Integrated fMRI EEG MEG

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Integrated fMRI EEG MEG Powered By Docstoc
					     Integrated
fMRI/MRI/EEG/MEG

   fMRI, BOLD & homodynamic response.
   EEG
   MEG
   A Multimodal approach.
       Functional magnetic resonance
              imaging (fMRI)
   During neuronal activation, metabolism is increased in the form of additional oxygen
    consumption by areas of greater neuronal activity, occurring with a delay of
    approximately 1-5 sec. after stimulation.

   The hemodynamic response to a stimulus results in site specific concentration
    differences in oxyhemoglobin and deoxyhemoglobin and changes in cerebral blood
    flow (CBF) . As hemoglobin courses through the capillaries of the brain, oxygen is
    consumed by means of metabolic processes.

   The resulting heterogeneity can be used as an endogenous contrast agent. Blood
    Oxygenation Level Dependent (BOLD) contrast.

   When hemoglobin is oxygenated it is diamagnetic (non-magnetic), but paramagnetic
    (magnetic) when deoxygenated. The paramagnetic species precesses at a different rate
    around the local magnetic field (B0).

   Because the deoxyhemoglobin does not precess at the same frequency as that of the
    local magnetic field (w=γBo) it will act as a t2* contrast agents.
             homodynamic response
   When a neuron, or a group of neurons is activated, cerebral blood flow (CBF) ,
    cerebral blood volume (CBV) and oxygen delivery is increased. The sudden flow of
    excess oxygenated hemoglobin into specified voxels, the ratio of oxygenated to
    deoxygenated hemoglobin is slightly increased compared to that at rest.

   As the diamagnetic ratio increases due to changes in CBF and CBV, T2* varies. Faster
    dephasing, decreasing T2*
         BOLD Temporal Response
   Sampling
        The basic sampling unit for temporal resolution is
         repetition time (TR)
        TR range from 500ms – 4000ms.
        The limitations of temporal resolution in fMRI is
         based on the vasculature of the brain and not
         physical limitations of the imaging methodologies.


   Limitations
        After a stimulus is presented the BOLD signal
         increases approximately 2 sec later. At around 5
         sec. later signals is peaked for a short-duration
         stimulus, or maintains a plateau for stimuli of a
         greater duration.
        After peak the signal undershoots to below
         baseline level, remaining so for an extended
         period of time.
        Therefore increasing TR won’t necessarily give us
         increased temporal resolution.
                        WAIT!

   What color and shape was that?
     This was presented to you for 50 ms.
     In this time the red oval stimulated a cascade of
      neural and cognitive processes. You were presented
      with a stimulus and you were able to become aware
      of it, eventually using descriptive language to convey
      what you saw.
                  Limitations cont.
   What if you were repeatedly presented with a stimulus?

   BOLD signal changes have been detected at ~34ms in the
    human visual system (Savoy et al., 1995). However as seen
    before the hemodynamic response, which BOLD is dependent
    is a relatively slow process, lasting up to several seconds for a
    single presentation.

   This proves to be a problem when studying cognition. If we
    assume the BOLD signal to be an accurate correlate of neuronal
    activity we are in trouble.
   In fact there does seem to be a
    refractory period where the
    hemodynamic response does not
    follow the principle of superposition.


                                                                                          -5       0       5       10       15       20         25     30



   Huettel and McCarthy showed that the
    BOLD signal response to a second                                          1.40                                                                               0
    stimulus in a pair separated by 1 sec                                                                                                                        6




                                             Signal Change over Baseline(%)
                                                                              1.20
                                                                                                                                                                 4
    was reduced by more then 40% and                                          1.00
                                                                                                                                                                 2
    delayed by approximately 1 sec. As the                                    0.80
                                                                                                                                                                 1
    interval between stimuli increase the                                     0.60


    amplitude and latency of the                                              0.40


    homodynamic response returns to                                           0.20


    normal values.                                                            0.00

                                                                              -0.20

                                                                              -0.40
                                                                                      0   1    2       3       4   5    6        7        8      9   10     11   12   13

                                                                                               Time since onset of second stimulus (sec)


                                                                                                                                              Huettel & McCarthy, 2000
Where does that leave us…?

