Home  |  Login  |  Inquiries | TOC Alerts  |  Sitemap |  

Advanced Search
J Exerc Rehabil > Volume 17(3);2021 > Article
Stanek, Brown, Barrack, and Parish: A novel manual therapy technique is effective for short-term increases in tibial internal rotation range of motion


The coupled motions of tibial internal rotation (T-IR) and ankle dorsiflexion (DF) are necessary for proper lower-limb function. Anecdotally, clinicians have been performing techniques to restore T-IR to improve ankle DF, however, no evidence exists to support their efficacy. Therefore, the two objectives were to: (a) determine the effectiveness of a manual therapy technique for improving T-IR range of motion (ROM) and (b) Examine the relationship between ankle DF and T-IR ROM. Twenty-four participants qualified to participate and were randomly allocated to either the control (n=12) or manual therapy (n=12) group. Closed-chain ankle DF and T-IR ROM were assessed at baseline and immediately posttreatment. Control group participants sat quietly for 5 minutes. The experimental group performed 3 sets of 15 repetitions of a manual therapy, mobilization with movement technique. With the patient in a kneeling lunge position, the examiner wrapped an elastic band around the tibia and fibula and was instructed to lunge forward while the examiner simultaneously manually internally rotated the lower leg. T-IR ROM significantly increased following the intervention for the manual therapy group when compared to the control group. There were no significant changes in standing or kneeling DF ROM. No significant correlation was found between T-IR and both standing and kneeling DF ROM. A single mobilization with movement treatment is effective for improving tibial IR ROM in the short-term compared to no treatment. However, active tibial IR and end-range dorsiflexion range of motion do not appear to be correlated based on these methods.


Clinicians routinely quantify and track joint range of motion (ROM) as part of the evaluation and rehabilitation process. Limitations in tibial ROM are often overlooked due to the difficulty in measuring transverse plane motion (Makowski et al., 2005). The embedded compass app of an iPhone (iPhone 6 model A1549, Apple, Inc., Cupertino, CA, USA) has recently been shown to reliably assess tibial internal and external rotation ROM making it convenient and easy to quantify (Stanek et al., 2020). Rotational motion at the tibia is essential for knee and ankle function and is often implicated as a compensatory strategy for various lower extremity conditions (Bell-Jenje et al., 2015; Bonci, 1999; Griffin et al., 2000; Matsumoto et al., 2000; Zhang et al., 1993). Previous authors have described tibial rotation as an important, yet often understudied (Makowski et al., 2005; Matsumoto et al., 2000; Zhang et al., 1993). A thorough understanding of rotational motion of the tibia contributes to an accurate evaluation of knee mobility, as well as provides a better understanding of function at the hip, ankle, and foot.
A previous investigation described potential complications from abnormal variations in tibial rotation (Lusin and Gajdosik, 1983). These pathologies include the development of chondromalacia patella and other degenerative joint changes. Alterations in tibial rotation have also been implicated with meniscal lesions and injuries to the cruciate ligaments (Hallen and Lindahl, 1966). Furthermore, tibial external rotation, along with anterior translation of the knee, and hindfoot eversion have been implicated with dynamic valgus at the knee (Bell et al., 2008; Hewett et al., 2006). This positioning has been correlated with iliotibial band syndrome (Ferber et al., 2010), patellofemoral pain syndrome (Levinger et al., 2006; Molgaard et al., 2011), tibial stress fractures (Milner et al., 2006), posterior tibial tendon dysfunction (Ness et al., 2008), anterior cruciate ligament tears (Powers, 2010), and osteoarthritis of the knee (Chang et al., 2005).
Much of the previous literature has focused on the relationship between hip and knee alignment, especially as it relates to dynamic valgus. However, a more recent study found individuals with <17° of ankle dorsiflexion (DF) exhibited 6.5° higher hip adduction angles during an elevated step down task (Bell-Jenje et al., 2015). Interestingly, the higher hip adduction angles were normalized to the group with >17° DF with a heel lift, suggesting that lost DF ROM contributed to the valgus knee positioning. During normal lower extremity biomechanics, several motions must couple in order to achieve optimal function. For example, during closed-chain activities, the tibia must internally rotate (IR) to allow ankle DF and pronation to occur (McClay and Manal, 1997). Loss of DF ROM is commonly observed in both the athletic and general population and is believed to be a predisposing factor for lower extremity injury (Backman and Danielson, 2011; Neely, 1998; Tabrizi et al., 2000; Wang et al., 2006; Willems et al., 2005; You et al., 2009). Typically, DF ROM deficits are believed to be caused by tightness of the triceps surae, a decrease in the posterior glide of the talus, and/or accessory motion loss at the tibiofibular, subtalar, and/or midtarsal joints (Denegar and Hertel, 2002; Leanderson et al., 1993). Because the motions of DF and T-IR are coupled, lost T-IR could also contribute to deficits in DF ROM. Despite wide ranges in reported normative values for T-IR (Lusin and Gajdosik, 1983; Makowski et al., 2005; Stanek et al., 2020), findings from a previous study using the compass app showed average T-IR ROM to range from 12°–14° (Stanek et al., 2020). Anecdotally, clinicians have been performing techniques to restore T-IR and potentially improve ankle DF. Several variations of the technique using elastic bands have been published in blog or online video posts (Physical Therapy Nation, YouTube, San Bruno, CA, USA) to provide guidance for how to perform the technique, however, no peer-reviewed, published literature exists to support their efficacy. Furthermore, the use of elastic bands, such as the VooDoo floss band (Rogue Fitness, Columbus, OH, USA), is scarce amongst the literature (Kiefer et al., 2017). Therefore, the purposes of this exploratory study were to determine the effectiveness of a manual therapy, mobilization with movement (MWM) technique for improving T-IR and secondarily to examine the relationship between T-IR and DF ROM. We hypothesized that the manual therapy technique would immediately improve T-IR ROM. We also hypothesized that T-IR and DF ROM would be positively correlated.



