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Supplementary materials
1) Pilot study 1: VO2peak determination
The effects of exercise on cognition vary with the intensity of exercise, which is
also participant to change among participants. To maintain a moderate-intensity for
each participant, moderate-intensity exercise was defined as 50% of a subjects’ peak
oxygen intake (VO2peak) based on classification of physical activity intensity of the
American College of Sports Medicine (ACSM, 2014).
To determine VO2peak, all participants underwent a graded exercise testing on a
recumbent ergometer (Strength-ergo 240, Mitsubishi Electric Corporation, Tokyo,
Japan). After a warm-up exercise of 3 minutes at 30W, the work rate increases by
20W (female: 15W) per minute in a constant and continuous manner to exhaustion.
The pedaling rate was kept at 60 rpm.
We measured heart rate (HR) and the participant’s rating of perceived exertion
(RPE) every minute (Borg, 1982). Ventilation parameters, oxygen intake (VO2) and
carbon dioxide output (VCO2) were measured breath-by-breath by using a gas
analyzer (Aeromonitor AE280S, Minato Medical Science, Osaka, Japan). The
respiratory exchange ratio (R) was calculated as a VO2 / VCO2 ratio. VO2peak was
determined once two of the following criteria were satisfied: R exceeding 1.05,
achievement of age-predicted peak HR (HR peak), and a RPE of 19 or 20. VO2peak and
other respiratory and metabolic parameters at VO2peak are shown in Table 1.
Table 1. Participant characteristics.
R RPE HR (bpm) Workload (W)VO2peak
(ml・kg・min -1)
50% VO2peak 0.9 ± 0.1 12.1 ± 2.8 115.6 ± 5.6 84.3 ± 23.5
VO2peak 1.1 ± 0.1 19.4 ± 1.1 168.2 ± 8.3 185.4 ± 47.1 38.8 ± 6.4
Inter-subject mean values of respiratory exchange ratio (R, VO2 / VCO2), rating of perceived exertion
(RPE), heart rate (HR), workload (W), and peak oxygen intake (VO2peak) recorded at the end of the
exercise at an intensity of 50% VO2peak and an intensity of VO2peak.
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To determine exertion needed achieve 50% of VO2peak, it is plotted VO2 against
the output power of the strength ergometer to VO2peak (Wasserman et al., 1973). It is
linearly regressed the measured points using the least square method, and 50% VO2peak
was estimated from delta VO2peak (VO2peak - VO2 at the resting period) for each subject.
2) Pilot study 2: Assessment of non-cortical physiological changes induced by
exercise.
fNIRS is a powerful equipment for investigating the effects of exercise on
cognitive function. In most studies, cognitive tasks were performed at few minutes
after the end of the exercise. However, simply performing cognitive tasks at any one
time may not be appropriate for fNIRS measurement because its measurements are
susceptible to exercise-induced physiological signals as well as cerebral
hemodynamics (Katura et al., 2006). Especially, increases in skin blood flow by an
acute of exercise significantly effect on fNIRS measurement (Davis, 2006). Moreover,
mild hypoxic condition reduced hemodynamic responses to electrical stimulation in
the forepaw, but EEG responses remained unchanged compared with the normoxic
condition (Sumiyoshi et al., 2012). Thus, decreasing percutaneous arterial oxygen
saturation (SpO2) and regional cerebral tissue oxygenation (Cerebral rSO2) may affect
fNIRS measurement.
Five young adults (mean age 20.2 ± 2.8 years (range 18 to 25 years); 3 female)
participated in this pilot study. Some physiological parameters including the middle
cerebral artery mean blood velocity (MCA Vmean), skin blood flow (SBF), respiration
properties (oxygen intake: VO2; carbon dioxide output: ETCO2), heart rate (HR),
percutaneous arterial oxygen saturation (SpO2) and regional cerebral tissue
oxygenation (cerebral rSO2) were monitored before, during, and after 15 minutes of
moderate intensity exercise under hypoxia (FIO2 = 0.135) to set the appropriate
experimental protocol. At the beginning of the experiment, the participants were
exposed to the hypoxic or normoxic gas for 10 min while sitting on the cycle
ergometer. The timing of the post cognitive task as well as brain monitoring with
fNIRS should be determined when those parameters returned to the basal level and
stabilized to eliminate any contaminations.
