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ISSN : 1225-8962(Print)
ISSN : 2287-982X(Online)
Physical Therapy Korea Vol.24 No.4 pp.46-53
DOI : https://doi.org/10.12674/ptk.2017.24.4.046

Comparison of the Foot Muscle EMG and Medial Longitudinal Arch Angle During Short Foot Exercises at Different Ankle Position

Hyeo-bin Yoon1, Ji-hyun Kim1, Joo-hee Park1, Hye-seon Jeon2,3
1Department of Physical Therapy, The Graduate School, Yonsei University
2Department of Physical Therapy, College of Health Science, Yonsei University
3Department of Ergonomic Therapy, The Graduate School of Health Science, Yonsei University
Corresponding author : Hye-seon Jeon hyeseonj@yonsei.ac.kr
October 12, 2017 October 12, 2017 November 11, 2017

Abstract

Background:

The MLA is supported by both the abductor hallucis (ABH) and the extrinsic muscles. Insufficient muscular support may lower the MLA when the body’s weight is applied to the foot. The short foot exercise (SFE) is effective in increasing the height of the MLA for people with flat feet. Most of the research related to the SFE has simply evaluated the efficiency of the exercise using enhanced ABH electromyography (EMG) activation. Since the tibialis anterior (TA), peroneus longus (PER), and ABH are all involved in supporting the MLA, a new experiment design examining the EMG of the selected muscles during SFE should be applied to clarify its effect.

Objects:

Therefore, this study aimed to clarify the effect of the SFE in different ankle position on the MLA angle and the activation of both the intrinsic and extrinsic muscles and to determine the optimal position.

Methods:

20 healthy subjects and 12 subjects with flat feet were recruited from Yonsei University. The surface EMG and camera were used to collect muscle activation amplitude of TA, PER, and ABH and to capture the image of MLA angle during SFE. The subjects performed the SFE while sitting in three different ankle positions—neutral (N), dorsiflexion (DF) at 30 degrees, and plantar flexion (PF) at 30 degrees.

Results:

ABH EMG amplitudes were significantly greater in N and DF than in PF (p<.05). Muscle activation ratio of TA to ABH was the lowest in PF (p<.05). MLA angle in both groups significantly decreased in PF (p<.01). The TA and ABH was activated at the highest level in DF. However, in PF, subjects significantly activated the ABH and PER with relatively low activation of TA.

Conclusion:

Therefore, researchers need to discuss which SFE condition most effectively use the arch support muscle for flat foot.


초록


    Introduction

    The medial longitudinal arch (MLA) is a concave structure consisting of the calcaneus, talus, and navicular bones; three cuneiform bones; and the first to third metatarsal bones, and it contributes to body weight distribution and shock absorption during standing, walking, and other weight-bearing activities (Franco, 1987). It is supported by various passive and active structures. Strong ligamentous structures, such as the spring ligament and plantar fascia, create tension to prevent downward displacement of the arch (Franco, 1987; Neumann, 2013). Together with the ligaments, active muscular structures such as the tibialis anterior (TA), tibialis posterior (TP), peroneus longus (PL), and abductor halluces (ABH) (Jung et al, 2011; Murley et al, 2009; O’Connor and Hamill, 2004) are also critical to supporting the MLA in more challenging and dynamic situations (Neumann, 2013).

    Flat foot, the excessive pronation of the foot, is vulnerable to musculoskeletal conditions including fatigue or pain (Heo and An, 2014; Rose, 1991), plantar fasciitis (Pohl et al, 2009), hallux valgus (Easley and Trnka, 2007), and laxity of the ligaments (Bertani et al, 1999). In addition, those with flat feet experience challenges in controlling balance and gait (Tsai et al, 2006). Various passive and active therapeutic approaches have been used to treat flat feet. A systematic review reported moderate to good results from foot orthosis in improving physical function and decreasing pain and rear foot inversion. However, these passive therapeutic methods have only low level evidence to improve pain, reduce rearfoot eversion, alter loading and impact forces and reduce rearfoot inversion and eversion moments in flat foot (Banwell et al, 2014).

    Various extrinsic and intrinsic foot muscles contribute significantly to supporting the MLA in dynamic situations. Therefore, strengthening exercises, such as the toe curl exercise (Jung et al, 2011), picking up objects, and shin curls (Prentice and Kaminski, 2004; Anderson and Parr, 2013), are recommended to manage excessive pronation of the foot and to maintain the normal height of the MLA. More recently, the short-foot exercise (SFE) has been recognized as an outstanding method for achieving a normal MLA. The SFE is closely associated with immediate enhancement of ABH muscle activity and decreases in the MLA angle (Jung et al, 2011). According to previous experiments, the SFE is more effective at achieving these goals than other exercises. However, no research has been done to more inclusively evaluate the effect of the SFE on the activation of the arch support muscles (ABH, TA, and PER) together: In addition, a previous study suggested that different ankle positions could alter the effectiveness of the SFE secondary to the length-tension relationship, and no study has examined intrinsic and extrinsic arch support muscle activation during SFE at different ankle positions.

