ライフサイエンスコーパス: EMG

1 EMG activation with HFLD-ICMS was evaluated while two ma

2 EMG electrodes were implanted bilaterally in selected mu

3 EMG from the left resting flexor carpi radialis (FCR) mu

4 EMG in muscle disease continues to have a role, particul

5 EMG intensity differs significantly from level running o

6 EMG recordings were made from right ankle dorsiflexor an

7 EMG revealed predominantly myopathic changes in the axia

8 EMG served as a measure of response conflict by detectin

9 EMG signals were decoded with a pattern-recognition algo

10 EMG was obtained by hydrolyzing native guar gum using al

11 EMG-EMG coherence in the beta and gamma frequency bands

12 EMG-EMG coherence was calculated from two separate elect

13 However, in voluntary activation, EMG- and ultrasound-detected activation onsets may not c

14 motor areas and electromyographic activity (EMG) from affected neck muscles were recorded before and

15 EUS reflex electromyographic activity (EMG), innervation of pelvic and perineal structures, and

16 mperature (Tb ), electromyographic activity (EMG), metabolic rate (M) and whole-body thermal sensatio

17 pted for a longer period after HX than after EMG or dye injection surgeries.

18 e at high frequency, associated with altered EMG patterns and hindlimb kinematics during gait.

19 ively correlated with EEG gamma activity and EMG activity, which is indicative of cortical activation

20 Therefore, we collected behavioral and EMG data in the flanker task, a standard paradigm to inv

21 elevation of the power for both the EEG and EMG activities with muscle fatigue, the fatigue weakens

22 Male albino rats were implanted with EEG and EMG electrodes, abdominal temperature/activity transpond

23 Results: The power of both EEG and EMG increased significantly while their coherence decrea

24 EEG and EMG recordings revealed that ppDIO increases sleep durin

25 The entire duration of the EEG and EMG recordings was divided into the first half (stage 1

26 We used EEG and EMG to investigate the development of corticomuscular an

27 e-body plethysmograph, together with EEG and EMG.

28 erent relative magnitudes of EEG --> EMG and EMG --> EEG directed coherence might underlie the observ

29 A/2J and A/J mice were divided into EMG+ and EMG- groups.

30 Movement kinematics and EMG from the wrist extensors and flexors and sternocleid

31 ed framework captured the rate, latency, and EMG surface of partial errors, along with the speed of t

32 cle and muscle-tendon unit (MTU) length, and EMG activity of SO, lateral gastrocnemius (LG) and media

33 were placed over 9 residual limb muscles and EMG signals were recorded as patients ambulated and comp

34 st the hypothesis that thalamic neuronal and EMG activities during intention essential tremor are sim

35 J morphology, neuromuscular transmission and EMG data were found only in mdx following injury.

36 We recorded sensorimotor EEGs and EMGs from three intrinsic hand muscles in human subjects

37 -impaired sides using linear electrode array EMG recordings.

38 etry ( approximately 128 strides) as well as EMG magnitude and timing ( approximately 40-100 and appr

39 both descending (EEG --> EMG) and ascending(EMG --> EEG) directions at beta frequencies.

40 SOL (and probably TA) background EMG activity recovered faster in TU rats than in TC rats

41 This new combination of detailed behavioral, EMG, and tDCS techniques clarifies the neurophysiology o

42 Coherence between EMG activity and pallidal activity was mainly found in p

43 The different coupling between EMG and movement in posture and when moving must pose a

44 Consequently, the gain between EMG and acceleration is maximal at the frequency where t

45 ts indicated variable time intervals between EMG- and motion onset, median (interquartile range) 96 (

46 on in individual intercostal nerve branches, EMG sites and motor units reported in a companion paper.

47 The stress caused by EMG instrumentation may be distinctively manifested base

48 c responses) were not severely influenced by EMG+ in either strain.

49 muscles below the SCI level, as measured by EMGs, resulting in marked improvement in their walking i

50 Multi-channel EMG and M-mode ultrasound revealed regional differences

51 Chronic EMG electrodes were implanted into vastus lateralis, bic

52 ic causal modeling of concurrently collected EMG-fMRI data in two cohorts of Parkinson's patients, we

53 by individual motor units from the composite EMG signals.

54 ed brain activity and tremor with concurrent EMG-fMRI.

