Plyometric drop jumps (DJs) are frequently used by athletes as a means of developing lower body power (7,30,31). Although it is often recommended that DJs be performed when the neuromuscular system is not fatigued (31), thereby maximizing neural activation, the principle of specificity dictates that there is a clear justification for athletes who compete under fatigued conditions to develop lower limb power under such fatigued conditions (7) using a variety of training exercises, including DJs. In fact, plyometric exercises, including DJs, have been shown to enhance performance in endurance running (29,32,34). However, performing DJs from inappropriately large heights or when fatigued may predispose athletes to lower limb injuries associated with high impact loads and accelerations (7,22). In reaction to the foot contacting the ground during landing, a reactionary force causes a transient acceleration (“shock wave”), which travels up the musculoskeletal system from the foot to the head (4,13,21,22). When these impact accelerations and loads are excessive relative to the strength of the tissue, they may cause a number of musculoskeletal overuse injuries, including stress fractures (18,39), osteoarthritis (26,36,38), and articular cartilage and joint degeneration (6,27,36). Given that the body attempts to attenuate such impact accelerations using various neuromuscular and joint kinematic control strategies (8,25), there is a potential to increase the risk of injury if DJs are completed when the neuromuscular system is fatigued (15,16,22). Indeed, increased impact acceleration measured on the tibia has been observed extensively in fatigued running with associated changes in knee kinematics during landing (5,21).
Only one study to date appears to have examined the effect of endurance fatigue on the magnitude of impact accelerations when performing DJs (from 30 and 50 cm) (22). The authors concluded that fatigue had a negative effect on impact accelerations although tibial impact acceleration were only greater from 30 cm, but not from 50 cm. They argued that the neuromuscular system was not capable of effectively controlling the increased impact accelerations from the higher drop height (50 cm), and therefore when inhibited as a result of fatigue, no further significant detriment in control was evident. Although their conclusion is tenable, it was based on results from only 2 drop heights. Clearly there is a need to examine the effect of endurance fatigue on impact accelerations from a greater number of drop heights. In addition, given that the only study to date has examined this effect in males, it would be beneficial to increase the generalization of the results by examining the effect in females.
The main aim of the present study was to determine if impact acceleration, measured at the proximal tibia during DJs from increasing heights, was significantly affected by endurance fatigue. A secondary aim was to investigate if the action of the knee during the initial contact and landing phase was also affected by endurance fatigue. It was hypothesized that endurance fatigue would result in greater impact accelerations at low(er) drop heights, but not at high(er) drop heights.
Experimental Approach to the Problem
To examine if endurance fatigue affected either the impact accelerations applied to the body or the knee kinematics used by the body, DJs were completed by all participants under nonfatigued and fatigued conditions during a single session. Three drop heights were selected. Although a number of methods have been proposed to identify an athlete's optimal drop height for training (2,11,40), no studies have shown the effectiveness of one method over another for improving leg power. Therefore, the drop heights selected were based on previous DJ studies (1,22) and training literature (7). Running was used to induce endurance fatigue, rather than resistance training-based exercises, because it is perhaps the most common means by which athletes become fatigued in sport.
Fifteen female soccer players (age, 20.9 ± 1.1 years; mass, 63.4 ± 4.9 kg; height, 1.66 ± 0.10 m) were recruited. All participants had been playing competitive soccer for at least the last 3 years and currently trained a minimum of 4 times per week during the competitive season. Throughout their season, participants undertook at least 2 gym-based resistance training session per week and testing was completed between 5 and 6 weeks into their competition season. The study inclusion criteria required participants to have at least 6 weeks of prior experience in the last 2 years in performing DJs as a means of training. Written informed consent was obtained in accordance with the university's ethical committee's guidelines. Participants were excluded from the study if they had any history of lower extremity injury. Two weeks before the experimental trial, participants were demonstrated the DJ as to be used in the present study and practiced it from all 3 experimental drop heights until they could demonstrate proficiency, which was subjectively judged by 2 trainers who had taught DJ training for a minimum of 5 years. The DJ was deemed proficient provided there was: (a) no significant horizontal travel between takeoff and landing; (b) a short duration in the landing phase; and (c) a toe-first landing pattern. Participants wore their own, appropriate athletic footwear during the test. Participants were instructed to refrain from eating for 2 hours before testing and from strenuous physical activity for 48 hours before testing.