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MCA Vmean was sampled every minute by a transcranial Doppler ultrasonography
(WAKI 1-TC, Atys Medical, France). A 2-MHz Doppler probe was placed over the
right temporal window (Zhang et al., 2002). The probe was fixed with an adjustable
headband and adhesive ultrasonic gel. The MCA Vmean at the resting period was set at
100% and the relative percentage change of MCA Vmean was sampled every minute.
SBF was monitored with a laser-Doppler probe (FLO-C1, Omegawave, Japan)
attached at Fpz of the international 10-20 system. The SBF at the resting period was
set at 100% and the relative percentage change of SBF was sampled every minute. HR
and ETCO2 were continuously monitored as aforementioned and the average HR and
VCO2 were calculated every minute. SpO2 was monitored every minute by a pulse
oximeter (OLV-3100, Nihon Kohden, Japan) placed on the left earlobe. The cerebral
rSO2 was monitored every minute by a NIRS system (BOM-L1 TRW, Omegawave,
Japan). A probe holder was attached at the left side of the forehead, as previously
studies (Ando et al., 2013, 2010; Komiyama et al., 2015). The effect of exercise,
compared to the resting period (of the 3 minutes before exercise), was evaluated using
a t-test with Dunnett correction. Statistical significance was set at p < 0.05.
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Fig. 1. Illustrations of the physiological parameters at rest, during, and after an acute exercise
bout. Inter-subject mean of physiological parameters at each time point are plotted. Error bars indicate
with standard deviations. Time points with significant exercise effects compared to the signal intensity
at the onset are indicated with asterisks (p<0.05, Dunnet’s test). (A) MCA Vmean: middle cerebral artery
mean blood velocity; SBF: skin blood flow; HR: Heat rate; ETCO2: end-tidal carbon dioxide (B) SpO2:
percutaneous arterial oxygen saturation; cerebral rSO2: cerebral oxygen saturation output at rest,
during, and after the 10 minutes of exercise at 50% of peak oxygen intake under hypoxia (FIO2 = 0.13).
MCA Vmean and ETCO2 didn’t alter by exercise. Significant increase of SBF was
observed from 9 minutes after the onset of exercise to 2 minutes after the end of
exercise. HR increased rapidly, reaching a significant level at 1 minute after the onset
of exercise, and decreased to an insignificant level 3 minute after the end of the
exercise. Significant decrease of SpO2 was observed from 2 minutes after the onset of
exercise to 2 minutes after the end of exercise. Cerebral rSO2 significantly decreased
for 6 minutes from 2 minutes after the onset of exercise. The exercise-induced
physiological parameters returned to the baseline level and stabilized at an average of
3 minutes after the end of exercise (Fig. 1).
In the present study, 10 minutes of moderate intensity exercise significantly
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impacted on non-cortical physiological parameters including skin blood flow, MCA
Vmean, respiratory profiles, and HR as our previous studies confirmed with different
intensity and mode of exercise (Timinkul et al., 2008; Yanagisawa et al., 2010).
Furthermore, moderate intensity exercise under hypoxia also impacted SpO2 and
cerebral rSO2. However, these effects were diminished within 3 minutes after the
exercise. In addition, it takes more than 3 minutes to instrument the fNIRS probe on
subject’s head after the exercise. Therefore, the cortical responses measured at 15
minutes after the end of exercise under hypoxia in the current study could be free
from contaminated physiological signals, just similar as previously study in normoxia
(Yanagisawa et al., 2010).
2) Pilot study 3: Assessment of cortical activation induced by normobaric
hypoxia.
