Recruiting from the university population and surrounding area via posters and word of mouth, participants were selected who demonstrated hip mobility of less than the 50th percentile, ideally in both extension and total rotation (IR plus external rotation [ER]), based on normative data published by Moreside and McGill (16). In total, approximately 250 men between the ages of 19 and 30 years were measured in an attempt to find participants who fit the criteria. Twenty-seven participants were identified with limited hip mobility who were willing to commit to a longer term study. Two participants dropped out because of other commitments and 1 participant because of illness, resulting in a total of 24 participants completing the study (mean height: 178.3 [7.1] cm, mean weight: 81.2 [15.05] kg). These were randomly assigned to the 4 experimental groups. All participants were healthy without current hip or back pain or past pathology in these regions. Participants completed a written informed consent document approved by the University Office for Research Ethics.
In addition to the passive hip ROM, torso endurance, and hip/spine disassociation measurement protocols that took place at the beginning and end of the 6-week intervention (17), data characterizing several dynamic movements were also collected. Although passive ROM outcomes were collected on the same day as the dynamic movement testing, the endurance outcomes were collected approximately 2 days after the dynamic to minimize any effect the endurance and dynamic tasks might have on performance of the other.
The dynamic activities were as follows: actively extend their right hip to their perceived maximum while in an upright standing posture (Figure 1A). Minimal guidance as to how to perform the action was given, other than to attempt to keep their upper body erect (i.e., avoid leaning the trunk forward). Each activity was performed twice, with the second repetition being used for analysis. This hip extension activity was chosen to observe active peak hip extension, together with associated spine extension and rotation. Next, participants completed a forward lunge: from standing position, the floor was marked at a distance 1.5× their shin length in front of the left foot. They were instructed to step forward with the left foot until their toe reached the floor marking and lunge down into forward left hip flexion (right hip extension) as low as was comfortable while keeping their upper body erect (Figure 1B). Right heel raise was permitted, but they were to maintain full right knee extension. Of interest was the amount of peak sagittal motion of the hip and back, recognizing that the hip extension in this maneuver was more of a passive stretch, thus less concentric in nature than the previous active hip extension. The third functional trial was a twist and reach activity: 2 poles were set up aside the participants in their frontal plane. The distance between the poles was 110% times their body height, with the participant standing in the middle, feet shoulder width apart. Small knobs on the poles were secured at approximately the participant’s waist height. They were instructed to reach around and touch the knob on the right pole with their left hand, and the left pole with the right, without moving their feet (Figure 2). The focus of this activity was hip and lumbar rotation, as well as associated hip/spine flexion and lumbar side bending.
Finally, participants exercised on the elliptical trainer (Octane Fitness, Brooklyn Park, MN USA) at a self-selected speed: one which they would choose if expecting to exercise for 30 minutes. This speed varied from 40 to 70 cycles per minute with a mean speed of 53 (7) cycles per minute. Although the stride length, hand position, and speed were varied at the time, the results being discussed in this study used the 66 cm stride length, a speed 30% faster than self-selected, with hands holding onto the oscillating handles of the elliptical trainer. Once they were up to speed and appeared comfortable with the activity, the motion was sampled twice, capturing 4 cycles. The elliptical trainer was chosen, in that the resulting motion is somewhat similar to one used in walking, but with slightly increased sagittal and transverse motion in the lumbar spine (18). It was also thought that variability resulting from arm motion, stride length, and velocity would be less, in that the hand and foot positions are constrained when using the elliptical trainer, as well as offering digital velocity feedback.