The pre-experiment warmup consisted of running on a treadmill at 6 mph for 4 minutes followed by stretching exercises for the major muscles of the lower extremities (22). Each participant performed blocks of 3 DJs from 15, 30, and 45 cm with approximately 10 seconds recovery between each DJ from a given height. The order of drop jump heights was counterbalanced. In addition, in the nonfatigued condition, a further 2 minutes' rest was given between each block of DJs.
Each participant was instructed to jump vertically with maximum effort while trying to spend as little time on the floor as possible (23). The flooring was a 1.9-cm polyurethane multipurpose covering laid over a cement surface. Data on impact acceleration, knee kinematics, and jump height were collected for each jump. The average of each block of 3 DJs was used in the subsequent analysis.
An incremental running protocol on a treadmill was used to induce whole body endurance fatigue (22). Participants began running at 6 mph with a 3% grade with a 1.5% incremental increase in gradient applied every minute thereafter. A rating of perceived exertion (RPE) was taken every 2 minutes and used to determine when physiological fatigue had occurred. RPE was used because it is less invasive than more direct measures (eg, blood lactate concentration, oxygen uptake), it has been shown to be a physiologically valid tool for prescribing exercise intensity (33), and it has been used widely in this manner (14,22). An RPE of 17 (“very hard”) was chosen to indicate when an endurance-based fatigued state was reached. Participants then repeated the DJs in the fatigued condition in the same order as carried out in the nonfatigued condition. The time from the end of the fatiguing protocol to when the DJ protocol was initiated again was always <1 minute.
In reaction to the foot contacting the ground when drop jumping, an impact acceleration (or “shock wave”) travels through the body, which, when excessive, may cause musculoskeletal injury (as detailed previously). Impact accelerations were measured at the proximal end of the tibia using a lightweight (17 g) uniaxial accelerometer (ADXL78; Analog Devices, Limerick, UK; sensitivity 38 mV/g, range ± 50 g) attached to the skin overlying the proximal anterior-medial aspect of the right tibia. The accelerometer was attached to the skin with double-sided tape and prewrap (Durapore; 3M, Bracknell, UK) and aligned along the longitudinal aspect of the tibia. An elastic belt wrapped around the shank pressed the accelerometer onto the skin as tightly as comfortably allowed (35). It is recognized by the authors that accelerometers are sensitive to their orientation relative to gravity and in the present study were attached to the skin rather than directly on bone. Orientation sensitivity will introduce a nonconsistent error in measures of peak acceleration if either fatigue or drop height results in different tibia angles at landing. However, in a previous study on DJs from 30 cm, this error was shown to be very small (1.5%) (22). This potential error was taken into consideration when examining the magnitude of any effects in the present study. Although mounting an accelerometer on the skin with double-sided tape may underestimate the magnitude of accelerations (12), the effect is considered to be relatively consistent across conditions (fatigued and nonfatigued) and, most importantly, does not require an invasive procedure. Skin-mounted accelerometers have been used previously to examine impact accelerations in running (5,21,35) and DJs (22).
