Over the last few years much research has been devoted to investigating the synchronization between cortical motor and muscular activity as measured by EEG/MEG-EMG coherence. The main focus so far has been on corticomuscular coherence (CMC) during static force condition, for which coherence in beta-range has been described. In contrast, we showed in a recent study  that dynamic force condition is accompanied by gamma-range CMC. The modulation of the CMC by various dynamic force amplitudes, however, remained uninvestigated. The present study addresses this question. We examined eight healthy human subjects. EEG and surface EMG were recorded simultaneously. The visuomotor task consisted in isometric compensation for 3 forces (static, small and large dynamic) generated by a manipulandum. The CMC, the cortical EEG spectral power (SP), the EMG SP and the errors in motor performance (as the difference between target and exerted force) were analyzed.
For the static force condition we found the well-documented, significant beta-range CMC (15–30 Hz) over the contralateral sensorimotor cortex. Gamma-band CMC (30–45 Hz) occurred in both small and large dynamic force conditions without any significant difference between both conditions. Although in some subjects beta-range CMC was observed during both dynamic force conditions no significant difference between conditions could be detected. With respect to the motor performance, the lowest errors were obtained in the static force condition and the highest ones in the dynamic condition with large amplitude. However, when we normalized the magnitude of the errors to the amplitude of the applied force (relative errors) no significant difference between both dynamic conditions was observed.
These findings confirm that during dynamic force output the corticomuscular network oscillates at gamma frequencies. Moreover, we show that amplitude modulation of dynamic force has no effect on the gamma CMC in the low force range investigated. We suggest that gamma CMC is rather associated with the internal state of the sensorimotor system as supported by the unchanged relative error between both dynamic conditions.
Synchronization between neurons in motor cortex and motor units has been extensively investigated since the early 90s. A major break through was a study on monkeys showing that cortical and motor oscillations were synchronized with the motor units of the contralateral muscles . Conway et al. showed for first time this mechanism in humans: Using one MEG channel they recorded the cortical motor activity and the surface electromyogram (EMG) of a contralateral active muscle during maintained voluntary contraction. Applying coherence analysis, these authors demonstrated coherence between cortical rhythms and rectified EMG confined to the beta (15–30 Hz) frequency range. They interpreted this beta-range synchronization as evidence for the involvement of the cortical motor neurons in the motor units' synchronization.
For the last ten years, research on the beta-range CMC has shown that it is task dependent [4,5], that it reflects attention and precision [6,7], compliance of the gripped objects [8,9], displacement , magnitude of force  and learning processes . A major step towards understanding the functional significance of the beta-range CMC during steady-state force was provided only recently: Kristeva, Patino & Omlor  demonstrated that the CMC correlates with motor performance, namely that increased beta-range CMC improves motor performance. Therefore, the authors suggested that the beta-range CMC reflects effective corticospinal interaction.
Although the studies mentioned above have extended our knowledge about motor control, the investigation of the CMC was restricted mainly to steady-state motor output (isometric contraction and precision grip). This contrasts with the existence of many dynamic processes in daily life, which generally require constant adaptation of the motor outputs. Moreover, it has been suggested that static and dynamic force can be controlled by fundamentally different processes within the central nervous system . These arguments call for the investigation of CMC under dynamic condition. In a recent study of us the EEG-EMG coherence during a steady-state motor output was compared to a periodically modulated dynamic isometric force output . In the static condition, significant coherence was confined to the beta-range. In the dynamic condition, the most distinct coherence occurred in the gamma-range and the significant beta-range coherence was strikingly reduced. We concluded that during dynamic force the corticospinal oscillation mode shifts towards higher (principally gamma) frequencies for the rapid integration of the visual, somatosensory and cognitive information required to produce the appropriate motor command.
The aim of the present study was to investigate the modulation of the CMC by the amplitude of the periodically modulated dynamic force. Two dynamic force amplitudes were selected for this purpose. The periodically modulated target force, which had to be compensated isometrically by the subject, had the same frequency but different amplitudes. Static force was used as the control condition. Additionally, we investigated cortical spectral power (SP) and the motor performance during all three conditions.