A Vicon MX Motion System and Nexus software (Vicon Motion Systems, Oxford, United Kingdom) were used for capturing body segment kinematics via 8 infrared cameras, collecting at a frequency of 60 Hz. Rigid plates with 4 reflective markers on each were attached via elastic straps to body segments bilaterally as follows: shin, thigh, foot, hand, upper arm, and overlying the midline of the posterior pelvis, T12, and forehead. In addition, single markers for calibration purposes only were attached over the posterior right (Rt) scapula, C7 spinous process, sternal notch, and bilaterally over the medial and lateral aspects of each ankle, knee, wrist, elbow, anterior superior iliac spine (ASIS), posterior superior iliac spine (PSIS), greater trochanters, acromions, and earlobes. The local coordinate system of the pelvis was defined by markers atop the ASIS and PSIS, with the x, y, and z axes being posterior/anterior, right/left, and vertical, respectively.
Marker data were initially processed using the Vicon Nexus software and then exported to Visual 3D (C-Motion Inc., Kingston, Canada) for further processing. Three-dimensional lumbar and hip angles relative to the pelvis were calculated using a Visual 3D algorithm with a Cardan sequence of rotations. Joint angles were filtered with a 6-Hz dual-pass Butterworth filter. Signals were screened for abnormalities, processing errors, and marker movement. For the elliptical trials, maximum and minimum joint angles were taken from the entire capture time, unless the signal drifted over time because of body position changes (i.e., neck flexion, which tended to increase lumbar flexion), in which case the maximum/minimum joint angles were extracted from a complete cycle deemed representative of the normal scope of motion. Symmetry was assumed in the elliptical and twist trials, and the right leg was used for statistical analysis. For the lunge and hip extension trials, joint angles were calculated at the instant where relevant peak joint motion occurred: that is, for a left leg forward lunge, spine and right hip angles were calculated at the moment of peak left hip flexion. Similarly during the right hip extension trials, angles were calculated at the instant of peak right hip extension. For the twist conditions, maximum and minimum angles were calculated based on the entire trial.
A series of repeated measures analyses of variance (SPSS, version 17; Chicago, IL, USA) were performed for each dependant variable (relevant spine and hip angles) using a within-subject factor of pretreatment/posttreatment and between-subject factor of treatment group. Paired t-tests were conducted on individual pairs of preresults and postresults of interest, with Bonferroni adjustments. Significance level was chosen at α = 0.05. Cohen’s d effect sizes were also calculated to aide with intervention outcome interpretations.
Functional Hip Motion
Despite large increases in passive hip mobility in groups 1 and 2, there were no significant increases in hip extension or rotation used during dynamic activities (Table 1); mean (SD) (in degrees) of increased ROM for extension: 14.0 (6)° and 10.3 (8)°; IR: 7.7 (4)° and 11.1 (4)°; ER: 14.2 (5)° and 12.4 (7)° for groups 1 and 2, respectively. Instead, average peak hip extension actually decreased an average of 2.2° and 0.8° in groups 1 and 2, respectively, during the active hip extension trials (Figure 3A) while changing less than 1° in the elliptical and lunge trials. Similarly, there was no evidence of increased hip rotation being used during the elliptical and twist/reach trials. Instead, total hip rotation decreased 2.3° and 1.6° for groups 1 and 2, respectively, on the elliptical trainer. In the twist/reach trials, group 1 hip rotation averaged a decrease of 4.6° (effect size = 0.81), whereas group 2 demonstrated a nominal increase of 0.4° (Table 1).
Functional Spine Motion
There was only one instance where lumbar motion was significantly different across all groups postintervention: lumbar rotation associated with active hip extension was less (p = 0.015, power = 0.72) (Figure 4). The largest change was demonstrated in group 2, who received both stretching and disassociation exercises, reducing their lumbar rotation from an average (SD) of 8.3(2)° to 4.2(3)° (effect size = 1.39; p = 0.105 with t-tests). As shown in Figure 6, 5 of the 6 participants in both groups 2 and 3 demonstrated decreased lumbar rotation during active hip extension after the 6-week intervention. Group 2 also demonstrated a 7° decrease in side bending during the twist and reach maneuver, resulting in a large effect size of 1.37 (p = 0.029; not significant because of the stringent 0.0125 level of significance required with Bonferroni adjustments). There was also a large increase in lumbar extension demonstrated by group 1 (stretching only) during the active hip extension trials (Figure 3B). As shown in Figure 5, every group 1 participant demonstrated increased lumbar extension when asked to extend their hip, with pregroup and postgroup measurements averaging 9.2 (5)° and 15.1 (4)°, respectively (effect size = −1.30; p = 0.04) (Figure 3B).
