Details of the measurement are described elsewhere (Yamada et al., 2010 (link)). Briefly, electrodes for current injection (20 × 20 mm, Red Dot; 3M, United States) were placed over the dorsal surfaces of the right hand and right foot. Sensing electrodes (20 × 20 mm, Red Dot; 3M, United States) were attached on the dorsal surface of the right wrist and right ankle for whole-body PhA measurement, and attached on the right greater trochanter and the lateral aspect of the knee joint space of the right lower limb for thigh PhA measurement. By using SFB7 (ImpediMed, Australia), reactance and resistance of the whole-body and thigh were measured three times. PhA was calculated as [arctangent (reactance/resistance) × 180°/π] for each measurement at single frequency of 50 kHz. Mean values of three values for whole-body and thigh PhA were used for further analyses.
Red dot
Manufactured by 3M
Sourced in United States, Germany, Belgium
The Red Dot is a laboratory equipment product manufactured by 3M. It serves as a general-purpose adhesive dot for various applications in the laboratory setting. The product's core function is to provide a simple and convenient way to temporarily adhere or mark items within the laboratory environment.
Automatically generated - may contain errors
Lab products found in correlation
Zerowire wireless emg system, by Aurion (2 mentions)
Model ds7a, by Digitimer (1 mentions)
T pump, by Stryker (1 mentions)
D360 amplifier, by Digitimer (1 mentions)
Micro 1401, by Cambridge Electronic Design (1 mentions)
Blue sensor n, by Ambu (1 mentions)
Ced 1902, by Cambridge Electronic Design (1 mentions)
Keithley 6514, by Tektronix (1 mentions)
Intellivue mx700 monitor, by Philips (1 mentions)
21 protocols using red dot
1
Whole-Body and Thigh Phase Angle Measurement
2
Electrophysiological Assessment of Cardiac Conduction
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After cannulation of the right jugular vein, quadripolar catheters were placed under fluoroscopic guidance at the junction of the superior vena cava to the right atrium and in the right ventricular apex. A UHS 20 stimulus generator (Biotronik, Berlin, Germany) was used for intracardiac stimulation and the EP Lab duo system (Bard Electrophysiology Division, Lowell, MA) was used for recording, analyzing, and storing ECGs. If induction of AF episodes required electrical cardioversion, electrophysiological studies were paused for at least 30 minutes afterwards.
Pacing thresholds ranged from 0.5 to 2 V at 2.9 ms, and stimulation was performed at twice the diastolic pacing threshold. For measurements of effective refractory periods, a conditioning train of 9 basic stimuli (S1) was followed by a diastolic extrastimulus (S2) starting 150 ms longer than the expected effective refractory period. Coupling intervals of extrastimuli were decreased in 10‐ms decrements until refractoriness of the S2 stimulus was achieved. The shortest coupling interval eliciting a propagated atrial response was taken as the effective refractory period. Surface ECGs were recorded using conventional adhesive electrodes (3M red dot, 3M, Maplewood, MN) in the classical Einthoven /Goldberger /chest‐lead configurations, and QT intervals were corrected using Bazett's formula.19
Pacing thresholds ranged from 0.5 to 2 V at 2.9 ms, and stimulation was performed at twice the diastolic pacing threshold. For measurements of effective refractory periods, a conditioning train of 9 basic stimuli (S1) was followed by a diastolic extrastimulus (S2) starting 150 ms longer than the expected effective refractory period. Coupling intervals of extrastimuli were decreased in 10‐ms decrements until refractoriness of the S2 stimulus was achieved. The shortest coupling interval eliciting a propagated atrial response was taken as the effective refractory period. Surface ECGs were recorded using conventional adhesive electrodes (3M red dot, 3M, Maplewood, MN) in the classical Einthoven /Goldberger /chest‐lead configurations, and QT intervals were corrected using Bazett's formula.