    We therefore designed an experimental protocol to identify the most effective ankle position during SFE according to the activity of the TA, PER, and ABH and the MLA angle. We compared three different ankle positions—neutral, dorsiflexion, and plantar flexion.

    Methods

    Subjects

    In this study, 20 healthy subjects (8 males and 12 females, age=22.3, height=167.8 ㎝, mass=61.4 ㎏) with normal arches and 12 subjects with flat feet (5 males and 7 females, age=23.9, height=170.1 ㎝, mass=63.1 ㎏) were recruited from Yonsei University. The examiner conducted the navicular drop (ND) test twice. Based on the average values found by the ND test, we categorized the subjects into the normal arch group (ND=5-9 ㎜) and the flat foot group (ND>10 ㎜). Demographic information is shown in Table 1.

    Subjects with any neurological disorders, past or current inflammatory arthritis, lower limb surgeries or amputations, foot deformities, or diabetes were excluded from the experiment. Prior to the data collection, all experimental protocols were explained to the subjects using written instructions, and all sub- jects signed a written informed consent form. This study protocol was approved by the Institutional Review Board of Yonsei University (approval number: 1041849-201705-BM-055-01).

    Instrumentation

    The muscle activation data for the TA, PER, and ABH were recorded using surface EMG (Noraxon TeleMyo DTS, Noraxon Inc., Scottsdale, AZ, USA) with a wireless telemetry system. The sampling rate was 1000 ㎐, and a digital band-pass filter (Lancosh FIR) between 20 and 450 ㎐ was used. Rootmean- square values were calculated with a moving window of 50 ㎳. The EMG data were analyzed using the Noraxon MyoResearch 1.06 software (Noraxon Inc., Scottsdale, AZ, USA). During the SFEs, the change of the MLA angle was captured by a personal camera (Sony a500, Sony Korea, Seoul, South Korea). The ABH muscle belly was detected by sonographic guidance (Mysono U6, Medison, Seoul, South Korea).

    Procedure

    EMG data collection and analyses

    Prior to the attachment of the electrodes, the patients’ skin was shaved and cleaned with rubbing alcohol using a sterile gauze pad to minimize impedance of the EMG signal. Surface electrodes (Ag/AgCl) were placed on the most prominent parts of the muscle bellies of the TA, PER, and ABH with an inter-electrode distance of 20 ㎜, parallel to the direction of the muscle fiber. The electrodes were located as follows: for the TA, one-third of the distance between the head of the fibula and the tip of the medial malleolus on the leg measured to identify the correct location; for the PER, one-quarter of the distance between the head of the fibula and the tip of the lateral malleolus; for the ABH, on the point 10-20 ㎜ posterior to the navicular tuberosity and just anterior to the imaginary line outlining the anterior margin of the medial malleolus. The examiner confirmed the location of the ABH muscle belly by real-time sonographic imaging (Incel et al, 2003).

    The EMG data were normalized to the maximal voluntary isometric contraction (MVIC) of each subject. The MVIC was measured by the standard manual muscle testing methods. The TA MVIC was obtained in the sitting position with the knee joint flexed to 90 degrees. The examiner gripped the subject’s distal calf and applied manual resistance to the medial and dorsal surface of the foot in the opposite direction (Kendal et al, 1983). To measure the MVIC of the PER, the investigator applied manual resistance to the lateral and plantar surface of the foot to resist eversion and plantar flexion. The MVIC of the ABH was tested with the ankle in the neutral position, and manual resistance was applied to the medial side of the first metatarsal and proximal phalanx to generate abduction of the metatarsophalangeal joint of the big toe. The participants performed three MVIC trials for each muscle, and in each trial, each participant maintained the maximal contraction for five seconds. The mean surface EMG amplitudes obtained in the middle 3s were used to calculate the MVIC percentage of each muscle.

    MLA angle

    To measure the MLA angle, the investigator positioned each participant’s foot in a neutral position (relaxed state) by comparing the height of the medial and lateral talar heads. Three reflective markers were then attached on the navicular tuberosity, the medial side of the first metatarsal head, and the medial aspect of the calcaneal bone. For women, the calcaneal marker was placed 30 ㎜ from the most posterior part of the calcaneus and 30 ㎜ from the bottom using a ruler; for men, the marker was placed 40 ㎜ and 35 ㎜ from each respective reference location (Jung et al, 2011) (Figure 1). The camera was faced with three markers within a distance of 2 m and captured images in the resting position and during the SFE.

