Skip to main content
Download PDF
  • Research article
  • Open access
  • Published:

The effects of a subsequent jump on the knee abduction angle during the early landing phase

BMC Musculoskeletal Disorders volume 19, Article number: 379 (2018) Cite this article

Abstract

Background

A double-leg landing with or without a subsequent jump is commonly used to evaluate the neuromuscular control of knee abduction. However, the differences in frontal plane knee biomechanics between landings with and without a subsequent jump are not well known. The purpose of the present study was to investigate the effects of a subsequent jump on knee abduction, including during the early landing phase, in female and male subjects.

Methods

Twenty-one female subjects and 21 male subjects participated. All subjects performed drop landing task (a landing without a subsequent jump) and drop vertical jump task (a landing with a subsequent jump). The subjects landed from a 30-cm height. In drop vertical jump, the subjects also performed a maximum vertical jump immediately after landing. The knee abduction angle and moment were analyzed using a 3D motion analysis system. A two-way analysis of variance (task × time) was performed to examine the effects of a subsequent jump on the knee abduction angle during the early landing phase in female and male subjects. Another two-way analysis of variance (task × sex) was performed to compare peak knee abduction angles and moments.

Results

In female subjects, the knee abduction angle was significantly greater during drop vertical jump than during drop landing, as measured 45 to 80 ms after initial contact (P < 0.05). Significant task-dependent effects in the peak knee abduction angle (P = 0.001) and the abduction moment (P = 0.029) were detected. The peak knee abduction angle and the abduction moment were greater during drop vertical jump than during drop landing.

Conclusions

Subsequent jumps cause greater knee abduction during the early landing phase only in female subjects. This finding may relate to the sex discrepancy in non-contact anterior cruciate ligament injuries. Additionally, the presence of a subsequent jump significantly increases the peak knee abduction angle and the peak knee abduction moment during landings. Therefore, compared with a landing task without a subsequent jump (drop landing), a landing task with a subsequent jump (drop vertical jump) may be advantageous for screening for knee abduction control, especially in female athletes.

Peer Review reports

Background

Anterior cruciate ligament (ACL) injuries occur frequently in non-contact situations, such as landing from a jump, cutting, or pivoting [1,2,3]. Female athletes are at a higher risk of a non-contact ACL injury than male athletes [4]. Although ACL prevention programs that target female athletes do have a preventive effect [5,6,7], the overall number of ACL injuries in female athletes remains high [4]. One of the reasons for the continued elevated incidence of female ACL injury is that prevention programs have not spread effectively to athletes or coaches [8]. It is therefore important that preventive interventions emphasize those with a higher risk of ACL injury due to modifiable factors [8].

Hewett et al. [9] found that the peak knee abduction angle and the peak abduction moment during a landing were significant predictors of ACL injury. Video analysis studies of ACL injuries showed that valgus collapse occurs in most female cases [2, 10,11,12]. ACL injuries were believed to occur immediately after ground contact [11,12,13], and one study suggested that a rapid increase in the knee abduction angle during the early landing phase was a mechanism behind ACL injury [11]. Therefore, evaluating knee abduction control during the early landing phase as well as the peak knee abduction angle and the knee abduction moment during landing is important.

Since a double-leg landing is one of the most frequent causes of an ACL injury [12], landings with or without a subsequent jump are commonly used to evaluate the neuromuscular control of knee abduction [9, 14,15,16,17,18]. However, the differences in frontal plane knee biomechanics between landings with and without a subsequent jump remain poorly characterized. A previous study that directly compared landing tasks with and without a subsequent jump could not detect a difference in the knee abduction moment or the abduction angle at peak tibial shear forces [15]. Bates et al. [14] observed a significant difference in the peak knee abduction moment and the abduction angle between the 1st and 2nd landings of a drop vertical jump task, but the two landings involved different horizontal movements before landing. In addition, no study has examined the effects of a subsequent jump on knee abduction during the early landing phase. Understanding the effects of a subsequent jump on frontal plane knee biomechanics, including during the early landing phase, would be informative for clinicians as they evaluate knee abduction control. Furthermore, although the effects of a subsequent jump on sagittal plane biomechanics during a landing were found to differ between females and males [19], it remains unknown whether changes in frontal plane knee biomechanics also differ between females and males. Since sagittal plane hip and knee kinematics relate to frontal plane knee biomechanics during a landing [18], the effects of a subsequent jump on frontal plane knee biomechanics may differ between female and male subjects. Investigating sex differences in the effects of a subsequent jump on frontal plane knee biomechanics during a landing would be helpful in understanding the sex discrepancy in the incidence of ACL injuries.

