Effects of Running on Sand vs. Stable Ground on Kinetics and Muscle Activities in Individuals With Over-Pronated Feet

Background: In terms of physiological and biomechanical characteristics, over-pronation of the feet has been associated with distinct muscle recruitment patterns and ground reaction forces during running.

Objective: The aim of this study was to evaluate the effects of running on sand vs. stable ground on ground-reaction-forces (GRFs) and electromyographic (EMG) activity of lower limb muscles in individuals with over-pronated feet (OPF) compared with healthy controls.

Methods: Thirty-three OPF individuals and 33 controls ran at preferred speed and in randomized-order over level-ground and sand. A force-plate was embedded in an 18-m runway to collect GRFs. Muscle activities were recorded using an EMG-system. Data were adjusted for surface-related differences in running speed.

Results: Running on sand resulted in lower speed compared with stable ground running (p < 0.001; d = 0.83). Results demonstrated that running on sand produced higher tibialis anterior activity (p = 0.024; d = 0.28). Also, findings indicated larger loading rates (p = 0.004; d = 0.72) and greater vastus medialis (p < 0.001; d = 0.89) and rectus femoris (p = 0.001; d = 0.61) activities in OPF individuals. Controls but not OPF showed significantly lower gluteus-medius activity (p = 0.022; d = 0.63) when running on sand.

Conclusion: Running on sand resulted in lower running speed and higher tibialis anterior activity during the loading phase. This may indicate alterations in neuromuscular demands in the distal part of the lower limbs when running on sand. In OPF individuals, higher loading rates together with greater quadriceps activity may constitute a proximal compensatory mechanism for distal surface instability.

Introduction

There is compelling evidence that the regular performance of running exercise has positive effects on both, markers of health and physical fitness (Thompson et al., 2003). However, a negative side effect of running exercise is the high rate of musculoskeletal injuries. On average, 100 h of running exercise results in one running-related injury (Requa et al., 1993). A prominent running-related injury risk factor is over-pronation of the feet (OPF) (Aryana and Artha, 2019). OPF prevalence rates range between 2 and 23% in adults (Dunn et al., 2004). There is evidence that OPF during the stance phase of running might result in a hyper-flexible, and thus unstable foot (Cheung and Ng, 2007). Moreover, it may create excessive movement transferred into tibial rotation (Hintermann and Nigg, 1998).

In terms of physiological characteristics, OPF has been associated with distinct muscle recruitment patterns (Murley et al., 2009). OPF may develop from deficits in muscle strength, joint instability, and/or overstrain due to the long-term usage of lower limbs structures (Ashnagar et al., 2019). It has been proposed that the triceps surae, peronei, tibialis anterior/posterior muscles act as dynamic stabilizers of the medial longitudinal arch (Thordarson et al., 1995; O’Connor and Hamill, 2004). Accordingly, the foot muscles appear to play a vital role in stabilizing the medial longitudinal arch (Thordarson et al., 1995; O’Connor and Hamill, 2004).

Surprisingly little is known on the effects of exercise programs on muscle activities and function in OPF individuals. A previous study demonstrated that an 8-weeks exercise program designed to strengthen the intrinsic foot muscles improved the medial longitudinal arch in adult patients with chronic ankle instability and OPF (Chung et al., 2016).

Running on sand could be a promising exercise intervention for OPF treatment because it is rather easy-to-access and produces hardly any costs. From a health-related perspective, the unstable element sand may strengthen foot and ankle muscles, improve function, and reduce OPF (Pinnington et al., 2005). Due to these positive characteristics, recreational and high-performance athletes and coaches have previously used running on sand as a successful adjunct to firm surface training regimes (Wischnia, 1982). The increased energy cost of running on sand compared with firm surface running can partly be attributed to an increased activation of distal lower limb muscles associated with greater hip and knee range-of-motion (Pinnington et al., 2005). Of note, sand is a yielding surface that provides constant instability during running. There is evidence from previous studies showing that running and walking on sand compared with stable ground has a major impact on kinematics and kinetics in healthy individuals and patients with multiple sclerosis (Pinnington et al., 2005; van den Berg et al., 2017). A previous study demonstrated lower gait speed when walking on sand compared with stable ground in OPF individuals. In addition, lower peak positive free moments were found during the push-off phase and lower loading rates during the loading phase (Jafarnezhadgero A. et al., 2019). A comparison between walking and running at comparable speeds has demonstrated a number of specific differences concerning ground reaction forces (GRFs; e.g., peak GRFs amplitudes in three dimensions) and muscle activity (e.g., gastrocnemius muscle) patterns (Grillner et al., 1979; Thorstensson et al., 1982; Lichtwark and Wilson, 2008). Accordingly, it is timely to examine this research question during running in OPF individuals. To the authors’ knowledge, there is no study available that examined the effects of running on sand vs. stable ground in OPF individuals. Therefore, the aim of this study was to contrast the effects of running on sand vs. stable ground on GRFs and activities of selected lower limb muscles in OPF individuals compared with healthy age-matched controls. With reference to the relevant literature (Pinnington et al., 2005; van den Berg et al., 2017), we hypothesized lower loading rates, and higher muscle activities when running on sand compared with stable ground in both experimental groups. We further expected that these surface-related effects are more pronounced in OPF individuals compared to the healthy controls (Murley et al., 2009).

Materials and Methods

Experimental Design

The main research question of this study was to examine the effects of running on sand vs. stable ground on kinetics and muscle activities in individuals with over-pronated feet and healthy controls. To address this research question, a cross-sectional study was designed (Figure 1). Participants were tested on 1 day with sufficient rest in between the experimental conditions to minimize the effects of fatigue. The experimental conditions were sequenced in random order.

