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01-12-2021 | Research | Uitgave 1/2021 Open Access

# Influence of the medial longitudinal arch of the foot in adult women in ankle isokinetic performance: a cross-sectional study

Tijdschrift:
Journal of Foot and Ankle Research > Uitgave 1/2021
Auteurs:
Leandro C. Guenka, Aline C. Carrasco, Alexandre R. M. Pelegrinelli, Mariana F. Silva, Laís F. Dela Bela, Felipe A. Moura, Jefferson Rosa Cardoso
Belangrijke opmerkingen

## Publisher’s Note

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Abbreviations
MLA
Medial longitudinal arch
MD
Mean difference
ω2 p
Partial omega squared
3D
Tridimensional
IRB
Institutional review board
PT/BM
Peak torque per body mass
LR
ROM
Range of motion
Md
Median
25–75 %
Quartiles
BMI
Body mass index
Mean
SD
Standard deviation
AHI
Arch height index
AHF
Arch height flexibility
AngPT
Angle of peak of torque
N.m/kg
Newton meter/kilogram
°/s
Degrees per second
r
Pearson correlation coefficient

## Background

Studies suggest that a relationship between the medial longitudinal arch of the foot (MLA) and the biomechanical alterations of the lower limb may predispose a person to pain and injuries such as lateral ankle sprain [ 1, 2]. The height of the MLA can be categorized as high (pes cavus), normal, or flat arch (pes planus) and clinically, the MLA height index has proven to be a robust measure [ 35] and disfunctions are often associated with foot type [ 6, 7].
Two studies support the fact that lower MLA flexibility may accompany higher stress in soft-tissue and medial injuries [ 8, 9]. In pes cavus, there is a shortening of soft tissues that support the longitudinal arch, such as the plantar fascia and tibialis posterior muscles, with common ankle instability and lateral foot overload [ 10, 11], leading to abnormal stress in the medial capsule-ligament structures of the foot [ 12].
MLA structure is linked to intrinsic factors such as sex, and women may be at a greater risk for soft-tissue injuries than males and may even have a posterior tibial tendon dysfunction, a condition that is associated with flatfoot [ 13, 14]. Women also have less flexibility in the MLA when compared to men [ 9], accompanied by greater stress in the MLA, increasing the risk of injuries such as plantar fasciitis [ 8]. Furthermore, the literature suggests that there are differences in muscle strength and patterns of muscle recruitment strategies between men and women [ 1517]. Previous research has focused on the isometric and concentric analysis of ankle muscle performance only in men and compensations were identified in plantarflexion at 30 °/s with greater stress in the medial compartment of the ankle [ 18, 19]. Beside this, variations in the height of the MLA in men correlate negatively with peak torque per body mass (PT/BM) for cavus feet in plantarflexion at 120 °/s, when compared with other types of feet [ 19].
The isokinetic dynamometer is the gold standard for assessing ankle isokinetic performance [ 20]. Identifying deficits and their relationship with changes in the MLA of the foot height can be used clinically to identify an increased risk of predisposition to lower limb injuries and can be a marker of recovery during musculoskeletal treatment after injury or surgical interventions [ 21, 22], as well as giving a general indication of the functional capacity of a subject [ 20, 23]. The use of isokinetic devices involves three phases of range of motion (ROM): (a) acceleration; (b) sustained velocity or load range, and (c) deceleration [ 21, 22]. The majority of studies do not take into account these three isokinetic phases, which may lead to measurement errors at high contractile velocities, since the subject may not benefit from the machine-offered resistance. Another way of assessing ankle isokinetic performance is through 3D surface maps. This method considers the torque–angle–velocity relationship, creating a behavioral map of these three variables throughout movement [ 24], adding information about the muscle action during exercise performance at different velocities. Thus, the aims of this study were to evaluate the muscular performance of cavus, planus, and normal feet by means of torque/body mass and the isokinetic phases, to generate 3D surface map analysis, and to verify whether there is a relationship between MLA height and arch height flexibility with isokinetic performance.

## Methods

### Study Design

This is a cross-sectional study with descriptive and analytical components.

