Abstract:To date, there has not been a direct examination of the effect that tissue composition (lean mass/muscle, fat mass, bone mineral content) differences between males and females has on how the tibia responds to impacts similar to those seen during running. To evaluate this, controlled heel impacts were imparted to 36 participants (6 M and 6 F in each of low, medium and high percent body fat [BF] groups) using a human pendulum. A skin-mounted accelerometer medial to the tibial tuberosity was used to determine the… Show more
“…The first set of three trials was applied using a human pendulum (Duquette & Andrews, 2010;Flynn, Holmes, & Andrews, 2004;Lafortune & Lake, 1995;Schinkel-Ivy et al, 2012), with participants securely strapped supine to the pendulum, and the right knee joint space aligned with the leading edge of the pendulum frame. The pendulum was manually pulled back a distance (between 50 and 65 cm) in order to achieve a velocity (linear voltage differential transformer attached to the pendulum; Celesco DV301, Don Mills, ON, Canada) of 1.0-1.15 m · s -1 and a force of 1.8-2.8 times body weight (Cavanagh & Lafortune, 1980;Duquette & Andrews, 2010;Flynn et al, 2004;Holmes & Andrews, 2006; Schinkel-Ivy, Burkhart, & Andrews, 2010).…”
Section: Methodsmentioning
confidence: 99%
“…However, Burkhart, Schinkel-Ivy, and Andrews (2013) identified a relationship between the soft tissue composition of the distal lower extremity and the development of lower extremity injuries in basketball, soccer and track and field athletes. In addition, Schinkel-Ivy et al (2012) found that the peak shock (measured as acceleration) at the tibial tuberosity was significantly affected by the mass of the tissues located in the distal lower extremity. Pain and Challis (2002) suggested that ignoring the role of soft tissue motion may limit our understanding of injury prevention strategies.…”
Section: Introductionmentioning
confidence: 97%
“…The movement of soft tissue masses (fat, muscle, skin) with respect to the underlying bone in the lower extremities is thought to serve a protective role during drop landings (Pain & Challis, 2006;Schinkel-Ivy, Burkhart, & Andrews, 2012), walking (Zelik & Kuo, 2010) and running (Cole, Nigg, Van Den Bogert, & Gerritsen, 1996) by attenuating potentially injurious impact forces. In many biomechanical analyses of such events, soft tissue movement relative to bone has been viewed as error (or soft tissue/motion artefact) and researchers typically quantify its magnitude and remove it from their data rather than studying its importance (Peters, Galna, Sangeux, Morris, & Baker, 2010).…”
Quantifying soft tissue motion following impact is important in human motion analysis as soft tissues attenuate potentially injurious forces resulting from activities such as running and jumping. This study determined the reliability of leg soft tissue position and velocity following heel impacts. A grid of black dots was applied to the skin of the right leg and foot (n = 20). Dots were automatically detected (ProAnalyst(®)) from high-speed records of pendulum and drop impacts. Three trained measurers selected columns of dots on each participant for analysis; one measurer 6 months later. Between- and within-measurer differences in kinematic variables were all relatively small (<0.8 cm for position; <3.7 cm/s for velocity) between-measurers and (<0.5 cm for position; <2.6 cm/s for velocity) within-measurer. Good (coefficients of variation (CV) ≤ 10%) to acceptable (CV > 10% and ≤20%) reliability was shown for 95% of the position measures, with mean CVs of 10% and 11% within-measurers and between-measures, respectively. Velocity measures were less reliable; 40% of the measures showed good to marginal (CV > 20% and ≤30%) reliability. This study established that leg soft tissue position data from skin markers could be obtained with good to acceptable reliability following heel impacts. Velocity data were less reliable but still acceptable in many cases.
