The contractile performance of skeletal muscle may be either reduced or enhanced based on its recent contractile history. Some contractions may result in muscle force, rate of force development (RFD), or both being increased in subsequent contractions through postactivation potentiation (PAP) (35). A conditioning activity, usually taking the form of a maximum voluntary isometric contraction (MVIC) or other maximal volitional exercise, is required. Studies have reported that short-duration activities (i.e., MVIC ≤10 seconds) elicit PAP, whereas long-duration (i.e., MVIC ≥60 seconds) activities elicit both PAP and fatigue (40,41). The coupling of PAP and fatigue determines the net muscle force response (38).
Central and peripheral mechanisms are responsible for muscle behavior during volitional movement (15,19). Postactivation potentiation has most often been measured as twitch potentiation (TP), defined as the force characteristics produced in response to a single muscle stimulation after a conditioning activity (13,39). However, this is a consequence of actin-myosin cross-bridge kinetics due to myosin light chain phosphorylation and possibly increased stimulus efficacy, and fails to account for the influence of the nervous system in muscle recruitment during volitional effort (17,23). The Hoffmann reflex (H-reflex) is the electromyographic (EMG) signal in response to a stimulus that elicits an H-wave. The electrical muscle response to a stimulation intensity that elicits the largest magnitude H-wave (Hmax) is widely recognized as an index of measuring peripheral nervous system motor neuron pool excitability (44). Typically, the H-wave is reported as a ratio of the EMG response to an electrical stimulation of the α-motoneuron to produce a muscle contraction (M-wave). An increase in the Hmax-to-Mmax ratio (Hmax/Mmax) after a conditioning activity has been termed reflex potentiation (RP) (11,37). A larger ratio can be attributed to more or larger motor units, or both, being recruited (15,44). Methods of recruiting more motor units may be important in performance training. Complex training, executed by performing a “complex pair” of a resistance exercise followed by plyometrics several minutes later, has been used to help achieve preferential acute and chronic physiological adaptations through eliciting greater force, RFD, or both, than if both exercises were not coupled (7,9). However, the PAP response is highly variable between individuals based on the amount of time since the activity and a variety of individual factors (e.g., maximum strength, training status, muscle architecture, etc.) (4,8), and also seems to be specific to velocity-related attributes rather than strength-related attributes (7,24).
Enoka et al. (10) first reported that a reduction in H-wave amplitude (postactivation depression [PAD]) occurs after muscle contractions. Three studies have investigated the time course of H-wave amplitude after a conditioning activity, each reporting PAD followed by RP 3-plus minutes after the conditioning activity (11,15,37). In contrast to TP which is highest immediately after the conditioning activity (40) and quickly subsides due to myosin regulatory light chain dephosphorylation (20), the timing of the neural response better relates temporally to when PAP has been reported with volitional movements (43). This indicates that neural factors may play an important role in force and RFD production during volitional muscle activation designed to induce PAP. Torque and RFD responses to a twitch at Hmax intensity have been previously described as a method of measuring the coupled muscle and neural influences to PAP (11). No previous studies have investigated the relative contributions of muscle and neural factors responsible for PAP in the triceps surae nor RFD in any muscle. Therefore, the purpose of this study was to test the contribution of muscle and neural factors to PAP in the triceps surae muscles. We hypothesized that: (a) both TP and RP would significantly contribute to PAP, and (b) the gastrocnemius would contribute more than the soleus.
Experimental Approach to the Problem
A repeated-measures design was used. Participants performed 2 testing sessions separated by at least 96 hours: Control and MVIC (experimental). On the Control day, the force and EMG responses to stimulations at supramaximal (i.e., 120% of the stimulation intensity determined to result in Mmax) and submaximal (i.e., Hmax) intensities were recorded at select time points over a 20-minute period to establish a baseline. The MVIC condition was similar, except it examined the muscle responses after a 10-second plantarflexion MVIC. Testing was conducted at approximately the same time of day in a quiet laboratory.