An examiner-blinded, cohort study design with randomization was used to examine the impact of the manual therapy intervention on DF ROM. Participants were required to report to the athletic training clinic for a single session. Participants were randomized into to either the control or manual therapy group using block randomization. Limb dominance was self-reported by the participant as the preferred kicking limb.


Based on a data from a previous reliability study (Stanek et al., 2020), and a simple, online sample size calculator using an alpha level of 0.05 and an intraclass correlation coefficient of 0.85, an estimated sample size of 11 participants per group was recommended. Twenty-seven participants were initially recruited and screened for inclusion. A total of 24 participants (age, 20.1±1.2 years; weight, 68.9±13.5 kg; height, 171.3±10.4 cm) met the inclusion criteria and qualified for the study (Table 1). Participants were recruited via verbal announcements and advertisements throughout the School of Kinesiology and Recreation. All participants were recreationally physically active and needed to meet the inclusion criteria. To be included in the study, participants needed to have less than 12° of T-IR, have no prior history of lower extremity surgery to the limb, and have no recent history (within the past 6 months) of lower extremity injury to the limb. The threshold of 12° was based on a previous study showing average normative values for T-IR ROM measured using a compass app ranged from 12°–14° (Stanek et al., 2020). In total, 42 limbs were randomly allocated to either the control (12 participants) or intervention (12 participants) group. In instances when both limbs of the participant qualified, both limbs were allocated to the same group. Prior to beginning data collection, the Institutional Review Board of Illinois State University reviewed and approved the study (IRB No. 2018-93). All participants provided written informed consent prior to study participation.


Participants’ T-IR and closed-chain ankle DF in standing and kneeling were assessed immediately before and after the intervention. To assess T-IR, the compass app on an iPhone (iPhone 6 model A1549, Apple, Inc., Cupertino, CA, USA) was secured to the lower leg using the Premium Tribe Sports Armband (Tribe Fitness, Seattle, WA, USA) following previously used methods (Stanek et al., 2020). The smartphone was secured to the lower leg so the bottom of the device rested immediately superior to the ankle mortise.
Closed-chain ankle DF was assessed in both standing and kneeling with a digital inclinometer (SmartTool, Pro 3600, MD Building Products, Oklahoma, OK, USA) on the anterior aspect of the tibia, immediately below the tibial tuberosity. Previous authors have shown this to be a highly reliable method for evaluating DF ROM (Powden et al., 2015; Stanek et al., 2018).


