High strain rate compressive properties of bovine muscle tissue determined using a split Hopkinson bar apparatus

Sligtenhorst, Caleb Van; Cronin, Duane S.; Brodland, G. Wayne

doi:10.1016/j.jbiomech.2005.05.015

Cited by 108 publications

(76 citation statements)

References 17 publications

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“…Further, Figure 4 shows that the SHPB experimental true stressstrain curve actually measures the first invariant of stress, rather than the uniaxial loading-direction stress-strain behavior. While most other studies [12][13][14][15][16][17][18] simply present the experimental results, Figure 3 shows that such a representation of the mechanical response of a biomaterial would underestimate the uniaxial response, which is relevant for FE modeling simulation of real world boundary value problems (BVPs). Hence, a use of the SHPB experimental result alone would be erroneous if it not coupled with FE-type modeling to assess the uniaxial behavior.…”

Section: Representative Resultsmentioning

confidence: 99%

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A Coupled Experiment-finite Element Modeling Methodology for Assessing High Strain Rate Mechanical Response of Soft Biomaterials

Prabhu

Whittington

Patnaik

et al. 2015

JoVE

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This study offers a combined experimental and finite element (FE) simulation approach for examining the mechanical behavior of soft biomaterials (e.g. brain, liver, tendon, fat, etc.) when exposed to high strain rates. This study utilized a Split-Hopkinson Pressure Bar (SHPB) to generate strain rates of 100-1,500 sec -1. The SHPB employed a striker bar consisting of a viscoelastic material (polycarbonate). A sample of the biomaterial was obtained shortly postmortem and prepared for SHPB testing. The specimen was interposed between the incident and transmitted bars, and the pneumatic components of the SHPB were activated to drive the striker bar toward the incident bar. The resulting impact generated a compressive stress wave (i.e. incident wave) that traveled through the incident bar. When the compressive stress wave reached the end of the incident bar, a portion continued forward through the sample and transmitted bar (i.e. transmitted wave) while another portion reversed through the incident bar as a tensile wave (i.e. reflected wave). These waves were measured using strain gages mounted on the incident and transmitted bars. The true stress-strain behavior of the sample was determined from equations based on wave propagation and dynamic force equilibrium. The experimental stress-strain response was three dimensional in nature because the specimen bulged. As such, the hydrostatic stress (first invariant) was used to generate the stress-strain response. In order to extract the uniaxial (one-dimensional) mechanical response of the tissue, an iterative coupled optimization was performed using experimental results and Finite Element Analysis (FEA), which contained an Internal State Variable (ISV) material model used for the tissue. The ISV material model used in the FE simulations of the experimental setup was iteratively calibrated (i.e. optimized) to the experimental data such that the experiment and FEA strain gage values and first invariant of stresses were in good agreement. Video LinkThe video component of this article can be found at

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Section: Representative Resultsmentioning

confidence: 99%

“…Previous studies have shown that SHPB testing has three major flaws associated with it [12][13][14][15][16][17][18] . The first and most significant one is the material inertial effect, which shows up in the high strain rate mechanical response of a biomaterial specimen as an initial spike.…”

Section: Background On Split-hopkinson Pressure Bar (Shpb) and Internmentioning

confidence: 99%

A Coupled Experiment-finite Element Modeling Methodology for Assessing High Strain Rate Mechanical Response of Soft Biomaterials

Prabhu

Whittington

Patnaik

et al. 2015

JoVE

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“…• Time post-mortem prior to testing: Van Sligtenhorst et al (2006) showed that there was a significant difference in the mechanical properties of specimens 1.5 and 3.5 hours post mortem when compared to specimens 5,6,7,9 and 27 hours post-mortem; this was largely supported by Van Loocke et al (2006) who suggested that dehydration of tissues may lead to an increased stiffness.…”

Section: Structure and Composition Of Organic Muscle Tissuementioning

confidence: 97%

“…Consequently, very few studies presented are of human tissues (Chawla et al, 2009;Balaraman et al, 2012). Much more of the muscle characterisation research published being obtained from testing on more accessible organic animal specimens such as bovine (McElhaney, 1966;Van Sligtenhorst et al, 2006) or porcine sources (Song et al, 2007;Van Loocke et al, 2006, 2009. It is suggested that these tissues exhibit anatomically and biologically similar structures to humans (Douglas, 1972;Snedeker et al, 2005).…”