FIGURE 1

Figure 1. Study design with randomly applied experimental conditions. Participants ran at preferred speed. OPF stands for over-pronated feet.

Participants

The freeware tool G × Power (Version 3.1.9.2, University of Kiel, Germany) was used to compute a one-sided a priori power analysis with the F-test family (ANOVA for repeated measures, within-between interaction) and the respective statistical test based on a related study that examined walking on sand kinetics in adults with OPF (Jafarnezhadgero A. et al., 2019). The power analysis was calculated with an assumed Type I error of 0.05, a Type II error rate of 0.20 (actual power 0.80), and an effect size of 0.80 (i.e., interaction effects) for walking kinetics (i.e., peak vertical GRF). The analysis revealed that 20 participants per group would be sufficient to observe significant group-by-time interactions. Due to potential drop-outs, 33 healthy individuals (21 females, 12 males) aged 22.2 ± 2.5 years (body height: 178.0 ± 6.6 cm; mass: 75.0 ± 8.2 kg; body-mass-index: 23.8 ± 3.4 kg/m²) and 33 OPF individuals (24 females, 9 males) aged 22.2 ± 1.9 years (body height: 163.9 ± 5.5 cm; mass: 68.4 ± 18.4 kg; body-mass-index: 25.2 ± 5.3 kg/m²) were enrolled in this study. All participants were sedentary and were not physically active according to WHO guidelines (150 min per week of moderate to vigorous physical activity). All participants were right footed as determined by a kicking ball test. Participants were included in the OPF group, if they showed a navicular drop of>10 mm, and a foot posture index of>10 (Farahpour et al., 2018). For the control group, participants were eligible to be included if they showed a navicular drop of<10 mm and>6 mm, and a foot posture index of<5 and>0 (Redmond et al., 2006). Navicular drop (OPF: 13.1 ± 0.8 mm; control: 7.3 ± 0.6 mm) and foot posture index (OPF: 11.1 ± 0.7; control: 3.2 ± 1.1) in the OPF group were greater than that control group (p < 0.001). In the current study, a modified version of the navicular drop described by Brody (1982) was used to determine the sagittal plane displacement of the navicular between seated position and standing on one leg. During testing, participants were seated on a chair with both feet flat on the ground and knees flexed at an angle of 90°. The most medial aspect of the navicular was marked. The height of the navicular was measured using a ruler. Thereafter, the participant was asked to stand on one leg by flexing the contralateral knee. The single-limb stance position was used because recent work by McPoil and Cornwall (1996) has shown that measurements taken from this position more accurately represent the position of the foot during the midstance phase of walking. Again, the height of the navicular was measured using a ruler. The difference between the height of the navicular in seated position vs. standing on one leg was recorded as navicular drop. The foot posture index was evaluated by a podiatrist with ∼10 years of professional experience. For this purpose, a visual analog scale was used. The foot posture index consists of six items used to quantify and classify foot posture (Redmond et al., 2006; Gijon-Nogueron et al., 2015). These are (i) palpation of the head of the talus; (ii) curvatures above and below the lateral malleolus; (iii) position of the calcaneus in the frontal plane; (iv) prominence of the malleolus; (v) congruence of the medial longitudinal arch; and (vi) abduction/adduction of the forefoot. Each item was rated on a visual analog scale ranging from –2 to +2, resulting in a total score of –12 to +12. Negative values indicate a supinated foot posture, and positive values indicate a pronated foot posture. Of note, values of 10–12 in the foot posture index were classified as over-pronated feet (Redmond et al., 2006; Gijon-Nogueron et al., 2015). A detailed description of the foot posture index can be found elsewhere (Redmond et al., 2006; Gijon-Nogueron et al., 2015). Exclusion criteria comprised for both groups a history of musculoskeletal surgery at the lower limbs, neuromuscular or postural disorders (except for OPF individuals), and limb length differences larger than 5 mm. All participants were rearfoot strikers. The Institutional Review Boards of the Medical Sciences University of Ardabil, Iran approved the research protocol (IR.ARUMS.REC.1398.119). Prior to the start of the study, written informed consent was obtained from all participants.

Apparatus and Data Processing

The experimental study design included two runways (18-m long, 1-m wide, and 0.25-m deep) with a specifically constructed frame (Jafarnezhadgero A. et al., 2019). The stable runway was covered with reinforced plywood and an embedded force plate (Bertec Corporation, Columbus, OH, United States). The unstable runway was filled with dry sand to simulate a common deformable surface environment. A Bertec force plate with a sampling rate of 1,000 Hz was embedded in the runway (20 cm underneath the sand; Xu et al., 2015) and used to collect GRF data. The frame consisted of two steel rectangles concentrically aligned with 6 mm clearance between the walls (Figure 2). Previous studies showed that this runway construction is well-suited to accurately assess GRFs while running (Merryweather, 2008; Yoo, 2014; Xu et al., 2015). The force plate was embedded halfway through the 18 m runway. The participants started the test trial on the runway and ran a distance of 9 m before they stepped on the base plate. Running speed was monitored using two sets of infrared photocells.

FIGURE 2

Figure 2. Schematic image of the runway and the location of the force plate.

Kinetic data were recorded in accordance with a previous study (Jafarnezhadgero A. et al., 2019). In brief, a 20 Hz low-pass filter (4th order Butterworth filter, zero lag) was used to process GRF data (Damavandi et al., 2012). Heel strike and toe off events during running were identified using the Bertec force plate. Accordingly, a 10 N threshold was used to detect the stance phase of the running trials. GRF data were normalized to body weight (BW). The x, y, and z force components represent medio-lateral, antero-posterior, and vertical directions. GRF data were analyzed by computing the first (Fz_HC) and second vertical peak force (Fz_PO) (Jafarnezhadgero et al., 2017). In addition, braking (Fy_HC) and propulsion forces (Fy_PO) were recorded from the anterior-posterior force curve. The positive (lateral) peak (Fx_HC) and the negative (medial) peak (Fx_PO) were additionally calculated (Jafarnezhadgero et al., 2017). Time-to-peak (TTP) was defined as the time between the initial heel contact and the respective Fz_HC peak value. Vertical loading rates were computed as the average slope between 20 and 80% of the vertical GRF (Jafarnezhadgero et al., 2017). For all computed running parameters, the average of three trials was used for statistical analyses.