The first hypothesis that increased passive hip extension and rotation would result in increased hip ROM used during functional movements was rejected. Large increases in passive hip extension were achieved with training but were not used during active hip extension or lunging, both of which would be expected to result in full hip extension. Surprisingly, the 2 stretching groups averaged less hip extension postintervention during the lunge, elliptical, and active hip extension maneuvers, although not significantly so. Comparing Figures 3A and B, both stretching groups tended to decrease the amount of hip extension used during active hip extension while increasing the associated lumbar extension after 6 weeks. Thus, although they may have been focusing on positioning the right leg further behind, it seems they did not differentiate between hip and spine motion. It is notable that group 3 (core endurance) demonstrated the most consistent increase in dynamic hip ROM over the numerous trials: in 7 of the 8 hip measurements, group 3 demonstrated increased dynamic hip ROM used postintervention, with 6 of those being greater than improvements in either groups 1 or 2 (Table 1). Interestingly, some of the largest hip ROM changes occurred in peak flexion or total flexion/extension, with flexion not expected to be directly affected by the stretching routines of groups 1 and 2. However, it is in keeping with the previous findings of this research group, that 6 weeks of core stabilization exercises resulted in improved range of passive hip rotation, and adds a further dynamic component to the suggestion that improved proximal stability will facilitate increased distal mobility, as suggested by Kibler et al. (12).
Although the participants seemed to have difficulty distinguishing hip from spine extension, all intervention groups demonstrated less lumbar rotation during the active hip extension maneuver postintervention, thus the second hypothesis can be partially accepted. This finding suggests that the concept of restraining lumbar rotation may be more readily incorporated into movement, perhaps because it provides greater visual feedback and oscillates around an obvious midpoint of 0°. Constraining lumbar flexion/extension, however, was a much more difficult concept for the participants to incorporate into movement patterns, yet is one of the motions known to be injurious to the lumbar spine and intervertebral discs (3,6,27). Anecdotally, many participants tended to rotate their pelvis in an anterior or posterior tilt (i.e., around a medial/lateral axis) as they “set” their posture before the unilateral stance required for active hip extension. This type of pelvis rotation would affect both the hip and lumbar extension angles, at a time when unweighting of the right leg had not yet taken place.
Much of the literature discussing changes to movement patterns subsequent to an exercise routine is sport specific (8,13,15). In addition to basic stretches, participants in those studies practiced movements that were required of their sport, thus having more of a chance to “groove” new motor patterns. Although objective improvements in core endurance and hip flexibility were documented in the previous study (17), changing movement patterns requires that preferred modes of coordination be replaced with new patterns, which are characterized by efficiency and maximum exploitation of the passive structures (2,5,20). In our study, the elliptical trainer and twist/reach motions were not part of the motor control exercise routine. Doing so may have improved participants’ ability to transfer newfound motion to functional movement. The lunge and active hip extension were both an exercise (groups 2 and 3) and a test, yet the only improvement seen in spine control was lumbar rotation. No significant improvement in control of spine flexion/extension was detected after 6 weeks of intervention, despite the fact that these 2 exercises were specifically chosen as a sagittal and rotational challenge to spine control. These findings are similar to those of Frost et al. (7) in their analyses of Functional Movement Screen (FMS) scores before and after 12 weeks of exercise training/coaching. In both studies, participants were given latitude as to how they chose to move during specific dynamic activities, as opposed to the motion being highly cued. Because both studies documented minimal postintervention changes in FMS score or kinematics, the suggestion arises that allowing natural movement may permit excessive between-test variability to movement patterns (11), as evidenced in both studies by the large SDs and similar changes in the control groups, thus precluding statistical or biological significance.