Eleven men (mean ± SD: age 24.2 ± 2.9 years, range 21-29 years, height 182.2 ± 9.3 cm, body mass 94.2 ± 14.3 kg) and 4 women (age 28.0 ± 4.1 years, range 24-32 years, height 164.5 ± 13.0 cm, body mass 61.2 ± 12.6 kg) participated, excluding 3 participants who did not complete the study and whose data were not analyzed. Height, mass, and age variability presented as standard deviation. A minimum of 14 participants were required as determined by an a priori power analysis. All participants were healthy resistance-trained volunteers between 18 and 35 years of age, and were engaged in a whole-body resistance training program at least 3 times weekly for at least the previous 1 year. Men verbally asserted that they could maximally back squat a weight ≥1.5 times their bodyweight, and women ≥1.0 times their bodyweight (42). Participants were excluded if they had any history of neurological disorder or major lower-extremity neuromuscular injury as determined by a health history questionnaire and Par-Q. Participants were asked to refrain from strenuous exercise and avoid alcohol and caffeine consumption for at least 24 hours before testing. Institutional review board (IRB) approval was obtained for this investigation at the University of Kentucky. Participants provided written informed consent on an IRB approved form before taking part in any study procedures.
On both testing days, the stimulating and EMG electrodes were applied before participants were being positioned on the Biodex dynamometer. Once positioned, they sat passively for 20 minutes to remove any lingering potentiation (22). Several single stimulations of the tibial nerve were evoked at progressively greater intensities to acclimate participants (10,22). Thereafter, Hmax and Mmax stimulus response curves were determined by a series of single electrical stimuli of increasing intensity to the tibial nerve. Stimuli were delivered from 2 to 60 mA in 2 mA increments, temporally separated by 10 seconds. Immediately thereafter, the principal investigator manually identified Mmax and Hmax intensities from the data recordings. Five minutes thereafter, the 5 intensities in the region of Hmax were repeated to verify the previous maximum value (11). In the rare instances where the stimulation intensity required to elicit Hmax was not consistent, the higher intensity was used for that session's subsequent procedures. This difference did not exceed one increment (2 mA) for any subject.
During the Control condition, EMG and torque values for stimulations at Mmax and Hmax were established 10 minutes after Hmax and Mmax were determined (3). Mmax stimuli were elicited at: 10 and 30 seconds, and 1, 2.5, 4, 6, 8, 10, 12, 14, 16, and 18 minutes, and Hmax twitches at: 20 seconds, 1.5, 3, 4.5, 7, 9, 11, 13, 15, 17, and 20 minutes. Five minutes after baseline values were established, subjects performed 3–5 10-second familiarization MVICs, separated by 1 minute.
During the MVIC condition, participants rested passively on the Biodex dynamometer for 20 minutes, after which Hmax and Mmax were determined as described below. Five minutes thereafter, participants performed a 10-second max onset MVIC. Immediately after the MVIC, stimulations at Hmax and Mmax intensities were evoked, and the corresponding EMG and torque values were recorded, as described for the Control condition.
Participants were positioned on a Biodex Quick-Set System 4 isokinetic dynamometer (Rev. 1; Biodex Medical Systems, Shirley, NY, USA) for testing. The dominant leg, described as the preferred one used to kick a ball, of each participant was used. All participants were right-leg dominant. The dynamometer's isometric mode measured torque produced from MVICs and electrical stimulations. Participants were positioned in the dynamometer to a relative anterior hip flexion angle of 100°, relative posterior knee flexion angle of 120°, and relative ankle angle of 90° (2,17,18,27,30,32–34). The lateral malleolus was aligned with the dynamometer's armature axis of rotation. Two straps secured the foot to the foot plate, which was wrapped using a heel-lock technique to prevent the heel from coming off of the foot plate during isometric plantarflexions (Ank-L Wrap; Cramer Products, Inc., Gardner, KS, USA). The Biodex settings associated with subject positioning were recorded to ensure consistency between testing days. Participants were instructed to keep their lower-extremity musculature relaxed during testing, except while performing the MVIC.
Stimulation and Electromyogram Recording
To reduce impedance, the skin was shaved, abraded with a gauze pad, and cleaned with isopropyl alcohol before the stimulating or EMG electrodes were placed on the skin. The lateral gastrocnemius and soleus were evoked by surface stimulation of the tibial nerve delivered by square-wave impulses through a constant current stimulator (DS7AH; Digitimer Ltd., Welwyn Garden City, United Kingdom) using 2 custom-sized 2 × 3 cm reusable rubber electrodes. The cathode (positive lead) was placed on the skin over the tibial nerve in the popliteal fossa as determined by palpation, whereas the anode (negative lead) was placed over the midportion of the thigh approximately 2 cm proximal to the superior border of the patella (17,27). Conductor gel was placed on the stimulating electrodes before them being placed and taped on the skin using surgical tape. Pulse durations were 1 ms for all stimulations (22). All stimulations were controlled using custom-written Matlab code (Mathworks, Inc., Natick, MA, USA).