A wireless EMG system (Biometrics Ltd., Nine Mile Point Ind. Est, Newport, United Kingdom) with eight pairs of bipolar Ag/AgCl surface electrodes was applied to assess tibialis anterior (TA), gastrocnemius medialis (Gas-M), biceps femoris (BF), semitendinosus (ST), vastus lateralis (VL), vastus medialis (VM), rectus femoris (RF), and gluteus medius (Glut-M) muscle activities of the dominant limb (Farahpour et al., 2018). Center-to-center electrode distance was 25 mm. Input impedance and common mode rejection ratio was set at 100 MΩ and>110 dB, respectively. The raw EMG signals were digitized at 1,000 Hz. According to the European recommendations for surface electromyography (SENIAM), skin surface was shaved and cleaned with alcohol (70% Ethanol–C₂H₅OH) over the respective muscle bellies. Thereafter, the skin was gently abraded before electrode placement. The surface electrodes were placed on the muscle belly, longitudinally to the muscle fibers (Farahpour et al., 2018). GRFs and EMG data were synchronized using Nexus software (Oxford Metrics, Oxford, United Kingdom). EMG data were processed in accordance with a previous study (Farahpour et al., 2018). In brief, test-trials were divided into the loading (0–15% of running cycle), mid-stance (15–25% of running cycle), and push-off (25–40% of running cycle) phases (Ounpuu, 1994; Dugan and Bhat, 2005). Maximum voluntary isometric contraction (MVIC) was assessed using a handheld dynamometer to normalize EMG during running to MVIC.

Experimental Procedures

During testing, all participants were equipped with the same shoe model (Adidas, Climacool vento shoes) that best fitted the size of their foot. This shoe model was used for participants with a normal foot. The midsole drop of these shoes were 10 mm (heel: 20.5 mm/forefoot: 10.5 mm). Before the start of the study, participants were familiarized with the applied tests and instruments. Participants performed two familiarization trials before the actual tests were recorded. For each participant, 7 trials were recorded and on average, 5 trials were successful, i.e., provided useful data. During testing, individuals were kindly asked to run at preferred speed and in randomized order over stable ground and sand. A 5 min rest was scheduled between running conditions and a 1 min rest between running trials to minimize the effects of fatigue (Figure 1). A trial was considered successful if the foot landed in the middle of the force plate and if EMG signals were artifact free upon visual examination of the online screen. All participants were rearfoot strikers and the foot strike was monitored between conditions. MVIC tests were applied after the running analyses for each muscle separately to normalize EMG data.

Statistical Analyses

The Shapiro-Wilk-Test confirmed normal data distribution. Accordingly, data were presented as group mean values and standard deviations. To examine the effect of ground surface during running, a separate 2 (group: healthy vs. OPF) × 2 (surface: stable ground vs. sand) ANOVA with repeated measures was computed on speed adjusted (i.e., differences between running on sand vs. stable ground) GRF and EMG variables. Post-hoc analyses were computed using Bonferroni adjusted paired sample t-tests. In addition, effect sizes were calculated by converting partial eta-squared (η²_p) to Cohen’s d. According to Cohen, d < 0.50 indicate small effects, 0.50 ≤ d < 0.80 indicate medium effects, and d ≥ 0.80 indicate large effects. The significance level was set at p < 0.05. The Statistical Package for Social Sciences (SPSS) version 24.0 was used to calculate inferential statistics.

Results

Running Speed

A significant main effect of “surface” was found for running speed (p < 0.001; d = 1.38). The post-hoc test demonstrated that running on sand (3.17 ± 0.23 m/s) resulted in lower speed compared with stable ground running (3.32 ± 0.13 m/s) (p < 0.001; d = 0.83; 95% CI: 0.02, 0.27). No significant main effects of “group” and group-by-surface interactions were found for running speed (p > 0.05; d = 0.23–0.39) (Figure 3).

FIGURE 3

Figure 3. Running speed in both groups. *Indicates significant within group differences.

Running Kinetics

The speed adjusted analysis demonstrated significant main effects of “surface” for Fy_HC and Fy_PO (p < 0.002; d = 0.86–1.02) (Table 1). Post-hoc tests revealed significantly lower Fy_HC (p < 0.001; d = 0.88) and Fy_PO (p = 0.001; d = 0.86) when running on sand compared with stable ground. Moreover, we observed significant main effects of “group” for Fz_PO and loading rate (p < 0.015; d = 0.37–0.63). Post-hoc tests showed significantly lower Fz_PO (p = 0.014; d = 0.59) and larger loading rates (p = 0.004; d = 0.72) in OPF individuals compared with controls (Table 1). No statistically significant group-by-surface interactions were found for loading rate during running (p > 0.05; d = 0.00–0.24).

TABLE 1

Table 1. Data are means and standard deviations for ground reaction forces (GRF) during running on sand vs. stable ground in over-pronated feet (OPF) individuals compared with healthy controls.

Muscle Activities

With regards to muscle activities, the speed adjusted analysis revealed statistically significant main effects of “surface” for TA and Gas-M activities during the loading phase (p < 0.033; d = 0.55–0.58) (Table 2). Post-hoc tests showed significantly higher TA activities (p = 0.024; d = 0.28) and lower Gas-M activities (p = 0.032; d = 0.43) when running on sand compared with stable ground.