This seems to be one of the first studies suggesting that increasing the ROM of a joint may not translate into function or change a default movement pattern. A limitation for interpretation of the data is that the subject numbers are low. Nonetheless, more robust studies can now be designed to better isolate and identify the variables that influence the effectiveness and application of stretching protocols. Studies on stretching have questioned the efficacy for injury resilience and performance enhancement (24,25). Perhaps, the data reported here will augment the interpretation of this collection of works. Furthermore, healthy young adults were chosen to participate in this study in an attempt to reduce the likelihood that reduced hip mobility was because of arthritic change. Results may not transfer to an older population or those with low back pain. Male participants were chosen to reduce the number of variables, as hip/spine movement patterns differ between sexes (1,4,23,26). As seen in the outcome graphs, variability in hip/spine motion is high. Despite attempts to standardize motion with movements relative to anthropometric measurements (lunge and twist distances), it was noticed that people moved differently from trial to trial, let alone day to day. Similarly, intersubject variability was high, as indicated by the SDs. Yet to constrain motion further would have interfered with “normal motion.” This biological variability compromises statistical analysis power, yet it was essential that freedom of movement choice not be compromised and individual response be recognized.
Stretching and core endurance protocols are incorporated into many rehabilitation and training programs, but evidence of their transference to function is lacking. This study suggests that, although both flexibility and endurance may be improved over a 6 week intervention, there was minimal evidence that these changes resulted in changes to functional movement patterns: large improvements in passive hip extension and rotation did not result in greater use of this newfound range during functional activities that were specifically chosen to challenge these motions. Similarly, although improved core endurance resulted in decreased lumbar rotation during a hip extension maneuver, there was no reduction in lumbar rotation or flexion/extension during other activities. In fact, many participants seem to have difficulty differentiating hip motion from spine motion when doing an active hip extension maneuver, suggesting that a greater focus on practicing and creating default peripheral joint motion on a stable trunk is warranted. These findings imply that a successful stretching or core endurance program may require simultaneous movement repatterning: practicing the desired movement patterns to ensure that the newfound mobility or core endurance is incorporated into functional movement patterns.
The authors acknowledge the funding assistance from the Natural Sciences and Engineering Research Council of Canada.
1. Anders C, Wagner H, Puta C, Grassme R, Scholle HC. Healthy humans use sex-specific co-ordination patterns of trunk muscles during gait. Eur J Appl Physiol 105: 585–594, 2009.
2. Caillou D, Nourrit D, Deschamps T, Lauriot B, Delignieres D. Overcoming spontaneous patterns of coordination during the acquisition of a complex balancing task. Can J Exp Psychol 56: 283–293, 2002.
3. Callaghan JP, McGill SM. Intervertebral disc herniation: Studies on a porcine model exposed to highly repetitive flexion/extension motion with compressive force. Clin Biomech (Bristol, Avon) 16: 28–37, 2001.
4. Chumanov ES, Wall-Scheffler C, Heiderscheit BC. Gender differences in walking and running on level and inclined surfaces. Clin Biomech (Bristol, Avon) 23: 1260–1268, 2008.
5. Delignières D, Nourrit D, Sioud R, Leroyer P, Zattara M, Micaleff J. Preferred coordination modes in the first steps of the learning of a complex gymnastics task. Hum Movement Sci 17: 221–241, 1998.
6. Drake JD, Callaghan JP. Intervertebral neural foramina deformation due to two types of repetitive combined loading. Clin Biomech (Bristol, Avon) 24: 1–6, 2009.
7. Frost DM, Beach TA, Callaghan JP, McGill SM. Using the functional movement screen to evaluate the effectiveness of training. J Strength Cond Res 26: 1620–1630, 2012.
8. Grimshaw PN, Burden AM. Case report: Reduction of low back pain in a professional golfer. Med Sci Sports Exerc 32: 1667–1673, 2000.
