [30]. The results obtained
with two cochlear implants compared to one may suggest
the influence of hidden non-linguistic aspects of signals on
cerebral activity that needs further investigations.
It is currently important to determine the utility of
bilateral cochlear implants. The TVA PET activation
studies examined a group of patients to objectively dem-
onstrate the binaural advantages resulting from improve-
ments in the peripheral spectral representation of the
stimuli. The number of independent channels was an
important characteristic. We found an enhanced cortical
representation of the voice when using both CI, but the
activation of a right fronto-parietal attention network could
also facilitate spectral sound discrimination.
Acknowledgments We thank the Beaujon Hospital clinical team
for their assistance and the patients for their participation in this
study. This work was supported by the Institut National de la Sante et
de la Recherche Medicale, Inserm, France, and the Commissariat a
l’Energie Atomique, CEA, France. The authors declare that they have
no competing financial interests.
Conflict of interest No duality of interest to declare.
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Table 4 Monaural and binaural CI stimulation comparison
Area Voice ? non-voice versus silence
x y z Z t Cluster
size
Binaural versus monaural CI stimulation
Precentral Gyrus (BA4) 52 -12 58 4.24 4.32 32
Inferior parietal lobule
(BA40)
40 -44 42 4.19 4.27 30
Inferior frontal Gyrus
(BA47)
40 30 -18 4.17 4.25 13
Monaural versus binaural
CI stimulation
No significant differences
Coordinates, size and Z score of areas activated by voice and non-
voice condition compared to silent condition
Approximate Brodmann numbers (BA) associated with anatomical
regions of the STS are given in parentheses. Coordinates (in standard
stereotaxic space [15]) of voxels correspond to local maxima of
Z value, above Z = 4.16 (p = 0.0001) within each focus of activa-
tion. x: distance (mm) to right (?) or left (-) of the midsagittal line;
y: distance anterior (?) or posterior (-) to vertical plane through the
anterior commissure; z: distance above (?) or below (-) the inter-
commissural (AC-PC) line. The cluster size refers to the number
(k) of voxels in a given cluster (voxel size, in mm: 2 9 2 9 2); for
statistical parametric mapping, SPM(Z) maps were thresholded at
t = 3.78 (p = 0.0001, uncorrected)
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