55 p was found to drive blood pressure control (EMG --> SBP) as well as control the postural sway (EMG -

56 pressure (BP), heart rate (HR), diaphragm (D(EMG)) and genioglossus muscle (GG(EMG)) activity were re

57 bition of the PVN increased BP, HR, minute D(EMG) and GG(EMG) activity and these increases were atten

58 sponse time distributions and accuracy data, EMG analyses of response agonist muscles challenged the

59 perturbation trials were used to deconstruct EMG time courses into error-feedback and learning compon

60 obese patients with apnea (Deltagenioglossus EMG/Deltaepiglottic pressure: -0.49 [-0.22 to -0.79] vs.

61 For this purpose, we acquired high-density EMG signals from the biceps brachii in 5 male transhumer

62 rful cortical and VTA EEG desynchronization, EMG activation, a large brain temperature increase, but

63 ency (fb ) and rate of rise of the diaphragm EMG increased in 6 of 7 animals but the group mean chang

64 respiratory frequency (fR) and diaphragmatic EMG (dEMG) amplitude in relation to the duration and fre

65 and intercostal, scalene, and diaphragmatic EMG activity was reduced using NIOV+O(2) compared with u

66 In organic dystonia, EMG power is commonly concentrated at the lowest frequen

67 ibed by ankle and hip EMG signals, with each EMG signal computed as a weighted sum of rectified EMG s

68 EEG, EMG, blood pressure and WBP signals were simultaneously

69 EEG, EMG, body temperature (Tb), and locomotor activity (LMA)

70 EEG, EMG, body temperature, and locomotor activity data were

71 was to address this issue by quantifying EEG-EMG coherence at times when muscles experienced minimal

72 The EEG-EMG coherence and power spectrum in each stage was compu

73 electroencephalography/electromyography (EEG/EMG) to discriminate wake-sleep states.

74 Sprague-Dawley rats, implanted for EEG/EMG recording, were orally administered vehicle (VEH), 1

75 sleep states were scored based either on EEG/EMG or on WBP signals and sleep-dependent respiratory an

76 Our goal was to compare the EEG/EMG-based and the WBP-based scoring of wake-sleep states

77 EG), Electrooculogram (EOG), Electromyogram (EMG), Electrocardiogram (ECG) and parameters along with

78 erative disease, we measured electromyogram (EMG) activity in hind limb muscles of SOD1G93A mice.

79 igh-fidelity transmission of electromyogram (EMG) and electroneurogram (ENG) signals from anesthetize

80 these target muscles produce electromyogram (EMG) signals on the surface of the skin that can be meas

81 Moreover, surface electromyogram (EMG) signals were concurrently detected from the TA musc

82 his hypothesis, we recorded electromyograms (EMGs) from 12-16 upper arm and shoulder muscles from bot

83 t may contribute to surface electromyograms (EMGs).

84 ent study demonstrates that electromyograms (EMGs) obtained during locomotor activity in mice were ef

85 d amplitude analyses of the electromyograms (EMGs) during these vocalizations were analyzed.

86 nd extensor muscles and the electromyograms (EMGs) of the corresponding muscles were recorded.

87 yrus in combination with an electromyograph (EMG) electrode patch implanted in the nuchal muscle.

88 Electromyographic (EMG) analysis indicating denervation occurred between 10

89 lantarflexion errors) and electromyographic (EMG) activity.

90 ncephalographic (EEG) and electromyographic (EMG) electrodes for the recording of sleep-wake states a

91 crostimulation (ICMS) and electromyographic (EMG) recordings to test whether neuroplastic changes occ

92 ) morphology derived from electromyographic (EMG) signals in patients with OSA versus control subject

93 izing kinematic, kinetic, electromyographic (EMG), and metabolic data taken from five participants wa

94 itude, and (3) latency of electromyographic (EMG) activation associated with HFLD-ICMS-evoked movemen

95 gered averaging (StTA) of electromyographic (EMG) activity is a form of intracortical microstimulatio

96 We found that the use of electromyographic (EMG) signals from natively innervated and surgically rei

97 0 and 100 mg of S44819 on electromyographic (EMG) and electroencephalographic (EEG) measures of corti

98 s (20-40 years) to record electromyographic (EMG) activities and pulmonary ventilation (VI) at rest a

99 -leads to the result that electromyographic (EMG) synergies will arise without the need to conclude t

100 percentage of CRs or the electromyographic (EMG) activity of the orbicularis oculi muscle during con

