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EEG & MEG: spatial localization
Lecture: PSY394 Foundations of Neuroimaging
Logan Trujillo, Ph.D.Department of Psychology
UT Austin
Non-Invasive Brain Imaging
–
Good spatial resolution, poor temporalresolution
–
Good temporal resolution, poor spatial resolution
Magnetic Resonance
Imaging (MRI)
FunctionalMRI
Electro-encephalography
(EEG)
Magneto-encephalography
(MEG)
&
&
Figure adapted from Cohen and Bookheimer
(1994)
Small neural source at
cortex
Bioelectric signals are spatially blurred as they pass through the csf, brain, skull, & scalp.
Large spatial blurring at scalp
To understand the reason for the blurring,need to understand biophysics of EEG/MEG
9.67
-9.67
0 μV
EEG measures the electric potential differences across scalp arising from current flow within the head & brain.
V = IR
V = electric potential (“voltage”) analogous towater pressure
I = electric current (analogous to rate of water flow)
R = resistance to flow of electricity (size of pipes)
σ
~ 1/R = conductance of flow of electricity
What are EEG and MEG Signals?
VFigure from Halliday, Resnick, & Krane, 1992)
MEG measures the magnetic fields produced by current flow within the head & brain.
An electric current (flow of electrons) produces a magnetic field around it.
Images from Wikipedia
EEG and MEG signals arise primarily from synaptic activity
Figures from Speckman
and Elger
(1999)
EEG/MEG signals represent the summed activity of large populations of synchronously firing neurons
Figure from Speckmannand Elger(1999)
EEG/MEG sources arewell approximated ascurrent dipoles/dipole layers
Neural dipoles => electromagnetic field changes throughout the head
=> current flow through head and scalp.
-
+
Figure adaptedfrom Spehlman, 1981
Image Adapted from Wikipedia
FigurefromNunez (1995)
2) EEG ~ Gyrus
sourcesMEG ~ Sulci
sources
Figures from Lorente
de No. (1947) & Hubbard et al. (1969).
Dipolar nature of neural sourcesImplies:
1)primarily cortical EEG & MEG signals observable at scalp
EEG signal spatial distortion arises from differencesin head tissue electrical resistance (R) /conductance (σ).
Brain
σ1
CSF
σ2
Skull
σ3
Scalp
σ4
R1 R2 R3R4
Source Point(R0
,θ0
)
Field Point(R4
,θ)
High R (low sigma):=> More collisions of electrons
with tissue molecules & thusgreater deviation from trajectories determined by electric fields of neural sources.
Skull & scalp have lower σ
(high R) than brain and CSF => most spatial blurring of electric current due to skull
& scalp.
Blurring of scalp potentials is even greater.
MEG signals are less affected by conductance/resistance (signal falls off rapidly from source ~ 1/r2
& magnetic fields of impressed currents are very small), & thus have better spatial resolution than EEG.
Figure from Halliday, Resnick, & Krane, 1992)
Outer Scalp
RInner Scalp
Scalp Level Spatial Enhancement of EEG SignalsIt is possible to improve the resolution of scalp EEG
signals by transforming the signals into measures of electric current. (Nunez & Srinivasan, 2005)
R = radius of head
Laplacian
Current Source Density (CSD) Transform
02
2
2
2
2
22 =
∇=
∂Φ∂
+∂Φ∂
+∂Φ∂
=Φ∇σJ
zyxLaplace’s
Eq.
z
x
y
Jz-
=> no net current through spherical scalp “shell”.0=
∇σJ
J ~ I/m2
Jz+
Jx-
Jx+
Jy-
Jy+
ScalpLaplacian ⎟⎟
⎠
⎞⎜⎜⎝
⎛∂Φ∂
+∂Φ∂
−=∂Φ∂
=yxz
yxL 2
2
2
2
2
2
),(
z
x
y
ΔΦx
ΔΦ y
ΔΦz
radial electric currentthrough scalp
~
02
2
2
2
2
2
=∂Φ∂
+∂Φ∂
+∂Φ∂
zyx
ModelSource
Distribution
IsopotentialMap
LaplacianMap
Law, Nunez, and Wijesinghe, R.S. (1993)
EEG/MEG Source Reconstruction-
estimating cortical source distribution of scalp
recorded electromagnetic signals
Source reconstruction principles are the same for EEG & MEG; only differ in the mathematical details.
Usually performed on ERPs
in order to reduce effects of noise on source solutions.
The Inverse Problem:
Any measured scalp electromagnetic distribution may be described by an infinite number of possible source distributions
Must use functional–anatomical criteria to constrain the number of possible source distributions
?=
1) 2)
or 3)
Two steps to EEG/MEG Source Reconstruction:
1)Create a model of brain, skull, and scalp.
2)Use this model to solve for “best fitting” source distributions, where “best fit” determined by
i) minimization of error btw model prediction & actual measurements.
ii) Neuroanatomical
constraints (e.g. expectedregions of activation based on nature of stimulus & task).