To determine if changes in knee kinematics occurred after the fatiguing protocol, and if these changes may have explained any corresponding changes in the magnitude of impact acceleration, sagittal plane knee kinematics were examined. Knee angles were used to assess the angle of the knees at initial impact and takeoff and subsequently to determine the range of joint motion used. Knee angular velocity was used to assess the degree of knee control during the landing phase. Knee motion was measured using an electrogoniometer (XM110; Biometrics Ltd, Cwmfelinfach, UK) attached using double-sided tape and prewrap (Durapore) and aligned with the center of the knee on the lateral side of the left knee. The left knee was used in case the electrogoniometer made contact with the accelerometer and caused erroneous results. The electrogoniometer was zeroed before both the nonfatigued and the fatigued series of DJs as the subject stood upright with a straight leg. Knee angle data were smoothed using a fourth-order zero-lag Butterworth digital filter (37) with a cutoff frequency of 20 Hz to retain the subtleties in the velocity-time traces (22). Angular velocities were calculated by simple differentiation (37). The start and end of foot-to-ground contact was registered using a foot switch apparatus (TF100; Biometrics Ltd) attached to the underside of the forefoot of each participant's right shoe. The foot switch data were used to identify initial ground contact as well as the flight time of the subsequent jump, the latter of which was used to determine jump height as an indicator of neuromuscular fatigue. Jump height was calculated from flight time (3). To reduce the potential for damage to the switch, it was removed before the fatiguing running protocol; its site of attachment was clearly marked to facilitate accurate reattachment for the second set of DJs. The foot switch was tested before and after each experiment by pinching the pressure sensor and was found to work effectively on all occasions. The accelerometer, electrogoniometer and the switch were sampled simultaneously at a rate of 1,000 Hz (DataLINK; Biometrics Ltd).
To assess the reliability of the results, 8 participants repeated the test protocol on a second day using only the drop height of 30 cm. A break of at least 4 days was given between test sessions.
The average of each block of 3 trials was used in the analysis, a 2 (condition: nonfatigued and fatigued) by 3 (drop height: 15, 30, and 45m) within-subjects analysis of variance. Tibial peak impact acceleration, angle of knee flexion at ground contact, peak knee flexion during the landing phase, range of knee flexion between these 2 points, peak knee flexion angular velocity during the landing phase, and jump height were the dependent variables assessed. Where a significant main effect of drop height was found, a repeated-measures analysis of variance was performed followed by post hoc multiple paired t-tests with appropriate Bonferroni adjustment. Where a statistically significant interaction was found, planned comparisons using paired t-tests with appropriate Bonferroni adjustment were completed. The interday reliability of all dependent variables was assessed using intraclass correlation analysis (ICC). The level of statistical significance in all tests was set at p = 0.05. SPSS for Windows version 10 (SPSS Inc, Chicago, IL) was used.
Subjects ran on average for 8.6 ± 2.7 minutes, attaining a final gradient of 15.9 ± 3.8% during the fatiguing protocol.
The interday reliability (ICC) of measures ranged from 0.82 to 0.98 (Table 1).
Tibial peak impact acceleration, angle of knee flexion at ground contact, peak knee flexion during the landing phase, range of knee flexion between these 2 points, peak knee flexion angular velocity during the landing phase, and jump height were the dependent variables assessed.
Tibial Peak Impact Acceleration
Condition (F = 36.8, p = 0.000), drop height (F = 103.34, p = 0.000), and their interaction (F = 8.3, p = 0.001) had a significant effect on tibial peak impact acceleration (Figure 1). Post hoc analyses revealed that endurance fatigue had a significant effect at 15 cm (t = −8.08, p = 0.000) and 30 cm (t = −3.79, p = −.002), but not at 45 cm (t = −1.21, p = 0.25), with increases in peak accelerations of 32, 17, and 2%, respectively. With each increase in drop height, peak impact acceleration also significantly increased in both fatigued (F = 65.5, p = 0.000) and nonfatigued (F = 135.8, p = 0.000) conditions (fatigued: 15 vs. 30 cm = 37% [t = −11.3, p = 0.000], 15 vs. 45 cm = 103% [t = −14.0, p = 0.000], and 30 vs. 45 cm = 48% [t = −8.9, p = 0.000]; nonfatigued: 15 vs. 30 cm = 55% [t = −7.0, p = 0.000], 15 vs. 45 cm = 162% [t = −9.3, p = 0.000], and 30 vs. 45 cm = 68% [t = −6.6, p = 0.000]).