101 Tongue electromyographic (EMG) activity is increased in patients with OSA.

102 Electromyography (EMG) was used to measure activation in muscles relevant

103 conduction study (NCS) and electromyography (EMG) attributes that might differentiate POEMS from CIDP

104 ed tomography (n = 39) and electromyography (EMG) of the abdominothoracic wall (n = 32) during basal

105 photodetector arrays, and electromyography (EMG) sensors, from their preparation substrates to vario

106 penditures; $7.5 billion), electromyography (EMG; 20% of expenditures; $2.6 billion), and electroence

107 blood pressure (SBP), calf electromyography (EMG), and resultant center of pressure (COPr) can quanti

108 ctroencephalography (EEG), electromyography (EMG), locomotor activity, and subcutaneous temperature.

109 ctroencephalography (EEG), electromyography (EMG), muscle biopsy, high-resolution molecular karyotype

110 nset can be estimated from electromyography (EMG)-registered muscle excitation and from ultrasound-re

111 ly the tip of the iceberg: electromyography (EMG) revealed fast subthreshold muscle activation in the

112 test called intramuscular electromyography (EMG).

113 ssayed using the timing of electromyography (EMG) activity recorded from the tibialis anterior (TA) a

114 forget the contribution of electromyography (EMG) to the investigation of paediatric peripheral neuro

115 algorithm based on surface electromyography (EMG) for differentiation between convulsive epileptic an

116 h vastus lateralis surface electromyography (EMG).

117 A number of TMS-electromyography (EMG) and TMS-electroencephalography (EEG) studies have i

118 euromuscular transmission, electromyography (EMG), and NMJ morphology were assessed 24 h after injury

119 Here we used electromyography (EMG) to compare neural correlates of learning and feedba

120 nk reflex as measured with electromyography (EMG).

121 d respiratory control during sleep with EMG (EMG+) or without EMG (EMG-).

122 during sleep with EMG (EMG+) or without EMG (EMG-).

123 However, the EUS EMG response is significantly larger when induced by gen

124 oiding frequency (-60%, n = 7) and tonic EUS EMG activity (-38%, n = 6) or completely inhibited voidi

125 ursting of external urethral sphincter (EUS) EMG and expulsion of urine from the urethral meatus.

126 1 from which ICMS could simultaneously evoke EMG responses in different combinations of LAD, RAD, and

127 common temporal pattern of HFLD-ICMS-evoked EMG activity (58% of responses) was a sharp rise to a pl

128 HFLD-ICMS-evoked EMG activity was largely stable across all parameters te

129 ) and long-latency (late) stimulation-evoked EMG responses was observed throughout the step cycle.

130 normal, but increased jitter in single-fibre EMG studies indicated unstable neuromuscular transmissio

131 Preventing acetylation did not impact final EMG induction levels during meiosis.

132 ing (10-20 ms) central peak was observed for EMG-EMG synchronization in older infants.

133 Early meiotic gene (EMG) repression during mitosis is achieved by recruiting

134 Genioglossus EMG signals were analyzed offline by automated software

135 In 6-8 weeks genioglossus EMG and dynamic MRI of the upper airway were performed b

136 i) and tonic and phasic components of the GG EMG activity.

137 e PVN increased BP, HR, minute D(EMG) and GG(EMG) activity and these increases were attenuated after

138 aphragm (D(EMG)) and genioglossus muscle (GG(EMG)) activity were recorded in anaesthetized, ventilate

139 hat different relative magnitudes of EEG --> EMG and EMG --> EEG directed coherence might underlie th

140 rage phase delays of 26.4 ms for the EEG --> EMG direction and 29.5 ms for the EMG --> EEG direction

141 was significant in both descending (EEG --> EMG) and ascending(EMG --> EEG) directions at beta frequ

142 f xanthan gum (XG) and enzyme-modified guar (EMG) gum mixtures on the physicochemical properties and

143 The durations of high EMG activity and of CMs were statistically indifferent.

144 We examined the characteristics of hindlimb EMG activity evoked in response to epidural stimulation

145 activations were described by ankle and hip EMG signals, with each EMG signal computed as a weighted

146 tely 76%, 46%, and 50% of the rats after HX, EMG, and dye injection surgeries, respectively.