 Using the hemodynamic response as an
 inference to neural activity carries a lot of
 weight, however directly measuring neuronal
 activity could give us better temporal resolution
 and a more accurate measure of signal
 processing.
What are we measuring?
     When an excitatory/inhibitory postsynaptic potential (PSP)
     is initiated extracellular electric fields are generated as ion
     channels open and allow for the influx of cations (Na+). A
     current sink ensues as the inward flow of Na+ through
     voltage-sensitive channels causes the cell to depolarize.

      PSP’s travel down the axon, conducting impulses at unmyelinated portions (Nodes of Ranvier) of
       the axon. At unexcited portions of the neuronal membrane there is an outward flow of K+,
       establishing a current source.




                                                                                                  http://neuroimage.usc.edu/ResearchMEGEEGModeling.html
      The extracellular current flow, from the influx at the sink, and the efflux at the source is called the
       volume current. The extracellular electric field produced amid the minute distance between these
       two points is referred to as the current dipole. The signal is radially directed outward, the strength
       of which decays with the inverse square of the distance.
      By continuously recording the fluctuating field potentials, a result of the summation of PSP’s we
       are able to more directly measure neuronal activity.
            Waveform Activity Types
   Delta (≤ 4 Hz). Usually associated
    with deep sleep, coma and brain injury.

   Theta (4-8 Hz). States of on-line
    hippocampus related tasks; working
    memory, quiet focus.

   Alpha (8-12 Hz). Relaxed, alert state of
    consciousness.

   Beta (> 12 Hz). Active, busy or
    anxious thinking and active
    concentration.

   Gamma (26-100 Hz). Higher mental
    activity; perception, problem solving.
    Electroencephalography (EEG)
      Through the use of electrodes placed directly on the scalp
       (2,3,8,19 or even up to 100) graded post synaptic potentials
       (PSP) of the cell body, large dendrites and vertically oriented
       pyramidal cells in layers III-V are measurable. (Lopes del Silva,
       1991)




    http://www.ucl.ac.uk/HCS/research/

                                                          http://williamcalvin.com/bk9/img/3d-colmn.jpg
            EEG electrode placement
   Each electrode is connected to a differential amplifier, used to amplify
    voltages changes over time at each electrode.
   The electrode-amplifier relationship is arranged in one of three montages.




                                                                                                           http://www.ebme.co.uk/arts/eegintro/eeg2.htm
   1) Common reference derivation:
        Each amplifier records the difference between a scalp electrode and a reference electrode. A
         single reference electrode is placed somewhere along the midline or attached to both earlobe
         electrodes.
   2) Average reference derivation:
        Activity from all the electrodes are recorded and averaged before being passed through a
         high value resistor. The resulting signal is then used as a reference point for each amplifier.
   3) Bipolar derivation:
        Electrodes are connected in a straight line from the front to the back of the head or
         transversely across the head. An amplifier sequentially measures the difference between two
         electrodes.
    Magnetoencephalography (MEG)
   The conductivity of the skull is relatively low,
    (1/80 to 1/100) to that of the brains
    conductivity (Toga. TW, et al., 2002).

   The electrical field is best detected from
    electrodes placed directly on the scalps
    surface. The magnetic field can be measured
    outside of the head because the signal is not
    impeded to the same degree as the electrical
    field.

   The goal is to record EMF’s at varying
    locations outside the head and to then
    calculate the most probable source currents
    within the brain.
                                                       http://www.ion.ucl.ac.uk/images/IE05MEGscanner.jpg
                       Data Acquisition
   The magnetic signals produced by evoked
    magnetic fields (similar to ERP’s) are weak,
    on the order of 100 femtoTesla (an fT is 10-15
    Tesla).

