Scapula behavior associates with fast sprinting in first accelerated running
© The Author(s). 2016
Received: 13 January 2016
Accepted: 5 May 2016
Published: 20 May 2016
The arm-swing motion is important for coordinated lower limb movement during a fast sprint and is composed of three-dimensional scapulothoracic and glenohumeral joint motion. Here, we aimed to clarify the role of the scapula during the initiation of a sprint running when sprinter run with high horizontal acceleration. Ten sports-active students participated in four 5-m dashes, with scapular constraint using non-elastic therapy tape (constraint condition) and without scapular constraint (free condition). The sprinting kinematics was assessed by a 16-camera motion capture system. In the constraint condition, the 2-m sprint time was significantly longer than that in the free condition. At the instants of foot-contact and take-off during the first step, no significant difference in the humerothoracic flexion angle was seen between these two conditions. In contrast, at the instants of foot-contact and take-off during the first step, the humerothoracic extension angle in the constraint condition was significantly smaller than that in the free condition. The forward leaning vector angle of center of mass during the first step was significantly greater than that in the constraint condition. Although no significant difference in hip extension and foot forward leaning angles was seen at the instant of foot contact during the first step between the two conditions, at the instant of take-off, the hip extension and foot forward leaning angles in the constraint condition were significantly smaller than those in the free condition. Therefore, scapular behavior in first accelerated running contributes to larger upper- and lower-limb motions and facilitates coordinating whole-body balance for a fast sprint.
For a fast sprint running, upper and lower limb movements have to be coordinated (Lockie et al. 2003). Running speed is reduced when the arm-swing motion is constrained, such as when holding a rugby ball (Grant et al. 2003) or a field hockey stick (Wdowski and Gittoes 2013). During jogging, the momentum at horizontal component of the upper arm, forearm and hand (we define these three segments as “arm”) is not directly associated with that of the whole-body center of mass (COM) because the backward- and forward-swinging motions of the arms are in opposite directions and the momentum is cancelled (Hinrichs 1987; Hinrichs et al. 1987). In contrast, in first accelerated running, the whole-body COM leans forward from the foot contact position (Kugler and Janshen 2010), suggesting that the relative momentum at horizontal component of both arms is not cancelled. Momentum is an indication of changes in velocity; therefore, the arm-swing motion in first accelerated running would contribute to generation of the sprint speed as well as plays a role in balancing the opposing extension and flexion motions of the lower limbs (Mann 1981; Slawinski et al. 2010b). In fact, in first accelerated running, the arm-swing motion affects lower limb kinematics (Lockie et al. 2014) and relates to the performance level of the sprinter in the 100-m dash (Slawinski et al. 2010a) and the sprint time (Lockie et al. 2003).
Humeral motion relative to the thorax is contributed by scapular motion relative to the thorax and humeral motion relative to the scapula (joints that relate to these motions are defined as humerothoracic, scapulothoracic, and glenohumeral joints, respectively (Codman 1934). Humerothoracic flexion and extension are associated with arm-swing motion in accelerated running, and this may be comprised of three-dimensional (3D) motion of the scapulothoracic and glenohumeral joints. The range of motion (ROM) of the scapulothoracic joint is half that of the glenohumeral joint during humerothoracic elevation (Inman et al. 1994), and the ROM of the scapulothoracic joint increases according to the movement velocity of the humerothoracic joint (Fayad et al. 2006). In first accelerated running, the flexion and extension angular velocity of the humerothoracic joint is high (approximately 700°/s) (Slawinski et al. 2010b), indicating that the ROM of the scapulothoracic joint is important during sprint running to enhance the ROM of the humerothoracic joint and the sprint speed. Therefore, the scapular behavior would be important for fast sprinting in first accelerated running.
Field sports such as football, lacrosse and field hockey require the skill to generate sprint speed quickly from a static or near static position (Sayers 2000). Sprint running is a fundamental skill required in most sports (Reilly et al. 2000; Sayers 2000). Therefore, clarifying the role of the scapula in first accelerated running will be useful for the players and coaches of many sports. The purpose of this study was to clarify the role of the scapula in sports-active students in first accelerated running. We hypothesized that when scapular motion is constrained, the arm-swing motion would be reduced, which changes the lower limb behavior and reduces the sprint speed.
