Failure modes and fracture toughness in partially torn ligaments and tendons

Forell, Gregory A. Von; Hyoung, Peter; Bowden, Anton E.

doi:10.1016/j.jmbbm.2014.03.020

Cited by 24 publications

(17 citation statements)

References 36 publications

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“…It is well known that tissues tend to fail in specific ways that relate to their fiber orientation [13][14][15][16][17]. In this work, we demonstrated that a multiscale model with a simplified fiber-based failure algorithm could predict the crack propagation pattern in a double-notched sample, and that the model predictions were in agreement with experimental observations on collagen gels.…”

Section: Discussionsupporting

confidence: 75%

“…Dissection of an ascending thoracic aortic aneurysm, for example, tends to run along the z-h plane, delaminating the vessel wall between elastic layers [13,14], and the characteristic failure of the glomerular basement membrane in Alport syndrome has a similar delaminating quality [15]. The angle-ply structure of the annulus fibrosus is known to provide increased strength [16], and tendons and ligaments are extremely effective at resisting propagation of transverse tears [17]. The toughness of fiber composites is well established in nonbiological contexts, but translation of fiber-composite concepts to the failure of tissues containing a complex network of interacting fibers is by no means trivial.…”

Section: Introductionmentioning

confidence: 99%

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Crack Propagation Versus Fiber Alignment in Collagen Gels: Experiments and Multiscale Simulation

Vanderheiden

Hadi

Barocas

2015

Journal of Biomechanical Engineering

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It is well known that the organization of the fibers constituting a collagenous tissue can affect its failure behavior. Less clear is how that effect can be described computationally so as to predict the failure of a native or engineered tissue under the complex loading conditions that can occur in vivo. Toward the goal of a general predictive strategy, we applied our multiscale model of collagen gel mechanics to the failure of a double-notched gel under tension, comparing the results for aligned and isotropic samples. In both computational and laboratory experiments, we found that the aligned gels were more likely to fail by connecting the two notches than the isotropic gels. For example, when the initial notches were 30% of the sample width (normalized tip-to-edge distance ¼ 0.7), the normalized tip-to-tip distance at which the transition occurred from between-notch failure to across-sample failure shifted from 0.6 to 1.0. When the model predictions for the type of failure event (between the two notches versus across the sample width) were compared to the experimental results, the two were found to be strongly covariant by Fisher's exact test (p < 0.05) for both the aligned and isotropic gels with no fitting parameters. Although the double-notch system is idealized, and the collagen gel system is simpler than a true tissue, it presents a simple model system for studying failure of anisotropic tissues in a controlled setting. The success of the computational model suggests that the multiscale approach, in which the structural complexity is incorporated via changes in the model networks rather than via changes to a constitutive equation, has the potential to predict tissue failure under a wide range of conditions.

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Section: Discussionsupporting

confidence: 75%

Section: Introductionmentioning

confidence: 99%

Crack Propagation Versus Fiber Alignment in Collagen Gels: Experiments and Multiscale Simulation

Vanderheiden

Hadi

Barocas

2015

Journal of Biomechanical Engineering

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“…Wide opening and blunting of edge cracks, with no crack extension, has been previously observed in physical testing of tissue and scaffolds (Stok and Oloyede, 2003; Koh et al, 2013; Von Forell et al, 2014). Plastic inter-fibril sliding occurs in tendon (Szczesny and Elliott, 2014).…”

Section: Discussionmentioning

confidence: 55%

“…This test configuration was not included in the present work because it leaves the fibers unloaded, but it has been previously applied to spine ligament, tissue engineered cartilage, deep zone articular cartilage, and temporomandibular joint disc (Von Forell et al, 2014; Koombua et al, 2006; Von Forell et al, 2014; Oyen-Tiesma and Cook, 2001). Cracks did not extend in spine ligament (Von Forell et al, 2014), did extend in tissue engineered cartilage (Oyen-Tiesma and Cook, 2001), and also extended in a subset of articular cartilage specimens (Chin-Purcell and Lewis, 1996; Taylor et al, 2012). It was ambiguous whether the temporomandibular joint disc failed by fracture (Koombua et al, 2006; Taylor et al, 2012).…”