We confirmed our previous result  that CMC is predominantly confined to gamma-range during dynamic force condition. Moreover, we show that the gamma-range CMC during dynamic force output is amplitude independent, i.e. that gamma-range CMC is not modulated by changes in target force amplitude, at least for the range of amplitude modulation and level of force investigated.
All subjects performed the task according to the instructions. None of the subjects reported fatigue during the experimental session.
The lowest absolute performance error was observed in the static force condition (SF) and the highest one in the large dynamic (lD) force condition. The absolute performance differences between the three conditions were statistically significant (p = 0.002, Friedman test, n = 8 throughout the whole manuscript). In detail, the pair-wise comparisons yielded statistical significance between SF than small dynamic (sD) condition (p = 0.015, Wilcoxon test; n = 8 throughout the whole manuscript), between SF and lD condition (p = 0.007, Wilcoxon test), and between sD and lD condition (p = 0.0234, Wilcoxon test). The mean absolute performance error across all 8 subjects is shown in Fig. 1 (upper panel).
Figure 1. Performance Analysis. Motor performance error, upper panel absolute error, lower panel relative error (the error after normalization to the amplitude of the force) for 8 subjects (Grand average). The static force (SF) condition is marked as grey line, the small dynamic (sD) condition as dotted black line and large dynamic (lD) condition as thick black line.
However, no significant difference between both dynamic conditions was observed for the relative performance errors (p = 0.742, Wilcoxon test; Fig. 1, lower panel).
Corticomuscular coherence (CMC)
Significant broad-band coherence during SF and during both dynamic conditions was observed. For subjects 1 to 6, coherence was most pronounced over the left motor cortex contralateral to the active right index finger (EEG channels C3, C1, FC3 and FC1) with the flexor digitorum superficialis and, for subjects 7 and 8, with the first dorsal interosseus. CMC during SF output was observed as expected in the beta-band. During both dynamic conditions, CMC was principally in the gamma band, which confirms our previous findings . Inter-individual differences were however found. Figure 2 displays original curves of CMC in the three conditions (SF, sD and lD), as well as the grand average for all eight subjects.
Figure 2. Frequency-coherence plots. Frequency-coherence plots for EEG-EMG coherence during static force (SF) condition (left panel) during small dynamic (sD) condition (middle panel) and large dynamic (lD) condition (right panel) for single subjects and as grand average. The beta-range (15–30 Hz) is marked in light grey, the gamma-range (30–45 Hz) in dark grey. Note that during the SF condition the most prominent activity occurs in the beta-range. During both dynamic conditions previous beta-range coherence is decreased and the general activity is shifted towards high frequencies, principally in gamma-range. During sD condition remains significant beta-range CMC, which is absent during lD condition.
Subject 2, representative of the majority of the subjects (6 out of the 8), showed as expected beta-range CMC with a maximum peak at 21.5 Hz in the SF condition. In the sD force condition, CMC was observed predominantly in the gamma-range (41 Hz), with some significant beta-range CMC which was however lower than in the SF condition. In the lD condition, only a prominent gamma-range CMC peak at 35.2 Hz was observed.
Two other subjects (S3 and S5) displayed quite different patterns. Subject 3 had CMC at higher beta frequencies during sD as compared to SF and, in the lD condition, CMC predominantly in the gamma-range without any beta. It is important to note that for this subject during the SF output the predominant peak occurred at 13.7 Hz which was reduced in sD condition. The second subject with a different CMC pattern (S5) showed during SF condition CMC in high beta and low gamma band. During both, sD and lD conditions, the main CMC occurred at higher frequencies in the gamma band.
When the results were pooled for all subjects (lowest panel in Fig. 2) the following picture occurred: In the SF condition a significant broad-band beta CMC was observed with maximum amplitude ranging from 0.012 to 0.051 across subjects. In the sD condition, the most prominent CMC occurred in the gamma-range with two predominant peaks at 35.2 and 43 Hz. This gamma-band CMC yielded amplitude values from 0.018 to 0.035. One significant peak also remained in beta-range at 25.4 Hz but was smaller than in the SF condition (p = 0.0156, Wilcoxon test). In the lD condition, only one significant CMC peak in the gamma-band (35.2 Hz) was obtained with an amplitude in the range from 0.013 to 0.042. The beta-range CMC decreased significantly compared to that in the SF condition (p = 0.0078, Wilcoxon test).