Experimental approach to the problem
No previous studies have clarified the role of the scapula in sprint running. Noninvasively, mechanical and physiologic roles of a partial body position can be examined according to acute reduction by using joint taping (Koyama et al. 2014), a gripping tool (Grant et al. 2003; Wdowski and Gittoes 2013), or hypothermic anesthesia (Meyer et al. 2004). Many polyarticular muscles are attached around the shoulder joint, which is proximally located relative to the hand and foot. Therefore, based on the available methods, scapulothoracic joint taping can be considered the best valid method to restrict scapular behavior of the runner, and we compared the kinematics in first accelerated running between the scapula constrained condition and normal condition.
Ten sports-active male students participated in this study [mean ± standard deviation (SD), age: 21.3 ± 1.1 years; height: 176.2 ± 6.0 cm; body mass: 69.3 ± 9.4 kg]. Each participant practiced daily physical activities that involved sprint running, including soccer (n = 5), rugby (n = 2), basketball (n = 2), and tennis (n = 1). The experimental protocol was approved by the Research Ethics Committee involving Living Human Participants at Ritsumeikan University (BKC-human-2013-12). All participants gave informed written consent before participation.
The participants performed four 5-m dashes without (free condition) and with the scapula constrained (constraint condition). The participants sprinted from the same comfortable standing position with maximal effort in each trial. The order of the experimental trials in the free and constraint conditions was randomized. The experimental trials were performed in the laboratory room after a sufficient warm-up of 10 min including several submaximal dashes.
Humerothoracic flexion and extension functional tests and sprinting kinematics were assessed by a 16-camera motion capture system (Raptor-E digital; Motion Analysis Corporation, Santa Rosa, CA, USA). The capture volume was 3.0 m × 2.0 m × 2.5 m (length × width × height). The 53 retro-reflective markers (9-mm diameter) were attached to the respective anatomical position of the whole-body based on modified marker set used by Slawinski et al. (2010a, b) (Fig. 1b). The validity of this method has been studied (Janes et al. 2012), and the measurement errors are estimated to be at a few degrees, which is similar to the magnetic sensor method (Lempereur et al. 2014). The 3D displacement data of the reflective markers was collected and sampled at 250 Hz. The ground reaction force (GRF) data was recorded at 1250 Hz using a force plate (TF-4060; Tec Gihan Corp., Kyoto, Japan) and was synchronized with the motion capture system by an analog/digital board.
2-m sprint time This was calculated using the displacement of the COM. The 2 m was the longest running distance using an integer within the capture length (3.0 m). This 2-m distance is used to assess performance in the first accelerated run (Otsuka et al. 2014).
Step length to first step Horizontal distance between the toe of the front leg at set position and the next toe of the opposite leg of first step was calculated.
Step frequency to first step Step frequency from start to touchdown of first step was calculated. Step frequency was calculated using the inverse of the stepping duration.
Variables during the first step: Increase in sprint speed was calculated by dividing the horizontal GRF impulse during the first step by the body mass. Sprint velocity at instant of take-off was calculated using the horizontal velocity of the COM. Forward leaning angle of the COM was calculated using the mean value of orientation angle of the vector from the center of pressure to the COM during the first step using the arc tangent. The vector was projected onto the sagittal plane. Contact time was calculated during the stance phase of first step using vertical GRF. Humerothoracic joint angles and ROMs were calculated using 3D Euler angle with creating local coordinate systems of thorax and humerus and joint coordinate system by the method of Wu et al. (2005) (Fig. 1c). X-axis rotation to be the most important because the arm-swing motion primarily involves flexion and extension motion of the humerothoracic joint (Slawinski et al. 2010b); therefore, the rotation sequence of the humerothoracic joint was X–Y–Z. The humerothoracic joint ROMs were calculated using the difference between the maximal and minimal values during the first step. Hip extension, knee flexion, ankle flexion and foot forward leaning angles of the stance leg were calculated using these angles in the sagittal plane two-dimensionally because the sprint performance is finally determined by the leg motion onto anterior direction.
The average value of the all four trials was used in each condition for further analysis. All data are shown as mean ± SD. Prior to testing for mean differences, the samples were tested for normal distribution using the Kolmogorov–Smirnov test. In the case of normally distributed samples, paired t-tests were applied. Otherwise, the Wilcoxon test was used for paired samples. The effect size between free and constraint conditions was calculated for each variable using Cohen’s d (Cohen 1988). Relative magnitude of the effect was assessed based on Cohen’s guidelines with d ≤ 0.20 representing a small difference, >0.20 but <0.80 a moderate difference and ≥0.80 a large difference between the means. The Cohen’s d statistic was calculated when means and SD were reported. The statistical power was calculated using the G*Power software version 3.1.7 (Franz Faul, Keil, Germany). The significance level was set at P < 0.05.