Section: Discussionmentioning

confidence: 99%

“…Taylor’s review of these studies indicated that most did not actually produce fracture (Taylor et al, 2012). Von Forell et al noted a lack of crack extension in their fracture tests of Achilles tendon and anterior longitudinal spine ligament (Von Forell et al, 2014). Although fracture is not necessarily a relevant failure mode for all fibrous tissues (Taylor et al, 2012), cracks in fibrocartilage clearly do grow in vivo.…”

Section: Introductionmentioning

confidence: 99%

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A comparison of stress in cracked fibrous tissue specimens with varied crack location, loading, and orientation using finite element analysis

Peloquin

Elliott

2016

Journal of the Mechanical Behavior of Biomedical Materials

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Cracks in fibrous soft tissue, such as the intervertebral disc annulus fibrosus and knee meniscus, cause pain and compromise joint mechanics. A crack concentrates stress at its tip, making further failure and crack extension (fracture) more likely. Ex vivo mechanical testing is an important tool for studying the loading conditions required for crack extension, but prior work has shown that it is difficult to reproduce crack extension. Most prior work used edge crack specimens in uniaxial tension, with the crack 90° to the edge of the specimen. This configuration does not necessarily represent the loading conditions that cause in vivo crack extension. To find a potentially better choice for experiments aiming to reproduce crack extension, we used finite element analysis to compare, in factorial combination, (1) center crack vs. edge crack location, (2) biaxial vs. uniaxial loading, and (3) crack-fiber angles ranging from 0° to 90°. The simulated material was annulus fibrosus fibrocartilage with a single fiber family. We hypothesized that one of the simulated test cases would produce a stronger stress concentration than the commonly used uniaxially loaded 90° crack-fiber angle edge crack case. Stress concentrations were compared between cases in terms of fiber-parallel stress (representing risk of fiber rupture), fiber-perpendicular stress (representing risk of matrix rupture), and fiber shear stress (representing risk of fiber sliding). Fiber-perpendicular stress and fiber shear stress concentrations were greatest in edge crack specimens (of any crack-fiber angle) and center crack specimens with a 90° crack-fiber angle. However, unless the crack is parallel to the fiber direction, these stress components alone are insufficient to cause crack opening and extension. Fiber-parallel stress concentrations were greatest in center crack specimens with a 45° crack-fiber angle, either biaxially or uniaxially loaded. We therefore recommend that the 45° center crack case be tried in future experiments intended to study crack extension by fiber rupture.

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Injectable Biomedical Devices for Sensing and Stimulating Internal Body Organs

et al. 2020

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The rapid pace of progress in implantable electronics driven by novel technology has created devices with unconventional designs and features to reduce invasiveness and establish new sensing and stimulating techniques. Among the designs, injectable forms of biomedical electronics are explored for accurate and safe targeting of deep‐seated body organs. Here, the classes of biomedical electronics and tools that have high aspect ratio structures designed to be injected or inserted into internal organs for minimally invasive monitoring and therapy are reviewed. Compared with devices in bulky or planar formats, the long shaft‐like forms of implantable devices are easily placed in the organs with minimized outward protrusions via injection or insertion processes. Adding flexibility to the devices also enables effortless insertions through complex biological cavities, such as the cochlea, and enhances chronic reliability by complying with natural body movements, such as the heartbeat. Diverse types of such injectable implants developed for different organs are reviewed and the electronic, optoelectronic, piezoelectric, and microfluidic devices that enable stimulations and measurements of site‐specific regions in the body are discussed. Noninvasive penetration strategies to deliver the miniscule devices are also considered. Finally, the challenges and future directions associated with deep body biomedical electronics are explained.

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Failure modes and fracture toughness in partially torn ligaments and tendons

Cited by 24 publications

References 36 publications

Crack Propagation Versus Fiber Alignment in Collagen Gels: Experiments and Multiscale Simulation

Crack Propagation Versus Fiber Alignment in Collagen Gels: Experiments and Multiscale Simulation

A comparison of stress in cracked fibrous tissue specimens with varied crack location, loading, and orientation using finite element analysis

Injectable Biomedical Devices for Sensing and Stimulating Internal Body Organs

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