TABLE 2

Table 2. Data are means and standard deviations for muscle activity during the loading phase [% maximum voluntary isometric contraction (MVIC)] when running on stable ground and sand.

Significant main effects of “group” were observed for VM and RF activities (p < 0.002; d = 0.91–0.93) during the loading phase (Table 2). Post-hoc tests showed significantly larger VM (p < 0.001; d = 0.89) and RF (p = 0.001; d = 0.61) activities during the loading phase in OPF individuals compared with healthy controls.

No statistically significant group-by-surface interactions were detected for activities of selected lower limb muscles during the loading phase (p > 0.05; d = 0.00–0.30) (Table 2).

The speed adjusted analysis showed significant main effects of “surface” for Gas-M, VL, and RF activities during the mid-stance phase (p < 0.033; d = 0.55–0.58) (Table 3). Post-hoc tests revealed significantly lower Gas-M (p = 0.005; d = 0.50) and VL (p = 0.027; d = 0.28) activities and larger RF activities (p = 0.044; d = 0.30) when running on sand.

TABLE 3

Table 3. Data are means and standard deviations for muscle activity during the mid-stance phase [% maximum voluntary isometric contraction (MVIC)] when running on stable ground and sand.

Significant main effects of “group” were found for Gas-M and RF activities (p < 0.022; d = 0.59–1.00) during the mid-stance phase of running (Table 3). Post-hoc tests showed significantly larger Gas-M (p < 0.001; d = 0.95) and RF (p = 0.020; d = 0.65) activities in OPF individuals compared with controls.

The statistical analysis revealed significant group-by-surface interactions for Glut-M activities (p = 0.008; d = 0.69) during the mid-stance phase of running (Table 3). Control but not OPF individuals showed significantly lower Glut-M activities (p = 0.022; d = 0.63) when running on sand.

The speed adjusted analysis revealed significant main effects of “surface” for Gas-M and ST activities during the push-off phase (p < 0.006; d = 0.72–1.26) (Table 4). Post-hoc tests indicated lower Gas-M (p < 0.001; d = 1.05) and ST (p = 0.046; d = 0.34) activities when running on sand.

TABLE 4

Table 4. Data are means and standard deviations for muscle activity during the push-off phase [% maximum voluntary isometric contraction (MVIC)] when running on stable ground and sand.

Significant main effects of “group” were identified for VL, VM, RF, and ST activities during the push-off phase (p < 0.018; d = 0.62–1.08) (Table 4). Post-hoc tests showed greater VL (p = 0.017; d = 0.60), VM (p = 0.004; d = 0.69), RF (p < 0.001; d = 1.04), and ST (p = 0.010; d = 0.65) activities in OPF individuals compared with controls.

Finally, significant group-by-surface interactions were found for Gas-M activities (p = 0.022; d = 0.59) during the push-off phase (Table 4). OPF individuals showed lower Gas-M activities when running on sand (p < 0.001; d = 0.93).

Discussion

This study examined the effects of running on sand vs. stable ground on GRFs and activities of selected lower limb muscles in OPF individuals compared with healthy age-matched controls. The main findings of this study were that running on sand resulted in lower running speed, irrespective of the experimental group. Due to this outcome, all statistical analyses were adjusted for the observed surface-related differences in running speed. OPF individuals showed larger loading rates and greater vastus medialis and rectus femoris activities during the loading phase. Irrespective of the experimental groups, running on sand produced a higher tibialis anterior activity during the loading phase, a lower VL activity during the mid-stance phase, and a lower semitendinosus activity during the push-off phase.

This study revealed lower running speed along with lower peak posterior and anterior GRF amplitudes in both experimental groups when running on sand vs. stable ground. Given that we adjusted our statistical model for surface-related differences in running speed, it seems justified to argue that these differences were surface and not speed-related. This study showed that running on sand resulted in lower peak anterior GRFs during the push-off phase which may have been caused by a lower medial gastrocnemius activity. Of note, lower peak anterior GRF amplitudes during running on sand may indicate instability of the foot and/or ankle most likely due to deficits in the mid-tarsal locking mechanism during the late stance phase of running. It can be speculated that running on sand demands a greater effort to accelerate the body’s center of mass within the sagittal plane, i.e., plane of locomotion (Damavandi et al., 2012) to achieve similar speed compared with stable ground running.

Similar loading rates were found when running on sand vs. stable ground. During the loading phase of running on sand, higher tibialis anterior and lower medial gastrocnemius activities were observed in both groups. The loading phase of running is characterized by ankle plantarflexion. During this phase, eccentric tibialis anterior actions are needed to gently lower the foot to the ground (Whittle, 2014). This study revealed a higher tibialis anterior muscle activity when running on sand compared with firm ground.

There is evidence that the relationship between medial gastrocnemius activity and the resultant plantarflexion moment is influenced by the underlying force-length relation (Arnold et al., 2013). The medial gastrocnemius muscle contributes to knee flexion and plantarflexion of the ankle joint (Li et al., 2002). A previous study demonstrated that knee flexion was greater during the loading phase when running at different velocities (8 and 11 km.h^–1) on sand compared with firm ground (Luheff et al., 2005). Thus, the plantarflexion moment generated through medial gastrocnemius activity when running on sand could be affected by the knee angle (Yong et al., 2014). Accordingly, greater knee flexion due to shortened medial gastrocnemius length may result in lower medial gastrocnemius activity which could cause a lower ankle plantarflexion moment (Li et al., 2002). The complex relationship between muscle length and its force-generating capacity is likely the reason why medial gastrocnemius activity is lower when running on sand.