A Delsys Bagnoli-8 EMG system (Delsys, Inc., Boston, MA, USA) was used to record EMG signals. Model DE-2.1 single differential surface electrodes (Delsys, Inc.) with a bipolar configuration recorded action potentials. The Ag electrode sensors on the electrodes were 1 mm wide with an intersensor distance of 1 cm. The electrode housing was internally shielded and contained a preamplifier. The EMG electrodes were placed over the longitudinal axis of the soleus muscle belly approximately 4 cm below the inferior margin of the gastrocnemius (22), and over the muscle belly of the lateral gastrocnemius at 1/3 the distance from the fibular head to the calcaneus (37). The ground electrode was placed on the ipsilateral patella. Stimulating and EMG electrode placements were marked with a marker to ensure consistency for both testing sessions. Electromyographic signals were amplified (×1,000) and band-pass filtered (20–450 Hz).
Data Measurements and Analysis
Torque values were recorded from the analog output of the dynamometer. Analog torque and EMG data were collected through a 16-bit AD board (model USB-2659 BNC; National Instruments, Austin, TX, USA) connected to a personal computer. Data were sampled at 4 kHz using commercial software (EMGWorks, version 4.0; Delsys, Inc.). Torque and EMG responses to all stimulations were recorded. Peak twitch torque, average RFD, and peak-to-peak EMG of the gastrocnemius and soleus were calculated. Average RFD for each twitch response was calculated using time and force values from between when the signal crossed 20% of the difference between the start and peak of the signal, and the peak force of each response. To attenuate signal noise, torque data were filtered using a low-pass fourth-order zero-lag Butterworth filter, with a cutoff frequency of 24 Hz as determined by a residual analysis. Data were analyzed and compiled using standard functions and custom-written code (EMGWorks, version 4.0; Delsys, Inc.; Excel 2013; Microsoft Corporation, Redmond, WA, USA; Matlab, version R2012b; Mathworks, Inc.).
Data are reported as mean ± SD. The Hmax and Mmax EMG amplitudes from stimulations at Hmax intensity were normalized to the temporally nearest Mmax EMG value to determine Hmax/Mmax ratios. In situations where Hmax was elicited at the temporal midpoint between 2 Mmax stimulations, Hmax was normalized to the preceding Mmax stimulation. Two-way repeated-measures analyses of variance (condition × time) were performed to determine significant differences between the MVIC and Control conditions. Specifically, torque, RFD, and EMG values in response to stimulations at Mmax were analyzed at 12 time points between 10 seconds and 18 minutes. Torque and RFD values for stimulations at Hmax were analyzed at 11 time points between 20 seconds and 20 minutes.
Linear regression analyses were performed on the MVIC condition to calculate coefficients of determination (e.g., R2 values) and the significance of the regression coefficients at select time points corresponding with when Hmax torque and RFD were greatest. The variance of PAP (e.g., Hmax torque and RFD) accounted for by TP and RP was computed for: Hmax torque vs. Mmax torque, and Hmax torque vs. Hmax/Mmax ratios for the gastrocnemius and soleus; and for Hmax RFD vs. Mmax RFD, and Hmax RFD vs. Hmax/Mmax ratios for the gastrocnemius and soleus. Because Hmax and Mmax stimulations were elicited at different time points, Hmax comparisons with Mmax were made using the temporally closest time point. All statistical analyses were performed using the Statistical Package for the Social Sciences (SPSS, version 22; IBM Corporation, Armonk, NY, USA). The level of significance was set a priori at α p ≤ 0.05.
