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Reduction and Fixation of Sacroiliac joint Dislocation by the Combined Use of S1 Pedicle Screws and an Iliac Rod
Published in Kai-Uwe Lewandrowski, Donald L. Wise, Debra J. Trantolo, Michael J. Yaszemski, Augustus A. White, Advances in Spinal Fusion, 2003
Kai-Uwe Lewandrowski, Donald L. Wise, Debra J. Trantolo, Michael J. Yaszemski, Augustus A. White
Myogenic recording can be performed at one or multiple peripheral muscles of choice by using surface or needle electrodes (Fig. 2). The motor response is recorded as a compound muscle action potential (CMAP). Logically, muscle relaxants influence the use of this potential. Hence, complete neuromuscular blockade must be avoided during monitoring, and if muscle relaxants are needed, the administration of muscle relaxants has to be titrated to such level that it is still possible to record muscle responses. The great advantage of myogenic monitoring is that the amplitudes are large and the latencies are reliable so that no averaging processes are needed. Furthermore, the surface electrodes can be placed on several different muscles providing a practical and simple monitoring method that also allows monitoring of individual muscle groups.
Grip strength of occupational workers in relation to carpal tunnel syndrome and individual factors
Published in International Journal of Occupational Safety and Ergonomics, 2020
Greesh Kumar Singh, Sanjay Srivastava
The stimulus level was determined for each subject by increasing and reapplying a stimulus along the median nerve fibers, until a clearly defined action potential response was produced. The resultant waveform of the nerve action potential was recorded as the baseline measure. The filter setting was 2 Hz to 10 kHz for surface motor nerve action potential recordings [25]. The motor conduction velocity of the median nerve, from elbow to wrist, was recorded for each subject. The latency was measured from the stimulus artifact to the beginning of the compound muscle action potential of the APB muscle. The distance between the stimulating electrode at the wrist and the recording electrode at the APB muscle was 125 ± 5 cm. The distance between the stimulating electrode at the wrist and the stimulating electrode at the elbow was 25 ± 5 cm. MNCV can be calculated using Equation (1): where MNCV = motor nerve conduction velocity.
Facial muscle reanimation by transcutaneous electrical stimulation for peripheral facial nerve palsy
Published in Journal of Medical Engineering & Technology, 2019
Eeva Mäkelä, Hanna Venesvirta, Mirja Ilves, Jani Lylykangas, Ville Rantanen, Tuija Ylä-Kotola, Sinikka Suominen, Antti Vehkaoja, Jarmo Verho, Jukka Lekkala, Veikko Surakka, Markus Rautiainen
The NCS and needle EMG data were obtained from 21 subjects. Three subjects declined the examination. Numeric data for the bilateral NCS of the facial nerve were available from 16 subjects. The compound muscle action potential amplitude registered from the nasalis muscle ranged between 0.0 and 1.8 mV (M = 0.8, SD = 0.6) for the paralysed side and from 0.9 to 2.3 mV (M = 1.7, SD = 0.5) for the unaffected side. Needle EMG data were available for the frontalis and orbicularis oris muscles from all 21 subjects and for the orbicularis oculi muscle from 20 subjects. Five subjects had signs of ongoing reinnervation in at least one muscle. Four subjects had a finding of total denervation of at least one muscle. The severity of the neurogenic damage in the needle EMG data correlated positively to the degree of the paresis assessed with SFGS in the frontalis muscle (rs = 0.701, p < .001). The correlation was not, however, significant between the needle EMG finding and the degree of the paresis in the orbicularis oris muscle (rs= −0.307, p > .05) nor in the orbicularis oculi muscle (rs= −0.063, p > .05).
Effects of sleep deprivation on perceived and performance fatigability in females: An exploratory study
Published in European Journal of Sport Science, 2022
Justine R. Magnuson, Hogun J. Kang, Mathew I. B. Debenham, Chris J. McNeil, Brian H. Dalton
Through a combination of complementary assessments, one can gain insights into physiological changes occurring from the motor cortex to muscle as a result of SD. For example, stimulation of the motor cortex, peripheral nerve, or muscle belly during a maximal voluntary contraction (MVC) reveals suboptimal voluntary activation (VA) of a muscle if additional force (a superimposed twitch, SIT) is evoked (Merton, 1954). Moreover, external stimuli can assess excitability at different levels of the nervous system. In a non-exercised state, lower VA with SD was reported for some (Arnal et al., 2016; Skein et al., 2011) but not all studies (Skurvydas et al., 2020). Neural excitability appears to be unaffected by SD, as assessed by the F-wave and motor evoked potential (MEP) (Manganotti et al., 2001) or H-reflex and V-wave (Gonçalves et al., 2021). However, given the challenges of interpreting H-reflexes, V-waves and F-waves (McNeil et al., 2013), clearer insight into peripheral, motoneuronal, and cortical excitability would be obtained by recording the maximal compound muscle action potential (Mmax), cervicomedullary motor evoked potential (CMEP) normalized to Mmax, and MEP normalized to CMEP, respectively. Further, measures of VA or neural excitability do not reveal if perceptions of fatigue and effort are factors that underlie potential SD-related impairments (e.g. reduced strength; Arnal et al., 2016; Skein et al., 2011). As such, VA as well as cortical, motoneuronal, and peripheral excitability should be evaluated alongside perceptions of fatigue and effort to elucidate sources of SD-related impairments in neuromuscular function.