http://journal.frontiersin.org/article/10.3389/fneur.2016.00035/full?
- 1Laboratory of Neurophysiology and Magnetoencephalography, Department of Neurophysiology, Institute of Care and Research, S.Camillo Hospital Foundation, Venice, Italy
- 2Institute of Medical Psychology and Behavioral Neurobiology, University of Tübingen, Tübingen, Germany
- 3Section of Rehabilitation, Department of Neuroscience, University of Padova, Padova, Italy
Introduction
The introduction in the early 1980s of
magnetoencephalography (MEG) recording devices boosted its clinical
application: multichannel MEG provided a superior spatial resolution
compared to electroencephalography (EEG) and the possibility of
detecting dipoles tangential to the cortical surface were its main
advantages. MEG was initially deployed in the presurgical evaluation of
epileptic foci, given both the reliability in localizing superficial
cortical epileptic foci (1) and the precise indications for placement of intracranial electrodes (2).
It became subsequently obvious that processing of natural language is
more accessible with MEG than with EEG or functional magnetic resonance
imaging (fMRI) because the magnetic field changes can be more precisely
free from noise and artifacts (3).
The high variability in the localization of frontal and parietal
language processing sources creates considerable difficulties for the
neurosurgeon to discriminate between eloquent areas involved in speech
and language and “silent” brain tissue, so that the removal of tumors
and other malformations of the brain and its vasculatum becomes a
challenging operation. The combination of MEG and structural MRI
provides the optimal solution to this problem because of the small
fiducials positioning and localization errors (i.e., approximately 2 mm)
assuring a reliable coregistration of functional and structural data (4).
With the installation of the new generation MEG
having more than 250 sensors able to provide even further improved
spatial resolution and accessibility of source localization algorithms
(see below) to deeper brain structures and cerebellum, MEG technology
has been successfully introduced to resolve the more complex problems of
recovery and brain reorganization after stroke and other types of
brain injury. Particularly, recovery prediction and assessment has
become the focus of interest in clinical use of MEG in rehabilitation.
Magnetoencephalography has maintained part of its
advantages even after the introduction of high-density EEG, consisting
of a spatial sampling up to more than 250 electrodes. Although signals
detected by the two recording techniques appear to be generated by
different limbs of the same circuit, recent studies (5–8)
have suggested that they have at least partially distinct generators.
Indeed, MEG is particularly sensitive to activity originating in the
cortex directly underlying sensors and is insensitive to radial dipoles,
whereas EEG seems to reflect volume conducted activity and is sensitive
to radial and tangential dipoles (9). Thus, the two techniques should be considered mutually complementary rather than mutually exclusive.
Finally, the rapid development of non-invasive
Brain–Machine Interface Research [BMI or also termed brain–computer
interfaces (BCI)] during the last 10–15 years (10–12)
has launched a completely new and challenging field of application to
MEG technologies: on-line recordings from selected MEG–sensor
combination has been used to drive exoskeletons and computer switches
for therapeutic purposes (see below). With BMI research, MEG has been
transformed from a passive recording and documentation/diagnostic device
into an active treatment and rehabilitation instrument (13).
The success of BMIs has reactivated the tradition of
neurofeedback research, popular in the EEG community from the 60s–80s of
the last century (14).
MEG allows simultaneous observation and self-control of extremely
specific localized dynamic sources of neuromagnetic activity together
with widespread, more general, brain activity changes. In addition, the
availability of fast computing algorithms for providing feedback of
dynamic connectivity changes has introduced a new area of interest for
directly manipulating changes and the related functional connectivities
of oscillatory brain activity. When such algorithms allow modeling of
oscillatory sources’ directionality, the effective connectivity can be
estimated by describing how anatomically connected areas interact with
each other (15).
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