Twitch and Reflex Responses
There was a significant interaction (condition × time) effect for TP (i.e., the Mmax stimulations) for torque and RFD (p < 0.001). The experimental condition showed significant TP vs. the Control condition for both torque (Figure 1; p < 0.001, p = 0.027 at 10 and 30 seconds after MVIC) and RFD (Figure 2, p < 0.001, p = 0.007 at 10 and 30 seconds after MVIC). There were no significant differences in either torque or RFD TP responses between the Control and MVIC conditions from the 30-second post-MVIC time point to the 18-minute time point.
Temporally, torque at Hmax was highest at 3 minutes after MVIC (Figure 3) and Hmax RFD was highest at 4.5 minutes (Figure 4). There were no significant differences between conditions for Hmax torque throughout the 20-minute measurement period (p > 0.05). Rate of force development at Hmax was significantly greater in the MVIC condition than the Control condition at 4.5 minutes after MVIC (p = 0.03).
Reflex potentiation was not observed in this study (Figures 5 and 6). There were no statistically significant differences in the Hmax/Mmax ratio for the gastrocnemius or soleus between conditions at any of the time points analyzed (p > 0.05).
Coefficients of Determination
Coefficients of determination that were calculated for the 2 measures of PAP (torque and RFD at Hmax) at initial (20 seconds), Hmax peak (3 minutes for torque and 4.5 minutes for RFD), and end time points (20 minutes) after MVIC are shown in Table 1. Mmax torque and RFD significantly contributed to Hmax torque and RFD at all time points analyzed (torque: R2 = 0.54, 0.76, and 0.70 at 20 seconds, 3 minutes, and 20 minutes, p ≤ 0.05; RFD: R2 = 0.46, 0.59, and 0.53 at 20 seconds, 4.5 minutes, and 20 minutes, p ≤ 0.05). The soleus' EMG ratio significantly contributed to Hmax torque variance at 20 seconds and 20 minutes after MVIC (R2 = 0.26 and 0.34, p ≤ 0.05). It also significantly contributed to Hmax RFD at 20-second, 4.5-minute, and 20-minute time points (R2 = 0.65, 0.52, 0.41, p ≤ 0.05). The gastrocnemius EMG did not significantly contribute to the variation in Hmax torque or RFD at any time point.
Our most novel findings are the contributions of the muscle and reflex mechanisms to peak torque and average RFD in response to stimulations at Hmax, and the timing of these contributions. Muscle mechanisms (TP) significantly accounted for between 54 and 76% of the variance in Hmax torque, increasing between the first and last time points. Neural mechanisms (RP) accounted for 22–34% of the variance in Hmax torque in the soleus. It has previously been inferred that torque PAP is closely related to TP soon after an MVIC, and closely related to RP starting approximately 3 minutes after (11). In our study, TP accounted for approximately 50% of the variance in Hmax RFD throughout the 20 minutes of post-MVIC testing. This was a smaller portion than with torque, especially as more time elapsed after the MVIC. Supramaximal stimulation muscle responses have been shown to be related to volitional performance in both the quadriceps (27) and plantarflexors (28) for up to 4 minutes after a conditioning activity, suggesting inferences of volitional performance may be made from supramaximal stimulation muscle responses during this period. In addition, H-reflex amplitude has been reported to be closely related to force for up to 11 minutes after MVICs (15). Therefore, it was unexpected that the contribution of RP to PAP and relative values of RP either did not increase or only marginally increased as time progressed after MVIC. Possible reasons for the discrepancy between the aforementioned and present investigations are the nature of the conditioning activities and muscles assessed.
Our results suggest that neural factors play a more prominent role with RFD production than with torque production, particularly soon after a conditioning activity. The soleus' mean Hmax/Mmax R2 value relative to Hmax RFD declined consistently from 0.65 to 0.41 between the 20-second and 20-minute time points. These values are considerably higher than those for Hmax torque, where muscle factors were more responsible. There may be 2 contributing causes responsible for this finding. First, conditioning activities result in phosphorylation of the myosin light chains (29), which has been shown to increase calcium sensitivity (26) by moving the myosin head closer to the thin filament (31,36). Increased calcium sensitivity would lead to a greater Hmax/Mmax ratio due to a greater number of myosin-actin attachments. However, although proximity increases the probability of attachment, it does not increase the rate of attachment. Thus, the second factor is likely related to the acute reflexive contribution to neural drive (19). A clearer understanding of the mechanisms responsible for these findings requires further research.