Sprint performance (mean ± SD)
2-m sprint time (s)
0.73 ± 0.04
0.76 ± 0.04*
Step length to first step (m)
0.88 ± 0.07
0.84 ± 0.07*
Step frequency to first step (Hz)
2.15 ± 0.18
2.16 ± 0.17
Variables during the first step
Increase in sprint speed (m s−1)
0.94 ± 0.10
0.91 ± 0.08*
Sprint speed at instant of take-off (m s−1)
4.31 ± 0.20
4.19 ± 0.23*
Forward leaning angle of center of mass (°)
25.48 ± 1.99
24.49 ± 1.95*
Contact time (s)
0.186 ± 0.021
0.186 ± 0.010
The study was the first to clarify the changes in sprint speed and kinematic parameters in the constraint condition of the scapulothoracic joints. During the first step, the humerothoracic extension ROM of the backward-swinging arm and the hip extension angle of the stance leg at the instant of take-off in the constraint condition were significantly smaller than those in free condition even though the statistical powers were low. In the free condition, the 2-m sprint time was significantly shorter than that in the constraint condition. These findings suggest that in first accelerated running, the scapular behavior in the backward-swinging arm coordinates with humerothoracic extension and contralateral hip extension, thereby enhancing sprint speed.
In previous studies, many authors have shown interest in the relation between arm swing and sprint performance. Sprint speed was significantly different between the without constraint condition and with constraint condition created carrying a field hockey stick; the difference was significant at 1.2 % (Wdowski and Gittoes 2013). Compared with sprinting 20 m without the ball, that with the ball in both hands led to the greatest decrement in sprint speed, although left-arm and right-arm handed methods also reduced the sprint speed (Grant et al. 2003). These significant differences were 1.7, 1.0 and 0.9 %, respectively. In this study, the sprint time in the constraint condition was longer than that in the free condition. This relative difference between the two conditions was 4.1 % and was interestingly higher than that in previous studies (Grant et al. 2003; Wdowski and Gittoes 2013). Compared to the constraint of the arm-swing motion, the limited scapular motion may have a stronger effect on the decrease of sprint speed.
X-axis rotations of humerothoracic joints are important because the arm-swing motions primarily involve humerothoracic flexion and extension motions (Slawinski et al. 2010b). In the constraint condition compared with the free condition, the humerothoracic flexion ROM of the forward-swinging arm did not change in first accelerated running. In contrast, humerothoracic extension of the backward-swinging arm was smaller in the constraint condition compared with that in the free condition. Moreover, in the functional tests, the humerothoracic extension ROM was limited more than that of humerothoracic flexion (44.9 % decrease vs. 17.1 % decrease). These findings suggest that compared with the humerothoracic flexion motion, extension is more sensitive to constraint of the scapulothoracic joint. The coracohumeral ligament, which is a part of the hard tissue in front of the glenohumeral joint, has a greater effect on the stability of glenohumeral joint when performing the humerothoracic extension than during the flexion motion (Arai et al. 2014). The glenohumeral extension ROM is smaller than that of glenohumeral flexion because the coracohumeral ligament is strained during early glenohumeral extension (Izumi et al. 2011). Therefore, a larger 3D motion of the scapulothoracic joint is more required for sufficient humerothoracic extension than that for humerothoracic flexion. The difference in the anatomical features of the shoulder between the forward- and backward-swinging arms might lead to different contribution of the scapulothoracic and glenohumeral joints to the humerothoracic joint during the first step.