In general terms, we observed a shift of the CMC from lower to higher frequencies (principally from beta to gamma) when comparing static and dynamic conditions (p = 0.0098, Friedman test) which is in accordance with our previous study . This shift is best visualized on the display of the individual CMC centres of gravity (Fig. 3).
Figure 3. Center of gravity for frequency. (a) Individual frequency values of maximum coherence (centre of gravity) calculated for the whole range study (15–45 Hz). Each subject is represented by a number. Filled circles and square: individual values and their mean for the SF condition. Small empty circles and square: values and mean for the sD condition. Large empty circles and square: values and mean for the lD condition. The beta-range (15–45 Hz) is marked in light grey, the gamma-range (30–45 Hz) in dark grey. Note that the frequency values for the both dynamic conditions are systematically higher than for the static condition, but there are no differences of the frequency values between both dynamic conditions.
In 6 subjects, the centre of gravity was shifted from beta- to gamma-range, between the SF and sD condition, the extent of this shift varying between 7 and 23 Hz. In subject S3 we did not obtain any shift over the frequency range 15–45 Hz and subject 5 showed the shift within gamma-range. The CMC frequency shift between SF and lD force occurred in all subjects and ranged from 7 to 24 Hz. The difference in the dominant frequencies of the CMC among the three conditions was statistically significant (p = 0.0098, Friedman test). The shifts to higher frequencies between SF and sD as well as between SF and lD were highly significant (p = 0.0156 and p = 0.0078 respectively, Wilcoxon test). In contrast, we did not find any statistically significant difference in CMC frequency between both dynamic force conditions (p = 0.9453, Wilcoxon test).
Cortical motor spectral power (SP)
We calculated EEG spectral power for the channel of maximal coherence. Fig. 4 shows the EEG spectral power for all subjects investigated and the grand average. We observed a beta-range SP decrease in six out of the eight subjects investigated (S2, 3, 4, 5, 6, 7) in sD condition and in five subjects (S2, 3, 4, 5, 7) in lD condition, as compared to SF. However, the beta- and gamma-range SP differences among the three conditions were not statistically significant.
Figure 4. EEG spectral power plots. EEG spectral power during SF output (left panel), during sD force output (middle panel) and during lD force output (right panel) for single subjects and as grand average. The beta-range (15–30 Hz) is marked in light grey. The gamma-range (30–45 Hz) is marked in dark grey.
EMG spectral power
Fig. 5 shows the EMG spectral power data. We observed statistically significant differences among all three conditions in both frequency ranges, beta (p = 0.0208 Friedman test) and gamma (p = 0.0111, Friedman test). The highest EMG SP was observed during lD condition and the lowest EMG SP during SF (Fig. 5). The paired Wilcoxon test revealed significant differences for both frequency ranges in the comparisons between SF and sD (beta p = 0.0391, gamma p = 0.0156), between SF and lD (beta p = 0.0156, gamma p = 0.0156), and between sD and lD (beta p = 0.0391, gamma p = 0.0234).
Figure 5. EMG spectral power plots. EMG spectral power during SF output (left panel), during sD force output (middle panel) and during lD force output (right panel) for single subjects and as grand average. The beta-range (15–30 Hz) is marked in light grey. The gamma-range (30–45 Hz) is marked in dark grey. Note the highest EMG SP during lD condition.
The main goal of the present study was to determine whether the amplitude modulation of dynamic force output has an influence on the CMC. Our results show that the frequency range of synchronization and the amount of CMC during the two dynamic conditions with different amplitudes are similar. Consistent with our previous work  we found a CMC shift from lower frequency (beta) during static force output to higher frequency (principally gamma) during dynamic force output.