147 eriod in 27 female rats before and after HX, EMG, and/or dye injection surgeries and in HX rats that

148 Accordingly, we examined: (1) if EMG can be eliminated for assessing sleep-wake states; a

149 A significant (p = 0.002) decline in EMG --> SBP causality was observed in the elderly group,

150 However, a delay in EMG induction was observed, which became more severe in

151 iaphragm contraction (19% +/- 3% increase in EMG score and 12 +/- 2 mm descent; P < .001 vs basal val

152 ercostal contraction (14% +/- 3% increase in EMG scores and 6 +/- 1 mm increase in thoracic antero-po

153 also accompanied by a bilateral reduction in EMG throughout the gait cycle.

154 support at stance, and lower variability in EMG parameters than nontrained rats, and these propertie

155 Individual values were more variable in EMG+ mice.

156 Including EMG signals and historical information in the real-time

157 The very existence of covert incorrect EMG activity ("partial error") during the evidence accum

158 Those analyses revealed covert incorrect EMG activity ("partial error") in a fraction of trials i

159 , we found that: (1) perturbations increased EMG activity of the gluteus medius and postural control

160 Importantly, in contrast to training-induced EMG increases, the increase in coherence was maintained

161 transducers), and activity (using indwelling EMG).

162 ay-old DBA/2J and A/J mice were divided into EMG+ and EMG- groups.

163 Intramuscular EMG electrodes were implanted to monitor and compare the

164 of motor units identified from intramuscular EMGs detected from gastrocnemius and soleus while five p

165 me dyspnea reduction correlated with isotime EMG reduction (r = 0.42, P = 0.0053).

166 ith the head pitched down the medium-latency EMG response was abolished while the short-latency EMG r

167 sponse was abolished while the short-latency EMG response was maintained.

168 - 460 ms before the start of significant LFP-EMG coherence.

169 Upper limb EMGs were recorded to control for covert muscle activity

170 ials, motion onset was detected before local EMG onset.

171 ariation of the time intervals between local EMG- and ultrasound-detected activation onset.

172 These novel results indicate (i) locomotor EMG activity might be an early measure of disease onset;

173 Locomotor EMGs could have potential use as a clinical diagnostic t

174 was high; MTs were present during silent/low EMG activity.

175 d by bilateral reflex depression of masseter EMG caused by auditory input from the coil discharge.

176 were found during upslope walking, where MG EMG activity was greatest across slopes (P < 0.05) and g

177 However, in neonatal mice EMG instrumentation could induce stress, altering their

178 In mice, EMG with behavioral indices (coordinated movements, CMs;

179 MRI, EMG, and EEG should receive close scrutiny in the develo

180 Rectified forearm extensor muscle EMG and physiological hand tremor were recorded.

181 were extracted from the genioglossus muscle EMG signals.

182 xercise duration, surface inspiratory muscle EMG, Spo(2), transcutaneous Pco(2), and Borg dyspnea sco

183 ovements were quantified by laryngeal muscle EMG activity and subglottal pressure changes.

184 ted in conscious rats while EEG, neck muscle EMG, blood pressure (BP), and breathing were recorded.

185 recorded differences in leg depressor muscle EMGs and with differences in the responses of depressor

186 haustion while their brain (EEG) and muscle (EMG) activities were recorded.

187 Stroop task by combining electro-myography (EMG) and event-related brain potentials (ERPs).

188 NCS/EMG of POEMS patients identified through retrospective r

189 NCS/EMG of POEMS syndrome suggests both axonal loss and demy

190 in temperatures), cortical and VTA EEG, neck EMG activity, and locomotion in freely moving rats.

191 eminal ganglion sensory-evoked responses nor EMG activity were detected during the same period.

192 the timing of activity and the amplitude of EMG bursts in SOD1G93A mice.

193 neural hijacking." Evidence from analysis of EMG activity evoked by repetitive microstimulation (200

194 An analysis of EMG activity showed that the rake task involved a comple

195 ear components contribute to the decoding of EMG of major muscles used in the task.

196 pinal cord hemisection (HX), implantation of EMG wires into selected hind limb muscles, and/or inject

197 le has raised awareness of the importance of EMG for its early detection.