### Participants

In total, 105 asymptomatic adult women, recruited through social media, aged between 20 and 40 years with no pain, discomfort, or disorders in the lower limbs in the previous 12 months. Women with a history of prior surgery to musculoskeletal structures (bones, joint structures, nerves, and fractures) and/or deformities in the lower limbs were excluded. Women with neurological, cardiovascular, or musculoskeletal dysfunction that prevented them from performing the evaluation, or pregnant were also excluded.
The sample size was calculated using the program G*Power 3.1.9.4 [ 25]. The F test was used to find differences in means between three independent groups, with an effect size of 0.60, based on a previous study [ 26], an acceptable margin of error of 5 % (α), and 80 % power. The necessary number of women for each group was 35. The signed informed consent was obtained from all women and the study design was approved by the IRB-Universidade Estadual de Londrina (#90238618.8.0000.5231).
The anthropometric measurements of the feet were taken only in the dominant limb. The dorsal height (measured at 50 % of the total foot length) and truncated foot length (the distance from the posterior heel to the first metatarsal head) were measured along the medial border of the foot [ 14]. The dominant member was defined by asking the individual: [ 27].
The arch height flexibility (AHF) was defined as the change in arch height (distance from the dorsal surface to the ground) from sitting to standing because of the change in load borne by the arch during these activities. The flexibility of the MLA was calculated by change the height of the arch (distance from the dorsal surface to land) between sitting and standing positions (cm), divided by 0.4 times the body mass (kg) and multiplied by 100 N [ 28]. The sample was categorized into three groups according to the Arch Height Index (AHI) classification: 1, cavus feet; 2, normal feet, and 3, planus feet [ 3, 4]. The validity and reliability of the AHI were previously established by Butler et al. [ 3].

### Protocol

Isokinetic performances of plantarflexion (gastrocnemius, plantaris, soleus, and fibularis longus) and dorsiflexion (tibialis anterior, extensor hallucis longus, and extensor digitorum longus) were measured using the Biodex System 4® Dynamometer (Biodex Medical System Inc., Shirley, NY), in concentric mode at 30, 60, and 90 °/s, with a sampling frequency of 100 Hz, per the standard Biodex recommendations for ankle strength assessment [ 29].
The study required a single visit, during which the demographic data were collected (height, weight, and age), and assessment of the AHI and arch height flexibility were carried out. Before the tests, the warm-up consisted of 10 min on a stationary ergometer at a target speed of 30 km/h [ 30] under the supervision of the examiner. After the warm-up, women performed the equipment familiarization, with two repetitions before the test at each velocity. This was their first experience with ankle isokinetic testing. Finally, the real testing was carried out. Similar procedures to the warm-up and familiarization were performed according to the study [ 31]. The ankle isokinetic protocol was characterized by a set of six repetitions at each velocity, performed in a simple draw, with a rest period of 90 s between sets.
The women were instructed not to perform high intensity running exercise on the day of the test, since studies have verified that strength loss can occur after running events [ 32, 33] which could affect the test result.
Previously the test, the ROM limits was standardized (40 ° plantarflexion and 20 ° dorsiflexion), with a total of 60 degrees, for all the evaluated individuals, similar range of motion to the study [ 34] who tested the reliability of ankle isokinetic performance. The women were seated on the dynamometer, and stabilized with belts around the trunk, pelvis, and thigh. The dynamometer set-up was as follows: orientation = 90 °, tilt = 0 ° (axis direction), seat orientation: 90 °, seatback tilt: 70 °, and knee flexion: 30 °; the axis passed through the body of the talus and lateral malleolus or just above the medial malleolus. The women were instructed to perform maximum effort during all repetitions, and verbal encouragement and visual feedback were provided. Tests were assessed by the same researcher with experience in performing dynamometer isokinetic testing/treatment. For reliability purposes, a coefficient of variation of less than 10 %, for each set, was considered acceptable, as described in Malina et al. [ 35].

### Data processing

The ankle isokinetic data were processed using MATLAB® (The MathWorks, Inc., Natick, USA) algorithms. The torque signal of each test was first filtered by a second-order low-pass Butterworth filter, with a cut-off frequency of 10 Hz. In the three velocities performed, with five repetitions each, the average values of each specified variable were withdrawn. The percentages of each isokinetic phase (acceleration - ACC, sustained velocity - load range - LR, and deceleration - DC) were calculated in relation to the total range of motion. The mean of total ROM in each repetition was calculated, because the limits of range of motion is not achieved at all repetitions. Peak torque/body mass (PT/BM) and angle of peak of torque were also calculated only during the load range phase [ 22]. The PT/BM results is presented in percentage in relation the body mass.