Comparison of motor performance between SF, sD and lD
Slobounov, Hallett & Newell  hypothesize that the increase in performance error corresponds to task difficulty. In our case, the lowest absolute error was during SF condition and therefore, we conclude that SF was the easiest task to control and perform. The finding that the error in lD is significantly higher than in sD suggests that large dynamic force condition has a higher level of difficulty. However, the similar relative errors indicate that sD and lD conditions were controlled by the subjects in a similar way. This means that the two dynamic conditions have the same level of difficulty for the subjects.
Cortical and spinal neurons are synchronized at gamma frequency during dynamic force conditions
Our results clearly show that during isometric compensation for a periodically modulated force with two amplitudes the CMC is in a similar frequency range, predominantly at gamma frequencies, and also occurs with similar amplitude. This demonstrates that the amplitude of dynamic force does not modulate the CMC. The following aspects make both dynamic conditions similar: (i) Both dynamic forces have a similar temporal pattern, as the modulation frequency is the same. (ii) Thus, both dynamic tasks require the same level of prediction and therefore, readiness to respond should also be the same. (iii) Thus, we can hypothesize that both sD and lD conditions required from the subjects a similar level of attention. (iiii) If the amount of attention and prediction are similar, the complexity of processing involved in motor planning should be also similar .
During both dynamic conditions, neurons in motor cortex and spinal motoneurones are synchronized at higher frequency (for 7 out of the 8 subjects it was gamma frequency range) compared to the static force condition. Moreover, the degree of this shift was the same for both dynamic conditions. Therefore, we conclude that both sD and lD force conditions require the same level of sensorimotor and visual integration. This is well in line with the similar motor performance in both dynamic conditions, revealed by the similar relative errors.
Taking the frequency range of CMC into account, we found large inter-individual differences for both beta- and gamma-band (Fig. 3). This is the reason for the low strength of CMC in the grand average (Fig. 2). These large inter-individual differences in the beta-range correspond to previous results in humans  and monkeys . The large inter-individual differences in the gamma-range also are in accordance to our previous findings . These present data support the assumption that frequency and strength of CMC are characteristic for every single subject.
Our findings about EEG spectral power confirm the complicated relationship between spectral power and CMC described by others  and ourself [1,13]. In this respect, it is important to note that the CMC increase in our experiment is not associated with higher EEG power. For example subject 7 in Fig. 4 shows in SF high SP in beta and gamma range while the CMC in this condition was restricted to beta range. The clarification of this relationship surely requires further exploration, e.g. using electrocorticogram.
Possible function of gamma CMC activity
A number of previous studies suggest that the gamma-range CMC could be the consequence of greater attention to the task [1,11,19,20] and that it is connected to the readiness to respond . In  we showed that during the control of a more complex task like our visuomotor dynamic force modulation the sensorimotor system is synchronized at gamma frequencies to rapidly integrate visual, proprioceptive, tactile and cognitive (prediction and planning) information.
An investigation on the deafferented patient GL showed that the proprioceptive feedback is mandatory for the genesis of gamma-range CMC . Our present observation that the amplitude of the dynamic force does not modulate the CMC suggests that changes in proprioceptive input during dynamic forces in the range from 1.6 to 4% MVC were not distinct enough for this modulation.
To conclude, during the control of dynamic forces, the brain engages into a neural state characterized by synchronization at gamma range to rapidly integrate visual, prioprioceptive, tactile and cognitive information and timely recalibrate the motor system to generate the required force, independently of its magnitude.
Eight healthy volunteers (mean age 28 ± 13 years, 2 men) without any history of neurological disease participated in the study. All subjects were right handed according to the modified Edinburgh Handedness Inventory . They gave written consent to the experiment in accordance with the declaration of Helsinki and all procedures were approved by the local ethics committee.
During the experimental session, the subject sat in an electrically shielded, dimly lit room. The right arm was supported by a splint and the subject was instructed to place the hand over a sphere, and the right index finger in the ring of a home-made manipulandum (cf. Fig. 6a, b).