Knee Joint Kinematics
Only drop height had a significant effect on the angle of knee flexion at initial ground contact (F = 194.8, p = 0.000) with a significantly greater angle evident from 15 cm (23.8 ± 5.2°) and 30 cm (23.7 ± 5.8°) than from 45 cm (18.5 ± 4.5°) (Figure 2).
Condition (F = 1.05, p = 0.32), drop height (F = 1.65, p = 0.21), and their interaction (F = 0.72, p = 0.49) did not have a significant effect on the angle of peak knee flexion (Figure 3).
Only drop height significantly affected the range of knee flexion (F = 7.0, p = 0.003) with a greater range from 45 cm (58.7 ± 15.6°) than from 30 cm (48.7 ± 7.1°) and 15 cm (48.3 ± 9.9°) (Figure 4).
The same trend in results was evident for knee peak angular velocity during the eccentric phase as for tibial peak impact acceleration. Condition (F = 190.5, p = 0.000), drop height (F = 54.5, p = 0.000), and their interaction (F = 27.1, p = 0.000) were all significant (Figure 5). Post hoc analysis revealed that fatigue had a significant effect at 15 cm (t = 13.5, p = 0.000) and 30 cm (t = 14.3, p = 0.000), but not at 45 cm (t = 1.6, p = 0.13) with increases of 21, 20, and 2%, respectively. Increased drop height also had a significant affect when both fatigued (F = 62.9, p = 0.000) and nonfatigued (F = 42.2, p = 0.000) with increases in angular velocity evident at each increase in drop height (fatigued: 15 vs. 30 cm = 24% [t = −4.9, p = 0.000], 15 vs. 45 cm = 72% [t = −6.5, p = 0.000], and 30 vs. 45 cm = 40% [t = −6.5, p = 0.000]; nonfatigued: 15 vs. 30 cm = 24% [t = −4.2, p = 0.001], 15 vs. 45 cm = 104% [t = −6.5 p = 0.000], and 30 vs. 45 cm = 64% (t = −6.5, p = 0.000]).
Both condition (F = 187.8, p = 0.000) and drop height (F = 24.9, p = 0.000) had a significant effect on jump height (Figure 6). Post hoc analyses revealed that jump height was greater from both 45 and 3 0cm than from 15 cm. Endurance fatigue caused a similar reduction in jump height at all 3 drop heights (approximately 8%).
Based on the decrease in jump height after the fatiguing running protocol (Figure 6), endurance-based neuromuscular fatigue appears to have been induced, indicating the appropriate use of the running protocol and the PRE scale. Although not assessed directly in the present study, it is likely that both central (neural) and peripheral (contractile component) activation pathways were affected (24).
Although it is generally recommended that DJs are performed when the neuromuscular system is not fatigued (31), thereby maximizing neural activation, the principle of specificity clearly indicates that for athletes who need to produce high-power output when fatigued, there is a need to develop lower limb power under such fatigued conditions (7). DJ training is commonly used to increase lower limb power. However, this gives rise to the question of whether completing DJs when fatigued will result in an increase in impact accelerations, which are associated with an increase in the risk of injury (6,16,26). The present study found a significant interaction between endurance fatigue and drop height for impact accelerations measured at the proximal tibia during drop jumping. Tibial accelerations were significantly larger from drop heights of 15 cm (32%) and 30 cm (17%) when participants were fatigued in comparison to nonfatigued, but no significant difference was evident from the higher drop height of 45 cm (2%) (Figure 1). In addition, the increase in peak acceleration associated with endurance fatigue was significantly larger from 15 than 30 cm. This trend in results showing a negative effect of fatigue, especially at lower drop heights, is in agreement with the hypothesis of the present study and the findings of Moran and Marshall (22). The findings are interpreted as indicating that at greater heights, the neuromuscular system's capacity to control the greater impact acceleration per se is notably reduced irrespective of whether it is fatigued or nonfatigued. Support for this assertion is taken from 2 sources. First, in the present study, a similar pattern of results was found for the effect of drop height and endurance fatigue on knee flexion peak angular velocities during the landing phase as that for impact accelerations (Figures 1 and 5). Because the neuromuscular system acts to decrease knee angular velocities during the landing phase, the knee angular velocity data illustrate that the neuromuscular system had a reduced capacity during the loading phase in DJs from 45 cm, whether fatigued or nonfatigued, but was able to positively affect jumps from 15 and 30 cm. Second, in comparing findings from the present study with 2 previous studies on running (20,35) there is a clear trend that as impact accelerations increase per se, the relative effect of fatigue diminishes. For running, in which impact accelerations are lower than DJs (approximately 68 m.s−2 ), Mizrahi et al (20) and Voloshin et al (35) reported that endurance fatigue caused an increase in proximal tibial peak acceleration of 62% and approximately 60%, respectively. In contrast, in the present study, as impact accelerations increased with increases in drop height (on average: 102.0 ± 24.3 m.s−2 from 15 cm, 148.1 ± 27.4 m.s−2 from 30 cm, and 232.8 ± 58.9 m.s−2 from 45 cm), the relative effect of endurance fatigue decreased (32% from 15 cm,17% from 30 cm, and just 2% from 45 cm).