### Statistical analysis

For statistical analyses, the numerical variables were evaluated for the distribution of normality using the Shapiro–Wilk test. The results are presented as mean ( $$\overline{x}$$) and standard deviation, except for the anthropometric characteristics, which are presented in median and quartiles (25–75 %) because they failed to meet the Gaussian distribution. Mean difference (MD) and 95 % confidence intervals (CI) were also calculated between groups. Anthropometric variables were compared at the beginning of the study using one-way ANOVA or Kruskal-Wallis. The three groups were compared for isokinetic variables by means of one-way ANOVA, followed by the Levene test to confirm the homogeneity of the variances. If the F test was statistically significant, we used the Post-hoc of Bonferroni. For the results that showed differences between the groups, the effect size was calculated (partial omega-squared, ω 2 p), which is an estimate of how much variation in response variables is explained by explanatory variables; ω 2 p can have values between ± 1, zero indicates no effect. If the observed F is less than one, the ω 2 p will be negative. The magnitude of the effect was considered as 0.01 small 0.06 moderate, and 0.15 large [ 36, 37].
Pearson correlation coefficient (95 % CI) was calculated to verify the relationship between the variable flexibility and the height of the MLA and peak of torque (dorsiflexion/plantarflexion) in the sustained velocity phase. Significance was stipulated at 5 % and all analyses were performed with SPSS version 25.0 (IBM SPSS®, Armonk, NY, USA).