All procedures for evaluating T-IR followed the methods of Stanek et al. (2020) for measuring tibial rotation using a smartphone compass app and these methods showed excellent reliability. Based on this study, standard error of the measurement (SEM) for these procedures was 2.24–2.82 (Stanek et al., 2020). Participants arrived at the lab and reviewed the study purpose and procedures by reading through the informed consent document. Participants agreeing to participate signed the informed consent document and completed the preparticipation questionnaire. To standardize activity levels, all participants were instructed to ride a stationary bike with moderate resistance for 5 minutes. Participants removed shoes and socks and sat on an adjustable stool with the height adjusted so the hip and knee angles were at 90°. The phone was secured to the lower leg with the armband so it sat immediately superior to the talocrural joint. Using a vertical plumb line, the test limb was placed in neutral by aligning the tibial tuberosity with the center of the talocural joint. The rater stabilized the participant’s femur and taught the motions of T-IR. As the participant was taught the movement, the individual was asked to maintain the neutral, resting position of the foot in order to avoid excessive pronation and supination. The rater visually verified the movements and the test limb was returned to neutral after each movement. To assess tibial rotation ROM, the rater recorded an initial reading from the compass app while in neutral, followed by the participant moving into T-IR (Fig. 1). The rater recorded a second reading from the compass app at the end ROM, with the difference between the two positions recorded for the measurement. The average of the 3 trials for T-IR was used for analysis.
Next, the participant’s closed-chain DF was measured in standing (Fig. 2) and kneeling (Fig. 3) using a modified weight-bearing lunge test. Previous authors have shown this to be a highly reliable method for evaluating DF ROM (Bennell et al., 1998; Hall and Docherty, 2017; Powden et al., 2015; Stanek and Pieczynski, 2020). The participant stood, positioned the test leg behind the nontest leg on a strip of tape that was perpendicular to the wall, and leaned forward until the first point of stretch was felt in the calf and/or when the heel began to rise. The trial was deemed successful if the test knee remained straight and the heel-maintained contact with the floor. The digital inclinometer was placed on the anterior tibia, immediately below the tibial tuberosity. Next, participants’ kneeling DF ROM was assessed by instructing the participant to kneel on the opposite leg being tested with the test limb visually placed in 90° of hip and knee flexion. The participant placed their front foot on the tape line as previously stated. The participant was then instructed to lunge forward while keeping their heel in contact with the ground and their foot in line with the tape. The participant was instructed to lunge forward until their first felt a stretch in their distal calf and/or the heel began to rise. The inclinometer was placed in the same position as the standing measurement. The average of three measurements was recorded.
Participants allocated to the control group were instructed to sit quietly on the exam table for 5 minutes. Experimental group participants positioned the test limb forward in a kneeling lunge. A 7-foot (2.13 m) VooDoo Floss Band (Rogue Fitness, Columbus, OH, USA) was wrapped with moderate tension from just above the ankle mortise, in the direction of IR superiorly around the lower limb. Next, the participant was instructed to lunge forward while simultaneously the clinician guided the participant into the DF position and internally rotated the tibia. Both the T-IR and DF ROM were moved to end-range with each repetition and each trial was completed to the beat of a metronome set at 45 beats per minute. A total of 3 sets of 15 repetitions of the manual therapy MWM technique were completed with 1-minute rest between sets. These methods followed a modified version of a previously used MWM technique (Collins et al., 2004). All participants had postmeasurements completed using the previously described methods.

Statistical analysis

All statistical analyses were performed using IBM SPSS Statistics ver. 24.0 (IBM Co., Armonk, NY, USA). Preliminary analyses were conducted and showed no difference between groups at baseline for demographics (age, height, and mass), T-IR, standing, or kneeling DF ROM measures (P>0.05). To compare the effectiveness of the manual therapy intervention, change scores were calculated for T-IR, standing, and kneeling DF ROM by subtracting the postmeasurement from the premeasurement. Independent samples t-test were used to determine significant differences between groups. To determine relationships between T-IR and DF ROM, Pearson product-moment correlation coefficient were calculated. Prior to running the analyses, preliminary assumption testing for normality and homogeneity of variance were completed with no violations. Effect sizes were calculated using the Cohen d and categorized as trivial (≤0.20), small (0.21–0.49), moderate (0.50–0.79), or large (≥0.80) (Lakens, 2013). The α level was set a priori at P<0.05.