The purpose of the present study was to investigate the effects of a subsequent jump after a landing on knee biomechanics, especially for the frontal plane, including during the early landing phase, in female and male subjects. The hypotheses of the study are that the knee abduction angle and the abduction moment are greater during landings followed by a jump than during landings without a subsequent jump and that the effects of a subsequent jump on knee abduction differ between female and male subjects.

Methods

Subjects

Twenty-one female subjects (mean ± SD: age 21.3 ± 1.2 years; height 161.5 ± 6.6 cm; mass 54.5 ± 7.8 kg) and 21 male subjects (age 21.4 ± 1.7 years; height 173.4 ± 5.2 cm; mass 63.2 ± 8.1 kg) participated in this study. All subjects had experience with regular sports activities, such as basketball, soccer, and handball. Subjects were excluded from this study if they reported any history of a musculoskeletal injury within the prior 6 months, a fracture or surgery of the lower extremities or trunk, or knee injuries, or had previously participated in jump/landing training or an ACL prevention program. Institutional review board approval and informed consent were obtained before this study was performed.

Procedures and data collection

The right legs of all subjects were analyzed because the dominant leg, which was defined as the leg used for kicking a ball, was the right one in all subjects. Retroreflective markers were placed on the sacrum and right iliac crest as well as the bilateral shoulders, anterosuperior iliac spines, greater trochanters, hips, medial and lateral knees, medial and lateral ankles, heels, second and fifth metatarsal heads, and right thigh and shank clusters of each subject who stood with bare feet (Fig. 1). Static standing trial data were then collected for each subject to obtain a zero reference. After the collection of zero-reference data, the subjects performed landings with or without a subsequent jump in random order. During landings without a subsequent jump (drop landing, DL), the subjects stood with their feet shoulder-width apart on a box that was 30 cm high [15]. The subjects then dropped off the box and landed on two force plates, one for each foot (Fig. 2a). During landings with a subsequent jump (drop vertical jump, DVJ), the subjects stood on the box, dropped off the box, and landed on the two force plates in the same way as in the task without a subsequent jump, but then performed a maximum vertical jump immediately after landing [9, 15] (Fig. 2b). The first landing from the box was analyzed. Through the two landing tasks, the subjects were asked to keep their hands at head level.

Fig. 1
figure 1

Marker placement

Full size image
Fig. 2
figure 2

The two landing tasks. In drop landing (DL, landings without a subsequent jump), the subjects drop off a 30-cm high box and land on the force plates (a). During drop vertical jump (DVJ, landings with a subsequent jump), the subjects drop off the box and then jump immediately after landing (b)

Full size image

All data were collected with EVaRT 4.4 (Motion Analysis Corporation, Santa Rosa, CA, USA) using a motion analysis system with six high-speed digital cameras (Hawk cameras, Motion Analysis Corporation) and synchronized force data (Type 9286, Kistler AG, Winterthur, Switzerland). The sampling rates were set at 200 Hz for camera data and at 1000 Hz for force data. The camera position was considered and standardized before testing to reduce marker-trajectory gaps less than 20 frames (10% of the capture frequency), as a previous study deemed good in trials [20].