Figure 6. Experimental setup. (a) High-resolution EEG recorded from 48 scalp positions together with the electrooculogram (EOG) and the EMG. (b) Manipulandum. (c) Visual feedback about the position of the ring displayed on a monitor in front of the subject. (d) Force profile generated by the manipulandum during static (SF), (e) small dynamic (sD) and (f) large dynamic (lD) condition. After a gradual increase of force to 4% MVC, the subject has to maintain the ring in its central position for 12 seconds. Both dynamic conditions have a superimposed sinusoidal function.
The manipulandum was designed for applying vertical forces on the finger, at the level of the metacarpophalangial joint. A computer-controlled tooth belt drive produced a variable upwards force on the ring. The force generated by the manipulandum was called target force (TF). The subject had to compensate the force generated by the manipulandum isometrically and maintain the ring in its initial position. The force exerted by the subject was called exerted force (EF). Visual feedback about the position of the ring was provided to the subject via a monitor 60 cm in front of him/her with two circles (Fig. 6c). The moving white inner circle (radius 2.5 mm) represented the position of the ring along the vertical axis, while the green outer circle (radius 7.5 mm) was fixed and represented the ring's reference position. The visual feedback of the actual displacement of the ring was enhanced, so that 1 mm of distance traveled by the ring was represented by 2.8 mm traveled by the white circle on the monitor. Then, the instruction given to the subject was to exert a compensating force, in order to keep the small white circle inside the green circle.
Three different experimental conditions were investigated in a given recording session:
• Static force (SF) condition: The manipulandum generated a steady force at 4% of the maximum voluntary contraction (MVC) determined prior to the experiment (cf. Fig. 6d).
• Small dynamic (sD) force condition: During this condition, the manipulandum generated a sinusoidal modulation of the 4% MVC force at frequency of 0.7 Hz and with peak-to-peak amplitude of 1.6% MVC (cf. Fig. 6e).
• Large dynamic (lD) force condition: During this condition, the manipulandum generated a sinusoidal modulation of the 4% MVC force at frequency of 0.7 Hz and with peak-to-peak amplitude of 4% MVC (cf. Fig. 6f).
Two of the conditions (SF and sD) were the same as in . The mean force level (4% MVC) was the same for all three conditions. Although an amplitude modulation of 2.5 times may not constitute a large step between "small" and "large" dynamic force condition we sought to investigate fine forces. This is based on findings that for finger isometric force the motor cortex activity is most sensitive to fine-graded low force under 10% MVC [24-26]. We therefore decided to use a force offset of 4% MVC which limits the range of peak-to-peak modulation.
To ensure a smooth start and end of the generated force by the manipulandum a rising cosine function with duration of 100 ms was used. After the increase of the force to 4% MVC, the subject had to keep the force required on the visual display, keeping the ring in its central position for 12 s. Subjects performed 35 trials for each condition. Rest intervals of approx. 10 s were inserted between trials. The subjects were instructed to avoid any other movements and to fix their gaze on the dysplay circle representing the position of the ring (the visual feedback during the task).
EEG (band pass 0–200 Hz, sampling rate 1000 Hz) was recorded from 48 scalp positions according to the extended 10–20 system (Synamp 2, NeuroScan, El Paso, TX, USA) referenced to Cz (Fig. 6a) with ground at FzA. Electrode impedances were under 5 kOhm. The EOG (same band pass and sampling rate as for EEG) was recorded to exclude trials contaminated with eye movements from further analysis. Electromyographic activity (EMG, band pass DC-200 Hz; sampling rate 1000 Hz) was recorded from the pars indicis of the right flexor digitorum superficialis muscle and from first dorsal interosseus (FDI). Both target force (TF) and exerted force (EF) were recorded in parallel with the electrophysiological data (same band pass and sampling rate as for EEG). EEG, EOG and EMG were stored and analyzed off-line.
Additionally each subject was given a short practice session prior to the experiment (5 trials for each condition) to become familiar with the behavioral task.
EEG and EMG data processing
Data analysis was performed with the commercial software Brain Vision Analyzer (Brain Vision Version 1.05, Brain Products GmbH, Munich, Germany).