Alterations in twitch torque at Hmax intensity did not reach statistical significance in the experimental condition compared with Control, being enhanced by approximately 7% at 20 seconds after MVIC. Two previous studies reported conflicting results in this area. Gullich and Schmidtbleicher (15) tested subjects for dynamic voluntary isometric force of the plantarflexors after MVICs. They reported that voluntary force was significantly depressed by approximately 12% for the first 2 minutes of recovery before being potentiated starting at 4 minutes. A more recent study measured torque at Hmax, similar to the methods used in the present investigation (11). The authors reported similar results as our study, although the percent change in their study reached up to approximately 20%. This difference may be due to the fact that we tested the plantarflexors vs. their testing of the quadriceps. The dissimilar results of these 3 studies may be due to the conditioning activities used. Although we and Folland et al. (11) used a 10-second MVIC, Gullich and Schmidtbleicher (15) used five, 5-second MVICs. The 25 seconds of MVICs could have elicited peripheral fatigue that the 10-second MVICs did not. However, peak twitch torque after 10- and 30-second plantarflexion MVICs has been reported to be similar (40), suggesting similar peripheral conditions. It may be that PAD was elicited as a result of the longer conditioning activity. This is substantiated by the authors reporting that H-wave amplitude was depressed by approximately 20% during the period where reduced voluntary plantarflexion force was observed (15).
Our study was the first to investigate RFD in response to stimulations at Hmax as a measure of PAP. The increase in RFD at Hmax reached statistical significance at its peak value, which occurred 4.5 minutes after MVIC. Previous studies have reported equivocal results for potentiation of RFD after a conditioning activity. In mammalian models, RFD is increased in response to a supramaximal stimulation (39) and tetanic stimulation (1). In humans, voluntary knee extension velocity was not increased after a 10-second MVIC (13). An increase in velocity would have been indicative of an enhanced RFD. However, increased velocity has been shown in the mouse extensor digitorum longus (14). In addition, Baudry and Duchateau (3) reported increased RFD in thumb adductors during maximum-effort contractions for the 5 minutes after a 6-second MVIC. The conflicting results during knee extension (13) vs. the aforementioned investigations could be due to the low velocity associated with maximum-effort contractions of the quadriceps because the relative effect of PAP is more pronounced at lower stimulation frequencies (3). These results, combined with the results of our investigation, suggest that RFD may be enhanced during high-velocity movements 4 to 5 minutes after a conditioning activity.
Twitch torque and RFD at Mmax were both significantly higher in the experimental condition vs. Control immediately after the MVIC. Twitch torque potentiation of approximately 38–50% in the plantarflexors has been reported previously (16). This corresponds with the results of this study. In the quadriceps, twitch torque potentiation after a conditioning activity has been shown to vary between 10.7% (27) and 66.6% (11,13). Not surprisingly, the 10-second MVIC used in this study showed significant TP of approximately 60% immediately after the conditioning activity. By 18 minutes after MVIC, both torque and RFD returned to near baseline. One study reported twitch torque potentiation to last for up to 18 minutes after a conditioning activity (11), whereas others have taken measurements for only up to 10 minutes (20,29). The mechanism for the increased torque and RFD at Mmax are both likely myosin light chain phosphorylation, mentioned previously (3,35). The number of cross-bridge attachments at a given calcium concentration increases because the probability of myosin attaching to actin increases as their separation distance decreases (25). More cross-bridges would result in both more force and force being produced more quickly, enhancing both twitch torque and RFD.
The gastrocnemius' contribution to Hmax torque or RFD was only significant at 4.5 minutes after MVIC for RFD. The gastrocnemius is composed of mostly type II fibers (21), which experience PAP to a greater degree than slow-twitch fibers (17). Like previous studies that used similar knee (10,15) and ankle (10,15,37) angles, we successfully elicited M- and H-waves in the gastrocnemius. The Hmax/Mmax ratios for the soleus and gastrocnemius were similar (Figures 5 and 6). However, as knee flexion increases from 180° (i.e., a straight-leg position) to 120°, the contribution of the gastrocnemius to isometric plantarflexion torque decreases (5). A recent investigation reported slightly, but significantly, higher-twitch torque and RFD in the medial gastrocnemius with an extended knee position vs. with a relative knee angle of 90° (12). It is possible that a greater contribution of the gastrocnemius to overall potentiation would have been observed if a more extended knee position was used, as was done in one other study (37).
