Abstract:SUMMARYThe present study reports the development of a detailed three-dimensional (3D) finite element (FE) foot model for investigating the effect of the material properties and thicknesses of the landing mat on stress distribution and concentration point within the metatarsals during landing at an inversion position. Foam material mat insert between the foot and ground with different thicknesses had been systematic studied. The predicted plantar pressure distribution showed a good agreement with the experiment… Show more
“…Poisson's ratio=0.3) [23]. As in previous works [11] and other literatures [24], the stiffness of the Cartilage, Plantar Fascia and Ligament is set at 1, 350 and 250 MPa, respectively; the Poisson's ratio is set as 0.4. The phalanges are assumed to have the same material properties as the bones [16].…”
Section: Materials Propertiesmentioning
confidence: 99%
“…The coefficients of the hyperelastic material used for the encapsulated soft tissue is C10=0.08556, C01=-0.0841, C11=-0.02319, C02=0.00851, D1 = 3.65273, D2=0. [11,25]. The data was obtained through an in vivo compression measurement with several cohorts and inverse parameter fitting, the model had been used in serval published biomechanical works [11,12,13].…”
Section: Materials Propertiesmentioning
confidence: 99%
“…[11,25]. The data was obtained through an in vivo compression measurement with several cohorts and inverse parameter fitting, the model had been used in serval published biomechanical works [11,12,13]. When D2=0, it represents full incompressibility.…”
Section: Materials Propertiesmentioning
confidence: 99%
“…The collision force of touching down is 1.5-3 times of the body weight [3]. Full contact was defined between the foot surface and the ground, with a surface to surface contact condition and the friction coefficient between foot plantar and the rigid plate was 0.6 [11,16,29].…”
Section: Boundary Loading Conditions and Convergence Studiesmentioning
confidence: 99%
“…FEM is commonly used in many biomechanical investigations with great success due to its ability to model complex material properties and irregular geometry as well as the capacity of simulating the internal stress in bones and tissue. Many published studies have focused on the foot stress under static standing load [11][12][13]. Stress in the bony foot structure was simulated during balance standing by Cheung noting a clear effect of the soft tissue stiffening and of the use of different types of foot support design [12,13], including the modelling of foot with medical conditions such as diabetic foot [14].…”
Due to the limitations of experimental approaches, comparison of the internal deformation and stresses of the human man foot between forefoot and rearfoot landing is not fully established. The objective of this work is to develop an effective FE modelling approach to comparatively study the stresses and energy in the foot during forefoot strike (FS) and rearfoot strike (RS). The stress level and rate of stress increase in the Metatarsals are established and the injury risk between these two landing styles is evaluated and discussed. A detailed subject specific FE foot model is developed and validated. A hexahedral dominated meshing scheme was applied on the surface of the foot bones and skin. An explicit solver (Abaqus/Explicit) was used to stimulate the transient landing process. The deformation and internal energy of the foot and stresses in the metatarsals are comparatively investigated. The results for forefoot strike tests showed an overall higher average stress level in the metatarsals during the entire landing cycle than that for rearfoot strike. The increase rate of the metatarsal stress from the 0.5 body weight (BW) to 2 BW load point is 30.76% for forefoot strike and 21.39% for rearfoot strike. The maximum rate of stress increase among the five metatarsals is observed on the 1st metatarsal in both landing modes. The results indicate that high stress level during forefoot landing phase may increase potential of metatarsal injuries.
“…Poisson's ratio=0.3) [23]. As in previous works [11] and other literatures [24], the stiffness of the Cartilage, Plantar Fascia and Ligament is set at 1, 350 and 250 MPa, respectively; the Poisson's ratio is set as 0.4. The phalanges are assumed to have the same material properties as the bones [16].…”
Section: Materials Propertiesmentioning
confidence: 99%
“…The coefficients of the hyperelastic material used for the encapsulated soft tissue is C10=0.08556, C01=-0.0841, C11=-0.02319, C02=0.00851, D1 = 3.65273, D2=0. [11,25]. The data was obtained through an in vivo compression measurement with several cohorts and inverse parameter fitting, the model had been used in serval published biomechanical works [11,12,13].…”
Section: Materials Propertiesmentioning
confidence: 99%
“…[11,25]. The data was obtained through an in vivo compression measurement with several cohorts and inverse parameter fitting, the model had been used in serval published biomechanical works [11,12,13]. When D2=0, it represents full incompressibility.…”
Section: Materials Propertiesmentioning
confidence: 99%
“…The collision force of touching down is 1.5-3 times of the body weight [3]. Full contact was defined between the foot surface and the ground, with a surface to surface contact condition and the friction coefficient between foot plantar and the rigid plate was 0.6 [11,16,29].…”
Section: Boundary Loading Conditions and Convergence Studiesmentioning
confidence: 99%
“…FEM is commonly used in many biomechanical investigations with great success due to its ability to model complex material properties and irregular geometry as well as the capacity of simulating the internal stress in bones and tissue. Many published studies have focused on the foot stress under static standing load [11][12][13]. Stress in the bony foot structure was simulated during balance standing by Cheung noting a clear effect of the soft tissue stiffening and of the use of different types of foot support design [12,13], including the modelling of foot with medical conditions such as diabetic foot [14].…”
Due to the limitations of experimental approaches, comparison of the internal deformation and stresses of the human man foot between forefoot and rearfoot landing is not fully established. The objective of this work is to develop an effective FE modelling approach to comparatively study the stresses and energy in the foot during forefoot strike (FS) and rearfoot strike (RS). The stress level and rate of stress increase in the Metatarsals are established and the injury risk between these two landing styles is evaluated and discussed. A detailed subject specific FE foot model is developed and validated. A hexahedral dominated meshing scheme was applied on the surface of the foot bones and skin. An explicit solver (Abaqus/Explicit) was used to stimulate the transient landing process. The deformation and internal energy of the foot and stresses in the metatarsals are comparatively investigated. The results for forefoot strike tests showed an overall higher average stress level in the metatarsals during the entire landing cycle than that for rearfoot strike. The increase rate of the metatarsal stress from the 0.5 body weight (BW) to 2 BW load point is 30.76% for forefoot strike and 21.39% for rearfoot strike. The maximum rate of stress increase among the five metatarsals is observed on the 1st metatarsal in both landing modes. The results indicate that high stress level during forefoot landing phase may increase potential of metatarsal injuries.
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