Continuous data between semi-automatically put markers (P1 and P2) (cf. Fig. 6d, e, f) was divided into successive non-overlapping segments of 512 ms length, allowing for a frequency resolution of 1.96 Hz. To avoid transient effects, data related to the initial and last force ramps phase were excluded from further analysis.
Artifact rejection was visually performed off-line trial-by-trial to exclude segments contaminated with eye movements. The EEG was then transformed into the reference free current source density distribution (CSD) which reflects the underlying cortical activity and removes nearly all volume conduction effects . The CSD was computed using the spherical spline interpolation method  as implemented in the commercial software "Brain Vision 1.05."
For EMG data we applied a high pass filter of 5 Hz. Then EMG signal was rectified as it is known that full wave rectification provides the temporal pattern of grouped firing motor units . The discrete 512 points Fourier transform was calculated for each segment for the whole 1 to 500 Hz frequency range. A total of 300 artifact-free segments were analyzed for each subject.
Calculation of the EEG-EMG coherence (CMC)
Coherence values (Coh) were calculated between the rectified EMG and the EEG channels in order to calculate the synchronization between the two signals. Coherence values (Coh) were calculated by the following formulae:
Sc1, c2(f) is the cross-spectrum for the EEG (channel c1) and the rectified EMG (channel c2) at a given frequency f, and SPc1(f) and SPc2(f) are the respective power spectra for channels c1 and c2 at the same frequency f. C1 and C2 are the Fourier transformed data of channels c1 and c2 in a given segment number i (i = 1 ... n) and '*' indicates the complex conjugate.
Thus, the coherence value Cohc1,c2(f) corresponds to the squared magnitude of a complex correlation coefficient, and is a real number between 0 and 1.
Coherence values were considered not to occur by chance if the resulting values lie above the confidence level (CL) , where:
n is the number of segments and α is the desired level of confidence. We considered coherence to be significant above the 95% confidence limit.
First, coherence values were calculated between the rectified EMG and all EEG channels. Significant CMC values were observed over the left sensorimotor area contralateral to the right index finger movement (FC1; FC3; C1; C3; CP1 and CP3). Then, that EEG-EMG pair, where maximal coherence was observed in each subject was chosen for further analysis . Maximum CMC was mostly localized over channels C3 and C1.
Calculation of the EEG and EMG spectral power (SP)
Power spectrum (SP) for a given channel (c) was further calculated according to the following equation
where Ci represents the Fourier transform of data segments i (i = 1 .... n) corresponding to channel c. '*' indicates the complex conjugate. EMG was rectified before SP analysis.
Analysis of behavioral data
Computation of absolute error
Behavioral signals related to the task, the target force (TF), together with the force exerted by the subject (EF), were filtered off-line (band pass 0.5–30 Hz) to eliminate offsets accumulated during the recording. The 30 Hz high cut-off was selected to avoid power supply artifacts and was large enough to record the behavioral changes.
To evaluate the visuomotor performance, we computed error in force E, defined as the difference between the TF and the EF:
Since the force generated by the manipulandum (TF) was the reference to which the subject had to adapt, we calculated the mean squared error, MSEi, of the EF around its reference (TF) with the following formula:
where again i = 1 ... n is the segment number, k = 1 ... s is the sampled point in the actual segment i and s = 512 is the number of sampled points in each segment.
Then we calculated the absolute cumulative mean squared error, aMSE, by adding up individual segment values
Computation of relative error
We normalized the magnitude of absolute cumulative errors aMSE to the amplitude of the target force.
Whereas the |TF| for the sD was 1.6% MVC and for the lD was 4%MVC. Thus we obtained the relative error rMSE for both dynamic conditions.
EEG-EMG coherence (CMC), EEG and EMG spectral power (SP)
To test for any statistical difference on CMC, cortical and muscles power between the SF and both dynamic conditions, we measured the area under the coherence curve and above the significance level Acoh, and under the spectral power curve Apow, in two frequency-windows: 15–30 Hz for the beta-range and 30–45 Hz for the gamma-range.
