The mechanism for interstitial fluid uptake into the lymphatics remains speculative and unresolved. A system of intralymphatic valves exists that prevents reflow along the length of the lymphatic channels. However, these valves are not sufficient to provide unidirectional flow at the level of the initial lymphatics. We investigate here the hypothesis that initial lymphatics have a second, separate valve system that permits fluid to enter from the interstitium into the initial lymph channels but prevents escape back out into the tissue. The transport of fluorescent microspheres (0.31 microm) across endothelium of initial lymphatics in rat cremaster muscle was investigated with micropipette manipulation techniques. The results indicate that microspheres can readily pass from the interstitium across the endothelium into the lumen of the initial lymphatics. Once inside the lymphatic lumen, the microspheres cannot be forced out of the lumen even after elevation of the lymphatic pressure by outflow obstruction. Reaspiration of the microspheres inside the lymphatic lumen with a micropipette is blocked by the lymphatic endothelium. This blockade exists whether the aspiration is carried out at the microsphere entry site or anywhere along the initial lymphatics. Nevertheless, puncture of the initial lymphatic endothelium with the micropipette leads to rapid aspiration of intralymphatic microspheres. Investigation of lymphatic endothelial sections fixed during lymph pumping shows open interendothelial junctions not found in resting initial lymphatics. These results suggest that initial lymphatics have a (primary) valve system at the level of the endothelium. In conjunction with the classical (secondary) intralymphatic valves, the primary valves provide the mechanism that facilitates the unidirectional flow during periodic compression and expansion of initial lymphatics.

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A detailed three-dimensional finite element model of the face is presented in this paper. Bones, muscles, skin, fat, and superficial muscoloaponeurotic system were reconstructed from magnetic resonance images and modeled according to anatomical, plastic, and reconstructive surgery literature. The finite element mesh, composed of hexahedron elements, was generated through a semi-automatic procedure with an effective compromise between the detailed representation of anatomical parts and the limitation of the computational time. Nonlinear constitutive equations are implemented in the finite element model. The corresponding model parameters were selected according to previous work with mechanical measurements on soft facial tissue, or based on reasonable assumptions. Model assumptions concerning tissue geometry, interactions, mechanical properties, and the boundary conditions were validated through comparison with experiments. The calculated response of facial tissues to gravity loads, to the application of a pressure inside the oral cavity and to the application of an imposed displacement was shown to be in good agreement with the data from corresponding magnetic resonance images and holographic measurements. As a first application, gravimetric soft tissue descent was calculated from the long time action of gravity on the face in the erect position, with tissue aging leading to a loss of stiffness. Aging predictions are compared with the observations from an "aging database" with frontal photos of volunteers at different age ranges (i.e., 20-40 years and 50-70 years).

The CellDrum technology (The term 'CellDrum technology' includes a couple of slightly different technological setups for measuring lateral mechanical tension in various types of cell monolayers or 3D-tissue constructs) was designed to quantify the contraction rate and mechanical tension of self-exciting cardiac myocytes. Cells were grown either within flexible, circular collagen gels or as monolayer on top of respective 1-mum thin silicone membranes. Membrane and cells were bulged outwards by air pressure. This biaxial strain distribution is rather similar the beating, blood-filled heart. The setup allowed presetting the mechanical residual stress level externally by adjusting the centre deflection, thus, mimicking hypertension in vitro. Tension was measured as oscillating differential pressure change between chamber and environment. A 0.5-mm thick collagen-cardiac myocyte tissue construct induced after 2 days of culturing (initial cell density 2 x 10(4) cells/ml), a mechanical tension of 1.62 +/- 0.17 microN/mm(2). Mechanical load is an important growth regulator in the developing heart, and the orientation and alignment of cardiomyocytes is stress sensitive. Therefore, it was necessary to develop the CellDrum technology with its biaxial stress-strain distribution and defined mechanical boundary conditions. Cells were exposed to strain in two directions, radially and circumferentially, which is similar to biaxial loading in real heart tissues. Thus, from a biomechanical point of view, the system is preferable to previous setups based on uniaxial stretching.

Fibroblast-populated collagen matrices provide a simplified tissue model for wound healing and development processes. A technology (CELLDRUM Technology) evaluating lateral mechanical tension in fibroblast-populated collagen matrices (tissue constructs) with a thickness of 1 mm was introduced. Defined mechanical boundary conditions together with the known number and orientation of the cells revealed precise data on the average tension exerted by a single cell. Circular cell-populated collagen gels were manufactured inside the CELLDRUM on top of a flexible membrane. The collagen matrix was then excited by a sound pulse. The resulting resonance oscillation was monitored by a laser-based deflection sensor and frequency and damping were analyzed giving information on mechanical properties of the tissue construct. Several evaluation experiments were performed. Calf serum enhanced contractile forces of fibroblasts dose dependently. After the gels were treated with cytochalasin D for 24 h, the cell forces were reduced by 42% of control. The remaining tension was attributed to the extracellular matrix remodeling occurring during cell growth and to other cytoskeletal structures like microtubules and intermediate filaments. We also found that only after a few hours of culture fibroblast-seeded collagen gels began developing significant mechanical tension. A mechanical tension profile of proliferating fibroblasts in collagen gels over culture time was obtained.

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A new technology to analyze mechanical properties of adherent cell monolayers grown on elastic silicon membranes is introduced. Measurements were performed using 3T3 (NIH) fibroblasts under the influence of Cytochalasin D and Thrombin. The stress-strain relation of the cell monolayer-silicon-composite was monitored. The drum-like construct of the culture chamber opens new roads for studying the mechanics of cell monolayers and of ultra flat tissue constructs. Steady state as well dynamic mechanical studies can be performed. Defined mechanical boundary conditions together with the known number and orientation of the cells allow precise information on the average tension exerted by a single cell within the monolayer.