“…The first set of three trials was applied using a human pendulum (Duquette & Andrews, 2010;Flynn, Holmes, & Andrews, 2004;Lafortune & Lake, 1995;Schinkel-Ivy et al, 2012), with participants securely strapped supine to the pendulum, and the right knee joint space aligned with the leading edge of the pendulum frame. The pendulum was manually pulled back a distance (between 50 and 65 cm) in order to achieve a velocity (linear voltage differential transformer attached to the pendulum; Celesco DV301, Don Mills, ON, Canada) of 1.0-1.15 m · s -1 and a force of 1.8-2.8 times body weight (Cavanagh & Lafortune, 1980;Duquette & Andrews, 2010;Flynn et al, 2004;Holmes & Andrews, 2006; Schinkel-Ivy, Burkhart, & Andrews, 2010).…”
Section: Methodsmentioning
confidence: 99%
“…However, Burkhart, Schinkel-Ivy, and Andrews (2013) identified a relationship between the soft tissue composition of the distal lower extremity and the development of lower extremity injuries in basketball, soccer and track and field athletes. In addition, Schinkel-Ivy et al (2012) found that the peak shock (measured as acceleration) at the tibial tuberosity was significantly affected by the mass of the tissues located in the distal lower extremity. Pain and Challis (2002) suggested that ignoring the role of soft tissue motion may limit our understanding of injury prevention strategies.…”
Section: Introductionmentioning
confidence: 97%
“…The movement of soft tissue masses (fat, muscle, skin) with respect to the underlying bone in the lower extremities is thought to serve a protective role during drop landings (Pain & Challis, 2006;Schinkel-Ivy, Burkhart, & Andrews, 2012), walking (Zelik & Kuo, 2010) and running (Cole, Nigg, Van Den Bogert, & Gerritsen, 1996) by attenuating potentially injurious impact forces. In many biomechanical analyses of such events, soft tissue movement relative to bone has been viewed as error (or soft tissue/motion artefact) and researchers typically quantify its magnitude and remove it from their data rather than studying its importance (Peters, Galna, Sangeux, Morris, & Baker, 2010).…”
Quantifying soft tissue motion following impact is important in human motion analysis as soft tissues attenuate potentially injurious forces resulting from activities such as running and jumping. This study determined the reliability of leg soft tissue position and velocity following heel impacts. A grid of black dots was applied to the skin of the right leg and foot (n = 20). Dots were automatically detected (ProAnalyst(®)) from high-speed records of pendulum and drop impacts. Three trained measurers selected columns of dots on each participant for analysis; one measurer 6 months later. Between- and within-measurer differences in kinematic variables were all relatively small (<0.8 cm for position; <3.7 cm/s for velocity) between-measurers and (<0.5 cm for position; <2.6 cm/s for velocity) within-measurer. Good (coefficients of variation (CV) ≤ 10%) to acceptable (CV > 10% and ≤20%) reliability was shown for 95% of the position measures, with mean CVs of 10% and 11% within-measurers and between-measures, respectively. Velocity measures were less reliable; 40% of the measures showed good to marginal (CV > 20% and ≤30%) reliability. This study established that leg soft tissue position data from skin markers could be obtained with good to acceptable reliability following heel impacts. Velocity data were less reliable but still acceptable in many cases.
“…For example, in comparison with rigid body models (representing bone) and wobbling mass models (representing rigid and soft tissues), the latter substantially reduced both external and internal loading (Gruber et al 1998;Liu and Nigg 2000;Pain and Challis 2001Gittoes et al 2006). Furthermore, Schinkel-Ivy et al (2012) found that greater shank tissue masses, specifically lean mass and bone mineral content, contributed to decreased acceleration responses measured at the proximal tibia following impact.…”
Section: Introductionmentioning
confidence: 93%
“…A human pendulum (, 13 kg; Flynn et al 2004;Holmes and Andrews 2006;Andrews 2010a, 2010b;Schinkel-Ivy et al 2012) was used to swing the participant towards a rigid impact apparatus. The participant was positioned supine on the pendulum with the left leg in full extension (knee joint line situated at the leading edge of the pendulum).…”
The purpose of this study was to determine whether modifying an existing, highly biofidelic full body finite element model [total human model for safety (THUMS)] would produce valid amplitude and temporal shock wave characteristics as it travels proximally through the lower extremity. Modifying an existing model may be more feasible than developing a new model, in terms of cost, labour and expertise. The THUMS shoe was modified to more closely simulate the material properties of a heel pad. Relative errors in force and acceleration data from experimental human pendulum impacts and simulated THUMS impacts were 22% and 54%, respectively, across the time history studied. The THUMS peak acceleration was attenuated by 57.5% and took 19.7 ms to travel proximally along the lower extremity. Although refinements may be necessary to improve force and acceleration timing, the modified THUMS represented, to a certain extent, shock wave propagation and attenuation demonstrated by living humans under controlled impact conditions.
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