Individual values for the area of the coherence were firstly transformed logarithmically to yield symmetric distributions according to the formula
To evaluate the relation in magnitude between beta- and gamma-range coherence, we subtracted significant area corresponding to the gamma-range from the coherent area in beta-range.
Afterwards the non-parametric Friedman test was applied to compare values A for CMC and Apow for SP measured in all 3 conditions for each single subject with the null hypotheses that the distributions of the values tested are the same across all 3 conditions. The Friedman test with the global null hypothesis was calculated first to avoid an alpha-adjustment in the simultaneous paired hypotheses. When the Friedman test indicated that not all of the three conditions were statistically equivalent, we performed a second non-parametric test (paired Wilcoxon test) on the resulting values A for CMC and Apow for spectral power. The null hypothesis was that the difference between the matched samples of coherence and power spectra arises from a distribution which is symmetric around zero. We applied this test on the following pairs: SF and sD condition, SF and lD condition and sD and lD condition. We used a third window between 15–45 Hz to evaluate the whole beta- and gamma-range activity together and calculated its centre of gravity (CoG, i.e. the frequency at which all CMC activity from 15–45 Hz could in theory be concentrated; around this frequency point, the CMC is balanced, i.e. is the same on the right and on the left). This was done according to:
where s = 1 ... n indicates the number of significant bins with its respective frequency value f and coherence amplitude C. We applied the Friedman test on the frequency values obtained from the centre of gravity for SF, sD and lD conditions to check whether there are any significant frequency shifts between all three conditions. We used paired Wilcoxon test on these frequency values for the same condition pairs as mentioned above.
To account for the inter-subject variability and to symmetrize the distribution, values corresponding to the behavioral performance were first logarithmically transformed:
The Friedman test was applied to check differences between all three conditions in terms of absolute performance errors. Afterwards we tested single pairs (SF-sD, SF-lD, sD-lD) using paired Wilcoxon test. The statistical difference in relative performance error between both dynamic conditions sD-lD was tested as well as using paired Wilcoxon test. A probability P value of less than 0.05 was considered significant for both statistical tests.
aMSE absolute cumulative mean squared performance error
CMC corticomuscular coherence
E error in force
EF exerted force
FFT Fast Fourier Transformation
lD large dynamic force output condition
MVC maximum voluntary contraction
rMSE relative cumulative mean squared performance error
sD small dynamic force output condition
SF static force output condition
SP spectral power
TF target force
AA carried out data acquisition, data analysis and interpretation and participated in writing the manuscript. LP participated in the design of the study, in data analysis and interpretation and writing the manuscript. J-RN participated in the design of the experiment, data analysis and interpretation and revised the manuscript. MW assisted in data acquisition, data analysis and participated in writing and revision of the manuscript. MCHR participated in the study design, interpretation of the data and revised the manuscript. RK conceived the study and participated in all the steps of the realization of the study.
All authors read and approved the final version of the manuscript.
Supported by DFG grant (Kr 1392/7-5) and KAAD.
Conway BA, Halliday DM, Farmer SF, Shahani U, Maas P, Weir AI, Rosenberg JR: Synchronization between motor cortex and spinal motoneuronal pool during the performance of a maintained motor task in man.
J Physiol (Paris) 1978, 74:287-291. PubMed Abstract
Prog Brain Res 1989, 80:451-463. PubMed Abstract
Nunez PL, Srinivasan R, Westdorp AF, Wijesinghe RS, Tucker DM, Silberstein RB, Cadusch PJ: EEG coherency: I: statistics, reference electrode, volume conduction, Laplacians, cortical imaging, and interpretation at multiple scales.
Electroencephalography and Clinical Neurophysiology 1997, 103:499-515. Publisher Full Text
Electroencephalography and Clinical Neurophysiology 1989, 72:184-187. Publisher Full Text
Halliday DM, Rosenberg JR, Amjad AM, Breeze P, Conway BA, Farmer SF: A framework for the analysis of mixed time series/point process data--theory and application to the study of physiological tremor, single motor unit discharges and electromyograms.