A biomechanical model of anther opening reveals the roles of dehydration and secondary thickening.

Understanding the processes that underlie pollen release is a prime target for controlling fertility to enable selective breeding and the efficient production of hybrid crops. Pollen release requires anther opening, which involves changes in the biomechanical properties of the anther wall. In this research, we develop and use a mathematical model to understand how these biomechanical processes lead to anther opening. Our mathematical model describing the biomechanics of anther opening incorporates the bilayer structure of the mature anther wall, which comprises the outer epidermal cell layer, whose turgor pressure is related to its hydration, and the endothecial layer, whose walls contain helical secondary thickening, which resists stretching and bending. The model describes how epidermal dehydration, in association with the thickened endothecial layer, creates forces within the anther wall causing it to bend outwards, resulting in anther opening and pollen release. The model demonstrates that epidermal dehydration can drive anther opening, and suggests why endothecial secondary thickening is essential for this process (explaining the phenotypes presented in the myb26 and nst1nst2 mutants). The research hypothesizes and demonstrates a biomechanical mechanism for anther opening, which appears to be conserved in many other biological situations where tissue movement occurs.

Finite indentation of highly curved elastic shells.

Experimentally measuring the elastic properties of thin biological surfaces is non-trivial, particularly when they are curved. One technique that may be used is the indentation of a thin sheet of material by a rigid indenter, while measuring the applied force and displacement. This gives immediate information on the fracture strength of the material (from the force required to puncture), but it is also theoretically possible to determine the elastic properties by comparing the resulting force-displacement curves with a mathematical model. Existing mathematical studies generally assume that the elastic surface is initially flat, which is often not the case for biological membranes. We previously outlined a theory for the indentation of curved isotropic, incompressible, hyperelastic membranes (with no bending stiffness) which breaks down for highly curved surfaces, as the entire membrane becomes wrinkled. Here, we introduce the effect of bending stiffness, ensuring that energy is required to change the shell shape without stretching, and find that commonly neglected terms in the shell equilibrium equation must be included. The theory presented here allows for the estimation of shape- and size-independent elastic properties of highly curved surfaces via indentation experiments, and is particularly relevant for biological surfaces.

Cell adhesion and mechanical properties of a flexible scaffold for cardiac tissue engineering.

Cardiac tissue engineering is focused on obtaining functional cardiomyocyte constructs to provide an alternative to cellular cardiomyoplasty. Mechanical stimuli have been shown to stimulate protein expression and the differentiation of mammalian cells from contractile tissues. Our aim was to obtain a flexible scaffold which could be used to apply mechanical forces during tissue regeneration. Poly(1,8-octanediol-co-citric acid) (POC) is an elastomer that can be processed into scaffolds for tissue engineering. We investigated the effect of modifying the porosity on the mechanical properties of the POC scaffolds. In addition, the effects of the storage method and strain rate on material integrity were assessed. The maximum elongation of POC porous films varied from 60% to 160% of their original length. A decrease in the porosity caused a rise in this elastic modulus. The attachment of HL-1 cardiomyocytes to POC was assessed on films coated with fibronectin, collagen and laminin. These extracellular matrix proteins promoted cell adhesion in a protein-type- and concentration-dependent manner. Therefore, POC scaffolds can be optimised to meet the mechanical and biological parameters needed for cardiac culture. This porous material has the potential to be used for cardiac tissue engineering as well as for other soft tissue applications.

Knoop microhardness anisotropy of the ovine radius.

The Knoop indenter has been used to characterise fully the Knoop microhardness (H(K)) anisotropy of compact bone. 2120 indentations were performed on mature ovine radii and a linear relationship was found between H(K) and the angle between the major diagonal of the indenter and the lamella boundaries (p<<0.001). H(K) increased significantly with ash fraction (p<0.001), but decreased with atmospheric vapour pressure (p<0.05). A significant interaction was found between ash fraction and atmospheric vapour pressure (p<0.01). H(K) significantly varied with indentation position along the diaphysis and around the cortex (both p<<0.001), however radial variation in H(K) was not statistically significant. The variation of ash fraction showed similar trends. These data show that H(K) varies similarly to Vickers microhardness, but in addition, can provide clear information on the anisotropy of Haversian bone without the need for excising many different indentation planes. A large number of indentations are required to obtain low type I and type II errors in the statistical analysis.

Microhardness anisotropy of lamellar bone.

The Knoop microhardness test has been utilised to observe in-plane microhardness anisotropy of rat tibiae. The elongated rhombohedral geometry of the Knoop indenter enables the Knoop microhardness (HK) to be calculated for a given indenter orientation. Two indenter orientations were used: the major axis of the indenter was aligned along the length of, and across the mid-sagittal section. The statistical analysis demonstrated that the variation in HK was primarily due to the orientation of the Knoop indenter (p < 0.001). HK was consistently greater when the indenter was aligned with the major diagonal radial on the mid-sagittal section.