198 ts with lower limb amputations, inclusion of EMG signals and temporal gait information reduced classi

199 and more symmetrical, and the modulation of EMG activity across the step cycle increased bilaterally

200 ed by observations of equivalent patterns of EMG discharges in spontaneously breathing preparations,

201 e, broad-duration (40-50 ms) central peak of EMG-EMG synchronization was observed for infants younger

202 ion (continuous mapping) based projection of EMG into external commands were applied while artificial

203 to re-evaluate the controversial reports of EMG-torque relation between impaired and non-impaired si

204 edian of 2 sessions (range, 1-3 sessions) of EMG-guided, respiratory-targeted biofeedback treatment;

205 that M1 output effects obtained with StTA of EMG activity are highly stable across widely varying joi

206 ts (facilitation or suppression) in StTAs of EMG activity are remarkably stable in the presence of jo

207 StTAs of EMG activity from 24 forelimb muscles were collected fro

208 the largely bell-shaped patterns typical of EMG activity associated with natural goal directed movem

209 re correlated with the regional variation of EMG and muscle motion onset, contraction level and speed

210 Analyses of EMGs using a nonnegative matrix factorization algorithm

211 14-32 Hz) frequencies in both SMC-EEG and OP-EMG decreased with age, correlating inversely with motor

212 face electromyogram of opponens pollicis (OP-EMG)], and their coherence in children (4-12 years of ag

213 had no discernible effect on food intake or EMG amplitude.

214 tor adaptation task (for either kinematic or EMG measures) on Day 1.

215 Paediatric EMG, while a daunting technical challenge to some practi

216 This PAG-EMG coupling was only present for the onset of freezing

217 Coherence between paired EMG recordings from tibialis anterior muscle in the 20-4

218 hanges in tremor amplitude (using peripheral EMG measures as a proxy for tremor-related neuronal acti

219 When SOL(R) EMG remained in a defined range, PT(R) stimulation just

220 rthritic rats, blockade of vlPAG EP3R raised EMG thresholds to C-nociceptor activation in the area of

221 sedated female cebus monkeys while recording EMG signals from intrinsic hand and forearm muscles.

222 orrelation between firing rate and rectified EMG.

223 gnal computed as a weighted sum of rectified EMG signals from multiple muscles at the given joint.

224 ol of both spinal nociceptive flexion reflex EMG activity and individual dorsal horn neuron firing pr

225 n vlPAG modulated noxious withdrawal reflex (EMG) thresholds to preferential C-nociceptor, but not A-

226 he size and shape of the gain curve relating EMG to acceleration.

227 In return, EMG data provided strong constraints to discriminate bet

228 n adipose tissue temperatures; and shivering EMGs in anesthetized rats following central and localize

229 idine (100 mug/kg, i.v.) inhibited shivering EMGs, BAT SNA, and BAT thermogenesis, effects that were

230 LFPs) and surface electromyographic signals (EMGs) from the extensor and flexor muscles of the contra

231 Simultaneous EMG and SBP were acquired from elderly group (69 +/- 4 y

232 dogs, multiunit and single motor unit (SMU) EMG activity was monitored in the dorsal portion of the

233 Prolonged agitation was observed in some EMG+ DBA/2J (5 of 13), but not in A/J mice.

234 comparison subjects, as reflected by startle EMG.

235 reinnervated muscles can produce sufficient EMG information for real-time control of advanced artifi

236 Surface EMG signals were recorded from all participants and deco

237 ode detects different sources from a surface EMG system, as only one MU spike train was found to be c

238 Torque and surface EMG signals were sampled continuously.

239 d based on expired gas analysis, and surface EMG was used to record the activity of four bilateral le

240 Ultrasound and surface EMG were recorded from the calf and tibialis anterior (T

241 e performed connectivity analysis of surface EMG from ten leg muscles to extract the muscle networks

242 nnel linear array was used to record surface EMG of the biceps brachii muscles from both impaired and

243 uscle, which cannot be analysed with surface EMG, with successful identification of MU activity.

244 hese instants to trigger and average surface EMGs detected from multiple skin regions along gastrocne

245 nemius and soleus are represented in surface EMGs detected with different inter-electrode distances.

246 ively may result in the detection of surface EMGs insensitive to gastrocnemius activity without subst

247 possibly leading to the detection of surface EMGs insensitive to muscle activity.

248 > SBP) as well as control the postural sway (EMG --> COPr) through the significantly higher causal dr

249 The EMG signals were decomposed into discharges of motor uni

250 The EMG+ A/J group showed longer sleep time and less MT coun

251 h the magnetic search coil technique and the EMG activity of the orbicularis oculi muscle.

252 cular transmission failure increased and the EMG measures decreased after injury in mdx mice only.