Whilst the hip extension angle of the stance leg at the instant of take-off in the free condition was larger than that in the constraint condition, no significant difference in knee and ankle angles of the stance leg was seen between the two conditions. This may be the cause of the lower foot forward leaning angle of the stance leg in the constraint condition than that in the free condition, and finally the lower forward leaning angle of the COM during the first step. Higher horizontal accelerations were generated by more forward leaning of the body at toe-off (Kugler and Janshen 2010). The forward leaning angle of the COM at the instant of take-off has a positive correlation with horizontal displacement of the COM during the stance phase (Hunter et al. 2004), suggesting that the forward leaning angle of the COM at take-off is important for enhancing sprint speed. Our results supported these findings of previous studies, and this limited leg motion of the stance leg in the constraint condition may cause loss of whole-body balance during kicking ground, thereby reduced sprint speed. Therefore, the 3D scapular behavior in first accelerated running may play a role in increasing humerothoracic extension of the backward arm and hip extension of the stance leg, thereby contributing to coordinated whole-body balance for great sprint acceleration. In addition, step length to first step was longer in the free condition than that in the constraint condition. This suggests that scapular behavior affects the beginning of motion in sprint running immediately before the first step, thereby affecting the ability of the sprinter to enhance sprint speed. Thus, our hypothesis was accepted.
There is a limitation in this study. Our study included a small number of participants, which might underpower our analysis of some variables. The findings in this study were based on ten participants; therefore, the statistical powers of some variables were low. Further study is needed with a larger sample size. Despite this limitation, our findings indicate an association between scapula behavior and fast sprinting in the first zone of accelerated running.
When the arm-swing motion was restricted by constraining scapular motion, it clearly limited the humerothoracic extension of the backward-swinging arm. As a result, this scapular constraint affected the stance-leg motion and whole-body position during the first step, thereby reducing the sprint speed. Our results demonstrated that 3D scapular motion is related to the sprint speed in accelerated running. Our findings may be applied to the followings: for athletes with low scapular flexibility, improving it by performing scapular flexibility exercises is important as it may be related to improvement in the generated sprint speed. Also, for female athletes, the effects of compressing both scapulae by a sports bra would affect to sprinting performance in first accelerated running. In fact, a sport bra affect to running kinematics and the performance relative to without that (White et al. 2009). Further researches are required to clarify these questions in detail in the future.
Conceived and designed the experiments: MO and TI. Performed the experiments: MO and TI. Analyzed the data: MO, TI and TH. Drafting the manuscript: MO and TI. Contributed reagents/materials/analysis tools: MO, TI, TI. Final approval of the version to be published: MO, TI, TH, and TI. All authors read and approved the final manuscript.
The authors thank all of the study participants. The authors received no funding for this study.
TI agree to be accountable for all aspects of the work in ensuring that questions related to the accuracy or integrity of any part of the work are appropriately investigated and resolved.
The authors declare that they have no competing interests.
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- Arai R, Nimura A, Yamaguchi K, Yoshimura H, Sugaya H, Saji T, Matsuda S, Akita K (2014) The anatomy of the coracohumeral ligament and its relation to the subscapularis muscle. J Shoulder Elbow Surg 23(10):1575–1581View ArticleGoogle Scholar
- Codman EA (1934) The shoulder. Thomas Todd, BostonGoogle Scholar
- Cohen J (1988) Statistical power analysis for the behavioral sciences. Lawrence Erlbaum Associates, HillsdaleGoogle Scholar
- Dempster WT, Gaughran GRL (1967) Properties of body segments based on size and weight. Am J Anat 120(1):33View ArticleGoogle Scholar
- Fayad F, Hoffmann G, Hanneton S, Yazbeck C, Lefevre-Colau MM, Poiraudeau S, Ravel M, Roby-Brami A (2006) 3-D scapular kinematics during arm elevation: effect of motion velocity. Clin Biomech 21(9):932–941View ArticleGoogle Scholar