    The MLA angle was calculated from the captured MLA images during the resting position and the SFE using the ImageJ software (US, National Institutes of Health, Maryland, USA) (Abramoff et al and Ram, 2014; Kuo et al and Galea, 2009). The MLA angle was defined as the angle between the line from the first metatarsal head to the navicular tuberosity and the line from the navicular tuberosity to the medial side of the calcaneal bone. The same researcher measured the angle twice from each image for intra-rater reliability.

    SFE

    Prior to the data collection, all participants were instructed on how to perform the SFE by demonstration and video clip instruction. They then practiced the SFE for 20 minutes under supervision to make sure that they activated the ABH during the exercise. The participants were seated in height-adjustable chairs with 90-degree hip and knee flexion. The subjects attempted to drag the distal end of the first metatarsal bone toward the heel without toe flexion while keeping the forefoot and heel on the surface (on the chair or on the inclined board). The SFE was performed in three randomly ordered ankle positions, as follows: the neutral position (N), the 30-degree dorsiflexion (DF), and the 30-degree plantar flexion (PF) (Figure 2). The participants performed three trials, holding each for five seconds, for each SFE, and the principal investigator measured the activation of the targeted muscles and the MLA angle during all sessions.

    Statistical Analysis

    A two-way mixed analysis of variance (ANOVA) was used for the statistical analysis. The independent variables were the groups (healthy and flat foot) and the ankle positions (neutral, dorsiflexion, and plantar flexion). When there was no group by ankle position interaction, the main effects of each independent variable were interpreted. For the dependent variables in group by ankle position interaction, the simple effect of ankle position within a group was examined by separate one-way repeated ANOVA followed by a post-hoc Bonferroni test. The PASW Statistics 23 software (SPSS Inc., Chicago, IL, USA) was used for all analyses, and p<.05 was considered statistically significant.

    Results

    Muscle activation

    Table 2 presents the results of conducting the SFE in N, DF, and PF. According to the results of the statistical analyses, no group by ankle position interaction was observed in the EMG amplitude of any measured muscles. The main effect of ankle position was significant only in the TA and ABH EMG amplitudes (Figure 3). Because there was no interaction effect, we analyzed the EMG data with one-way repeated ANOVA. The results of the one-way repeated ANOVA showed that the TA EMG amplitudes were significantly less in PF than in the other positions (p<.05), and the ABH EMG amplitude was significantly greater in DF than in N or PF (p<.05). The TA and ABH EMG values were highest in DF, although the TA value was not statistically significant.

    Muscle activation ratio

    There was no statistical significance among the group by ankle position interactions in the muscle activation ratio data, and no main effect by group was observed. A significant main effect of ankle position was found in the results of the muscle activation ratio of TA to ABH (p<.05) (Table 3). The post-hoc results showed that this ratio was the lowest in PF among all conditions (p<.05) (Figure 4). The activation ratio of PER to ABH was not statistically different among the ankle position conditions; however, it was highest in PF.

    MLA angle

    There was no statistical significance among the group by ankle position interactions in the MLA angle. Significant main effects of the ankle position and group variables were found in the MLA angle. The MLA angle of the flat foot group during the SFE was significantly smaller than that of the healthy group (p<.014) (Table 4). The post-hoc test revealed that the MLA angle in both groups significantly decreased in PF (p<.01), but there was no difference between the angles in N and in DF (Figure 5).

    Discussion

    The SFE is one of the most commonly used therapeutic exercises for people with flat feet. Performing SFE in the neutral ankle position immediately and effectively enhances the muscle activity of the ABH and decreases the MLA angle (Jung et al, 2011). The purpose of this study was to determine which exercise condition most effectively activates the arch support muscles during the SFE. This is the first experimental research to examine the muscle activity of the TA, PER, and ABH; the ratios of the activity of these muscles (TA to ABH and PER to ABH); and the MLA angle during SFE.

    The involvement of the TA, PER, and ABH in the SFE is simply explained by muscle geography and kinesiology. The TA originates from the lateral condyle and the proximal lateral shaft of the tibia, and the PER originates from the superior two-thirds of the medial surface of the fibula. While these two extrinsic foot muscles originate from different locations and function antagonist, they are commonly attached on the base of the first metatarsal bone. Therefore, the consequence of a co-contraction of these muscles is the pulling of the first metatarsal bone superiorly and posteriorly, each muscle offsetting the other’s actions. Because the ABH runs from the medial process of the calcaneal tuberosity and the plantar aponeurosis to the side of the base of the proximal phalanx of the greater toe, the contraction of the ABH can create flexion in the metatarsophalangeal (MTP) joint.

