Abstract:Summary
A finite element model of donkey hoof wall was constructed from measurements taken directly from the hoof capsule of the left forefoot. The model was created with a 2 mm mesh and consisted of 11608 nodes. A linear elastic analysis was conducted assuming isotropic material properties in response to a 375 newton (N) load, to simulate static loading. The load was applied to the wall via 400 laminae in order to simulate the way in which the pedal bone is suspended within the donkey hoof capsule. Displaceme… Show more
“…Previous FE models of the hoof capsule (wall and sole and frog in some cases) have shown that the general pattern of deformation and displacement of the models are in broad agreement with experimentally derived data (Hinterhofer et al 1997(Hinterhofer et al , 2000Newlyn et al 1998). The models all showed palmar movement of the toe, with abaxial flare of the quarters and heels, as seen in vivo (Lungwitz 1891;Roepstorff et al 2001).…”
Section: Introductionsupporting
confidence: 62%
“…The models all showed palmar movement of the toe, with abaxial flare of the quarters and heels, as seen in vivo (Lungwitz 1891;Roepstorff et al 2001). Magnitudes of displacement of specific regions of the wall were also plausible (Newlyn et al 1998). The models used here have been shown to deform and displace accurately (H. L. McClinchey et al, unpublished data).…”
Summary
Finite‐element (FE) methods have great potential in equine biomechanics in evaluating mechanical stresses and strains in tissues deep within the hoof. In this study, we critically assessed that potential by comparing results of FE analyses of capsular strain with in vivo data. Nine FE models were developed, corresponding to the shape of hooves for which in vivo principal strain data are available. Each model had the wall, laminarjunction, sole and distal phalanx (PIII). In a first loading condition (LC1), force is distributed uniformly to the bearing surface of the wall to determine reaction forces and moment on PIII. These reaction forces were subsequently applied to PIII in loading condition 2 (LC2) to simulate loading via the skeleton. Magnitude of the force resultant was equivalent to the vertical force on the hoof at midstance. Principal compressive strains ε2 were calculated at the locations of 5 rosette gauges on the real hooves and are compared with the in vivo strains at midstance.
FE strains were from 16 to 221% of comparable in vivo values, averaging 104%. All models in this, and reports by other workers, show predominance of stress and strain at the toe to a greater extent than in the real hoof. The primary conclusion is that FE modelling of strain in the hoof capsule or deeper tissues of individual horses should not be attempted without corroborating experimental data.
“…Previous FE models of the hoof capsule (wall and sole and frog in some cases) have shown that the general pattern of deformation and displacement of the models are in broad agreement with experimentally derived data (Hinterhofer et al 1997(Hinterhofer et al , 2000Newlyn et al 1998). The models all showed palmar movement of the toe, with abaxial flare of the quarters and heels, as seen in vivo (Lungwitz 1891;Roepstorff et al 2001).…”
Section: Introductionsupporting
confidence: 62%
“…The models all showed palmar movement of the toe, with abaxial flare of the quarters and heels, as seen in vivo (Lungwitz 1891;Roepstorff et al 2001). Magnitudes of displacement of specific regions of the wall were also plausible (Newlyn et al 1998). The models used here have been shown to deform and displace accurately (H. L. McClinchey et al, unpublished data).…”
Summary
Finite‐element (FE) methods have great potential in equine biomechanics in evaluating mechanical stresses and strains in tissues deep within the hoof. In this study, we critically assessed that potential by comparing results of FE analyses of capsular strain with in vivo data. Nine FE models were developed, corresponding to the shape of hooves for which in vivo principal strain data are available. Each model had the wall, laminarjunction, sole and distal phalanx (PIII). In a first loading condition (LC1), force is distributed uniformly to the bearing surface of the wall to determine reaction forces and moment on PIII. These reaction forces were subsequently applied to PIII in loading condition 2 (LC2) to simulate loading via the skeleton. Magnitude of the force resultant was equivalent to the vertical force on the hoof at midstance. Principal compressive strains ε2 were calculated at the locations of 5 rosette gauges on the real hooves and are compared with the in vivo strains at midstance.
FE strains were from 16 to 221% of comparable in vivo values, averaging 104%. All models in this, and reports by other workers, show predominance of stress and strain at the toe to a greater extent than in the real hoof. The primary conclusion is that FE modelling of strain in the hoof capsule or deeper tissues of individual horses should not be attempted without corroborating experimental data.
“…This is an important finding when considering corrective farriery based on the position of the distal phalanx within the hoof capsule. During the stance phase, the two main hoof deformations are horizontal spreading of the heels away from each other and bowing‐ in of the dorsal hoof wall . It appears that the load variation induced by a variation in stance alone is not enough to cause change in the position of the distal phalanx.…”
Hoof balance radiographs are commonly used as the basis for corrective farriery decision-making in horses, however there are limited published data quantifying effects of the stance of the horse or the horizontal radiographic beam angle. In this analytical study, the influence of variation of the horse's stance in the craniocaudal and lateromodial plane on hoof balance measurements as well as the influence of variation of the horizontal radiographic beam angle on dorsopalmar hoof balance measurements was examined. Distal left thoracic limb lateromedial radiographs were acquired using a standardized protocol while varying the craniocaudal stance of five horses, each selected to be sound and conformationally normal. Dorsopalmar foot radiographs were acquired while varying the lateromedial stance; and variable angle horizontal beam dorsopalmar foot radiographs were acquired while keeping the limb position constant. Analyses of measurements demonstrated that hoof pastern angle had a linear relationship (R = 0.89, P < 0.001) with craniocaudal stance of the horse. The relationship of joint angle and stance was greater for the distal interphalangeal joint angle (R = 0.89, P < 0.001) than the proximal interphalangeal joint angle (R = 0.65, P = 0.001). The distal phalanx angle did not change with craniocaudal stance variation. The proximal interphalangeal joint width, distal interphalangeal joint width, or distal phalanx height did not change with lateromedial stance variation, nor within a 15 degree dorsolateral to caudomedial and dorsomedial to caudolateral variation from the dorsopalmar axis. Findings indicated that positioning of the thoracic limb needs to be considered during radiographic interpretation and decision-making for corrective farriery.
“…The finite element method (Newlyn et al 1998;Hinterhofer et al 2001) was presented to simulate mechanics of a donkey and a horse digit model. A different computational distal forelimb model was presented to investigate strains in the flexor tendons (Chan and Lawson 2008), concluding that the high repeatability of the model is an indicator for its sensitivity.…”
Section: Oral Session 3: Measurement Techniques Limb and Trunk Mechamentioning
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