Neuromuscular electrical stimulation (NMES) is used in various contexts due to its benefits related to motor learning, preservation of denervated muscles, training in non-cooperative / sedated individuals, pain control and relief, and improvement of athletes, young, and elderly functional performance, besides people with severe cardiopulmonary disease. Even with the solid accumulated knowledge about NMES, its potential is not fully understood, with questions to be clarified for the achievement of greater effectiveness by clinicians and scientists in the various possibilities of application.

The effects of NMES have not been determined yet in quadriceps femoris muscle in different lengths, which can be accomplished by changing the angle of the joint or joints it crosses (hip and knee). There is probably only one trial (Fahey et al., 1984) addressing this issue. In the study, two positions were compared: knee and hip extended versus knee (65º) and hip (angle not mentioned) flexed, although the purpose of the study was to evaluate only the influence of knee position. Authors found that NMES can increase isometric and isokinetic strength, but that it may be more effective to improve isokinetic performance if knee is flexed during treatment. Questions are then raised because groups were tested only with knee flexed and not also extended, and because the change in hip angle probably influenced the results. This study was also the only one found by Bax et al. (2005).

Justificative: NMES is an established tool applied as the main or an supplementary treatment in rehabilitation programs. It is necessary to establish the influence of lower limb position in the outcomes. Therefore, this study will address for the first time the effects of NMES on quadriceps voluntary and evoked strength, electrical activity, architecture, and tendon properties.

Hypothesis: In healthy young adults, the variation of the hip and knee joint angle for NMES may affect the knee extensor torque, quadriceps muscle electromyographic activity, architecture, and tendon-aponeurosis complex elongation, and tendinous properties of the patellar tendon. These factors will be facilitated when the participants are seated with the knee at 60º flexion. On the other hand, when the quadriceps is more elongated (lying with knee at 60º) or shortened (dorsal decubitus or sitting with knee extended (0º), such adaptations will not be significant.

Methods: This is a crossover trial with healthy young male subjects. The procedures will be performed in the Neuromuscular Performance Laboratory of the Faculty of Ceilândia / University of Brasília and in the Force Laboratory of the Faculty of Physical Education / University of Brasília. Subjects will perform 5 visits to the laboratory (the first visit will be a familiarization session to test NMES in each position), with a minimum interval of 48 hours between visits. Volunteers will be informed of all the procedures, purposes, benefits, and risks of the study and will sign an informed consent form before participation (the project was approved by the University Research Ethics Committee N 99221818.9.0000.0029)