253 Six were used to compare the EMG and kinematic locomotor characteristics during walki

254 In postural conditions the EMG spectrum is relatively flat whereas the acceleration

255 e middle response was potentiated during the EMG bursts, whereas after 4 weeks, both the middle and l

256 he EEG --> EMG direction and 29.5 ms for the EMG --> EEG direction were closer to the expected conduc

257 cially introducing non-stationarities in the EMG signals.

258 y role of peripheral adaptive changes in the EMG-torque relations in chronic stroke.

259 remor cannot be attributed to changes in the EMG.

260 discharge activity and the magnitude of the EMG activity was equally constant during gait modificati

261 linked to the amplitude and duration of the EMG bursts during locomotion facilitated by epidural sti

262 ep cycle and step-to-step variability of the EMG, as well as flexor-extensor coactivation.

263 Distribution of the slope of the EMG-torque relations for the individual channels showed

264 onger sleep time and less MT counts than the EMG- A/J group.

265 These findings suggest that the EMG-torque relations are likely mediated and influenced

266 eir discharge rates were related more to the EMG activity of the OO muscle than to the learning curve

267 graphic recordings by experts blinded to the EMG results.

268 cle moment arms, and joint moments while the EMG data are used to estimate muscle activations.

269 Analysis of the EMGs demonstrated that these vocalizations consist of on

270 ort-interval intracortical inhibition, a TMS-EMG measure of synaptic GABAAergic inhibition, and other

271 ation of the CS was significantly coupled to EMG-related freezing behavior.

272 aluated differences in parameters related to EMG amplitude (peak and area) and timing (phase and skew

273 developing an alternative or adjunct test to EMG based on the appearance of nerve fibers in corneal m

274 hypothesis explaining the increase in tongue EMG activity in obese patients with OSA.

275 This increase in tongue EMG activity is thought to be related to either increase

276 e plant, defined as the mapping from the two EMG signals to the two segment angles.

277 pping from the two segment angles to the two EMG signals.

278 channel electrode transparent to ultrasound, EMG and M(otion)-mode ultrasound were recorded simultane

279 the onset of tremor episodes (assessed using EMG) drove network activity through the internal globus

280 ntrast to clinical diagnostic measures using EMGs, which are performed on quiescent patients, we moni

281 /- 19 mm) and 52 degrees C (M: 179 +/- 34 W, EMG: 3.3 +/- 2.1% MVC, WBTS: 53 +/- 28 mm).

282 ingestion at 37 degrees C (M: 215 +/- 47 W, EMG: 3.9 +/- 2.5% MVC, WBTS: 33 +/- 2 mm), values were d

283 g ingestion at 7 degrees C (M: 269 +/- 77 W, EMG: 5.5 +/- 0.9% MVC, WBTS: 14 +/- 12 mm), 22 degrees C

284 4 +/- 12 mm), 22 degrees C (M: 270 +/- 86 W, EMG: 5.6 +/- 1.0% MVC, WBTS: 18 +/- 19 mm) and 52 degree

285 In both strains, CMs occurred when EMG was high; MTs were present during silent/low EMG act

286 ) mechanical sensor data in combination with EMG data and historical information from earlier in the

287 aging is virtually noninvasive compared with EMG, such a test may be administered more liberally and

288 Rats were implanted with EMG electrodes in both solei (SOL(R) and SOL(L)) and rig

289 Sprague Dawley rats were implanted with EMG electrodes in SOL and TA and stimulating cuffs on th

290 hose levels of neuropathy were measured with EMG and from healthy subjects.

291 This distension can be reduced with EMG-guided, respiratory-targeted biofeedback therapy.

292 diated respiratory control during sleep with EMG (EMG+) or without EMG (EMG-).

293 though the correlation of this activity with EMGs of proximal arm muscles is as strong as in motor co

294 trol during sleep with EMG (EMG+) or without EMG (EMG-).

295 erved in these neonatal mice with or without EMG instrumentation.

296 s can be used to indicate wake state without EMG.

297 the viscosity of the emulsions containing XG/EMG gum mixtures was significantly higher (P<0.05) of al

298 rate of oxidation in emulsions containing XG/EMG gum mixtures, compared to XG, guar (GG), and XG/GG g

299 Increasing concentrations (0-0.3wt%) of XG/EMG gum mixtures did not affect the droplet size of emul

300 These results indicate that XG/EMG gum mixtures can be used in O/W emulsions to increas