## Results

Anthropometric characteristics and other variables are shown in (Table  1). Table  2 showed the results of the isokinetic phases and the ROM. In plantarflexion, statistically significant differences were observed in the percentage of deceleration at 60 °/s in the cavus group (MD = 1.7 %; ω 2 p = 0.05), when compared with the normal group. The ROM was higher in the planus group at 90 °/s in relation the normal group (MD = 2.6 °; ω 2 p = 0.09).
Table 1
Anthropometric characteristics of the sample by groups and classification of foot types
Variables
Normal
( n = 35)
Cavus
( n = 35)
Planus
( n = 35)
P
Age (years):
Md
(25–75 %)
25
(23.95–28.04)
23
(23.29–27.27)
21
(21.6–24.7)
0.07
BMI (kg/m 2 ):
Md
(25–75 %)
23.53
(22.17–24.19)
22.83
(22.39;24.35)
22.7
(21.6;23.7)
0.55
Abdominal circumference (cm):
Md (25–75 %)
75 (72.9–80)
78 (75–80)
71 (68.5–73.4)
0.24
AHI:
$$\overline{x}$$(SD)
[95 % CI]
0.35 (0.02)
[0.34;0.35]
0.38 (0.01)
[0.38;0.38]
0.28 (0.01)
[0.38;0.38]
0.001 a
AFH (m/kgf):
$$\overline{x}$$(SD)
[95 % CI]
1.42 (0.89)
[1.28;3.33]
Neutral
1.22 (0.84)
[0.93;1.51]
Rigid
2.80 (1.47)
[2.29;3.31]
Very flexible
0.004 b
Md: median; 25–75 %: quartiles; BMI body mass index; $$\overline{x}$$ mean; SD standard deviation; AHI arch height index (Normal AHI: 0.30 to 0.37, Cavus AHI ≥ 0.38, Planus AHI: ≤ 0.29 [ 4]); AHF arch height flexibility (very rigid < 0.9, rigid 0.9 to 1.3, neutral 1.3 to 1.6, flexible 1.6 to 2.0 and very flexible > 2.0 [ 16]); and m/kgf: meter/kilogram force. a difference between groups. b difference between the cavus and planus groups.
Table 2
Isokinetic phases represented by the percentage of range of motion
Ankle
Normal $$\overline{x}$$(SD) [95 % CI] ( n = 35)
Cavus $$\overline{x}$$(SD) [95 % CI] ( n = 35)
Planus $$\overline{x}$$(SD) [95 % CI] ( n = 35)
Plantar
flexion
ACC (%)
LR (%)
DC (%)
ROM (°)
ACC (%)
LR (%)
DC (%)
ROM (°)
ACC (%)
LR (%)
DC (%)
ROM (°)
30 °/s
8.27
(4.19)
[6.81;
9.71]
51.36 (20.52) [44.31;58.41]
40.36 (18.86)
[33.88;46.84]
52.31 (6.37) [50.12;54.50]
10.15 (6.82)
[7.81;12.50]
40.23 (21.44)
[32.86;47.58]
49.92 (17.23)
[44.00;55.84]
53.71 (5.60)
[51.78;55.63]
9.56 (4.60)
[7.98;11.14]
45.65 (20.01)
[38.78;52.53]
44.73 (19.03)
[38.19;51.27]
54.93 (5.38)
[53.08;56.7]
60 °/s
17.39 (20.31)
[10.41;24.37]
73.21 (20.69)
[66.10;80.31]
9.18 (3.35) [8.03;10.33]
54.77 (5.36)
[52.93;56.61]
19.76 (19.13)
[13.19;26.33]
72.77 (19.48)
[66,08;79.47]
7.44 (1.13) [7.05;7.83] a
55.82 (4.37) [54.32;57.33]
24.01 (21.24)
[16.72;31.31]
68.93 (18.01) [62.74;75.12]
8.06
(3.02)
[7.02;
9.10]
56.78 (4.86) [55.11;58.45]
90 °/s
36.25 (25.78) [27.40;45.11]
52.72 (27.54) [43.25;62.18]
10.16 (4.17)
[8.73;11.60]
55.60 (4.08)
[54.19;
57]
37.44 (27.17)
[28.10;46.77 ]
50.59 (29.05) [40.61;60.57]
11.23 (8.89)
[8.87;14.98]
56.97 (2.62) [56.07;57.87]
45.81 (25.17)
[37.16;54.45]
41.44 (29.42)
[31.33;51.54]
12.95 (13.08)
[8.46;
17.45]
58.26 (2.49) a
[57.40;59.11]
Dorsi-
flexion
ACC (%)
LR (%)
DC (%)
ROM (°)
ACC (%)
LR (%)
DC (%)
ROM (°)
ACC (%)
LR (%)
DC (%)
ROM (°)
30 °/s
2.85
(1.28)
[2.41;
3.29]
90.94 (4.15) [89.51;92.36]
6.17 (4.05) [4.78;7.57]
52.55 (5.75) [50.58;54.53]
3.57
(3.16)
[2.48;
4.66]
89.46 (5.72) [87.50;91.43]
6.88
(3.55)
[5.66;
8.10]
52.75 (5.16)
[50,98;
54,52]
3.00 (2.83)
[2.02;3.97]
90.70
(3.90) [89.36;92.04]
6.37
(3.49)
[5.17;
7.57]
53.93 (6.07)
[51.84;56.01]
60 °/s
7.10
(2.05)
[6.40;
7.81]
73.74 (18.07) [67.44;80.05]
19.20 (16.34)
[13.13;25.27]
54.97 (4.69) [53.35;56.58]
7.48
(2.15)
[6.75;
8.22]
68.24 (17.44) [62.25;74.24]
24.04 (16.97) [18.21;29.87]
55.65 (4.18) [54.21;57.08]
6.66 (1.84)
[6.02;7.29]
79.21 (8.70) [76.22;82.21] b
13.94 (8.85) [10.90;16.98] b
56.47 (4.06) [55.08;57.87]
90 °/s
17.51 (14.00)
[12.70;22.32]
29.39 (25.65) [20.57;38.20]
53.16 (25.80)
[44.29;62.02]
54.90 (4.65)
[53.30;56.50]
18.01 (13.29) [13.44;22.57]
38.16 (28.36) [28.42;47.90]
44.01 (23.80) [35.83;52.19]
56.58 (3.73) [55.81;57.67]
15.91 (4.55)