Data processing and reduction

Marker-trajectory gaps were filled based on the coordinate data of three other markers in the same segment. The kinematics of the knee joint were calculated using a joint coordinate system and global optimization techniques with the SIMM 6.0.2 software (Musculo Graphics, Santa Rosa, CA, USA) [21]. The knee joint center was defined as the midpoint of the medial and lateral epicondyle markers. The hip join center was identified based on a previous study [22]. Zero references were set at specific knee angles during standardized static standing [23]. The external knee abduction and flexion moments were calculated using the inverse dynamics technique and normalized to each subject’s body weight and height (Nm/(kg*m)) using a custom MATLAB program (MathWorks, Inc., Natick, MA, USA). The initial ground contact (IC) was defined as the time when the vertical ground reaction force exceeded 10 N [23]. The knee abduction and flexion angles were analyzed between 0 and 80 ms after IC, since an ACL injury is thought to usually occur within approximately 80 ms after IC [11]. The peak knee abduction and flexion moments from IC to peak knee flexion were also calculated.

Statistical analysis

Intraclass correlation coefficients (ICCs) were calculated as within-session reliability (ICC (3, k)) [23]. The ICC classifications were based on Fleiss (< 0.4 was poor, 0.4 to 0.75 was fair to good, > 0.75 was excellent) [24]. The typical errors that are reported in the measurement units were also calculated [23, 25].

A two-factor repeated measures analysis of variance (ANOVA) was used to examine the effects of subsequent jumps and time on knee abduction and flexion motions in the 80 ms after IC in female and male subjects. A mixed-model ANOVA was used to examine the effects of subsequent jumps and sex differences on the peak knee angle and moment. Bonferroni tests were used for post hoc comparisons. The statistical significance level was set at P < 0.05. These statistical analyses were performed using the IBM SPSS Statistics 22 software program (IBM, Armonk, NY, USA).

Results

The ICC values of knee abduction angle during the early landing phase were greater than 0.951 and were classified as excellent for both landing tasks. The average typical errors for DVJ and DL were 0.9 ± 0.1° (range 0.7–1.1°) and 0.8 ± 0.1° (range 0.6–0.9°). Concerning knee flexion angle during the early landing phase, the ICCs were greater than 0.941 and were classified as excellent for both landing tasks. The average typical errors for DVJ and DL were 1.7 ± 0.3° (range 1.4–2.3°) and 1.7 ± 0.2° (range 1.4–1.9°). The ICCs and typical errors for peak angles and peak moments are presented in Table 1. All ICCs for these discrete data were classified as excellent.

Table 1 Within-session reliability of discrete data
Full size table

For female subjects, the knee abduction angle was significantly greater during DVJ (landings with a subsequent jump) than during DL (landings without a subsequent jump), as measured 45 to 80 ms after IC (P = 0.002–0.027, power = 0.62–0.94) (Table 2 and Fig. 3a). The results of a two-way ANOVA demonstrated the significant impact of time and subsequent jumps as well as their interaction in female subjects (time effect: P < 0.001, subsequent jump effect: P = 0.024, interaction: P < 0.001). In contrast, there were no significant differences in knee abduction angle between DVJ and DL in male subjects (P = 0.059–0.996) (Table 2 and Fig. 3b). The 2-way ANOVA demonstrated the significant effects of time and the time-by-subsequent jump interaction (both: P < 0.001). A subsequent jump did not have a significant effect on the knee abduction angle of male subjects (P = 0.838). With respect to the peak knee abduction angle during landing, significant effects of sex and a subsequent jump were found (sex effect: P = 0.005, subsequent jumping effect: P = 0.001), while there was no interaction between sex and a subsequent jump (P = 0.741) (Fig. 3c). Female subjects demonstrated greater peak knee abduction angle than male subjects (95% CI 1.7–8.9°). The peak knee abduction angle was significantly greater during DVJ (landings with a subsequent jumps) than DL (landings without a subsequent jump) (95% CI 0.9–3.1°).