A previous study showed an association between running on stable ground and an increased risk of sustaining lower limb injuries (James et al., 1978). The magnitude and the rate of loading have been identified as risk factors for running-related injuries (Barrett et al., 1998), and changes in running style are effective in reducing vertical loading rate (Pirscoveanu et al., 2021). The active support system for the medial longitudinal arch includes appropriate tibialis anterior muscle activity (Oatis, 2009). In this study, we showed that running on sand vs. stable ground resulted in similar loading rates but higher tibialis anterior activity when running on sand. Accordingly, running on sand could be an adequate means to enhance tibialis anterior -activity during running. Higher tibialis anterior activity may restore the medial longitudinal arch in OPF individuals. However, more research is needed on the long-term effects of running on sand to better understand this issue.

Irrespective of the experimental group, we observed similar vertical impact peaks and quadriceps activities during the loading phase when running on sand and stable ground. There is evidence that running on soft or compliant surfaces reduces impact forces due to prolonged collision time (Barrett et al., 1998). Of note, a previous study showed a sharp spike in foot impact force which amounted to five times body weight when running on hard vs. soft ground (McMahon and Greene, 1979). Previously, researchers proposed that running on sand is an effective rehabilitative means to treat lower limb injuries because it produces low impact forces and high muscle activities (Barrett et al., 1998).

During mid-stance and push-off phases, medial gastrocnemius activity was lower when running on sand compared with stable ground. In this study, we found lower medial gastrocnemius activity when running on sand compared with stable ground which could be due to the fact that sand may absorb some of the impact energy during landing. Additionally, we showed larger loading rates in OPF individuals compared with healthy controls during running on sand and stable ground, as demonstrated in previous study (Jafarnezhadgero A. A. et al., 2019). Increased loading rates and impact shocks may represent biomechanical risk factors for sustaining orthopedic injuries such as knee osteoarthritis or stress fractures (Jefferson et al., 1990). Our findings revealed larger vastus medialis and rectus femoris activities during the loading phase of running in OPF individuals compared with controls. The larger vastus medialis and rectus femoris activities during the loading phase in OPF individuals can likely be interpreted as a compensatory mechanism for lower loading rates. These results are applicable to persons who run in running shoes with a rearfoot strike. Whether our findings can be translated to barefoot runners or hindfoot strike runners has to be clarified in future research. A previous study reported that running on sand produces higher energy costs compared with running on grass (Pinnington and Dawson, 2001). In addition, running on sand compared with firm ground resulted in greater hamstring, vastus lateralis, vastus medialis, and rectus femoris activities (Pinnington et al., 2005). Walking on sand has been shown to increase vertical center-of-mass displacement (Svenningsen et al., 2019), potentially increasing energy expenditure. In addition, increased energy costs when running on sand could be caused by higher lower limb muscle activities (Pinnington et al., 2005). In this study, we found higher rectus femoris activity in OPF individuals when running on sand. While this increase in muscle activity might have a positive therapeutic effect on the lower limbs of OPF individuals, it could also increase the risk of perceiving groin pain. More research is needed in this area to clarify this issue.

To the authors’ knowledge, there is no study available that examined the effects of running on sand in OPF individuals. Therefore, it is not possible to compare our results with findings from previous studies. Our results indicate reduced semitendinosus activities in both experimental groups during the push-off phase when running on sand. In the control but not the OPF group, running on sand resulted in significantly lower gluteus medius activity during the mid-stance phase. Anatomical studies on the gluteus medius suggest that this muscle plays an important role in stabilizing the hip and pelvis (Gottschalk et al., 1989). Previous studies reported associations between OPF and hip adduction during the early stance phase of walking, landing and running (Buist et al., 2010; Kagaya et al., 2015; Farahpour et al., 2018). This OPF-related mechanism affords higher hip abductor activities, mainly of the gluteus medius muscle (Farahpour et al., 2018). Of note, a study has shown OPF-related weakness of the gluteus medius muscle which functions as hip abductor (Farahpour et al., 2018). This may again increase the risk of sustaining injuries (Bellchamber and van den Bogert, 2000). During running, the gluteus medius contracts to maintain lower limb alignment from the pelvis through the femur, knee, tibia, and finally the foot (Bird et al., 2003; Semciw et al., 2013). However, running on sand did not affect gluteus medius activity in OPF individuals. There is evidence that running on sand may reduce OPF during the stance phase and might therefore lower the risk of sustaining injuries during running (Pinnington et al., 2005). Our results showed larger vastus lateralis, vastus medialis, rectus femoris, and semitendinosus activities during the push-off phase in OPF individuals compared with controls. The reason for the difference may also be due to weaker foot and leg muscles in OPF individuals compared with controls. A recent study reported that RF thickness was significantly smaller in OPF individuals compared with healthy peers (Ashnagar et al., 2019). In contrast, Ashnagar and co-workers reported that vastus lateralis and vastus medialis muscle thickness were not different in young OPF adults compared with healthy controls (Ashnagar et al., 2019).

A few methodological limitations should be discussed in the context of this study. First, a rather small study sample was recruited. However, we computed a priori power analysis and the outcomes support our initial cohort size. Second, we examined the acute effects of running on sand vs. stable surface. Future studies are needed to examine the long-term effects of running on sand to establish whether sand is suitable as a preventive/rehabilitative means. Third, our participants ran at preferred speed across the walkway. Surface-related differences in running speed were noted which is why the statistical ANOVA model was adjusted for running speed. Future studies should keep running speed constant when running on sand vs. stable ground to verify our findings. Fourth, perhaps a measurement of peroneus longus would have been interesting, since it affects forefoot eversion. Future studies should assess activities of peroneus longus as well.