[14.34;17.47]
35.20 (23.39) [27.16;43.23]
48.93 (23.44) [40.87;56.98]
57.94 (2.93)
[56.93;58.95] a
$$\overline{x}$$: mean; SD standard deviation; 95 % CI confidence interval; % percentage of each phase in relation to the total range of motion; ACC acceleration; LR load range; DC deceleration; ROM range of motion; and deg: degrees. a Significant difference compared to the normal group. b Significant difference between planus group and cavus group.
In dorsiflexion at 60 °/s, for the planus group, the DC phase was lower (MD = 10.1 %; ω 2 p = 0.05) when compared with the cavus group. This difference occurred because the load range increases in the planus group in relation to the cavus group (MD = 10.9 %; ω 2 p = 0.06). The range of motion was higher in the planus group (MD = 3.0 %; ω 2 p = 0.09) at 90 °/s in relation the normal group.
For PT/BM in dorsiflexion at 60 °/s, the cavus (MD = − 3 %; ω 2 p = 0.06) and planus (MD = − 1.1 %; ω 2 p = 0.06) groups presented a significant deficit when compared to the normal group (Table  3). The others velocities and in plantarflexion not showed differences between the groups.
Table 3
Comparison of normalized peak torque by body mass and peak torque angle at different velocities
Ankle
Normal $$\overline{x}$$(SD) [95 % CI]
Cavus $$\overline{x}$$(SD) [95 % CI]
Planus $$\overline{x}$$(SD) [95 % CI]
Plantar
flexion
PT/BM
(%)
AngPT
(°)
PT/BM
(%)
AngPT
(°)
PT/BM
(%)
AngPT
(°)
30 °/s
96.99 (29.70)
[86.78;107.19]
22.54 (3.00)
[21.51;23.57]
88.71 (31.35)
[77.94;99.48]
23.45 (4.63)
[21.86;25.05]
85.89 (32.09)
[74.86;96.91]
21.21 (5.69)
[19.25;23.16]
60 °/s
78.93 (28.05)
[69.29;88.57]
24.82 (6.39)
[22.62;27.02]
76.62 (23.47)
[68.55;84.69]
26.83 (8.91)
[23.76;29.89]
65.46 (25.21)
[56.79;74.12]
28 (6.86)
[25.64;30.36]
90 °/s
58.42 (25.11)
[49.79;67.05]
32.08 (9.17)
[28.93;35.23]
54.87 (27.57)
[45.40;64.35]
32.88 (10.87)
[29.15;36.62]
51.09 (26.67)
[41.92;60.25]
35.74 (11.47)
[31.80;39.68]
Dorsi-flexion
PT/BM
(%)
AngPT
(°)
PT/BM
(%)
AngPT
(°)
PT/BM
(%)
AngPT
(°)
30 °/s
29.79 (5.04)
[28.06;31.53]
17.03 (4.36)
[15.53;18.53]
27.59 (5.48)
[25.71;29.48]
17.38 (5.46)
[15.50;19.26]
31.31 (13.15)
[26.79;35.83]
16.85 (4.73)
[15.22;18.48]
60 °/s
26.81 (4.58)
[25.24;28.38]
18.10 (5.53)
[16.20;20]
23.88 (4.68)
[22.27;25.49]*
17.73 (5.79)
[15.74;19.72]
25.70 (4.79)
[25.05;28.34]*
20.22 (8.60)
[17.26;23.17]
90 °/s
21.63 (3.35)
[20.47;22.78]
11.40 (6.25)
[9.26;13.55]
21.04 (5.08)
[19.29;22.78]
10.86 (3.67)
[9.60;12.12]
21.78 (3.97)
[20.41;23.14]
13.26 (8.80)
[10.23;16.29]
$$\overline{x}$$: mean; SD standard deviation; 95 % CI confidence interval; °/s degrees per second; PT/BM peak torque/body mass; AngPT angle of peak of torque; and %: percentage of the peak of torque in relation the body mass.* P ≤ .05 compared with normal group (ω 2 p = 0.06 in both).
In the correlation of the arch height flexibility with the PT/BM, the cavus group presented a significant negative result of r = − .37, 95 % CI [− 0.64; −0.01] (Fig.  1), where 14.3 % of the PT/BM variation at 30 °/s in plantarflexion may be credited with manipulating the value of the arch height flexibility. For the planus feet group, we observed that r = − .21, 95 % CI [− 0.50; 0.13] (Fig.  2), where 4.4 % of the variation of PT/BM at 30 °/s in plantarflexion can be credited with manipulating the value of the arch height flexibility.
Regarding the MLA height with PT/BM, the planus group presented a positive correlation of 0.36 95 % CI [0.03; 0.61]; that is, 12.9 % of the variability of PT/BM at 90 °/s in plantarflexion may be credited to the manipulation of the value of the MLA height index of the foot. In addition, r = .30 95 % CI [0.57; 0.03] was observed in the planus group, where 9 % of the PT/BM variability at 60 °/s in dorsiflexion could be explained by the variability of the MLA height index of the foot (Table  4).
Table 4
MLA height correlation with muscle performance (r)