Although the present study did not attempt to identify the individual neuromuscular mechanisms responsible for attenuating impact accelerations, it is worth noting that endurance fatigue causes a decrease in proprioception (10,19) and contractile and reflex capacities (9) in stretch shortening activities such as drop jumping, which are important mechanisms in controlling the eccentric loading phase (9).
Previous studies on the affect of endurance fatigue in running have suggested that changes in tibial peak impact accelerations may be the result of changes in the angle of knee flexion at key times during the landing phase (5,21). The present study examined the effect of fatigue on the angle of knee flexion at initial ground contact, the end of the eccentric phase, and the range of motion between them. Fatigue was found to have no effect on these kinematic measures. Similar results have been reported previously (17), although these authors did note an increase in the angle of knee abduction and internal rotation. The contrast in results between DJs and running may be the result of the task requirement in DJs to remain in contact with the ground for as short a duration as possible or to the explosive action being less practiced than running, and the coordination pattern therefore being less susceptible to relative change, even when the neuromuscular system's capacity is compromised when fatigued (28). Therefore, the findings from the present study indicate that changes in peak impact accelerations induced by endurance fatigue cannot be explained by changes in the knee angles at key points during the landing phase. Although not assessed in the present study, it is possible that changes in hip or ankle kinematics may have occurred. However, in examining the effect of endurance fatigue on drop jumps from 50 cm, McClean et al found no changes in ankle and hip (dorsi-)flexion, abduction, or internal rotation.
Limitations to the Present Study
This study is based on the premise that a significant increase in impact accelerations will increase the risk of injury, yet there is a dearth of information available on what constitutes an “excessive” impact acceleration or load. In referring mainly to animal model studies that directly found joint cartilage and bone degeneration after high impact loading (6,27,36) and also to epidemiologic studies on subjects exposed to high loadings during their chosen activity (18), the general literature simply refers to “excessive” impact accelerations and/or loads predisposing to injury (13,16,18,21,26). Although a plyometric DJ training session may contain only between 30 and 100 ground impacts, tissue damage appears to be more dependent on the magnitude of loading rather than the number of impacts (36).
Given that the principle of “training specificity” indicates that to maximize power output during fatiguing conditions (eg, end of a basketball match), it may be beneficial to train power when fatigued, cognizance should be taken of any potential increase in the likelihood of injury associated with completing such exercises when fatigued. Although data do not currently exist on what constitutes an “excessive” magnitude of impact acceleration during DJ training, in terms of predisposing an individual to a greater risk of injury (eg, stress fractures, articular cartilage and joint degeneration, and osteoarthritis) (6,16,26), the present study indicates that caution should be taken in deciding to undertake plyometric DJs (15, 30, and 45 cm) when fatigued because of an associated significant increase in impact accelerations. However, in interpreting the findings of the present study, it is important to note that smaller impact accelerations were evident when performing DJs from 15 cm when fatigued than from 30 and 45 cm when nonfatigued. Similarly, smaller impact accelerations were evident when performing DJs from 30 cm when fatigued than from 45 cm when non-fatigued (Figure 1). This implies that it may still be safer, or at least as safe, to DJ from an appropriately low(er) drop height when fatigued than from a high(er) drop height when nonfatigued.