Descriptive statistics for all data are included in Table 2. There was a statistically significant amount of T-IR increase following the intervention for the manual therapy group (m=2.03°±2.24°) when compared to the control group (m=0.62°±2.61°); t(40)= 3.53, P=0.001, effect size=1.09, 95% confidence interval=0.44–1.74. There were no significant changes in standing (t[40]=0.04, P=0.97) or kneeling (t[40]=0.81, P=0.42) DF ROM. No significant correlation was found between T-IR and both standing (r=0.20, P=0.20) and kneeling (r=0.14, P=0.39) DF ROM (Figs. 4, 5).


The purpose of this study was to investigate the effectiveness of a manual therapy technique aimed at improving T-IR ROM and examine the relationship between T-IR and DF ROM. Our hypotheses were only partially supported. Results showed a single session of manual therapy can increase T-IR ROM but it had no effect on DF ROM. Additionally, end-range T-IR and DF ROM do not appear to be associated as there were small, nonsignificant correlations between T-IR and both standing and kneeling DF ROM. Because of the test position for the manual therapy technique, we chose to assess both standing and kneeling DF in the event the intervention had a different impact on these measures. However, results showed neither standing nor kneeling DF ROM was impacted from the intervention.
Manual therapy interventions are commonly used within rehabilitation settings, often with the goal of improving mobility. The manual therapy MWM technique employed in this study has been demonstrated online as a method for improving T-IR. Due to the nature of the technique, it is not surprising that it can increase motion since the technique passively moves the tibia into IR with each repetition. However, the weightbearing technique also passively moves the ankle into DF, therefore it was surprising to see no changes in DF mobility. It is possible the participants in this study had adequate DF mobility, creating a ceiling effect for further increases in DF ROM. A study among people with restricted DF mobility may have shown different results.
Reduced ankle DF ROM is a commonly found deficit within athletic and non-athletic populations and is commonly observed in patients following a lateral ankle sprain (Denegar et al., 2002; Hertel, 2002; Hubbard and Hertel, 2006; Tabrizi et al., 2000). However, reduced DF is also a risk factor for sustaining a lateral ankle sprain, therefore, numerous interventions for improving DF ROM have been studied (Terada et al., 2013). Traditionally, treatments for DF ROM deficits include the use of joint mobilizations for restoring the proper accessory motion, stretching of the triceps surae, modalities, or a combination of these therapies (Young et al., 2013). To our knowledge, no previous studies have examined the impact of T-IR ROM on DF mobility. Because previous studies have demonstrated the coupled motions of knee flexion, T-IR, and ankle DF ROM during functional tasks such as squatting or during gait (Bell-Jenje et al., 2015; McClay and Manal, 1997), we hypothesized that improving T-IR may also positively affect DF ROM. However, while the manual therapy intervention was effective at improving T-IR rotation in the short-term, it does not appear that this resulted in an increase in DF ROM.
Tibial IR ROM is not commonly quantified in the clinical environment, yet rotational motion at the tibia is essential for knee and ankle function and is often implicated as a compensatory strategy for various lower extremity conditions (Bell-Jenje et al., 2015; Bonci, 1999; Griffin et al., 2000; Matsumoto et al., 2000; Zhang et al., 1993). A previous reliability study using the same measurement technique showed average T-IR ROM to be approximately 13° with SEM ranging from 2.24–2.82 (Stanek et al., 2020). Because of the large standard deviations in the reliability study, the SEM was high. Using data from the current study and using the formula SEM=standard deviation x-√1-r, with r as the reliability of the measurement, the calculated SEM was 1.46. Collectively, participants in the current study started with approximately 8° of T-IR and participants in the intervention group reached values around 9.3°. Participants in the intervention group demonstrated over a 2° change in ROM with large effect sizes. These findings suggest clinically meaningful changes in T-IR ROM, however, additional research to support these findings is needed. Methods and instrumentation for assessing T-IR ROM vary greatly throughout the literature. Therefore, it is important for clinicians to have the ability to quantify and address limitations when necessary. Our results suggest this technique could be a simple, yet effective method for increasing T-IR in the short term.
This study is not without limitations. First, we measured active, end-range T-IR and DF ROM. While previous authors have demonstrated these motions are coupled during functional tasks, it is possible T-IR occurs early within the functional task and maximum IR occurs prior to end-range DF ROM. Therefore, increasing the T-IR did not have a substantial effect on end-range DF ROM. Secondly, we used a healthy population with limited T-IR ROM, but normative values of T-IR vary considerably. Previously forthcoming work using similar methodology showed T-IR values between 12°–14° (Stanek et al., 2020). Our inclusion criteria required participants to have less than 12° of T-IR to potentially prevent a ceiling effect with the manual therapy MWM technique. Because of the wide variability within previously published normative values for T-IR (Lusin and Gajdosik, 1983; Makowski et al., 2005), less than 12° may not be a sufficiently restricted degree of mobility for T-IR. Furthermore, our population did not have a DF ROM deficit. It is possible our results for changes in DF ROM would have been different if we recruited a population with a known T-IR and DF deficit. Future research is needed to quantify consistent and accurate values for normal tibial rotation mobility. Furthermore, additional research should examine the effects of this manual therapy technique on functional tasks such as gait or squatting. Lastly, we compared a single treatment to a true control condition receiving no intervention. It is possible comparing to another intervention or a placebo intervention could have resulted in different findings.
In conclusion, a single manual therapy, MWM treatment is effective at increasing T-IR ROM in the short-term compared to no treatment. However, it did not affect closed-chain DF ROM. Clinicians are encouraged to examine tibial rotation mobility within their patients for potential deficits. Patients with deficits in T-IR mobility may benefit from using this manual therapy technique.