    The ABH contributes to maintaining the normal height of the MLA. People with flat feet show decreased activation of the ABH, and the ABH can be activated by the SFE (Fiolkowski et al, 2003; Lee et al, 2016). In this experiment, the muscle activities of the TA and ABH were highest in the DF position. The PER showed no significant difference among the three positions. Previous research suggests that lengthened triceps surae can affect the activation of the ABH (Heo and An, 2014). In our study, we instructed the subjects to pull the forefoot toward the heel without flexing the toes while holding the heel in a starting position. Therefore, the subjects put relatively more effort into performing the SFE in the DF than in the N and PF ankle positions.

    The muscle activity ratio of TA to ABH was highest in DF and lowest in PF (p<.01). In contrast, the ratio of PER to ABH was lowest in DF and highest in PF. Murley et al (2009) reported that people with lowered MLAs tended to have an increased TA activation pattern and a decreased PER activation pattern compared to people with normal MLAs. It is well known that the TA is the arch support muscle and is most highly activated in DF. However, an over-activated TA compensates for a relatively weak ABH in flat foot patients. The findings of this study support the conclusion that performing SFE in PF allows flat foot patients to achieve a normalized muscle activation pattern by enhancing the activation of the ABH and preventing hyperactivation of the TA. However, determining the optimal ankle position between DF and PF is beyond the scope of this discussion.

    In this study, the MLA angle decreased during all SFE conditions and decreased most significantly in PF (p<.01). Previous research has reported an inverse relation between the activation of the ABH and the MLA angle (Jung et al, 2011), so we expected that this angle would be decreased in DF. However, the MLA angle was instead decreased in PF because, in the DF condition, all passive and active structures were already lengthened to the limit, and there was no room for the height of the MLA to increase.

    This study had several limitations. First, it could not include the tibialis posterior and flexor hallucis longus because they are located in deep compartments of the leg and cannot be measured using surface EMG. Second, because we captured the MLA angle using a two-dimensional camera, it was measured only on the sagittal plane. In the actual arthrokinematics of the foot, plantar flexion and dorsiflexion cause the transition of the navicular bone, which is the keystone for calculating the MLA angle. We also could not discount the influence of calcaneal pronation on the MLA angle. Third, because the electrode for the peroneus longus was enclosed by other lateral compartment leg muscles, cross talk could have affected the quality of the EMG data. Further longitudinal intervention research is required to examine all extrinsic and intrinsic arch support muscles and MLA angles in various ankle positions in order to determine the optimal treatment for flat foot.

    Conclusion

    The collected surface EMG data and calculated MLA angle data during the SFE showed similar tendencies between the flat foot and normal foot groups. In both groups, the TA and ABH were activated at the highest levels in DF and were also highly activated in PF and N. In PF, the subjects activated the ABH and PER the most highly and achieved relatively low activation of the TA. This suggests that researchers and clinical professionals should prescribe the PF position for alleviating flat foot

    Figure

    PTK-24-46_F1.gif

    The medial longitudinal arch angle.

    PTK-24-46_F2.gif

    Three different ankle position for short foot exercise.

    PTK-24-46_F3.gif

    The surface EMG amplitude (TA: tibialis anterior, ABH: abductor hallucis, MVIC: maximal voluntary isometric contraction, NE: neutral, DF: dorsiflexion, PF: plantar flexion).

    PTK-24-46_F4.gif

    The muscle activation ratio of TA to ABH (TA: tibialis anterior, ABH: abductor hallucis, MVIC: maximal voluntary isometric contraction, NE: neutral, DF: dorsiflexion, PF: plantar flexion)

    PTK-24-46_F5.gif

    The change of MLA angle during SFE (NE: neutral, DF: dorsiflexion, PF: plantar flexion)

    Table

    General characteristics of the subjects (N=32)

    amean±standard deviations
    bbody mass index
    cnavicular drop difference.

    Surface EMG amplitude (Unit: %MVIC)

    aneutral
    bdorsiflexion
    cplantar flexion
    dtibialis anterior
    emean±standard deviation
    fperoneus longus
    gabductor hallucis.

    Surface EMG amplitude ratio (Unit: %MVIC)

    aneutral
    bdorsiflexion
    cplantar flexion
    dtibialis anterior
    eabductor hallucis
    fmean±standard deviation
    gperoneus longus

    Main Effect of MLA angle by group

    amean±standard deviations.

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