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 activity of all the recorded finger muscles were sig

3 EMG activity was measured from the tibialis anterior and

4 EMG coherence declined with age and at the age of 10-12

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

6 EMG recordings were made from right ankle dorsiflexor an

7 EMG revealed predominantly myopathic changes in the axia

8 EMG showed silent contractures in approximately half of

9 EMG showed that learning augments the muscular response

10 EMG signals were decoded with a pattern-recognition algo

11 EMG was obtained by hydrolyzing native guar gum using al

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

13 EMG-EMG coherence was calculated from two separate elect

14 ring voiding and a reduction of the abnormal EMG high-frequency activity in the external urethral sph

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

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

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

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

19 reached the cortex at the same time or after EMG onset, consistent with the idea that the temporal or

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

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

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

23 n deep learning testing accuracy for ECG and EMG up to the wireless distance of 240 mm.

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

25 EEG and EMG recordings revealed that ppDIO increases sleep durin

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

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

28 spike rate variability, sample entropy, and EMG activity occurred in 6% desflurane with 40.0% freque

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

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

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

32 MMG and EMG amplitude and frequency were compared before, during

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 ion and 5-15 Hz coherence between antagonist EMGs was observed more frequently in children with cereb

38 no age-related decline in tibialis anterior EMG amplitude.

39 -impaired sides using linear electrode array EMG recordings.

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

41 apses are tonically active during background EMG activity.

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

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

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

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

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

47 ed that independent standing was promoted by EMG activity characterized by lower median frequency, lo

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

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

50 Chronic EMG electrodes were implanted into vastus lateralis, bic

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

52 by individual motor units from the composite EMG signals.

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

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

55 parable to those recorded using conventional EMG recording systems.

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

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

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

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

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

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

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

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

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

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

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

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

68 It can also account for the EEG, EMG, and autonomic profiles of wake, REM, and NREM state

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

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

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

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

73 s and sleep-related variables, we set up EEG/EMG and video recordings and found that A. cahirinus sle

74 the invasive nature of fine wire electrodes, EMG is impractical for use outside of a laboratory envir

75 and Electrocardiogram (ECG), Electromyogram (EMG), and Electrooculogram (EOG), respectively.

76 electroencephalogram (EEG), electromyogram (EMG), and autonomic profiles.

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 ion relative to the onset of electromyogram (EMG) activity rather than using the EEG peak.

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

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

82 ty trajectories from surface electromyogram (EMG) signals.

83 Bipolar surface electromyogram (EMG) was recorded from several muscles and was expressed

84 t contamination of voluntary electromyogram (EMG) during FES application makes the technique difficul

85 Surface electromyograms (EMGs) were taken from muscles that either move the pinna

86 t may contribute to surface electromyograms (EMGs).

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

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

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

90 Electromyographic (EMG) analysis indicating denervation occurred between 10

91 Electromyographic (EMG) and electroencephalographic (EEG) recordings were u

92 lantarflexion errors) and electromyographic (EMG) activity.

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

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

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

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

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

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

99 0 and 100 mg of S44819 on electromyographic (EMG) and electroencephalographic (EEG) measures of corti

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

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

102 As a result, the electromyographic (EMG) activity associated with digit movement at differen

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

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

105 Electromyography (EMG) is the standard technology for monitoring muscle ac

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

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

108 We collected kinematic and electromyography (EMG) data during forward and backward locomotion at diff

109 nt body regions in MRI and electromyography (EMG) data were collected from 108 classical ALS patients

110 etic resonance imaging and electromyography (EMG) experiment with viewing of emotional and neutral fa

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

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

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

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

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

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

117 imultaneously, fNIRS, EEG, electromyography (EMG), electrocardiography and behavioral measures were a

118 ecific, we measured facial electromyography (EMG) from five muscle sites (corrugator supercilii, leva

119 were assessed using facial electromyography (EMG), a proxy of affective state.

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

121 to extract synergies from electromyography (EMG).

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

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

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

125 h vastus lateralis surface electromyography (EMG).

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

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

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

129 conditioning protocol uses electromyography (EMG) to measure reflexes from specific muscles elicited

130 Motion capture with electromyography (EMG) assessment of 15 muscles was performed on 48 partic

131 The nanomembrane electrode array enables EMG recording from a large surface area on the skin and

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

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

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

135 1 from which ICMS could simultaneously evoke EMG responses in different combinations of LAD, RAD, and

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

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

138 cerebellum produced maximal CBI of PA-evoked EMG responses at an interstimulus interval of 5 ms (PA-C

139 t advances in wearable electronics, existing EMG systems that measure muscle activity for operant con

140 In both experiments, EMG recordings showed larger activity at the ear on the

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

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

143 effect of wrist posture on extrinsic finger EMG activity in able-bodied subjects, these results may

144 For the finger flexors, EMG variations with wrist posture were most prominent fo

145 Here, we introduce a novel framework for EMG data processing that implements spectral analysis by

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

147 by using an exponentially modified Gaussian (EMG) fitting model for near-Gaussian distributed subpeak

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

149 Genioglossus EMG signals were analyzed offline by automated software

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

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

152 ol removes cross-talk associated with global EMG recordings, thus allowing direct in vivo interrogati

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

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

155 d by high-density surface electromyogram (HD-EMG) decomposition to estimate muscle excitations.

