Development of a continuum mechanics model of passive skeletal muscle

Skeletal muscle force evaluation is difficult to implement in a clinical setting. Muscle force is typically assessed through either manual muscle testing, isokinetic/isometric dynamometry, or electromyography (EMG). Manual muscle testing is a subjective evaluation of a patient’s ability to move voluntarily against gravity and to resist force applied by an examiner. Muscle testing using dynamometers adds accuracy by quantifying functional mechanical output of a limb. However, like manual muscle testing, dynamometry only provides estimates of the joint moment. EMG quantifies neuromuscular activation signals of individual muscles, and is used to infer muscle function. Despite the abundance of work performed to determine the degree to which EMG signals and muscle forces are related, the basic problem remains that EMG cannot provide a quantitative measurement of muscle force. Intramuscular pressure (IMP), the pressure applied by muscle fibers on interstitial fluid, has been considered as a correlate for muscle force. Numerous studies have shown that an approximately linear relationship exists between IMP and muscle force. A microsensor has recently been developed that is accurate, biocompatible, and appropriately sized for clinical use. While muscle force and pressure have been shown to be correlates, IMP has been shown to be non-uniform within the muscle. As it would not be practicable to experimentally evaluate how IMP is distributed, computational modeling may provide the means to fully evaluate IMP generation in muscles of various shapes and operating conditions. The work presented in this dissertation focuses on the development and validation of computational models of passive skeletal muscle and the evaluation of their performance for prediction of IMP. A transversly isotropic, hyperelastic, and nearly incompressible model will be evaluated along with a poroelastic model.

Biomechanics of meniscal horn attachments

Menisci are anchored to the tibia by means of ligament-like structures called meniscal attachments. Failure material properties of bovine meniscal attachments were obtained. There were no significant differences in the structural properties or ultimate stress between the meniscal attachments (p>0.05). Furthermore, Glycosaminoglycan (GAG) fraction and crimping frequency was obtained for each attachment using histology and differential interference contrast (DIC) respectively. Results showed that the anterior attachment’s insertion had the greatest GAG fraction when compared to the posterior attachment’s insertion. Crimp frequency of the collagen fibrils was homogeneous along the length. Moreover, Scanning Electron Microscopy (SEM) technique was used to reveal the morphology of collagen in human meniscal attachments. Its midsubstance was composed of collagen fascicles running parallel to the longitudinal axis, with a few fibrils running obliquely, and others transversely. There were no differences between attachments for crimping angle or length. Since ligamentous-type tissues are comprised mainly of water, the fluid pressure within meniscal horn attachments was measured using a Fiber Optic Microsensor (FOM). Four cadaveric human joints were subjected to 2BW compressive load (ramp) at 0-, 15-, and 30-degrees of flexion for a minute and then the load was hold for 20 minutes (equilibrium). There were significant differences between 0- and 15- (p1– c5) were obtained. Significant differences were found on the straightened collagen fibers coefficient (c5) between MP and LA attachments (p