1. Bobbert, MF. Drop jumping as a training method for jumping ability. Sports Med
9: 7-22, 1990.
2. Bobbert, MF, MacKay, M, Schinkelshoek, D, Huijing, PA, and Van Ingen Schenau, GJ. Biomechanical analysis of drop and countermovement jumps. Eur J Appl Physiol
54: 566-573, 1986.
3. Bosco, C and Komi, PV. Mechanical characteristics and fibre composition of human leg extensor muscles. Eur J Appl Physiol
41: 275-284, 1979.
4. Derrick, TR. The effects of knee contact angle on impact forces and accelerations. Med Sci Sports Exerc
36: 832-837, 2004.
5. Derrick, TR, Dereu, D, and McLean, SP. Impacts and kinematic adjustments during an exhaustive run. Med Sci Sports Exerc
34: 998-1002, 2002.
6. Ewers, BJ, Dvoracek-Driksna, D, Orth, MW, and Haut, RC. The extent of matrix damage and chondrocyte death in mechanically traumatized articular cartilage explants depends on the rate of loading. J Orthop Res
19: 779-784, 2001.
7. Fleck, SJ and Kraemer, WJ. Designing Resistance Training Programs
. Leeds, UK: Human Kinetics, 2004.
8. Flynn, JM, Holmes, JD, and Andrews, DM. The effect of localized leg muscle fatigue on tibial impact acceleration. Clin Biomech
19: 726-732, 2004.
9. Gollhofer, A, Komi, PV, Fujitsuka, N, and Miyashita, M. Fatigue during stretch-shortening cycle exercises. II. Changes in neuromuscular activation patterns of human skeletal muscle. Int J Sports Med
8: 38-41, 1987.
10. Hiemstra, LA, Lo, IK, and Fowler, PJ. Effect of fatigue on knee proprioception: implications for dynamic stabilization. J Orthop Sports Phys Ther
31: 598-605, 2001.
11. Komi, P and Bosco, C. Utilisation of stored elastic energy in leg extensor muscles by men and women. Med Sci Sports Exerc
10: 261-265, 1978.
12. LaFortune, MA, Hennig, EM, and Valiant, GA. Tibial shock measured with bone and skin mounted transducers. J Biomech
28: 989-993, 1995.
13. LaFortune, MA, Lake, MJ, and Hennig, EM. Differential shock transmission response of the human body to impact severity and lower limb posture. J Biomech
29: 1531-1537, 1996.
14. Lamb, K, Eston, R, and Corns, D. Reliability of ratings of perceived exertion during progressive treadmill exercise. Br J Sports Med
33: 336-339, 1999.
15. Light, LH, McLellan, GE, and Klenerman, L. Skeletal transients on heel strike in normal walking with different footwear. J Biomech
13: 477-480, 1980.
16. Madigan, ML and Piecoe, PE. Changes in landing
biomechanics during a fatiguing landing
activity. J Electromyogr Kinesiol
13: 491-498, 2003.
17. McLean, SG, Felin, RE, Suedekum, N, Calabrese, G, Passerallo, A, and Joy, S. Impact of fatigue on gender-based high-risk landing
strategies. Med Sci Sports Exerc
39: 502-514, 2007.
18. Milgrom, C. The Israeli elite infantry recruit: a model for understanding the biomechanics of stress fractures. J R Coll Surg Edinb
34: 18-21, 1989.
19. Miura, K, Ishibashi, Y, Tsuda, E, Okamura, Y, Otsuka, H, and Toh, S. The effect of local and general fatigue on knee proprioception. J Arthrosc Relat Surg
20: 414-418, 2004.