156 playing asynchronous firing pattern and high EMG activity was found unexpectedly in deep anesthesia.

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

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

159 showed a significant age-related decline in EMG amplitude reaching an adult level at 10-12 years of

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

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

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

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

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

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

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

167 the cognitive control network, and increased EMG activity and heart rate during spider conditions in

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

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

170 rol of muscles targeted by our intervention, EMG signals are a suitable alternative to an EEG for ind

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

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

173 - 460 ms before the start of significant LFP-EMG coherence.

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

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

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

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

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

179 n with cerebral palsy generally showed lower EMG levels than typically-developing children and larger

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

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

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

183 were extracted from the genioglossus muscle EMG signals.

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

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

186 rough electrical stimulation or multi-muscle EMG recordings.

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

188 hods: Video polysomnography with neck-muscle EMG was performed in patients with COPD who were recover

189 icant coupling between the antagonist muscle EMGs.

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

191 NCS/EMG of POEMS patients identified through retrospective r

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

193 p-wake pattern was monitored by EEG and neck EMG recordings and breathing by whole-body plethysmograp

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

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

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

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

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

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

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

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

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

203 Loss of EMG amplitude due to the overlap of motor unit action po

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

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

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

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

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

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

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

211 effect of the sleep manipulation was seen on EMG.

212 ; it has potential to automatically optimize EMG electrode positioning, which may reduce setup time a

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

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

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

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

217 ally-developing children showed a broad peak EMG-EMG synchronization (>100 ms) associated with large

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

219 ce in parietal areas and affected the phasic EMG correlation between both arms.

220 Depending on the wrist posture, EMG activity changed by up to 70% in individual finger m

221 characterizing epidural stimulation-promoted EMG activity resulting in independent standing.

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

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

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

225 (EMGnc) is superior to the actual rectified EMG signal as estimator of the neural drive to muscle.

226 strated analytically that an ideal rectified EMG signal without amplitude cancellation (EMGnc) is sup

227 a stronger correlation between the rectified EMG and the neural drive and that amplitude cancellation

228 hed by the correlation between the rectified EMG and the neural drive only when the level of amplitud

229 r, may distort the spectrum of the rectified EMG and thereby its correlation with the neural drive.

230 This implies that valid use of the rectified EMG as an estimator of the neural drive requires low con

231 ation distorts the spectrum of the rectified EMG signal.

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

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

234 Active FES, the resulting EMG-FES system was validated in a typical use case among

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

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

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

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

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

240 d with low tibialis anterior and high soleus EMG with no significant coupling between the antagonist

241 Surface EMG signals were recorded from 15 healthy participants (

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

243 Torque and surface EMG signals were sampled continuously.

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

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

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

247 The rectified surface EMG signal is commonly used as an estimator of the neura

248 ctors, including skin impedance with surface EMG and the invasive nature of fine wire electrodes, EMG

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

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

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

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

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

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

255 Mean 'final' gait termination EMG activity (right gastrocnemius) was greater in the pa

256 The EMG signals were decomposed into discharges of motor uni

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

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

259 del of motor neuron activity, force, and the EMG signal.

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

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

262 cially introducing non-stationarities in the EMG signals.

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

264 remor cannot be attributed to changes in the EMG.

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

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

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

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

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

270 graphic recordings by experts blinded to the EMG results.

271 rominent for index finger muscles, while the EMG activity of all finger extensor muscles were modulat

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

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

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

275 Mechanomyography (MMG) is an alternative to EMG, which shows promise in pervasive applications.

276 paired with the similar results compared to EMG, suggest that such a system could be suitable in unc

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

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

279 everal muscles and was expressed relative to EMG during maximum contractions (%EMGmax).

280 measures of muscle activity were similar to EMG in timing, duration, and magnitude during the fatigu

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

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

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

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

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

286 k displacement, step timing, gait velocity), EMG responses, and subjective measures of state anxiety/

287 an optional comb filter to extract voluntary EMG from muscles under FES.

288 to date either poorly extract the voluntary EMG from the artefacts, require a special hardware or ar

289 Proportional control of FES using voluntary EMG may be used for this purpose.

290 /- 19 mm) and 52 degrees C (M: 179 +/- 34 W, EMG: 3.3 +/- 2.1% MVC, WBTS: 53 +/- 28 mm).

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

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

293 4 +/- 12 mm), 22 degrees C (M: 270 +/- 86 W, EMG: 5.6 +/- 1.0% MVC, WBTS: 18 +/- 19 mm) and 52 degree

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

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

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

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