3
Continuous Cardiac Monitoring in Dogs
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At baseline and on the follow-up days (1, 3, and 6 months after treatment), all conscious, resting dogs were subjected to a 1 h continuous Holter recording while they were in a quiet place with their owner, as previously described [20 (link)]. Basically, foam monitoring ECG electrodes (3 M™ Red Dot™, 3 M Health Care, St. Paul, MN, USA) were placed on to the skin over the thorax to form transthoracic leads (3 channels) and connected to a 3-channel cardiac Holter monitor Digital Walk (FM-180, Fukuda Denshi Co., Tokyo, Japan). Owners were advised to give drugs to the dogs before 08:00 am and the time for recording was arranged to be performed between 09:00 am and 11:00 am.
4
EMG Activity Recording and Normalization Protocol
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EMG activity was recorded using bipolar electrodes (Ambu Blue sensor N-10-A/25, Ambu A/S Ballerup; recording area 0.5 cm2, interelectrode distance 2 cm) placed over the soleus muscle and the proximal and distal parts of the tibialis anterior muscle (TAprox and TAdist, respectively). The skin was gently abraded with sandpaper (3M red dot; 3M, Glostrup, Denmark). A ground electrode was placed on the distal part of the tibia. EMG signals were filtered (band-pass, 5 Hz–1 kHz), amplified (500-2000x), sampled at 2 kHz, and stored on a PC for offline analysis.
All EMG and H-reflex measurements (see below) were normalized to the maximal M-response (Mmax) evoked in either the TA or soleus muscle by supramaximal stimulation (1 ms rectangular pulses; model DS7A, Digitimer, Hertfordshire, UK) of the common peroneal nerve or the tibial nerve, respectively. In these measurements, the intensity of stimulation of the respective nerves was increased from a subliminal level until there was no further increase in the peak-to-peak amplitude of the M-response with increasing stimulation intensity [22 (link)].
All EMG and H-reflex measurements (see below) were normalized to the maximal M-response (Mmax) evoked in either the TA or soleus muscle by supramaximal stimulation (1 ms rectangular pulses; model DS7A, Digitimer, Hertfordshire, UK) of the common peroneal nerve or the tibial nerve, respectively. In these measurements, the intensity of stimulation of the respective nerves was increased from a subliminal level until there was no further increase in the peak-to-peak amplitude of the M-response with increasing stimulation intensity [22 (link)].
5
ECG Monitoring during Feeding
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Daily surface ECGs were recorded using a Mortara ELI 230 ECG recorder (Mortara instrument Inc., Milwaukee, WI, United States) with conventional adhesive electrodes (3M red dot, 3M, Maplewood, MN, United States) in the classic Einthoven/Goldberger chest lead configuration during feeding, and QT intervals were corrected using the formula of Bazett (1920) (link).
6
Continuous Physiological Monitoring in Rats
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Electrocardiography, pulse oximetry, respiratory rate, and rectal temperature were monitored in a sentinel animal throughout the infusion (Supplementary Figure 2 ), as follows. Rats were continuously monitored using a Philips Intellivue MP70 patient monitor attached to SpO2 sensor (Covidien OxiMax Adhesive; Dublin, Ireland), neonatal pre-wired EKG monitoring electrodes (3M™ Red Dot™; St Paul, MN, United States) and a rectal temperature probe (Covidien 400 Series General Purpose Temperature Probe, 9Fr; Dublin, Ireland). Body temperature was maintained at 37–39°C using a perfused water pad underneath the animals (T/Pump, Stryker; Kalamazoo, MI, United States). Animals under ketamine infusion remained hemodynamically stable with blood oxygenation > 95% and in sinus rhythm. Total intravenous fluids administered did not exceed the recommended daily maintenance amount of 80 mL/kg/day (Waynforth and Flecknell, 1992 ). Physiological monitoring of the female group during ketamine infusion was also performed and parameters were within normal limits.