- Grant SJ, Oommen G, McColl G, Taylor J, Watkins L, Friel N, Watt I, McLean D (2003) The effect of ball carrying method on sprint speed in rugby union football players. J Sports Sci 21(12):1009–1015View ArticleGoogle Scholar
- Hanavan EP (1964) A mathematical model of the human body. In: Aerospace Medical Research Laboratories (ed) AMRL-TR-64-102. Wright-Patterson Air Force Base, Dayton, pp 1–149Google Scholar
- Hinrichs RN (1987) Upper extremity function in running. II: angular momentum considerations. Int J Sport Biomech 3(3):242Google Scholar
- Hinrichs RN, Cavanagh PR, Williams KR (1987) Upper extremity function in running. I: center of mass and propulsion considerations. Int J Sport Biomech 3(3):222Google Scholar
- Hunter JP, Marshall RN, McNair PJ (2004) Interaction of step length and step rate during sprint running. Med Sci Sports Exerc 36(2):261–271View ArticleGoogle Scholar
- Inman VT, Saunders JB, Abbott LC (1994) Observations of the function of the shoulder joint. J Bone Joint Surg 26:1–31Google Scholar
- Ito A, Fukuda K, Kijima K (2008) Mid-phase movements of Tyson Gay and Asafa Powell in the 100 metres at the 2007 World Championships in Athletics. New Stud Athl 23(2):39–43Google Scholar
- Izumi T, Aoki M, Tanaka Y, Uchiyama E, Suzuki D, Miyamoto S, Fujimiya M (2011) Stretching positions for the coracohumeral ligament: strain measurement during passive motion using fresh/frozen cadaver shoulders. Sport Med Arthrosc Rehabil Ther Technol 3(1):2View ArticleGoogle Scholar
- Janes WE, Brown JM, Essenberg JM, Engsberg JR (2012) Development of a method for analyzing three-dimensional scapula kinematics. Hand 7(4):400–406View ArticleGoogle Scholar
- Koyama K, Kato T, Yamauchi J (2014) The effect of ankle taping on the ground reaction force in vertical jump performance. J Strength Cond Res 28(5):1411–1417View ArticleGoogle Scholar
- Kugler F, Janshen L (2010) Body position determines propulsive forces in accelerated running. J Biomech 43(2):343–348View ArticleGoogle Scholar
- Lempereur M, Brochard S, Leboeuf F, Remy-Neris O (2014) Validity and reliability of 3D marker based scapular motion analysis: a systematic review. J Biomech 47(10):2219–2230View ArticleGoogle Scholar
- Lockie RG, Murphy AJ, Spinks CD (2003) Effects of resisted sled towing on sprint kinematics in field-sport athletes. J Strength Cond Res 17(4):760–767Google Scholar
- Lockie RG, Callaghan SJ, Jeffriess MD (2014) Acceleration kinematics in cricketers: implications for performance in the field. J Sport Sci Med 13(1):128–136Google Scholar
- Mann RV (1981) A kinetic analysis of sprinting. Med Sci Sport Exerc 13(5):325–328View ArticleGoogle Scholar
- Meyer PF, Oddsson LIE, Luca CJD (2004) The role of plantar cutaneous sensation in unperturbed stance. Exp Brain Res 156(4):505–512View ArticleGoogle Scholar
- Otsuka M, Shim JK, Yoshioka S, Kurihara T, Nokata N, Isaka T (2014) Effect of expertise on 3D force application during starting block phase and subsequent steps in sprint running. J Appl Biomech 30(3):390–400View ArticleGoogle Scholar
- Reilly T, Bangsbo J, Franks A (2000) Anthropometric and physiological predispositions for elite soccer. J Sport Sci 18(9):669–683View ArticleGoogle Scholar
- Sayers M (2000) Running techniques of field sport players. Sport Coach 23(1):26–27Google Scholar
- Slawinski J, Bonnefoy A, Leveque JM, Ontanon G, Riquet A, Dumas R, Cheze L (2010a) Kinematic and kinetic comparisons of elite and well-trained sprinters during sprint start. J Strength Cond Res 24(4):896–905View ArticleGoogle Scholar
- Slawinski J, Bonnefoy A, Ontanon G, Leveque JM, Miller C, Riquet A, Cheze L, Dumas R (2010b) Segment-interaction in sprint start: analysis of 3D angular velocity and kinetic energy in elite sprinters. J Biomech 43(8):1494–1502View ArticleGoogle Scholar
- Wdowski MM, Gittoes MJ (2013) Kinematic adaptations in sprint acceleration performances without and with the constraint of holding a field hockey stick. Sport Biomech 12(2):143–153View ArticleGoogle Scholar
- White JL, Scurr JC, Smith NA (2009) The effect of breast support on kinetics during overground running performance. Ergonomics 52(4):492–498View ArticleGoogle Scholar
- Wu G, van der Helm FC, Veeger HE, Makhsous M, Van Roy P, Anglin C, Nagels JR, Karduna A, McQuade K, Wang XW, Werner F, Buchholz B (2005) ISB recommendation on definitions of joint coordinate systems of various joints for the reporting of human joint motion—part II: shoulder, elbow, wrist and hand. J Biomech 38(5):981–992View ArticleGoogle Scholar