Laura Dubreuil Vall edited untitled.html  about 8 years ago

Commit id: e285dbbdbc76084ab420b4384bf6c0fc6f8b4f1a

deletions | additions      

       

reliable MEP in the contralateral ECR amplitude of >50 µV in at least 50% of  consecutive trials.[DE9] 

 

EEG data processing/statistical analysis

Resting quantitative EEG and corticospinal  excitability (transcranial magnetic stimulation; MEP) were recorded before (PRE)  and at the end (POST) of each intervention. Quantitative EEG measures included: mean power, mean frequency and mean coherence. The three measures were reported normalized  as the percentage change between PRE and POST stimulation, for each frequency band and electrode. The frequency bands were defined as: Theta= [4 8] Hz, Alpha-1=[8 10] Hz, Alpha-2=[10 12] Hz, SMR=[12 16] Hz, Beta-1=[16 25] Hz, Beta-2=[25 35] Hz, Gamma=[35 40] Hz. (ref???) GIULIO/LAURA

The Hz.

The  mean power is defined as the average power in each uV2 in a given  frequency band and for each electrode.The band. The  mean frequency is defined as the average  frequency in which there is the highest power in the a  given band, weighting each  frequency band. value by their corresponding power at that frequency.  The mean coherence of a given electrode is defined as the average coherence of this electrode with all the other ones.--> Giulio ones (i.e., the similarity of that signal with all the other electrodes).--> Giulio  to revise

The revise - DONE

The  EEG data were referenced to the average of all 8 electrodes. An automated quality check of  the data was then carried out using 8 sec epochs. Epochs have been rejected if  they do not meet quality criteria (too high mean power at full band or line 

MEP amplitude (peak-to-peak; ECR muscle) was measured following  single-pulse TMS (10/12) set at 120% [DE12] of the RMT over the C3[DE13] . Raw and normalized values were used for  analysis[DE14] . Results are presented as mean ± standard deviation (SD), and standard  error of the mean (SEM)[DE15] .

The (SEM)[DE15] .

After normalizing the EEG features as the percentage change between PRE and POST stimulation, statistical comparison between Sham and Active (1mA) stimulation has been done. The  p value in the T tests has been calculated with a Wilcoxon one-tail T test with the assumption of paired samples. Changes are considered statistically significant when p =< 0.05. Since all the features are measured in 8  channels at the same time, the Bonferroni correction has been applied to the significance of all features. [DE17] --> Bonferroni correction not applied, discuss with Giulio

 

PLEASE 0.05.

 

PLEASE  ADD THE STUDY DATA ANALYSIS – GIULIO / LAURA --> described Described  above

 

Results

 

Effects of tDCS on EEG

Normalized pre-post EEG power, frequency and coherence for those subjects who received 1mA tDCS compared to those who received sham stimulation shows: a) significant increase of the mean power in the 1mA group in the Gamma frequency  band under C3 (p=0.0035), the anodal stimulating electrode; b) a significant increment in the active group of mean frequency around the anode (stimulating)  electrode (C3, F3) (p=0.0047) with a decreased mean frequency in the Alpha band near the  return electrode (P4) (p=0.035); and c) significantly  increased mean coherence in the active group in the fastest frequency bands Beta2 under Cz and C4 (p=0.007), Gamma band under Cz electrode (p=0.0023), C3 electrode (p=0.0006) and C4 electrode (p=0.0006), and SMR band under C3 electrode (p=0.05).

 

LAURA – ADD THE TYPE OF TEST USED FOR THE RESULTS AND THE P VALUES  OBTAINED --> Described  above

 

Effects  above

 

Effects  of tDCS on Corticospinal excitability

Baseline values for resting MEP amplitude were similar between interventions (average: 0.37±0.05 mV; mean±SEM).  No significant changes were observed for 1 mA a-tDCS or sham. The stimulation  intensities used to obtain the RMT were not significantly different between 1 

population.

2. The effect of the TDCS in EEG  is location specific and band specific.

3. The fastest bands are more  affected. Augmented power and frequency of fast bands (Gamma and B2) under the  anode electrode - there is more fast activity under the anodal electrode.  Why Why  is this?

3.1. this?

3.1.  Anodal stimulation leads to increased spontaneous neuronal firing, increase motor  cortex excitability. So we would expect more fast activity and higher  amplitudes under the anode electrode.

3.2. Brain 

AND SENSORY MOTOR CORTEX?? – JANA

 

3.3. Anodal  tDCS makes C3 to be more related to the rest of the head, by increasing the  connectivity of the SMR under the stimulating electrode.

INTERPRETANTION OF THIS POINT TO GIULIO/LAURA,  ANYTHING PUBLISHED BEFORE?

 

3.4. BEFORE?

Here you have a reference using EEG coherence: 
Rafael Polanıia, Michael A. Nitsche, and Walter Paulus. "Modulating Functional Connectivity Patterns and  Topological Functional Organization of the Human  Brain with Transcranial Direct Current  Stimulation". Human Brain Mapping (2010).

 

3.4.  This is an excitability independent change (no TMS change associated). Can EEG pick  up changes in the brain than TMS cannot?

                                                      LABAR?

 

Conclusion

 

These findings show that t-DCS is  capable of inducing modulation of ongoing oscillatory brain rhythms captured by