Normal ( n = 35)
Cavus ( n = 35)
Planus ( n = 35)
Plantar
flexion
PT/BM (%) $$\overline{x}$$ (SD); r
PT/BM (%) $$\overline{x}$$ (SD); r
PT/BM (%) $$\overline{x}$$ (SD); r
30 °/s
96.99 (29.70); − 0.01
88.71 (31.35); 0.04
85.89 (32.09); 0.25
60 °/s
78.93 (28.05); − 0.16
76.62 (23.47); − 0.07
65.46 (25.21); 0.25
90 °/s
58.42 (25.11); 0.10
54.87 (27.57); − 0.20
51.09 (26.67); 0.36
Dorsi-flexion
PT/BM (%) $$\overline{x}$$ (SD); r
PT/BM (%) $$\overline{x}$$ (SD); r
PT/BM (%) $$\overline{x}$$ (SD); r
30 °/s
29.79 (5.04); − 0.23
27.59 (5.48); 0.17
31.31 (13.15); 0.17
60 °/s
26.81 (4.58); − 0.30
23.88 (4.68); 0.07
26.70 (4.79); 0.30
90 °/s
21.63 (3.35); − 0.22
21.04 (5.08); 0.12
21.78 (3.97); 0.10
MLA Medial Longitudinal Arch; r Pearson correlation coefficient; $$\overline{x}$$: mean; SD standard deviation; PT/BM peak torque/body mass; and % percentage of the peak of torque in relation the body mass.
Mean peak torque and the resulting surface maps surface models are shown in (Figs.  3 and 4) for women for both plantarflexor and dorsiflexor muscles. The dark gray area indicates the moments in which there were higher values of the peak torque while the areas in light gray are the instants of smaller values of this variable. There is a progressive and constant decrease in peak torque with an increase in velocity in plantarflexion for the normal foot group. However, in the cavus foot group there was an abrupt drop in the peak torque at 60 °/s. The planus foot group presented lower peak torque at all velocities when compared to the normal and cavus feet groups.
In dorsiflexion, there was a steep decline in the peak torque at 60 °/s in the three groups of feet. The normal foot group demonstrated a higher peak torque peak at 90 °/s when compared to the cavus and planus feet groups. The cavus foot group had the lowest peak torque at 90 °/s when compared to the normal and planus feet group. Finally, the planus foot group showed lower peak torque as it presented a light gray color, mainly at 30 °/s, when compared to the normal and cavus feet groups.