Table 2 The differences in knee joint angle between DVJ (landings with a subsequent jump) and DL (landings without a subsequent jump)
Full size table
Fig. 3
figure 3

Knee abduction angles during the early landing phase for female (a) and male subjects (b) and peak knee abduction angles during the landing phase (c). *indicates a significant difference (P < 0.05). IC, initial contact

Full size image

The knee flexion angles in female and male subjects were significantly greater during DVJ (landings with a subsequent jump) than during DL (landings without a subsequent jump), as measured 0 to 80 ms after IC (female: all P < 0.001, power > 0.99; male: all P < 0.001, power > 0.99) (Table 2 and Fig. 4). The 2-way ANOVA demonstrated the significant effects of time and a subsequent jump on the knee flexion angles of both female and male subjects (all P < 0.001), while no interaction effect was observed (female: P = 0.654, male: P = 0.227). There was no significant difference in the peak knee flexion angle between DVJ and DL in female subjects (P = 0.446, 95% CI -3.7–8.2°), while male subjects had a significantly greater angle during DVJ (landings with a subsequent jump) than during DL (landings without a subsequent jump) (P = 0.004, power = 0.70, 95% CI 3.0–14.9°) (Fig. 4c). The 2-way ANOVA demonstrated the significant effect of a subsequent jump on the peak knee flexion angle (P < 0.001). In contrast, sex did not have a significant effect, and there was no interaction between these factors (sex effect: P = 0.622, interaction: P = 0.113).

Fig. 4
figure 4

Knee flexion angles during the early landing phase for female (a) and male subjects (b) and the peak knee abduction angle measured during the landing phase (c). *indicates a significant difference (P < 0.05). IC, initial contact

Full size image

With respect to the peak knee abduction moment, we could not find a statistically significant difference between DVJ and DL in either female or male subjects (female: P = 0.179, male: P = 0.073) (Fig. 5a). There were no significant differences in the peak knee abduction moment between female and male subjects (DVJ: P = 0.636, DL: P = 0.824). The ANOVA demonstrated that a subsequent jump had a significant impact on the peak knee abduction moment (P = 0.029, 95% CI 0.05–0.081 Nm/(kg*m)). In contrast, sex did not have a significant effect, and there was no interaction between these factors (sex effect: P = 0.684, interaction: P = 0.738). The peak knee flexion moment in male subjects was significantly greater during DVJ (landings with a subsequent jump) than during DL (landings without a subsequent jump) (P < 0.001, power > 0.99, 95% CI 0.245–0.446 Nm/(kg*m)) (Fig. 5b), although we failed to detect a significant difference in female subjects (P = 0.067, 95% CI -0.007–0.194 Nm/(kg*m)). The 2-way ANOVA also found significant effects of the subsequent jump and an interaction with the peak knee flexion moment (subsequent jumping effect: P < 0.001, interaction: P = 0.001), while we could not detect a significant impact of sex on the peak knee flexion moment (P = 0.052).

Fig. 5
figure 5

Peak knee abduction (a) and flexion moments (b). *indicates a significant difference between DVJ and DL, as detected by the post hoc test (P < 0.05)

Full size image

Discussion

The purpose of this study was to clarify the effects of a subsequent jump on knee biomechanics, especially for the frontal plane. The results showed that the knee abduction angle was significantly greater during DVJ (landings with a subsequent jump), as measured 45 to 80 ms after IC, but only in female subjects. In addition, the significant main effects of a subsequent jump on the peak knee abduction angle and the peak abduction moment were confirmed. These findings suggest that a subsequent jump after a landing impacts frontal plane knee biomechanics during the landing, especially in female subjects.

A video analysis study of ACL injury cases suggested that ACL injuries occur within 80 ms after landing and that the knee abduction angle increased rapidly during the early landing phase [11]. Cadaveric simulation studies suggest that a knee abduction load with an anterior tibial shear force during the early landing phase plays a crucial role in ACL injury [13, 26,27,28]. The present study showed that the knee abduction angle of female subjects was significantly greater during DVJ (landings with a subsequent jump) than during DL (landings without a subsequent jump), as measured 45 to 80 ms after IC. The differences between the two landing tasks were small, but within-session reliability was classified as excellent, and those differences exceeded within-session typical errors. In contrast, male subjects did not demonstrate a significant difference in knee abduction angle within 80 ms after IC between the two landing tasks. The different effects of a subsequent jump on the knee abduction angle during the early landing phase between female and male subjects may relate to the sex discrepancy in the incidence of ACL injuries [4].