* Maximal Voluntary Isometric Contraction (MVIC): An isokinetic dynamometer will be used for recording torque. The equipment axis will be visually aligned with the axis of the knee (lateral epicondyle of the femur). The lever arm of the force transducer will be firmly attached 2-3 cm above the lateral malleolus with a strap. Angulations of hip and knee will be adjusted with a goniometer. Subjects will be firmly stabilized to the chair with belts across the chest and pelvic girdle to minimize body movement. Individuals will be instructed to cross their arms with hands on shoulders and extend the knee against the strap "by pushing gradually for 3 s (ramping contraction) up to the maximum force, maintaining it for 4 s, and then decrease de amount of force gradually for more 3 s". The number of contractions will correspond to the number of ultrasound evaluations: 4 muscles (rectus femoris and the three vastus) + proximal patellar tendon + distal patellar tendon x 3 measurements for each = 18, each one separated by 1 min of rest.
* Neuromuscular electrical stimulation (NMES): NMES will be used to produce a maximal electrically evoked isometric torque, which will be assessed in the familiarization and will be generated (15-18 times) after the end of the voluntary contractions protocol of the subsequent sessions. An electrical stimulator device will be used. Parameters will be verified using a digital oscilloscope. The device will be connected to cables that will be connected to two pairs of 25 cm2 adhesive electrodes. The first distal electrode will be placed at 80% of the line between the anterior superior iliac spine (ASIS) and the space where the medial ligament is located. The proximal electrode will be placed in the corresponding motor point, identified with a pen type electrode, in the vastus medialis. The other distal electrode will be positioned 2/3 of the line that forms from the ASIS to the lateral side of the patella, while the proximal electrode will be placed at the motor point, identified with a pen type electrode, in the muscular belly of the vastus lateralis. It will be used a pulsed current: frequency = 100 Hz, pulse duration = 400 μs, rise time = 3 s, ON time = 4 s, decay time = 3 s, and off time = 1 min. The intensity used will be the one obtained in the familiarization, or greater if tolerated.
* Surface electrical activity and activation level: Surface electromyography (EMG) activity of vastus lateralis, vastus medialis, and rectus femoris will be recorded bipolarly by two rounded electrodes of silver chloride, each measuring 20 mm in diameter and having a recording diameter of 10 mm and separated by an inter-electrode distance (center to center) of 20 mm. The electrodes will be positioned longitudinally in the muscle belly, and a reference electrode will be attached to the patella of the contralateral lower limb. As in the case of NMES electrodes, a marking will be made to ensure that in the following sessions the electrodes will be placed accordingly. The impedance reduction (\<5 kΩ) between the two electrodes will be obtained by abrasion of the skin with emery paper and cleaning with alcohol. EMG signals will be amplified with a bandwidth frequency of 15 Hz to 5.0 kilohertz (common mode rejection rate = 90 decibels, impedance = 100 milliohms, gain = 1000).
* Muscle architecture: Muscle thickness, pennation angle and fascicular length will be obtained in rest and during MVIC and NMES using a portable ultrasound in B mode with a linear transducer of 7.5 megahertz . Depth, gain, compression and ultrasound settings will be kept constant between assessments and from one patient to another. For each muscle, three videos will be obtained and the mean values will be used for statistical analysis. For better reproducibility, the evaluator will remove and reposition the transducer at the marked location. The videos will be stored on the device and then transferred to a computer for processing in specific softwares. The videos will be obtained with the transducer positioned in the longitudinal plane of the muscle, keeping it in parallel with the direction of the fascicles. Proper alignment of the transducer will be achieved when multiple fascicles are showed without interruption. Rectus femoris, vastus intermedius, vastus lateralis, vastus medialis will be evaluated, respectively, in the percentages 50%, 60% and 75% (proximal to distal) of the distance between the medial aspect of the anterior superior iliac spine and the superior border of the patella, as adapted from Blazevich et al. (2006). The rectus femoris and the vastus intermedius will be visualized on the anterior aspect of the thigh, the vastus lateralis will be visualized by moving the transducer 5 cm in the lateral direction from the midline and the vastus medialis will be visualized with the transducer 3 cm onto the medial direction of the thigh. The pennation angle is the angle formed between the echo of the deep aponeurosis of the muscles and the echo of the space between the fascicles, as measured 3 to 4 mm above the deep aponeurosis of the muscles. The fascicular length will be considered as the total length of the muscle fiber, however, because the fascicles are too long to be measured from the origin to the insertion, the estimated length will be obtained from the formula of Blazevich et al. (2006), which uses as variables the muscle thickness, the angle of the fascicle and the angle between the superficial and deep aponeurosis.
* Tendon-aponeurosis complex elongation: The myotendinous elongation will be estimated by the displacement of the deep aponeurosis. For the calculation will be used the recordings acquired for analysis of the muscular architecture. However, unlike the static nature of the data of the previous topic, this variable uses a dynamic approach, since the point (P) will be used as the contact point (insertion) of a fascicle in the deep aponeurosis at rest and the displacement of P when considering its final position during a maximum contraction. Therefore, the displacement of P (dL) is considered an indication of the elongation of the deep aponeurosis and the distal tendon.
* Tendon properties: The resting length of the patellar tendon will be measured by tracing its path with the ultrasound transducer in the longitudinal (sagittal) plane, starting from the patellar insertion to the insertion at the tibia, along the posterior surface of the tendon. The central region of the transducer will be placed in each of the tendon insertions (considering its posterior surface) and then a mark on the skin will be made at that point and a measuring tape will be used for the tendon length measurement. The cross-sectional area of the patellar tendon will be calculated from axial plane images at 25%, 50% and 75% of its length (at rest). The calculation of tendon force will use the ratio of the estimated total knee extension moment (corrected for the activation of the biceps femoris muscle obtained by electromyography) by the internal moment arm, which will be estimated by individually measuring the length of the femur, according to the equation of Visser et al (1990). Tendon stress will be calculated by the force ratio applied to the tendon by its cross-sectional area. The strain in the tendon will be calculated using the change in length over the original length (ΔL / Lo) and will be expressed as a percentage. The Young's modulus, or elastic modulus, will be obtained by dividing the stress by the strain. The tendinous stiffness will be calculated by dividing the force applied to the tendon by the elongation generated in its length. As the length of the transducer does not allow the entire visualization of the patellar tendon, a hypoallergenic echo-absorbent adhesive tape will be placed in the center of the tendon for reference. Thus, images will be obtained from the tape to the proximal insertion and then departing from the tape to the distal insertion. Images will be reconstructed for measurement. The deformation will be defined as the change in the length between the patella and the tibia, which will be measured frame-by-frame.