## Discussion

The primary results of this study found that adult women with planus feet presented better capacity to attain and sustain the velocity (load range) in dorsiflexion at 60 °/s when compared with the cavus feet group. The torque showed differences only in dorsiflexion at 60 °/s. The PT/BM variable in dorsiflexion at 60 °/s (planus and cavus) presented a deficit with significance, when compared with the normal group.
In the correlation of the arch height flexibility with the PT/BM, the planus group presented a negative result with the variation in the PT/BM at 30 °/s in plantarflexion. Regarding the MLA height with the PT/BM, the planus feet group presented a positive correlation with the PT/BM at 90 °/s in plantarflexion. For all others variables analyzed the type of foot not influenced the isokinetic muscle performance in the muscles involved in plantarflexion and dorsiflexion.
Studies have pointed out an association between planus feet and excessive tension of the triceps sural, fibular, and posterior tibial tendons [ 38, 39]. The present study found an increased percentage of load range in dorsiflexion at 60 °/s in the planus group, due to a possible adaptation of muscle performance in view of posterior tibial tendon dysfunctions and greater tension in the sural triceps.
A significant deficit in PT/BM (approximately 7.6 %, with small effect size) in dorsiflexion at 60 °/s for the cavus and planus groups compared with the normal group was also observed in this study. It is possible these results are related, because planus feet lead to deformity of the forefoot associated with muscular imbalance of the leg, with weakness of the anterior tibial, and extensors of the toes [ 40, 41].
Individuals with planus feet are typically considered as having flexible feet, while individuals with cavus feet are more likely to have more rigid feet [ 19]. Planus feet in adults showed posterior tibial tendon insufficiency, resulting in significant deformity and disability [ 42]. Data that may support the results of the current study found that planus feet showed a statistically significant difference (8.2 %) in the load range at 60 °/s in dorsiflexion, when compared to the normal group. Although in most cases planus feet show no symptoms such as pain and/or marked musculoskeletal disorders, in hypermobile (flexible) planus feet, there is shortening of the Achilles tendon, which could explain a greater load range through muscle compensation mechanisms to achieve an adequate dorsiflexion movement [ 43].
This study verified that the cavus and planus feet groups presented classifications of MLA height flexibility as rigid and very flexible, respectively [ 14]. These changes were reflected in the negative correlation between flexibility and PT/BM at 30 and 60 °/s in plantarflexion, mainly for the cavus group; 14.2 % of the variability in foot flexibility can be explained by the variability in the PT/BM (or vice versa) and 85.8 % is not explained. Variance in scores is due to other factors such as the severity of malalignment of cavovarus, the grade of forefoot in plantarflexion and pronation, and both intrinsic and extrinsic muscle imbalance [ 44] at both velocities, when compared with the normal group.
Another relevant result was the correlation of the height of the MLA with the PT/BM at 90 °/s in plantarflexion, for the planus feet group this presented 12.9 % of the variability in the PT/BM at 90 °/s may be explained by the variability in the height of the MLA (or vice versa) and 87.1 % (exclusive variance) is not explained. Variance in scores is due to other factors such as age-related posterior tibial tendon degeneration, peritendinous injections, recurring micro traumas, collagen diseases, vascular reasons, and accessory navicular bone [ 45]. In dorsiflexion at 60 °/s, 9 % of shared variance and 81 % of variance were observed exclusively for the planus group between the height of the MLA and the PT/BM. Outcomes of the present study show, mainly in dorsiflexion at 60 °/s velocity, that the normal group presented improved muscular performance than the other two groups, with a higher PT/BM and lower ROM of acceleration to reach the sustained velocity.
A decrease in the peak torque was observed with an increase in the angular velocity, as demonstrated in other studies [ 46, 47]. Surface maps provide a comprehensive understanding of dynamic behavior of a muscle compared to static assessments, due to focusing on length − tension and length − velocity relationships [ 24]. These results may allow for identification of muscular deficits and help during treatments for foot dysfunctions. Adult acquired flatfoot deformity or other dysfunctions are common disorders that typically affect middle-aged adults over 40 years of age and older women, resulting in foot pain, malalignment, and loss of function [ 48]. The sample of this research was constituted by adult women up to 40 years old with different types of feet, which explains some of the small differences found in the muscular performance.
Ankle strength can be used clinically as a marker of recovery during musculoskeletal treatment after injury or surgical interventions [ 49]. The results of the present study pointed out that dorsiflexor muscles in planus feet should be strengthened mainly at 60 °/s.
The study has some limitations, for example, we evaluated only women aged 20–40 years, however, the foot arch is a structure that changes with age [ 50] with lower foot circumference in women over 55 years of age compared to younger adults [ 51], which can influence the height of the MLA. Secondly, the inversion and eversion movements were not performed since most of the subjects reported difficulties or discomfort when generating maximal torque in the medio–lateral direction at higher velocities, as in the study of Gosonova et al. [ 34]. Lastly, we did not test muscle strength in the eccentric mode, considering that the higher tension forces generated with this type of contraction might have put our participants at risk for muscle-tendon injuries.

## Conclusions

The planus foot group differed in load range from the cavus group at 60 °/s in dorsiflexion. For PT/BM in dorsiflexion to 60 °/s, the cavus and planus groups presented a significant deficit when compared to the normal group. The flexibility of the MLA correlated negatively with the cavus group in plantarflexion at 30 °/s.

## Acknowledgements

The authors wish to thank the Carci Company for their technical support and FINEP (Financier of Studies and Projects, grants # 01/2007). The last author would also like to thank the National Council for Scientific and Technological Development (CNPq), a Brazilian research agency for the productivity scholarship granted to him.

## Declarations

### Ethics approval and consent to participate

We obtained signed informed consent from all women, and the study design was approved by the IRB (#90238618.8.0000.5231).

### Consent for publication

All individuals included in the study provided signed consent for publication. All authors provided consent for publication.

### Competing interests

The authors declare no conflicts of interest.

## Publisher’s Note

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