Conclusion

In summary, our results demonstrate that running on sand induces reduction in speed with a concomitant increase in the activity of ankle dorsiflexors. Runners presenting over-pronated feet generate greater vertical impact loading than neutral runners, while running on sand does not provide substantial reductions in this impact loading for both groups. Moreover, over-pronated feet runners demand greater quadriceps (vastus medialis and rectus femoris) activities during the loading absorption phase of running, likely to counteract instabilities related to foot misalignment.

Practical Applications

The results of this study demonstrated that sedentary people with over-pronated feet may be exposed to greater vertical impact loading during running when compared to sedentary people with neutral feet. Moreover, running on sand contributed only marginally to reducing the instantaneous vertical loading (∼11%) of runners with neutral and over-pronated feet, while an increased muscle activation was required from knee extensors. In practice, sedentary people considering starting a running training program should be aware of their running technique and adjust the training sessions to not overload musculoskeletal structures. Moreover, running coaches working with sedentary people should also be extra-cautious with this population, to avoid early injuries that might force clients to withdraw from practice.

Data Availability Statement

The original contributions presented in the study are included in the article/supplementary material, further inquiries can be directed to the corresponding author/s.

Ethics Statement

The studies involving human participants were reviewed and approved by the Institutional Review Boards of the University of Mohaghegh Ardabili, Iran approved the research protocol (IR.ARUMS.REC.1398.119). The patients/participants provided their written informed consent to participate in this study.

Author Contributions

AJ and MS: conceptualization, methodology, and supervision. NA and AF: data curation and writing-original draft preparation. AO: methodology, writing-reviewing, and editing. UG: conceptualization, methodology, writing-reviewing, and editing. All authors have read and approved the manuscript.

Funding

The authors acknowledge the support of the Deutsche Forschungsgemeinschaft and Open Access Publishing Fund of the University of Potsdam.

Conflict of Interest

The authors declare that the research was conducted in the absence of any commercial or financial relationships that could be construed as a potential conflict of interest.

Publisher’s Note

All claims expressed in this article are solely those of the authors and do not necessarily represent those of their affiliated organizations, or those of the publisher, the editors and the reviewers. Any product that may be evaluated in this article, or claim that may be made by its manufacturer, is not guaranteed or endorsed by the publisher.

Acknowledgments

We gratefully thank all participants for having volunteered to participate in this study.

References

Arnold, E. M., Hamner, S. R., Seth, A., Millard, M., and Delp, S. L. (2013). How muscle fiber lengths and velocities affect muscle force generation as humans walk and run at different speeds. J. Exp. Biol. 216, 2150–2160. doi: 10.1242/jeb.075697

PubMed Abstract | CrossRef Full Text | Google Scholar

Aryana, I. G. N. W., and Artha, I. A. A. (2019). Correlation between knee related injury and biomechanics in distance runners. Edorium J. Orthop. 5:100011O03WA2019.

Google Scholar

Ashnagar, Z., Hadian, M.-R., Olyaei, G., Talebian, S., Rezasoltani, A., Saeedi, H., et al. (2019). Ultrasound evaluation of the quadriceps muscles in pronated foot posture. Foot 38, 86–90. doi: 10.1016/j.foot.2019.01.003

PubMed Abstract | CrossRef Full Text | Google Scholar

Barrett, R. S., Neal, R. J., and Roberts, L. J. (1998). The dynamic loading response of surfaces encountered in beach running. J. Sci. Med. Sport 1, 1–11. doi: 10.1016/s1440-2440(98)80003-0

CrossRef Full Text | Google Scholar

Bellchamber, T. L., and van den Bogert, A. J. (2000). Contributions of proximal and distal moments to axial tibial rotation during walking and running. J. Biomech. 33, 1397–1403. doi: 10.1016/s0021-9290(00)00113-5

CrossRef Full Text | Google Scholar

Bird, A. R., Bendrups, A. P., and Payne, C. B. (2003). The effect of foot wedging on electromyographic activity in the erector spinae and gluteus medius muscles during walking. Gait Posture 18, 81–91. doi: 10.1016/s0966-6362(02)00199-6

CrossRef Full Text | Google Scholar

Brody, D. M. (1982). Techniques in the evaluation and treatment of the injured runner. Orthop. Clin. North Am. 13, 541–558. doi: 10.1016/s0030-5898(20)30252-2

CrossRef Full Text | Google Scholar

Buist, I., Bredeweg, S. W., Lemmink, K. A., Van Mechelen, W., and Diercks, R. L. (2010). Predictors of running-related injuries in novice runners enrolled in a systematic training program: a prospective cohort study. Am. J. Sports Med. 38, 273–280. doi: 10.1177/0363546509347985

PubMed Abstract | CrossRef Full Text | Google Scholar

Cheung, R. T., and Ng, G. Y. (2007). Efficacy of motion control shoes for reducing excessive rearfoot motion in fatigued runners. Phys. Ther. Sport 8, 75–81. doi: 10.1016/j.ptsp.2006.12.002

CrossRef Full Text | Google Scholar

Chung, K. A., Lee, E., and Lee, S. (2016). The effect of intrinsic foot muscle training on medial longitudinal arch and ankle stability in patients with chronic ankle sprain accompanied by foot pronation. Phys. Ther. Rehabil. Sci. 5, 78–83. doi: 10.14474/ptrs.2016.5.2.78

CrossRef Full Text | Google Scholar

Damavandi, M., Dixon, P. C., and Pearsall, D. J. (2012). Ground reaction force adaptations during cross-slope walking and running. Hum. Mov. Sci. 31, 182–189. doi: 10.1016/j.humov.2011.06.004