Short-term depression of the H-reflex occurs in response to conditioning activities comprised of electrical stimulations (6). Other studies have found PAD in the triceps surae after volitional muscle contractions (10,15,37), followed by RP several minutes thereafter. Although in our study neural factors significantly contributed to the kinetic responses at Hmax, there were no significant differences between the experimental and Control conditions for either the gastrocnemius or soleus Hmax/Mmax ratios at any of the time points analyzed. This may largely explain why, generally, significance between conditions for measures of PAP was not found. Trimble and Harp (37) reported PAD of the soleus and gastrocnemius for the first several minutes after dynamic plantarflexions and dorsiflexions. However, they observed equivocal results regarding RP of the gastrocnemius and soleus, with some subjects showing RP in one muscle and not the other, starting at 3 minutes after the conditioning activity. Enoka et al. (10) also reported a lack of RP in the soleus after isometric plantarflexions. By contrast, other authors have reported that the soleus H-reflex is highly related to torque depression and subsequent potentiation after tetanic nerve stimulation (23) or volitional force (15) using lower-extremity joint angles similar to those used in this study. Because of the gastrocnemius' lack of contribution to overall PAP, shown in Table 1, any possible RP would be due to the soleus. As shown in Figure 5, RP of the soleus was not statistically significant. However, it was highest at 4.5 minutes after MVIC, helping to explain why we observed significant PAP for RFD at Hmax at this time point.
There are some limitations to the current investigation that should be noted. The most notable is the inherently high intersubject variability in these neurophysiological measures, which has also been shown in applied studies relating to PAP (4). The study design used was necessary to measure the dependent variables required to answer the research question, but the isometric nature of the recorded kinetic values in this study is dissimilar to the dynamic nature of volitional training movements. However, the timing and application of our findings relate to applied investigations that used volitional movements (43), and further help explain the neuromuscular factors responsible for the results of those other investigations. In addition, as mentioned previously, a more extended relative knee angle may have led to a better indication of the gastrocnemius' contribution to PAP in our study while also providing a knee position more similar to what is experienced during the propulsive phase of in vivo dynamic movements such as jumping. Future studies should directly measure myosin light chain phosphorylation to gain a further understanding of the physiology involved with PAP as defined in this investigation and by Folland et al. (11). Finally, although our findings do relate to applied investigations, the relationship between the measures of isometric PAP and dynamic PAP requires further study (13).
This study was the first to statistically quantify the effects of TP and RP on PAP in vivo. Both TP and RP were significantly related to torque and RFD PAP factors for the duration of testing. In addition, neural factors were more highly related to RFD potentiation than to torque potentiation, with the opposite being true for muscle factors. Considering the relationship found between RP and RFD, persons who would benefit from increasing or maintaining high amounts of RFD, such as athletes or the elderly, may benefit from exercise methodologies designed to increase neural drive. Exercise methods that use a conditioning activity, such as complex training, may be especially helpful in this regard.
For the practitioner, the timing of using PAP seems important. The net muscle response may be most important to practitioners looking to enhance performance. Force PAP was not statistically enhanced at any time point, but was highest 3 minutes after MVIC, whereas RFD PAP was statistically elevated at 4.5 minutes after MVIC. Therefore, the TP response may not be important because of reduced neural efficiency right after a conditioning activity negating the effect of increased calcium sensitivity in the muscle. The timing of PAP in our investigation matches closely with when PAP has been detected in the previously mentioned studies which measured it during volitional movement, including that suggested in a recent meta-analysis (8). Sustained use of complex training may induce RFD-related variables such as velocity during dynamic power-oriented tasks (7), but not strength tasks (24). However, the phenomenon is a highly individual response (4) that is dependent on timing and a number of individual's attributes (8).
Supported by the Arvle and Ellen Turner Thacker Research Fund through the University of Kentucky's College of Education. The authors have no conflicts of interest to disclose.
1. Abbate F, Sargeant AJ, Verdijk PW, de Haan A. Effects of high-frequency initial pulses and posttetanic potentiation on power output of skeletal muscle. J Appl Physiol 88: 35–40, 2000.