Unlike other neuroimaging methods, fNIRS is compact, portable, and can be
easily installed in a gym (Timinkul et al., 2008). These features allow strict control of
exercise intensity well as that of hypoxic condition, and subsequent on-site
neuroimaging allows precise control of the interval between exercise and
neuroimaging experiments. In addition, fNIRS allows participants to perform tasks in
a natural and comfortable environment without being confined to a small, restricted
space, keeping possible outside influences on cognitive tasks minimal. On the other
hand, changes in cerebral hypoxia may affect the near-infrared signal independent of
changes in cerebral oxygenation, despite neural activity did not change (Sumiyoshi et
al., 2012). In this pilot study, we examine the hypoxic effect on cognition and cortical
hemodynamic change.
Ten right-handed young participants performed color-word Stroop task (CWST)
under normoxic (NO) or hypoxic conditions (HY) with the order being
counterbalanced across participants. In the HY condition, participants breathed the
hypoxic gas, which was mixture of 13.5% O2 and 0.03% CO2 in nitrogen N2 (FIO2 =
0.135; approximately 3,500m equivalent altitude), through a mask that was connected
to Douglas bags. In the NO condition, participants breathed the ambient air at sea
level (normoxic gas), through a mask that was connected Douglas bags. Expired air
was directly exhausted outside the mask so that the participants did not re-breathe the
expired air. The participants were exposed to the hypoxic or normoxic gas from 10
min before the pre-Stroop session. Cortical hemodynamic changes in regions of
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interest (ROIs) were monitored with an fNIRS while participants performed the
CWST. Reaction time were subjected to repeated measures two-way ANOVA with
trial (incongruent/neutral) and condition (NO/HY) as within-subject factors to
examine whether the general tendencies for the Stroop task could be reproduced in all
conditions. The reaction time of Stroop interference (incongruent – neutral) under HY
condition compared to NO condition, was evaluated using a t-test. The (incongruent –
neutral) contrasts of oxy-Hb signals were analyzed with paired t-test to compare with
NO and HY conditions. Statistical significance was set at p < 0.05.
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Fig. 2. Color-word Stroop task in reaction time (A) and Stroop interference for oxy-Hb signal (B) in
normoxic and hypoxic (FIO2 = 0.135) conditions. The prefrontal activation of the Stroop interference
was smaller at left DLPFC under hypoxic condition compared with normoxic condition, despite the
CWST performance did not change. For box-and-whisker plots, the tops and bottoms of the boxes are
third and first quartiles, respectively. The upper and lower ends of whiskers represent the highest
data points within 1.5 interquartile ranges of the upper quartiles and the lowest data points within
1.5 interquartile ranges of the lower quartiles, respectively. The bands inside the boxes indicate
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medians. The x’s show averages of reaction time and oxy-Hb signals.
Reaction time were subjected to a repeated measure two-way ANOVA with trial
(incongruent/neutral) and condition (NO/HY) being within-subject factors. The
ANOVA exhibited significant main effects of trial on reaction time (F(1,9) = 30.231, p
< 0.001). This analysis was limited to the main effect of the trial because the purpose
of the ANOVA was to examine the occurrence of the Stroop effect. These results
verified that Stroop interference could be generally observed in all the sessions used
in this experiment. Thus, to clarify the effect of hypoxic condition on a specifically
defined cognitive process, we focused on the analyses of Stroop interference
(incongruent - neutral). The reaction time of Stroop interference was no significantly
difference between NO and HY conditions (Fig. 2A).
Next, we assessed the effects of hypoxic condition on the prefrontal activation
focusing on Stroop interference. The difference of (incongruent – neutral) contrasts
between NO and HY conditions for each ROIs was analyzed with a t-test. Although
prefrontal activation of Stroop interference was not significantly different between
NO and HY conditions at all ROIs, the activations of all ROIs tended to decrease
under HY condition compared with under NO condition. This result was similar to
previous animal fMRI study reporting that the mild hypoxic condition reduced
hemodynamic responses to electrical stimulation in the forepaw, but EEG responses
remained unchanged compared with normoxic condition (Sumiyoshi et al., 2012).