   To detect these very weak fields
    Superconducting Quantum Interference
    Devices (SQUID’s) are used. Current
    neurmagnetometers contain more then 300          http://biomagnetism.kriss.re.kr/English/meg_application-e.htm

    SQUID’s, operating in liquid helium at 4 K
    (-269 C).

   The SQUID is a magnetic flux-to-voltage or
    current transducer.
                            Source Analysis
   Forward modeling.
        Find voltages at electrodes given source neuronal activity
        The calculation of scalp potentials (EEG) and magnetic
         fields near the scalp (MEG) given neuronal currents in the
         brain.
        In estimating the neural source of electromagnetic fields
         we employ a forward model that maps a source of known
         locations, strength and orientation to an array of sensors.
         (head model)

                                                                              http://neuroimage.usc.edu/ResearchMEGEEGPhWarping.html




   The Inverse problem.
        Find a source of neuronal activity given voltages at electrodes.
        Locating the source of field potentials is difficult to determine with certainty. The decay
         of electric field strength has varying affects on nearby electrodes, however dipoles will
         contribute similarly to more distantly placed electrodes.
        A priori source modeling is required.
                                     MEG/MRI
   MEG’s temporal resolution can detect changes occurring in <1ms, while
    spatial resolution ranges from a few millimeters up to a couple of centimeters.
         MEG recordings in a normal control                     MEG recordings in Alzheimers Disease




    Fig. 1. A, MEG recording (left hemisphere channels) with a coronal magnetic resonance image
    imposed on the waveforms shows normal baseline activity in a control subject. B, Similar MEG
    recording (left hemisphere channels) with a coronal magnetic resonance image imposed on the
    waveforms shows pronounced slow wave activity (5–6 Hz) in a patient with Alzheimer’s disease. White
    dots indicate dipole localization of increased slow wave activity in the left temporal lobe. The dipole
    localization is consistent with the neuronal destruction patterns associated with Alzheimer’s disease.
    (http://www.scripps.edu/news/sr/sr2005/mind05polich.html)
    Combination fMRI/EEG/MEG
   The spatiotemporal resolution differs depending on your imaging technique. MEEG
    both have good temporal resolution in the order of sub-millisecond, however there
    spatial resolution is poor due to physiological impedance and complex source
    modeling.

   fMRI has good spatial resolution (2-3 mm), but poor temporal resolution due to
    physiological limitations of the homodynamic response, not physical limitations of
    fMRI.

   A multimodal analysis of neuronal activity may provide us with superior
    spatiotemporal resolution. Providing a more direct and causal interpretation of
    neurocognitive systems.
                     EEG/fMRI methods

   Trigger fMRI
        Recorded EEG activity of interest triggers MRI acquisition. Due to delayed hemodynamic
         response (2-4 sec) the EEG can be measured soon after the end of the previous MRI block.
         This way there is limited distortion from the RF pulses or gradient fields from the MRI
         acquisition block (Goldman et al., 2000).
        The attenuation of EEG electrodes is limited, thereby limiting our window of measurement.
        Leads are typically constructed of carbon fiber (non-magnetic).


   Interleaved EEG/fMRI
        EEG is continuously recorded while fMRI data is acquired in blocks
        The EEG is continues.
        fMRI data is acquired 1 sec after the delay.




                                                                       http://scsnl.stanford.edu/Menon_Combined%20EEG_05.pdf
                                     Cont.
   Simultaneous EEG/fMRI
       Data is obtained simultaneously.
       Artifacts due to fMRI acquisition is unavoidable. Artifact removing methods are
        complex and only result in an estimated EEG signal.
       Good for researching neuronal activity of cognitively varying tasks.
                                                                    Artifacts
          EEG with no artifact




                                       Artifact correction

				
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posted:10/28/2011
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