20. Mizrahi, J, Verbitsky, O, and Isakov, E. Shock accelerations and attenuation in downhill and level running. Clin Biomech
15: 15-20, 2000.
21. Mizrahi, J, Verbitsky, O, Isakov, E, and Daily, D. Effect of fatigue on leg kinematics and impact acceleration in long distance running. Hum Mov Sci
19: 139-151, 2000.
22. Moran, KA and Marshall, BM. Effect of fatigue on tibial impact accelerations and knee kinematics in drop jumps. Med Sci Sports Exerc
38: 1836-1842, 2006.
23. Newton, R and Dugan, E. Application of strength diagnosis. Strength and Conditioning Journal
24: 50-59, 2002.
24. Noakes, T. Physiological models to understand exercise fatigue and the adaptations that predict or enhance athletic performance. Scand J Med Sci Sports
10: 123-145, 2000.
25. Radin, EL. Role of muscle in protecting athletes from injury. Acta Medica Scandica
711: 143-147, 1986.
26. Radin, EL, Eyre, D, Kellman, JL, and Schiller, AL. Effect of prolonged walking on concrete on the joints of sheep. Arthritis Rheum
22: 649, 1980.
27. Radin, EL, Parker, HG, Pugh, JW, Steinberg, RS, Paul, IL, and Rose, RM. Response of joints to impact loading-III: Relationship between trabecular microfractures and cartilage degeneration. J Biomech
6: 51-57, 1973.
28. Rodacki, AL, Fowler, NE, and Bennett, SJ. Multi-segment coordination: Fatigue effects. Med Sci Sports Exerc
33: 1157-1167, 2001.
29. Saunders, P, Telford, R, Pyne, D, Pelyola, E, Cunningham, R, Gore, C, and Hawley, J. Short-term plyometric training improves running economy in highly trained middle distance and long distance runners. Journal of Strength and Conditioning Research
20: 947-954, 2006.
30. Schmidtbleicher, D. Training for power events. In: Strength and Power in Sport. Encyclopaedia of Sports Medicine
. PV Komi, ed. Oxford, UK: Blackwell Science, 1992. pp. 381-395.
31. Siff, MC and Verkhoshansky, YV. Supertraining
. Denver, CO: Supertraining International 1999.
32. Spurrs, RW, Murphy, AJ, and Watsford, ML. effect of plyometric training on distance running and performance. Eur J Appl Physiol
89: 1-7, 2003.
33. Steed, J, Gaesser, G, and Weltman, A. Rating of perceived exertion and blood lactate concentration during submaximal running. Med Sci Sports Exerc
26: 797-803, 1994.
34. Turner, AM, Owings, M, and Schwane, JA. Improvement in running economy after 6 weeks of plyometric training. Journal of Strength and Conditioning Research
17: 60-67, 2003.
35. Voloshin, AS, Mizrahi, J, Verbitsky, O, and Isakov, E. Dynamic loading on the human musculoskeletal system-Effect of fatigue. Clin Biomech
13: 515-520, 1998.
36. Whiteside, RA, Jakob, RP, Wyss, UP, and Mainil-Varlet, P. Impact loading of articular cartilage during transplantation of osteochondral autograft. J Bone Joint Surg Br
87: 1285-1291, 2005.
37. Winter, DA. Biomechanics and Motor Control of Human Movement
. New York: Wiley-Interscience Publication, 2005.
38. Wosk, J and Voloshin, A. Wave attenuation in skeletons of young healthy persons. J Biomech
14: 261-267, 1981.
39. Yoshikawa, T, Mori, S, Santiesteban, AJ, Sun, TC, Hafstad, E, Chen, J, and Burr, DB. The effects of muscle fatigue on bone strain. J Exp Biol
188: 217-233, 1994.
40. Young, WB, Wilson, GJ, and Byrne, C. A comparison of drop jump training methods: Effects on leg extensor strength qualities and jumping performance. Int J Sports Med
20: 295-303, 1999.