2. Alway SE, Hughson RL, Green HJ, Patla AE, Frank JS. Twitch potentiation
after fatiguing exercise in man. Eur J Appl Physiol Occup Physiol 56: 461–466, 1987.
3. Baudry S, Duchateau J. Postactivation potentiation in a human muscle: Effect on the rate of torque development of tetanic and voluntary isometric contractions. J Appl Physiol 102: 1394–1401, 2007.
4. Chen ZR, Lo SL, Wang MH, Yu CF, Peng HT. Can different complex training improve the individual phenomenon of post-activation potentiation? J Hum Kinet 56: 167–175, 2017.
5. Cresswell AG, Loscher WN, Thorstensson A. Influence of gastrocnemius muscle length on triceps surae torque development and electromyographic activity in man. Exp Brain Res 105: 283–290, 1995.
6. Crone C, Nielsen J. Methodological implications of the post activation depression of the soleus H-reflex
in man. Exp Brain Res 78: 28–32, 1989.
7. Dobbs CW, Gill ND, Smart DJ, McGuigan MR. The training effect of short term enhancement from complex pairing on horizontal and vertical countermovement and drop jump performance. J Strength Cond Res, 2015. Epub ahead of print.
8. Dobbs WC, Tolusso DV, Fedewa MV, Esco MR. Effect of postactivation potentiation on explosive vertical jump: A systematic review and meta-analysis. J Strength Cond Res, 2018. Epub ahead or print.
9. Docherty D, Robbins D, Hodgson M. Complex training revisited: A review of its current status as a viable training approach. Strength Cond J 26: 52–57, 2004.
10. Enoka RM, Hutton RS, Eldred E. Changes in excitability of tendon tap and Hoffmann reflexes following voluntary contractions. Electroencephalogr Clin Neurophysiol 48: 664–672, 1980.
11. Folland JP, Wakamatsu T, Fimland MS. The influence of maximal isometric activity on twitch and H-reflex potentiation
, and quadriceps femoris performance. Eur J Appl Physiol 104: 739–748, 2008.
12. Gago P, Arndt A, Ekblom MM. Post activation potentiation of the plantarflexors: Implications of knee angle variations. J Hum Kinetics 57: 29–38, 2017.
13. Gossen ER, Sale DG. Effect of postactivation potentiation on dynamic knee extension performance. Eur J Appl Physiol 83: 524–530, 2000.
14. Grange RW, Cory CR, Vandenboom R, Houston ME. Myosin phosphorylation augments force-displacement and force-velocity relationships of mouse fast muscle. Am J Physiol 269: C713–C724, 1995.
15. Gullich A, Schmidtbleicher D. MVC-induced short-term potentiation of explosive force. New Stud Athletics 11: 67–81, 1996.
16. Hamada T, Sale DG, Macdougall JD. Postactivation potentiation in endurance-trained male athletes. Med Sci Sport Exer 32: 403–411, 2000.
17. Hamada T, Sale DG, MacDougall JD, Tarnopolsky MA. Postactivation potentiation, fiber type, and twitch contraction time in human knee extensor muscles. J Appl Physiol 88: 2131–2137, 2000.
18. Hamada T, Sale DG, MacDougall JD, Tarnopolsky MA. Interaction of fibre type, potentiation and fatigue in human knee extensor muscles. Acta Physiol Scand 178: 165–173, 2003.
19. Hodgson M, Docherty D, Robbins D. Post-activation potentiation. Sports Med 35: 585–595, 2005.
20. Houston ME, Grange RW. Myosin phosphorylation, twitch potentiation
, and fatigue in human skeletal muscle. Can J Physiol Pharm 68: 908–913, 1990.
21. Johnson MA, Polgar J, Weightman D, Appleton D. Data on the distribution of fibre types in thirty-six human muscles. An autopsy study. J Neurol Sci 18: 111–129, 1973.
22. Kitago T, Mazzocchio R, Liuzzi G, Cohen LG. Modulation of H-reflex
excitability by tetanic stimulation. Clin Neurophysiol 115: 858–861, 2004.
23. Klakowicz PM, Baldwin ERL, Collins DF. Contribution of M-waves and H-reflexes to contractions evoked by tetanic nerve stimulation in humans. J Neurophysiol 96: 1293–1302, 2006.