Head (Volume Conductor) ModelsTypical models in EEG & MEG: spherical, ellipsoidal
Brain
σ1
CSF
σ2
Skull
σ3
Scalp
σ4
R1 R2 R3R4
Source Point(R0
,θ0
)
Field Point(R4
,θ)
Structural MRI-based
models
MRI informs creation of head model
Individual subject:Volumetric boundary element method
=>
Group Analyses:Use MNI or Tailarach
brain 3D templates
Requires spatial co-registration of EEG-fMRI coordinate systems
LORETA-KEY figures
Electrode coordinates may be default 10-20 International System
Electrode coordinates can be scanned in from actual scalp locations via fMRI
scanner or
through use of 3D scanning technology
Dipole modeling
(Scherg, 1989)
Dipole position and moment is what gives best “fit” to scalp EEG/ERP data.
Assume a given brain response arises from brainelectrical activity equivalent to a few EM dipoles.
Dipole Current Source
P100 (rv
= 1.6) N170(rv
= 2.17)
-100 -50 0 50 100 150 200 Time (ms)
ERPs
may reflect activation of more than one brain region.
UP
Independent Components Analysis (ICA)decomposes signals into maximally temporally independent sub-signals.
P1 & N1 responses composed of early/late ICA components with different cortical locations.
Deblurring
Method (Le and Gevin, 1993)
02 ≠∇
=Φ∇σJ Poisson’s Eq.
=> net current throughvolume defined by scalp and cortical surfaces
Cortical surface expresses current distribution from active neural sources
Current flowsthrough scalpsurface, but does not leave it
0≠∇σJ
Cortex
Lead Field Method –
can estimate current sources in 3D space
Forward solutionΦ
= KJ is scalp potential
K represents the “lead field”, i.e. the biophysical volumetric model of scalp, skull, & brain.
J is vector of current elements, with 1-3 elements (depending on the model) per “voxel”.
Inverse Solution is thenJ = TΦ
where T = f(K)
Inverse Problem => must choose T that gives the “best” solution.
Several different methods to choose T.
Minimum Norm
Solution (Hämäläinen
and Ilmoniemi, 1994)
Notice small degree of localization error. Could be due to poor head model and/or limitations of Min Norm algorithm.
1
-1
0 A/m2
Limitations of Minimum Norm:Can sometimes exhibit large spatial error when localizing maxima of activations, especially with deep dipole sources.
Best source solutions obtained when recording EEG & MEG simultaneously & when temporal information taken into account (Dale & Sereno, 1993)
RadialDipole
EEG& MEG
EEGonly
MEGonly
Dale & Sereno(1993)
TangentialDipole
EEG& MEG
EEGonly
MEGonly
Dale & Sereno(1993)
EEG& MEG
Dale & Sereno(1993)
Deep Radial Dipole
EEG & MEG withInformation from other timepoints
taken into account.
Low Resolution Electromagnetic Tomography (LORETA) (Pascual-Marqui
et al., 1994)
LORETA solutions have the lowest activity maxima localization error of “lead field” methods (Pascual-Marqui,
1994), but solutions are more spread out spatially, hence the term “Low Resolution”.
0 A/m2
1
1) Only as good as head model2) Strong effect of data variance on the reconstruction
algorithms3) Inverse problem restrictions4) Intrinsic neuroanatomical
limitations of EEG (gyri)
& MEG (sulci). Best results when using EEG & MEG simultaneously (Dale & Sereno, 1993)
In the end: ~ same order of temporal resolutionOne -
two orders of magnitude better spatial
resolution then straight scalp topography
METHODLOGICAL LIMITATIONS
This problem may be reduced by new technology allowing simultaneously recording of EEG & fMRI
with task
paradigms involving irreversible cognitive/perceptual changes.
fMRI
& EEG/MEG Source LocalizationMRI technology can also play a role besides head model
creation.
fMRI
activations can be used to constrain dipole solutions, reduce source solution space created by inverse problem, & provide convergent evidence for a particular source solution.
Caveat: This role is limited in non-simultaneous combination of EEG & fMRI
with task paradigms
involving irreversible cognitive/perceptual changes.
Simultaneous method: fMRI
signal is modeled and subtracted from raw EEG signal
EX: Neuroscan
MAGLINK systemUncorrected/Corrected 64 Channel Spontaneous EEG
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resonance imaging. Trends Neurolog. Sci., 17, 268-77.
Dale, A.M. and M.I. Sereno
(1993) Improved localization of cortical activity by combining EEG and MEG with MRI cortical surface reconstruction: A linear approach. J. Cogn. Neurosci. 5, 162-176
Halliday, D., Resnick, R., and Krane, K.S. (1992). Physics, 4th
Edition. New York: John Wiley & Sons.
Hamalainen, M.S. and Ilmoniemi, R.J. (1994). Interpreting magnetic fields of the brain: minimum norm estimates. Med. Biol. Eng. Comp. 32, 35-42.
Hubbard, J.I., Llinas, R., and Quastel, D.M.J. (1969). Electrophysiological Analysis of Synaptic Transmission. London: Edward Arnold, Ltd.
Law, S.K., Nunez, P.L., and Wijesinghe, R.S. (1993). High resolution EEG using spline
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Lorete
do No., R. (1947). Action potential of the motoneurons
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RD. (1999) Review of methods for solving the EEG inverse problem. International Journal of Bioelectromagnetism 1, 75-86.
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