PubMed Abstract | CrossRef Full Text | Google Scholar

Dugan, S. A., and Bhat, K. P. (2005). Biomechanics and analysis of running gait. Phys. Med. Rehabil. Clin. 16, 603–621. doi: 10.1016/j.pmr.2005.02.007

PubMed Abstract | CrossRef Full Text | Google Scholar

Dunn, J., Link, C., Felson, D., Crincoli, M., Keysor, J., and McKinlay, J. (2004). Prevalence of foot and ankle conditions in a multiethnic community sample of older adults. Am. J. Epidemiol. 159, 491–498. doi: 10.1093/aje/kwh071

PubMed Abstract | CrossRef Full Text | Google Scholar

Farahpour, N., Jafarnezhadgero, A., Allard, P., and Majlesi, M. (2018). Muscle activity and kinetics of lower limbs during walking in pronated feet individuals with and without low back pain. J. Electromyogr. Kinesiol. 39, 35–41. doi: 10.1016/j.jelekin.2018.01.006

PubMed Abstract | CrossRef Full Text | Google Scholar

Gijon-Nogueron, G., Sanchez-Rodriguez, R., Lopezosa-Reca, E., Cervera-Marin, J. A., Martinez-Quintana, R., and Martinez-Nova, A. (2015). Normal values of the Foot Posture Index in a young adult Spanish population: a cross-sectional study. J. Am. Podiatr. Med. Assoc. 105, 42–46. doi: 10.7547/8750-7315-105.1.42

PubMed Abstract | CrossRef Full Text | Google Scholar

Gottschalk, F., Kourosh, S., and Leveau, B. (1989). The functional anatomy of tensor fasciae latae and gluteus medius and minimus. J. Anat. 166:179.

Google Scholar

Grillner, S., Halbertsma, J., Nilsson, J., and Thorstensson, A. (1979). The adaptation to speed in human locomotion. Brain Res. 165, 177–182. doi: 10.1016/0006-8993(79)90059-3

CrossRef Full Text | Google Scholar

Hintermann, B., and Nigg, B. M. (1998). Pronation in runners. Sports Med. 26, 169–176. doi: 10.2165/00007256-199826030-00003

PubMed Abstract | CrossRef Full Text | Google Scholar

Jafarnezhadgero, A. A., Shad, M. M., Majlesi, M., and Granacher, U. (2017). A comparison of running kinetics in children with and without genu varus: a cross sectional study. PLoS One 12:e0185057. doi: 10.1371/journal.pone.0185057

PubMed Abstract | CrossRef Full Text | Google Scholar

Jafarnezhadgero, A. A., Sorkhe, E., and Oliveira, A. S. (2019). Motion-control shoes help maintaining low loading rate levels during fatiguing running in pronated female runners. Gait Posture 73, 65–70. doi: 10.1016/j.gaitpost.2019.07.133

PubMed Abstract | CrossRef Full Text | Google Scholar

Jafarnezhadgero, A., Fatollahi, A., Amirzadeh, N., Siahkouhian, M., and Granacher, U. (2019). Ground reaction forces and muscle activity while walking on sand versus stable ground in individuals with pronated feet compared with healthy controls. PLoS One 14:e0223219. doi: 10.1371/journal.pone.0223219

PubMed Abstract | CrossRef Full Text | Google Scholar

James, S. L., Bates, B. T., and Osternig, L. R. (1978). Injuries to runners. Am. J. Sports Med. 6, 40–50.

Google Scholar

Jefferson, R., Collins, J., Whittle, M., Radin, E., and O’Connor, J. (1990). The role of the quadriceps in controlling impulsive forces around heel strike. Proc. Inst. Mechan. Eng. Part H 204, 21–28. doi: 10.1243/PIME_PROC_1990_204_224_02

CrossRef Full Text | Google Scholar

Kagaya, Y., Fujii, Y., and Nishizono, H. (2015). Association between hip abductor function, rear-foot dynamic alignment, and dynamic knee valgus during single-leg squats and drop landings. J. Sport Health Sci. 4, 182–187. doi: 10.1016/j.jshs.2013.08.002

CrossRef Full Text | Google Scholar

Li, L., Landin, D., Grodesky, J., and Myers, J. (2002). The function of gastrocnemius as a knee flexor at selected knee and ankle angles. J. Electromyogr. Kinesiol. 12, 385–390. doi: 10.1016/s1050-6411(02)00049-4

CrossRef Full Text | Google Scholar

Lichtwark, G., and Wilson, A. (2008). Optimal muscle fascicle length and tendon stiffness for maximising gastrocnemius efficiency during human walking and running. J. Theor. Biol. 252, 662–673. doi: 10.1016/j.jtbi.2008.01.018

PubMed Abstract | CrossRef Full Text | Google Scholar

Luheff, A., Brucker, J. B., and Hohmann, E. (2005). Kinematic Differences When Running on a Firm Surface Compared With Soft dry Sand, eds H. Pinnington, D. LLoyd, T. Besier, and B. Dawson (Notre Dame, IN: University Of Notre Darnme).

Google Scholar

McMahon, T. A., and Greene, P. R. (1979). The influence of track compliance on running. J. Biomech. 12, 893–904. doi: 10.1016/0021-9290(79)90057-5

CrossRef Full Text | Google Scholar

McPoil, T. G., and Cornwall, M. W. (1996). Relationship between three static angles of the rearfoot and the pattern of rearfoot motion during walking. J. Orthop. Sports Phys. Ther. 23, 370–375. doi: 10.2519/jospt.1996.23.6.370

PubMed Abstract | CrossRef Full Text | Google Scholar

Merryweather, A. S. (2008). Lower Limb Biomechanics of Walking on Slanted and Level Railroad Ballast, Ph.D. dissertation. Salt Lake City, UT: The University of Utah.