The results of this work support those of a previous study that measured significant differences in the peak knee abduction angle and abduction moment between the 1st and 2nd landings of DVJ [14]. Since the subjects dropped from the same height in both landing tasks, the differences in the peak knee abduction angle and abduction moment were thought to be caused by the subject’s preparation for generating the power required to perform a subsequent jump. The literature has shown that the presence of a subsequent jump also affected lower extremity muscle activities before and after a landing [29]. These muscle activity changes may affect frontal plane knee biomechanics during the landing. Further studies are needed to investigate muscle activity and knee biomechanics to better understand the mechanism that underlies the effects caused by a subsequent jump. Additionally, to the best of our knowledge, it remains unknown what role frontal plane knee biomechanics plays in plyometric jumping performance. Understanding how frontal plane knee biomechanics, including power or work calculations, contributes to plyometric jumping performance may help explain the mechanism that underlies the effects of a subsequent jump on frontal plane knee biomechanics during a landing.

We found that male subjects had a significantly greater peak knee flexion moment during DVJ (landings with a subsequent jump) than during DL (landings without a jump). A greater knee flexion moment reflects a greater quadriceps force during a landing task [30], and quadriceps contraction resists a knee valgus moment [31]. Male subjects may have increased frontal plane knee stability with a greater quadriceps force. In addition, previous studies have shown that females have greater laxity, or less stiffness, during knee valgus rotation than males [32,33,34]. These neuromuscular and structural differences may be reasons for the observed differences in the impact of a subsequent jump on the knee abduction angle during the early landing phase between female and male subjects.

With respect to clinical relevance, the present study shows that a landing task with a subsequent jump can result in greater knee abduction compared with landings without a subsequent jump, especially in females. Hewett et al. [9] reported that greater knee abduction moment and angle during a DVJ task were the significant predictors of ACL injury. Clinicians should use a landing task with a subsequent jump, e.g., DVJ, to evaluate knee abduction control. Additionally, ACL prevention programs should include landings with a jump as well as landings without a jump, in line with previous successful programs [5,6,7].

This study has some limitations. We examined double-leg landing tasks, while single-leg landing tasks with or without a subsequent jump are also commonly used to evaluate knee biomechanics. The effects of a subsequent jump after a single-leg landing may differ from the effects observed after a double-leg landing. Second, the present study did not investigate the mechanisms that underlie the effects of a subsequent jump on frontal plane knee biomechanics. If this mechanism is understood, an intervention may be developed. Future studies should include analyses of muscle activity and lower-extremity jumping mechanics.

Conclusions

The present study showed that a jump performed immediately after a landing significantly increases the knee abduction angle during the early landing phase in female subjects but not in males. These findings may relate to the known sex discrepancies in the incidence of non-contact ACL injuries. Additionally, the presence of a subsequent jump significantly impacts the subject’s peak knee abduction angle and abduction moment during a landing. A landing task with a subsequent jump, e.g., DVJ, is advantageous for evaluating knee abduction control in comparison with landings without a subsequent jump, especially in female subjects.

Abbreviations

ACL:

Anterior cruciate ligament

DL:

Drop landing

DVJ:

Drop vertical jump

IC:

Initial contact

References

  1. Boden BP, Dean GS, Feagin JA Jr, Garrett WE Jr. Mechanisms of anterior cruciate ligament injury. Orthopedics. 2000;23:573–8.

    CAS  PubMed  Google Scholar 

  2. Olsen OE, Myklebust G, Engebretsen L, Bahr R. Injury mechanisms for anterior cruciate ligament injuries in team handball: a systematic video analysis. Am J Sports Med. 2004;32:1002–12.

    Article  Google Scholar 

  3. Shimokochi Y, Shultz SJ. Mechanisms of noncontact anterior cruciate ligament injury. J Athl Train. 2008;43:396–408.

    Article  Google Scholar 

  4. Agel J, Rockwood T, Klossner D. Collegiate ACL injury rates across 15 sports: National Collegiate Athletic Association Injury Surveillance System Data Update (2004-2005 through 2012-2013). Clin J Sport Med. 2016;26:518–23.