No potential conflict of interest relevant to this article was reported.


The authors received no financial support for this article.


Backman LJ, Danielson P. Low range of ankle dorsiflexion predisposes for patellar tendinopathy in junior elite basketball players: a 1-year prospective study. Am J Sports Med. 2011;39:2626–2633.
crossref pmid

Bell DR, Padua DA, Clark MA. Muscle strength and flexibility characteristics of people displaying excessive medial knee displacement. Arch Phys Med Rehabil. 2008;89:1323–1328.
crossref pmid

Bell-Jenje T, Oliver B, Wood W, Rogers S, Green A, McKinon W. The association between loss of ankle dorsiflexion range of motion, and hip adduction and internal rotation during a step down test. Man Ther. 2015;21:256–261.
crossref pmid

Bennell K, Talbot RC, Wajsweiner H, Techovanich W, Kelly DH, Hall AJ. Intra-rater and inter-rater reliability of a weight-bearing lunge measure of ankle dorsiflexion. Aust J Physiother. 1998;44:175–180.
crossref pmid

Bonci CM. Assessment and evaluation of predisposing factors to anterior cruciate ligament injury. J Athl Train. 1999;34:155–164.
pmid pmc

Chang A, Dunlop D, Song J, Hurwitz D, Cahue S, Sharma L. Hip abduction moment and protection against medial tibiofemoral osteoarthritis progression. Arthritis Rheumatol. 2005;52:3515–3519.

Collins N, Teys P, Vicenzino B. The initial effects of a Mulligan’s mobilization with movement technique on dorsiflexion and pain in subacute ankle sprains. Man Ther. 2004;9:77
crossref pmid

Denegar C, Hertel J, Fonseca J. The effect of lateral ankle sprain on dorsiflexion range of motion, posterior talar glide, and joint laxity. J Orthop Sports Phys Ther. 2002;32:166–173.
crossref pmid

Denegar CR, Hertel J. Editorial: Clinical education reform and evidence-based clinical practice guidelines. J Athl Train. 2002;37:127–128.
pmid pmc

Ferber R, Noehren B, Hamill J, Davis IS. Competitive female runners with a history of iliotibial band syndrome demonstrate atypical hip and knee kinematics. J Orthop Sports Phys Ther. 2010;40:52–58.
crossref pmid

Griffin LY, Agel J, Albolm MJ, Arendt EA, Dick RW, Garrett WE. Noncontact anterior cruciate ligament injuries: risk factors and prevention strategies. J Am Acad Orthop Surg. 2000;8:141–150.
crossref pmid

Hall EA, Docherty CL. Validity of clinical outcome measures to evaluate ankle range of motion during the weight-bearing lunge test. J Sci Med Sport. 2017;20:618–621.
crossref pmid

Hallen LG, Lindahl O. The “screw-home” movement in the knee joint. Acta Orthop Scand. 1966;37:97–106.