Therefore, the Oxy-Hb response with CWST may be small in hypoxia despite the
neural activation of Stroop interference is occurred.
3) fNIRS data of experimental 2
The (incongruent – neutral) contrasts were analyzed with repeated measures of
two-way ANOVA including exercise (EX/CTL) and session (pre/post) as within-
subject factors. The ANOVA performed on each of the six ROIs revealed significant
interaction in the l-DLPFC (F(1, 14) = 10.708, p < 0.05, Bonferroni-corrected)(Fig.
4).
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Fig. 3. Time lines of changes of oxy-Hb and deoxy-Hb during the Stroop task for all ROIs in pre-
session (A) and in the post-session (B, C).
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Fig. 4. Oxy-Hb signal changes for Stroop interference in all 6 ROIs for Ex and Con sessions.
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4) Short Report for McNemar Test (Modified after Siegel, Sidney & Castellan,
1988).
Origin: first introduced by McNemar, Quinn in 1947
General use of this test: to test the difference between two associated*
proportions/frequencies in 2 x 2 dichotomous variables (can be repeated / matched
measure) where an ordinary chi-square test is inappropriate due to the violation of
assumptions of independence.
*This test can be also used for independent observations.
Advantages of using this method in the currently submitted article:
1) Because a large variability within participants and restricted range-like
problem after the treatments due to the nature of the manipulation made the
association ambiguous, it was not appropriate and robust to use parametric
tests such as Pearson r for the data.
2) In addition, observations of not strong interest (ones with no changes between
pre and post treatment) appeared to distort the results for ordinary
nonparametric tests such as Spearman rank-order correlation and Kendall’s
tau.
3) As a result, McNemar test was employed because directionality of the
variability in the data was consistent despite the problems discussed above,
and McNemar test was able to eliminate influences from uninterested
observations (diagonal cells A & D in Table 1 below).
Data format:
Table 1. Data format for McNemar test
Pre
1 0 Total
1 A B A+B
Post 0 C D C+D
total A+C B+D
A+B+C+
D
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Notes: frequency of positive (1) and change (0) infection pre and post the medication
Assumptions for McNemar test:
1) Variables should be dichotomous where diagonal (A & D) represent
unchanged observations.
2) It is commonly used for repeated / matched measures*.
*This test can be also used for independent observations.
3) Sample size: summed frequency at diagonal A + D should be larger than
10.
Hypothesis to be tested:
H0: p (pre = 0, post = 1) = p (pre = 1, post = 0)
H1: p (pre = 0, post = 1) p (pre = 1, post = 0)
Formula for ZMcNemar and 2McNemar:
ZMcNemar = FrecCFreqBFrecCFreqB
1||
, df = (rows - 1) (columns - 1) = 1
2McNemar = FreqCFreqB
FrecCFreqB
2)1|(|
, df = (rows - 1) (columns - 1) = 1
Problem and justification to use this method: Since this test compares p(pre = 1,
post = 0) and p(pre = 0, post = 1), it ignores the effects of two other probabilities p(pre
= 1, post = 1) =and p(pre = 0, post = 0). As shown below, data from Table 5 and Table
6 indicates the same significance level, but interpretation of result would be different.
As opposed to the data from Table 4, the data 2’s effect is actually larger. In other
words, ratio of decreasing positive infection is larger compared with remaining cells.
However, in the current study, our purpose was to find the directionality of change
after the treatment ignoring the observations that did not change between pre and post
treatments, this test fitted our aim.
ReferencesAmerican College of Sports Medicine. 2014. ACSM’s Guidelines for Exercise
Testing and Prescription.