9. Herman DC, Weinhold PS, Guskiewicz KM, Garrett WE, Yu B, Padua DA. The effects of strength training on the lower extremity biomechanics of female recreational athletes during a stop-jump task. Am J Sports Med 36: 733–740, 2008.
10. Hewett TE, Myer GD. The mechanistic connection between the trunk, hip, knee, and anterior cruciate ligament injury. Exerc Sport Sci Rev 39: 161–166, 2011.
11. James CR, Dufek JS, Bates BT. Effects of injury proneness and task difficulty on joint kinetic variability. Med Sci Sports Exerc 32: 1833–1844, 2000.
12. Kibler WB, Press J, Sciascia A. The role of core stability in athletic function. Sports Med 36: 189–198, 2006.
13. Kiesel K, Plisky P, Butler R. Functional movement test scores improve following a standardized off-season intervention program in professional football players. Scand J Med Sci Sports 21: 287–292, 2011.
14. Lee LW, Kerrigan DC, Della Croce U. Dynamic implications of hip flexion contractures. Am J Physical Med Rehab 76: 502–508, 1997.
15. Lephart SM, Smoliga JM, Myers JB, Sell TC, Tsai YS. An eight-week golf-specific exercise program improves physical characteristics, swing mechanics, and golf performance in recreational golfers. J Strength Cond Res 21: 860–869, 2007.
16. Moreside JM, McGill SM. Quantifying normal 3D hip ROM in healthy young adult males with clinical and laboratory tools: Hip mobility restrictions appear to be plane-specific. Clin Biomech (Bristol, Avon) 26: 824–829, 2011.
17. Moreside JM, McGill SM. Hip joint ROM improvements using 3 different interventions. J Strength Cond Res 26: 1265–1273, 2012.
18. Moreside JM, McGill SM. How do elliptical machines differ from walking: A study of torso motion and muscle activity. Clin Biomech (Bristol, Avon), 2012.
19. Myer GD, Chu DA, Brent JL, Hewett TE. Trunk and hip control neuromuscular training for the prevention of knee joint injury. Clin Sports Med 27: 425–448, ix, 2008.
20. Nourrit D, Delignieres D, Caillou N, Deschamps T, Lauriot B. On discontinuities in motor learning: A longitudinal study of complex skill acquisition on a ski-simulator. J Mot Behav 35: 151–170, 2003.
21. Panjabi MM. The stabilizing system of the spine. Part 1. Function, dysfunction, adaptation, and enhancement. J Spinal Disord 5: 383–389, 1992.
22. Schache AG, Blanch PD, Murphy AT. Relation of anterior pelvic tilt during running to clinical and kinematic measures of hip extension. Br J Sports Med 34: 279–283, 2000.
23. Schache AG, Blanch PD, Rath DA, Wrigley T, Bennell KL. Differences between the sexes in the three-dimensional angular rotations of the lumbo-pelvic-hip complex during treadmill running. J Sports Sci 21: 105–118, 2003.
24. Shrier I. Stretching before exercise does not reduce the risk of local muscle injury: A critical review of the clinical and basic science literature. Clin J Sport Med 9: 221–227, 1999.
25. Shrier I. Does stretching improve performance? A systematic and critical review of the literature. Clin J Sport Med 14: 267–273, 2004.
26. Sullivan MS, Dickinson CE, Troup JD. The influence of age and gender on lumbar spine sagittal plane range of motion. A study of 1126 healthy subjects. Spine (Phila Pa. 1976) 19: 682–686, 1994.
27. Tampier C, Drake JD, Callaghan JP, McGill SM. Progressive disc herniation: An investigation of the mechanism using radiologic, histochemical, and microscopic dissection techniques on a porcine model. Spine (Phila Pa. 1976) 32: 2869–2874, 2007.
Keywords:Copyright © 2013 by the National Strength & Conditioning Association.
core endurance; hip ROM; core stability; dynamic activity