Section: Structure and Composition Of Organic Muscle Tissuementioning

confidence: 99%

“…McElhaney (1966) conducted a seminal study characterising in vitro bovine tissues around the femur in uniaxial compression using both a Tinius-Olsen electromatic test machine and an air operated test machine for tests at low and high strain rates respectively. In recent years, authors have typically investigated the high strain rate response of soft tissues using a polymeric Split Hopkinson Pressure Bar (SHPB), capable of testing in the order of 10 3 s -1 (Van Sligtenhorst et al, 2006;Song et al, 2007;Chawla et al, 2009;Balaraman et al, 2012). There is, however, a paucity of information conducted under intermediate strain rate conditions in a similar range to those expected in sports impact scenarios (approximately 50-500s -1 ), based on a maximal velocity projectile impact from a cricket ball of 34.6ms -1 (Penrose et al, 1976).…”

Section: Structure and Composition Of Organic Muscle Tissuementioning

confidence: 99%

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Development of novel synthetic muscle tissues for sports impact surrogates

Payne

Mitchell

Bibb

et al. 2015

Journal of the Mechanical Behavior of Biomedical Materials

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Impact injuries are commonplace in sport and often lead to performance detriment and debilitation. Personal Protective Equipment (PPE) is prescribed as a mandatory requirement in most sports where these impacts are likely to occur, though the methods of governance and evaluation criteria often do not accurately represent sports specific injury scenarios. One of the key shortcomings of such safety test standards is the human surrogate to which the PPE is affixed; this typically embodies unrepresentative geometries, masses, stiffness and levels of constraint when compared to humans.A key aspect of any human surrogate element is the simulant material used. Most previous sports specific surrogates tend to use off-the-shelf silicone blends to represent all the soft tissue structures within the human limb segment or organ; this approach potentially neglects important human response phenomena caused by the different tissue structures.This study presents an investigation into the use of bespoke additive cure Polydimethysiloxane (PDMS) silicone blends to match the reported mechanical properties of human relaxed and contracted skeletal muscle tissues. The silicone simulants have been tested in uniaxial compression through a range of strain rates and fit with a range of constitutive hyperelastic models (Mooney Rivlin, Ogden and Neo Hookean) and a viscoelastic Prony series.

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Head and brain response to blast using sagittal and transverse finite element models

Singh

Cronin

Haladuick

2013

Numer Methods Biomed Eng

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Mild traumatic brain injury caused by blast exposure from Improvised Explosive Devices has become increasingly prevalent in modern conflicts. To investigate head kinematics and brain tissue response in blast scenarios, two solid hexahedral blast-head models were developed in the sagittal and transverse planes. The models were coupled to an Arbitrary Lagrangian-Eulerian model of the surrounding air to model blast-head interaction, for three blast load cases (5 kg C4 at 3, 3.5 and 4 m). The models were validated using experimental kinematic data, where predicted accelerations were in good agreement with experimental tests, and intracranial pressure traces at four locations in the brain, where the models provided good predictions for frontal, temporal and parietal, but underpredicted pressures at the occipital location. Brain tissue response was investigated for the wide range of constitutive properties available. The models predicted relatively low peak principal brain tissue strains from 0.035 to 0.087; however, strain rates ranged from 225 to 571 s-1. Importantly, these models have allowed us to quantify expected strains and strain rates experienced in brain tissue, which can be used to guide future material characterization. These computationally efficient and predictive models can be used to evaluate protection and mitigation strategies in future analysis.

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High strain rate compressive properties of bovine muscle tissue determined using a split Hopkinson bar apparatus

Cited by 108 publications

References 17 publications

A Coupled Experiment-finite Element Modeling Methodology for Assessing High Strain Rate Mechanical Response of Soft Biomaterials

A Coupled Experiment-finite Element Modeling Methodology for Assessing High Strain Rate Mechanical Response of Soft Biomaterials

Development of novel synthetic muscle tissues for sports impact surrogates

Head and brain response to blast using sagittal and transverse finite element models

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