Hertel J. Functional anatomy, pathomechanics, and pathophysiology of lateral ankle instability. J Athl Train. 2002;37:364–375.
pmid pmc

Hewett TE, Ford KR, Myer GD. Anterior cruciate ligament injuries in female athletes, part 2: a meta-analysis of neuromuscular interventions aimed at injury prevention. Am J Sports Med. 2006;34:490–498.
crossref pmid

Hubbard TJ, Hertel J. Mechanical contributions to chronic lateral ankle instability. Sports Med. 2006;36:263–277.
crossref pmid

Kiefer BN, Lemarr KE, Enriquez CC, Tivener KA, Daniel T. A pilot study: perceptual effects of the voodoo floss band on glenohumeral flexibility. Int J Athl Ther Train. 2017;22:29–33.

Lakens D. Calculating and reporting effect sizes to facilitate cumulative science: a practical primer for t-tests and ANOVAs. Front Psychol. 2013;4:863
crossref pmid pmc

Leanderson J, Wykman A, Eriksson E. Ankle sprain and postural sway in basketball players. Knee Surg Sports Traumatol Arthrosc. 1993;1:203–205.
crossref pmid

Levinger P, Gilleard WL, Sprogis K. Frontal plane motion of the rearfoot during a one-leg squat in individuals with patellofemoral pain syndrome. J Am Podiatr Med Assoc. 2006;96:96–101.
crossref pmid

Lusin GF, Gajdosik RL. Reliability of instrumentation and measurement procedures for active internal and external tibial rotation. J Orthop Sports Phys Ther. 1983;4:154–157.
crossref pmid

Makowski A, Birmingham T, Kramer J, Jogi P, Forwell L, Obright K. Test-retest and interrater reliability of goniometric tibial rotation range of motion measurements. Physiother Can. 2005;57:265–273.

Matsumoto H, Seedhom BB, Suda Y, Otani T, Fujikawa K. Axis location of tibial rotation and its change with flexion angle. Clin Orthop Relat Res. 2000;371:178–182.

McClay I, Manal K. Coupling parameters in runners with normal and excessive pronation. J Appl Biomech. 1997;13:109–124.

Milner C, Ferber R, Pollard C, Hamill J, Davis I. Biomechanical factors associated with tibial stress fracture in female runners. Med Sci Sports Exerc. 2006;38:323–328.
crossref pmid

Molgaard C, Rathleff MS, Simonsen O. Patellofemoral pain syndrome and its association with hip, ankle, and foot function in 16- to 18-year-old high school students: a single-blind case-control study. J Am Podiatr Med Assoc. 2011;101:215–222.

Neely F. Biomechanical risk factors for exercise-related lower limb injuries. Sports Med. 1998;26:395–413.
crossref pmid

Ness ME, Long J, Marks R, Harris G. Foot and ankle kinematics in patients with posterior tibial tendon dysfunction. Gait Posture. 2008;27:331–339.
crossref pmid

Powden CJ, Hoch JM, Hoch MC. Reliability and minimal detectable change of the weight-bearing lunge test: a systematic review. Man Ther. 2015;20:524–532.
crossref pmid

Powers CM. The influence of abnormal hip mechanics on knee injury: a biomechanical perspective. J Orthop Sports Phys Ther. 2010;40:42–51.
crossref pmid

Stanek J, Parish J, Rainville R, Williams J. Test-retest and intra-rater reliability of assessing tibial rotation range of motion by two devices. Int J Athl Ther Train. 2020;25:263–269.

Stanek JM, Pieczynski AE. Effectiveness of clinician- and patient-applied mobilisation with movement technique to increase ankle dorsiflexion range of motion. Int J Ther Rehabil. 2020;27:1–11.