    Article  Google Scholar 

  5. Hewett T, Lindenfeld T, Riccobene J, Noyes F. The effect of neuromuscular training on the incidence of knee injury in female athletes - a prospective study. Am J Sports Med. 1999;27:699–706.

    Article  CAS  Google Scholar 

  6. LaBella CR, Huxford MR, Grissom J, Kim K-Y, Peng J, Christoffel KK. Effect of neuromuscular warm-up on injuries in female soccer and basketball athletes in urban public high schools: cluster randomized controlled trial. Arch Pediatr Adolesc Med. 2011;165:1033–40.

    Article  Google Scholar 

  7. Mandelbaum BR, Silvers HJ, Watanabe DS, Knarr JF, Thomas SD, Griffin LY, et al. Effectiveness of a neuromuscular and proprioceptive training program in preventing anterior cruciate ligament injuries in female athletes: 2-year follow-up. Am J Sports Med. 2005;33:1003–10.

    Article  Google Scholar 

  8. Myer GD, Ford KR, Brent JL, Hewett TE. Differential neuromuscular training effects on ACL injury risk factors in “high-risk” versus “low-risk” athletes. BMC Musculoskelet Disord. 2007;8:39.

    Article  Google Scholar 

  9. Hewett TE, Myer GD, Ford KR, Heidt RS, Colosimo AJ, McLean SG, et al. Biomechanical measures of neuromuscular control and valgus loading of the knee predict anterior cruciate ligament injury risk in female athletes: a prospective study. Am J Sports Med. 2005;33:492–501.

    Article  Google Scholar 

  10. Hewett TE, Torg JS, Boden BP. Video analysis of trunk and knee motion during non-contact anterior cruciate ligament injury in female athletes: lateral trunk and knee abduction motion are combined components of the injury mechanism. Br J Sports Med. 2009;43:417–22.

    Article  CAS  Google Scholar 

  11. Koga H, Nakamae A, Shima Y, Iwasa J, Myklebust G, Engebretsen L, et al. Mechanisms for noncontact anterior cruciate ligament injuries: knee joint kinematics in 10 injury situations from female team handball and basketball. Am J Sports Med. 2010;38:2218–25.

    Article  Google Scholar 

  12. Krosshaug T, Nakamae A, Boden BP, Engebretsen L, Smith G, Slauterbeck JR, et al. Mechanisms of anterior cruciate ligament injury in basketball: video analysis of 39 cases. Am J Sports Med. 2007;35:359–67.

    Article  Google Scholar 

  13. Kiapour AM, Quatman CE, Goel VK, Wordeman SC, Hewett TE, Demetropoulos CK. Timing sequence of multi-planar knee kinematics revealed by physiologic cadaveric simulation of landing: implications for ACL injury mechanism. Clin Biomech (Bristol Avon). 2014;29:75–82.

    Article  Google Scholar 

  14. Bates NA, Ford KR, Myer GD, Hewett TE. Kinetic and kinematic differences between first and second landings of a drop vertical jump task: implications for injury risk assessments. Clin Biomech (Bristol Avon). 2013;28:459–66.

    Article  Google Scholar 

  15. Cruz A, Bell D, McGrath M, Blackburn T, Padua D, Herman D. The effects of three jump landing tasks on kinetic and kinematic measures: implications for ACL injury research. Res Sports Med. 2013;21:330–42.

    Article  Google Scholar 

  16. Kernozek TW, Torry MR, Van Hoof H, Cowley H, Tanner S. Gender differences in frontal and sagittal plane biomechanics during drop landings. Med Sci Sports Exerc. 2005;37:1003–12.

    PubMed  Google Scholar 

  17. Pappas E, Hagins M, Sheikhzadeh A, Nordin M, Rose D. Biomechanical differences between unilateral and bilateral landings from a jump: gender differences. Clin J Sport Med. 2007;17:263–8.