Google Scholar

Murley, G. S., Landorf, K. B., Menz, H. B., and Bird, A. R. (2009). Effect of foot posture, foot orthoses and footwear on lower limb muscle activity during walking and running: a systematic review. Gait Posture 29, 172–187. doi: 10.1016/j.gaitpost.2008.08.015

PubMed Abstract | CrossRef Full Text | Google Scholar

O’Connor, K. M., and Hamill, J. (2004). The role of selected extrinsic foot muscles during running. Clin. Biomech. 19, 71–77. doi: 10.1016/j.clinbiomech.2003.09.001

PubMed Abstract | CrossRef Full Text | Google Scholar

Oatis, C. A. (2009). Kinesiology: The Mechanics and Pathomechanics of Human Movement. Philadelphia, PA: Lippincott Williams & Wilkins.

Google Scholar

Ounpuu, S. (1994). The biomechanics of walking and running. Clin. Sports Med. 13, 843–863.

Google Scholar

Pinnington, H. C., and Dawson, B. (2001). The energy cost of running on grass compared to soft dry beach sand. J. Sci. Med. Sport 4, 416–430. doi: 10.1016/s1440-2440(01)80051-7

CrossRef Full Text | Google Scholar

Pinnington, H. C., Lloyd, D. G., Besier, T. F., and Dawson, B. (2005). Kinematic and electromyography analysis of submaximal differences running on a firm surface compared with soft, dry sand. Eur. J. Appl. Physiol. 94, 242–253. doi: 10.1007/s00421-005-1323-6

PubMed Abstract | CrossRef Full Text | Google Scholar

Pirscoveanu, C.-I., Dam, P., Brandi, A., Bilgram, M., and Oliveira, A. S. (2021). Fatigue-related changes in vertical impact properties during normal and silent running. J. Sports Sci. 39, 421–429. doi: 10.1080/02640414.2020.1824340

PubMed Abstract | CrossRef Full Text | Google Scholar

Redmond, A. C., Crosbie, J., and Ouvrier, R. A. (2006). Development and validation of a novel rating system for scoring standing foot posture: the Foot Posture Index. Clin. Biomech. 21, 89–98. doi: 10.1016/j.clinbiomech.2005.08.002

PubMed Abstract | CrossRef Full Text | Google Scholar

Requa, R. K., DeAvilla, L. N., and Garrick, J. G. (1993). Injuries in recreational adult fitness activities. Am. J. Sports Med. 21, 461–467. doi: 10.1177/036354659302100323

PubMed Abstract | CrossRef Full Text | Google Scholar

Semciw, A. I., Pizzari, T., Murley, G. S., and Green, R. A. (2013). Gluteus medius: an intramuscular EMG investigation of anterior, middle and posterior segments during gait. J. Electromyogr. Kinesiol. 23, 858–864. doi: 10.1016/j.jelekin.2013.03.007

PubMed Abstract | CrossRef Full Text | Google Scholar

Svenningsen, F. P., de Zee, M., and Oliveira, A. S. (2019). The effect of shoe and floor characteristics on walking kinematics. Hum. Mov. Sci. 66, 63–72. doi: 10.1016/j.humov.2019.03.014

PubMed Abstract | CrossRef Full Text | Google Scholar

Thompson, P. D., Buchner, D., Piña, I. L., Balady, G. J., Williams, M. A., Marcus, B. H., et al. (2003). Exercise and physical activity in the prevention and treatment of atherosclerotic cardiovascular disease: a statement from the Council on Clinical Cardiology (Subcommittee on Exercise, Rehabilitation, and Prevention) and the Council on Nutrition, Physical Activity, and Metabolism (Subcommittee on Physical Activity). Circulation 107, 3109–3116.

Google Scholar

Thordarson, D. B., Schmotzer, H., Chon, J., and Peters, J. (1995). Dynamic support of the human longitudinal arch. A biomechanical evaluation. Clin. Orthop. Relat. Res. 316, 165–172.

Google Scholar

Thorstensson, A., Carlson, H., Zomlefer, M. R., and Nilsson, J. (1982). Lumbar back muscle activity in relation to trunk movements during locomotion in man. Acta Physiol. Scand. 116, 13–20. doi: 10.1111/j.1748-1716.1982.tb10593.x

PubMed Abstract | CrossRef Full Text | Google Scholar

van den Berg, M. E., Barr, C. J., McLoughlin, J. V., and Crotty, M. (2017). Effect of walking on sand on gait kinematics in individuals with multiple sclerosis. Mult. Scler. Relat. Disord. 16, 15–21. doi: 10.1016/j.msard.2017.05.008

PubMed Abstract | CrossRef Full Text | Google Scholar

Whittle, M. W. (2014). Gait Analysis: An Introduction. Oxford: Butterworth-Heinemann.

Google Scholar

Wischnia, B. (1982). Beach running. Runners World 76, 48–49.

Google Scholar

Xu, H., Wang, Y., Greenland, K., Bloswick, D., and Merryweather, A. (2015). The influence of deformation height on estimating the center of pressure during level and cross-slope walking on sand. Gait Posture 42, 110–115. doi: 10.1016/j.gaitpost.2015.04.015

PubMed Abstract | CrossRef Full Text | Google Scholar

Yong, J. R., Silder, A., and Delp, S. L. (2014). Differences in muscle activity between natural forefoot and rearfoot strikers during running. J. Biomech. 47, 3593–3597. doi: 10.1016/j.jbiomech.2014.10.015

PubMed Abstract | CrossRef Full Text | Google Scholar

Yoo, B. (2014). The Effect of Carrying a Military Backpack on a Transverse Slope and Sand Surface on Lower Limb During Gait. Salt Lake City, UT: The University of Utah.

Google Scholar