7
Body Composition and Phase Angle Analysis
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Height, weight, and waist circumference were measured, and body mass index (BMI) was calculated as weight in kilograms divided by height in meters squared (kg/m2). The body composition was estimated, and the PhA was measured using the BIS (SFB7, ImpediMed, Pinkenba, Australia) as follows10 (link): Two injectable electrodes were placed on the dorsal surface of the right hand and foot, and detecting electrodes were placed on the dorsum of the right wrist and ankle (Red Dot, 3M Health Care, MN, USA). BIS was measured in the supine position, between 8 and 10 A.M., and before any physical fitness test. Fat-free mass (FFM), body cell mass (BCM), and percent body fat (%fat) were obtained using the BIS software (Bio-imp version 5.5.0.1, ImpediMed). Participants were divided into low and high PhA groups based on the sex-specific median of the PhA results (5.4 for women and 6.5 for men).
8
Non-invasive Auriculotemporal and Carotid Monitoring
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EC3 Conductive adhesive gel (Natus Medical Incorporated. CA, USA) was applied to the electrode surface using a syringe to improve conductivity. The device was then applied to the neck with the rostral electrode approximately at the skin above the Trigeminal nerve auriculotemporal branch and the nodose ganglion and the caudal electrode at the skin above the carotid artery. Once attached, the PET backing was peeled off (Fig. 1 a). The ZIF connector was attached to a breakout board (Adafruit Industries, Inc. NY, USA), which was then connected via cables to a biopotential data acquisition HackEEG board (Starcat LLC Seattle, WA) along with ground and reference electrodes (3 M Red Dot, 3 M, Inc—Saint Paul, MN). The impedance between the electrodes and the skin was measured by the Digitimer D360 amplifier (Digitimer Ltd, UK). Electrocardiography (ECG) was also monitored by the 3 M electrodes that were placed on the right upper chest and left bottom rib.
9
Quadriceps Motor-Evoked Potential Assessment
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To collect quadriceps motor-evoked potentials (MEPs), bipolar Ag-AgCl disc electrodes (Norotrode 20, Myotronics Inc., Kent, WA, USA) with an inter-electrode distance of 2.2 cm were placed on the skin overlying the vastus lateralis muscle belly in accordance with surface electromyography for the non-invasive assessment of muscles (SENIAM) guidelines [28 (link)]. A ground electrode (Red Dot, 3 M, St Paul, MN, USA) was positioned slightly below the midpoint of the bony surface of the tibia. Prior to electrode placement the skin was shaved, abraded and cleaned with alcohol to reduce signal impedance. All EMG signals were amplified (x1,000), filtered (10 Hz to 1,000 Hz) (AMT-8, Bortec Biomedical, Alberta, Canada) and sampled at 2,000 Hz (Micro 1401, Cambridge Electronic Design, Cambridge, UK) before being stored on a computer for further analysis. Three 5-s maximum effort voluntary contractions of the quadriceps were performed prior to the first baseline measurements. The largest amplitude root mean square of the vastus lateralis EMG signal within a 1-s window was taken as the MVC. This was used to standardise the level of muscle activation (approximately 10% of MVC) during the TMS measures performed during active muscle contraction.
10
Surface EMG Muscle Activity Recording
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Surface electromyography (EMG) was recorded from left BB, left pronator teres (PT) and right first dorsal interosseous (FDI) using disposable Ag/AgCl electrodes (10 mm diameter for left PT and right FDI, Blue Sensor N, Ambu, Denmark, 20 mm diameter for left BB, Red Dot, 3M, United States), following standard skin preparation. For BB and PT, the electrodes were placed over the muscle belly in a bipolar montage. The FDI electrodes were placed in a belly-tendon montage. EMG signals were amplified (CED 1902; Cambridge Electronic Design, Cambridge, United Kingdom), band-pass filtered (10–1000 Hz), sampled at 2 kHz (CED 1401), and stored to computer for offline analysis using Signal software (Signal V4.09).
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