24. MacDonald CJ, Lamont HS, Garner JC. A comparison of the effects of 6 weeks of traditional resistance training, plyometric training, and complex training on measures of strength and anthropometrics. J Strength Cond Res 26: 422–431, 2012.
25. MacIntosh BR. Role of calcium sensitivity modulation in skeletal muscle performance. News Physiol Sci 18: 222–225, 2003.
26. Metzger JM, Moss RL. Myosin light chain 2 modulates calcium-sensitive cross-bridge transitions in vertebrate skeletal muscle. Biophys J 63: 460–468, 1992.
27. Mitchell CJ, Sale DG. Enhancement of jump performance after a 5-RM squat is associated with postactivation potentiation. Eur J Appl Physiol 111: 1957–1963, 2011.
28. Miyamoto N, Kanehisa H, Fukunaga T, Kawakami Y. Effect of postactivation potentiation on the maximal voluntary isokinetic concentric torque in humans. J Strength Cond Res 25: 186–192, 2011.
29. Moore RL, Stull JT. Myosin light chain phosphorylation in fast and slow skeletal muscles in situ. Am J Physiol 247: C462–C471, 1984.
30. Paasuke M, Saapar L, Ereline J, Gapeyeva H, Requena B, Oopik V. Postactivation potentiation of knee extensor muscles in power- and endurance-trained, and untrained women. Eur J Appl Physiol 101: 577–585, 2007.
31. Persechini A, Stull JT, Cooke R. The effect of myosin phosphorylation on the contractile properties of skinned rabbit skeletal muscle fibers. J Biol Chem 260: 7951–7954, 1985.
32. Requena B, de Villarreal ESS, Gapeyeva H, Ereline J, Garcia I, Paasuke M. Relationship between postactivation potentiation of knee extensor muscles, sprinting and vertical jumping performance in professional soccer players. J Strength Cond Res 25: 367–373, 2011.
33. Requena B, Ereline J, Gapeyeva H, Paasuke M. Posttetanic potentiation in knee extensors after high-frequency submaximal percutaneous electrical stimulation. J Sport Rehabil 14: 248–257, 2005.
34. Requena B, Gapeyeva H, Garcia I, Ereline J, Paasuke M. Twitch potentiation
after voluntary versus electrically induced isometric contractions in human knee extensor muscles. Eur J Appl Physiol 104: 463–472, 2008.
35. Sale DG. Postactivation potentiation: Role in human performance. Exerc Sport Sci Rev 30: 138–143, 2002.
36. Sweeney HL, Stull JT. Phosphorylation of myosin in permeabilized mammalian cardiac and skeletal muscle cells. Am J Physiol 250: C657–C660, 1986.
37. Trimble MH, Harp SS. Postexercise potentiation of the H-reflex
in humans. Med Sci Sport Exer 30: 933–941, 1998.
38. Vandenboom R, Grange RW, Houston ME. Threshold for force potentiation associated with skeletal myosin phosphorylation. Am J Physiol 265: C1456–C1462, 1993.
39. Vandenboom R, Grange RW, Houston ME. Myosin phosphorylation enhances rate of force development in fast-twitch skeletal muscle. Am J Physiol 268: C596–C603, 1995.
40. Vandervoort AA, Quinlan J, McComas AJ. Twitch potentiation
after voluntary contraction. Exp Neurol 81: 141–152, 1983.
41. Vera-Ibanez A, Romero-Arenas S, Marin-Pagan C, Marquez G. Concurrence of fatigue and potentiation after a sustained maximal voluntary contraction. Rev Int Med Cienc Ac 18: 61–76, 2018.
42. Wallace BJ, Kernozek TW, Mikat RP, Wright GA, Simons SZ, Wallace KL. A comparison between back squat exercise and vertical jump kinematics: Implications for determining anterior cruciate ligament injury risk. J Strength Cond Res 22: 1249–1258, 2008.
43. Wilson JM, Duncan NM, Marin PJ, Brown LE, Loenneke JP, Wilson SMC, et al. Meta-analysis of postactivation potentiation and power: Effects of conditioning activity, volume, gender, rest periods, and training status. J Strength Cond Res 27: 854–859, 2013.
44. Zehr EP. Considerations for use of the Hoffmann reflex in exercise studies. Eur J Appl Physiol 86: 455–468, 2002.