    Article  Google Scholar 

  18. Pollard CD, Sigward SM, Powers CM. Limited hip and knee flexion during landing is associated with increased frontal plane knee motion and moments. Clin Biomech (Bristol Avon). 2010;25:142–6.

    Article  Google Scholar 

  19. Butler RJ, Willson JD, Fowler D, Queen RM. Gender differences in landing mechanics vary depending on the type of landing. Clin J Sport Med. 2013;23:52–7.

    Article  Google Scholar 

  20. Myer GD, Bates NA, DiCesare CA, Barber Foss KD, Thomas SM, Wordeman SC, et al. Reliability of 3-dimensional measures of single-leg drop landing across 3 institutions: implications for multicenter research for secondary ACL-injury prevention. J Sport Rehabil. 2015;24:198–209.

    Article  Google Scholar 

  21. Grood ES, Suntay WJ. A joint coordinate system for the clinical description of three-dimensional motions: application to the knee. J Biomech Eng. 1983;105:136–44.

    Article  CAS  Google Scholar 

  22. Bell AL, Pedersen DR, Brand RA. A comparison of the accuracy of several hip center location prediction methods. J Biomech. 1990;23:617–21.

    Article  CAS  Google Scholar 

  23. Ford KR, Myer GD, Hewett TE. Reliability of landing 3D motion analysis: implications for longitudinal analyses. Med Sci Sports Exerc. 2007;39:2021–8.

    Article  Google Scholar 

  24. Fleiss JL. The design and analysis of clinical experiments. New York: Wiley; 1986.

    Google Scholar 

  25. Hopkins WG. Measures of reliability in sports medicine and science. Sports Med. 2000;30:1–15.

    Article  CAS  Google Scholar 

  26. Bates NA, Schilaty ND, Nagelli CV, Krych AJ, Hewett TE. Novel mechanical impact simulator designed to generate clinically relevant anterior cruciate ligament ruptures. Clin Biomech (Bristol Avon). 2017;44:36–44.

    Article  Google Scholar 

  27. Bates NA, Schilaty ND, Nagelli CV, Krych AJ, Hewett TE. Validation of noncontact anterior cruciate ligament tears produced by a mechanical impact simulator against the clinical presentation of injury. Am J Sports Med. 2018;46:2113–21.

    Article  Google Scholar 

  28. Levine JW, Kiapour AM, Quatman CE, Wordeman SC, Goel VK, Hewett TE, et al. Clinically relevant injury patterns after an anterior cruciate ligament injury provide insight into injury mechanisms. Am J Sports Med. 2013;41:385–95.

    Article  Google Scholar 

  29. Ambegaonkar JP, Shultz SJ, Perrin DH. A subsequent movement alters lower extremity muscle activity and kinetics in drop jumps vs. drop landings. J Strength Cond Res. 2011;25:2781–8.

    Article  Google Scholar 

  30. Ueno R, Ishida T, Yamanaka M, Taniguchi S, Ikuta R, Samukawa M, et al. Quadriceps force and anterior tibial force occur obviously later than vertical ground reaction force: a simulation study. BMC Musculoskelet Disord. 2017;18:467.

    Article  Google Scholar 

  31. Lloyd DG, Buchanan TS. Strategies of muscular support of varus and valgus isometric loads at the human knee. J Biomech. 2001;34:1257–67.

    Article  CAS  Google Scholar 

  32. Boguszewski DV, Cheung EC, Joshi NB, Markolf KL, McAllister DR. Male-female differences in knee laxity and stiffness: a cadaveric study. Am J Sports Med. 2015;43:2982–7.

    Article  Google Scholar 

  33. Cammarata ML, Dhaher YY. The differential effects of gender, anthropometry, and prior hormonal state on frontal plane knee joint stiffness. Clin Biomech (Bristol Avon). 2008;23:937–45.

    Article  Google Scholar 

  34. Schmitz RJ, Ficklin TK, Shimokochi Y, Nguyen AD, Beynnon BD, Perrin DH, et al. Varus/valgus and internal/external torsional knee joint stiffness differs between sexes. Am J Sports Med. 2008;36:1380–8.