Ando, S., Hatamoto, Y., Sudo, M., Kiyonaga, A., Tanaka, H., Higaki, Y., 2013. The
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Effects of Exercise Under Hypoxia on Cognitive Function. PLoS One 8.
doi:10.1371/journal.pone.0063630
Ando, S., Yamada, Y., Kokubu, M., 2010. Reaction time to peripheral visual stimuli
during exercise under hypoxia. J. Appl. Physiol. 108, 1210–1216.
doi:10.1152/japplphysiol.01115.2009
Chernomordik, V., Amyot, F., Kenney, K., Wassermann, E., Diaz-Arrastia, R.,
Gandjbakhche, A., 2016. Abnormality of low frequency cerebral hemodynamics
oscillations in TBI population. Brain Res. 1639, 194–199.
doi:10.1016/j.brainres.2016.02.018
Davis, S.L., 2006. Skin blood flow influences near-infrared spectroscopy-derived
measurements of tissue oxygenation during heat stress. J. Appl. Physiol. 100,
221–224. doi:10.1152/japplphysiol.00867.2005
Komiyama, T., Sudo, M., Higaki, Y., Kiyonaga, A., Tanaka, H., Ando, S., 2015. Does
moderate hypoxia alter working memory and executive function during
prolonged exercise? Physiol. Behav. 139, 290–296.
doi:10.1016/j.physbeh.2014.11.057
Miyazawa, T., Horiuchi, M., Komine, H., Sugawara, J., Fadel, P.J., Ogoh, S., 2013.
Skin blood flow influences cerebral oxygenation measured by near-infrared
spectroscopy during dynamic exercise. Eur. J. Appl. Physiol. 113, 2841–2848.
doi:10.1007/s00421-013-2723-7
Sumiyoshi, A., Suzuki, H., Shimokawa, H., Kawashima, R., 2012. Neurovascular
uncoupling under mild hypoxic hypoxia: an EEG–fMRI study in rats. J. Cereb.
Blood Flow Metab. 32, 1853–1858. doi:10.1038/jcbfm.2012.111
Borg, G.A., 1982. Psychophysical bases of perceived exertion. Med. Sci. Sports
Exerc. 14, 377–381.
Davis, S.L., Fadel, P.J., Cui, J., Thomas, G.D., Crandall, C.G., 2006. Skin blood flow
influences near-infrared spectroscopy-derived measurements of tissue
oxygenation during heat stress. J. Appl. Physiol. 100, 221–224.
Harms, C.A., Wetter, T.J., McClaran, S.R., Pegelow, D.F., Nickele, G.A., Nelson,
W.B., Hanson, P., Dempsey, J.A., 1998. Effects of respiratory muscle work on
cardiac output and its distribution during maximal exercise. J. Appl. Physiol. 85,
609-618.
Katura, T., Tanaka, N., Obata, A., Sato, H., Maki, A., 2006. Quantitative evaluation of
interrelations between spontaneous low-frequency oscillations in cerebral
16
hemodynamics and systemic cardiovascular dynamics. NeuroImage 31, 1592–
1600.
Timinkul, A., Kato, M., Omori, T., Deocaris, C.C., Ito, A., Kizuka, T., Sakairi, Y.,
Nishijima, T., Asada, T., Soya, H., 2008. Enhancing effect of cerebral blood
volume by mild exercise in healthy young men: a near-infrared spectroscopy
study. Neurosci. Res. 61, 242–248.
Wasserman, K., Whipp, B.J., Koyl, S.N., Beaver, W.L., 1973. Anaerobic threshold and
respiratory gas exchange during exercise. J. Appl. Physiol. 35, 236–243.
Yanagisawa, H., Dan, I., Tsuzuki, D., Kato, M., Okamoto, M., Kyutoku, Y., Soya, H.,
2010. Acute moderate exercise elicits increased dorsolateral prefrontal activation
and improves cognitive performance with Stroop test. NeuroImage 50, 1702–
1710.
Zhang, R., Zuckerman, J.H., Iwasaki, K., Wilson, T.E., Crandall, C.G., Levine, B.D.,
2002. Autonomic neural control of dynamic cerebral autoregulation in humans.
Circulation 106, 1814-1820.
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