Stanek JM, Sullivan T, Davis S. Comparison of compressive myofascial release and the Graston Technique for improving ankle dorsiflexion range of motion. J Athl Train. 2018;53:160–167.
crossref pmid pmc

Tabrizi P, McIntyre WM, Quesnel MB, Howard AW. Limited dorsiflexion predisposes to injuries of the ankle in children. J Bone Jt Surg Br. 2000;82:1103–1106.

Terada M, Pietrosimone BG, Gribble PA. Therapeutic interventions for increasing ankle dorsiflexion after ankle sprain: a systematic review. J Athl Train. 2013;48:696–709.
crossref pmid pmc

Wang HK, Chen CH, Shiang TY, Jan MH, Lin KH. Risk-factor analysis of high school basketball-player ankle injuries: a prospective controlled cohort study evaluating postural sway, ankle strength, and flexibility. Arch Phys Med Rehabil. 2006;87:821–825.
crossref pmid

Willems TM, Witvrouw E, Delbaere K, Philippaerts R, Bourdeaudhuij ID, De Clercq D. Intrinsic risk factors for inversion ankle sprains in females: a prospective study. Scand J Med Sci Sports. 2005;15:336–345.
crossref pmid

You JY, Lee HM, Luo HJ, Lee CC, Cheng PG, Wu SK. Gastrocnemius tightness on joint angle and work of lower extremity during gait. Clin Biomech. 2009;24:744–750.

Young R, Nix S, Wholohan A, Bradhurst R, Bradhurst L. Interventions for increasing ankle joint dorsiflexion: a systematic review and meta-analysis. J Foot Ankle Res. 2013;6:2–18.
crossref pmid pmc

Zhang LQ, Dobson S, Shiavi RG, Peterson S, Limbird TJ. Changes in knee kinematics caused by ACL deficiency during fast walking. Gait Posture. 1993;7:144–156.

Fig. 1
Tibial internal rotation measurement.
Fig. 2
Standing dorsiflexion range of motion measurement.
Fig. 3
Kneeling dorsiflexion range of motion measurement.
Fig. 4
Correlation of tibial internal rotation and standing dorsiflexion range of motion.
Fig. 5
Correlation of tibial internal rotation and kneeling dorsiflexion range of motion.
Table 1
Demographic data for participants
Variable Control group (n=12) Intervention group (n=12)
Gender, male:female 5:7 5:7
Limbs 21 21
Age (yr) 19.9±1.2 20.3±1.2
Mass (kg) 71.0±16.6 66.9±9.7
Height (cm) 156.5±36.6 147.4±21.4

Values are presented as number or mean±standard deviation.

Table 2
Descriptive data for tibial internal rotation, standing, and kneeling dorsiflexion range of motion
Variable CON MT Tx
No. of limbs 21 21
Pre T-IR 8.52°±3.04° 7.29°±2.43°
Post T-IR 7.91°±3.78° 9.32°±3.22°
Change −0.62°±2.61° 2.03°±2.24°*
Pre Standing DF 40.51°±8.16° 40.12°±6.17°
Post Standing DF 41.88°±7.19° 41.52°±6.25°
Change 1.37°±2.93° 1.39°±2.92°
Pre Kneeling DF 44.18°±6.65° 41.32°±6.30°
Post Kneeling DF 44.21°±6.76° 42.04°±5.98°
Change 0.02°±2.63° 0.72°±2.94°

Values are presented as mean±standard deviation.

CON, control group; MT Tx, manual therapy treatment group; T-IR, tibial internal rotation; DF, dorsiflexion; Change, post–pre measure.

PDF Links  PDF Links
PubReader  PubReader
ePub Link  ePub Link
Full text via DOI  Full text via DOI
Download Citation  Download Citation
CrossRef TDM  CrossRef TDM
Related article
Editorial Office
Department of Urology, Chungnam National University Sejong Hospital
20, Bodeum 7-ro, Sejong 30099, Korea
Tel: +82-44-995-4701     FAX: +82-44-995-3209    E-mail: journal@kser.co.kr
Copyright © Korean Society of Exercise Rehabilitation.            Developed in M2PI