    Article  Google Scholar 

Download references

Availability of data and materials

The datasets used and analyzed during this study are available from the corresponding author upon reasonable request.

Author information

Authors and Affiliations

  1. Faculty of Health Sciences, Hokkaido University, Kita 12, Nshi 5, Kita-ku, Sapporo, 060-0812, Japan

    Tomoya Ishida, Yuta Koshino, Ryo Ueno, Shohei Taniguchi, Mina Samukawa, Hiroshi Saito & Harukazu Tohyama

  2. Faculty of Health Science, Hokkaido Chitose College of Rehabilitation, Satomi 2-10, Chitose, 066-0055, Japan

    Masanori Yamanaka

  3. Department of Rehabilitation, Hokushin Orthopaedic Hospital, Kikusui-motomachi 3-jo 3-chome 1-18, Sapporo, 003-0823, Japan

    Hisashi Matsumoto

  4. Department of Orthopaedic Surgery, Hokushin Orthopaedic Hospital, Kikusui-motomachi 3-jo 3-chome 1-18, Sapporo, 003-0823, Japan

    Yoshimitsu Aoki

Authors
  1. Tomoya Ishida
    View author publications

    You can also search for this author in PubMed Google Scholar

  2. Yuta Koshino
    View author publications

    You can also search for this author in PubMed Google Scholar

  3. Masanori Yamanaka
    View author publications

    You can also search for this author in PubMed Google Scholar

  4. Ryo Ueno
    View author publications

    You can also search for this author in PubMed Google Scholar

  5. Shohei Taniguchi
    View author publications

    You can also search for this author in PubMed Google Scholar

  6. Mina Samukawa
    View author publications

    You can also search for this author in PubMed Google Scholar

  7. Hiroshi Saito
    View author publications

    You can also search for this author in PubMed Google Scholar

  8. Hisashi Matsumoto
    View author publications

    You can also search for this author in PubMed Google Scholar

  9. Yoshimitsu Aoki
    View author publications

    You can also search for this author in PubMed Google Scholar

  10. Harukazu Tohyama
    View author publications

    You can also search for this author in PubMed Google Scholar

Contributions

TI, RU and ST collected the data. TI, YK, MY and HT designed the study and drafted the manuscript. TI, MS and HS performed data processing. RU, ST, MS, HS, HM and YA participated in designing the study. All authors read and approved the final manuscript.

Corresponding author

Correspondence to Masanori Yamanaka.

Ethics declarations

Ethics approval and consent to participate

All subjects read and signed informed consent forms prior to their inclusion in the present study. This study was approved by the Hokkaido University Institutional Review Board (Approval number: 11–55).

Consent for publication

The subject who is showed in figure has read and signed a consent form for publication.

Competing interests

The authors declare that they have no competing interests.

Publisher’s Note

Springer Nature remains neutral with regard to jurisdictional claims in published maps and institutional affiliations.

Rights and permissions

Open Access This article is distributed under the terms of the Creative Commons Attribution 4.0 International License (http://creativecommons.org/licenses/by/4.0/), which permits unrestricted use, distribution, and reproduction in any medium, provided you give appropriate credit to the original author(s) and the source, provide a link to the Creative Commons license, and indicate if changes were made. The Creative Commons Public Domain Dedication waiver (http://creativecommons.org/publicdomain/zero/1.0/) applies to the data made available in this article, unless otherwise stated.

Reprints and permissions

About this article

Check for updates. Verify currency and authenticity via CrossMark

Cite this article

Ishida, T., Koshino, Y., Yamanaka, M. et al. The effects of a subsequent jump on the knee abduction angle during the early landing phase. BMC Musculoskelet Disord 19, 379 (2018). https://doi.org/10.1186/s12891-018-2291-4

Download citation

  • Received:

  • Accepted:

  • Published:

  • DOI: https://doi.org/10.1186/s12891-018-2291-4

Keywords

BMC Musculoskeletal Disorders

ISSN: 1471-2474

Contact us