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EN
Micropatterned surfaces were created by UV light-irradiation of polytetrafluoroethylene through a metallic mask, by successive plasma polymerization of acrylic acid and 1,7-octadiene, or by creation of prominences and grooves by deposition of fullerenes C60 through a metallic mask. All these surface types were capable of inducing regionally-selective adhesion, proliferation and phenotypic maturation of vascular endothelial cells, vascular smooth muscle cells or human bone-derived MG 63 cells. Nanopatterned surfaces created by tethering GRGDSG oligopeptides through polyethylene oxide chains on a polymeric surface promoted spreading, formation of focal adhesion plaques and DNA synthesis in vascular smooth muscle cells. Surfaces nanopatterned with nanocrystalline diamond gave good support for the adhesion, growth and metabolic activity of osteoblast-like MG 63 cells.
EN
The tested materials were represented by a pure terpolymer of polytetrafluorethylene-polyvinyldifluoride-polypropylene (PTFE-PVDF-PP), pure polysulphone (PSU) and PSU modified with single- or multiwalled carbon nanotubes in concentrations of 0.5, 1 or 2 wt%. As control samples, a polystyrene cell culture dish and microscopic glass coverslips were used. The number and viability of human osteoblast-like MG 63 cells in cultures on these materials was detected with a Cell Viability Analyzer (Vi-CELL XR, Beckman Coulter) on 1, 3 and 7 days after seeding. On all tested samples, the cell number was similar or lower than that detected on the control polystyrene dishes. The cell viability on day 1 after seeding was relatively low on PTFE-PVDF-PP and some nanotube-containing samples, ranging from 10 to 100% of living cells, but on day 7 after seeding, it reached at least 90% on all tested samples. The cell spreading area was detected in cells after immunocytochemical staining of beta-actin on day 3 after seeding. In nanotube-containing samples, especially those with multi-walled nanotubes, this area was similar or even larger than that on the control materials. The beta-actin cytoskeleton was well developed in cells on all nanotube-containing materials and similar to that in cells on control surfaces. Thus, it can be concluded that nanotube-containing PSU supports the adhesion and growth of osteoblast-like cells and could be used for construction of bone implants in which the anchorage in the surrounding bone tissue is desirable.
EN
A series of metallic materials with different surface treatments were prepared: pure machined titanium (T), titanium polished by diamond paste (TL), machined Ti6Al4V alloy (TS), Ti6Al4V alloy polished by diamond paste (TSL), Ti5Al2.5Fe alloy treated by electro-erosion (A) and Ti5Al2.5Fe plasma-sprayed with Ti (PL). The materials were seeded with human osteoblast-like cells MG 63. One day after seeding, the highest cell numbers were obtained on the samples of medium surface roughness (T and TS; Ra 0.63-0.30 um and 0.89-0.57 um, respectively). From day 1 to 4, the cell proliferation was the quickest on the samples with the lowest surface roughness (TL and TSL; Ra 0.17-0.13 for both materials). The cells on TL also contained the highest concentration of integrin adhesion molecules with alpha V chain, i.e. receptors for vitronectin and fibronectin. One day 8 after seeding, the cell on all metallic samples as well as tissue culture polystyrene reached similar population densities. The cells on electro-eroded Ti5Al2.5Fe (samples A; Ra 15.27-0.74 um) contained the highest concentration of osteocalcin and osteopontin, i.e. markers of osteoblastic differentiation. Thus, the latter newly developed material could be considered as promising for construction of bone implants well anchored in the surrounding bone tissue.
EN
In this study we have investigated the effect of three groups of polymeric foils on the behavior of MG 63 osteoblast-like cells. These included (1) poly(L-lactide) (PLLA) compared with newly synthesized copolymer of L-lactide and trimethylene carbonate (PLTMC 50:50), (2) three samples made of glycolide and epsylon-caprolactone copolymer (PGCap) with different surface roughness and topography, and finally (3) copolymer of glycolide with L-lactide (PGLA) compared with its modification with hyroxyapatite deposits. On the 1st and 4th day of cultivation the cell number on all of the samples was lower than on control polystyrene culture dish. However, on day 8 after seeding, the values on the tested samples caught up with the control polystyrene. In the first group the cell number of PLTMC was higher than on polystyrene or PLLA. In the second group, the number of cells on PGCap samples of the lower surface roughness (RRMS 130 and 180 nm) was significantly higher than that on the control polystyrene, whereas on the PGCap samples with the rounghness in micrometers, it was comparable to the value on the polystyrene. Moreover, the surface roughness influenced the cell adhesion area. The cells on the sample with the highest roughness index were roundly shaped and their adhesion area was significantly lower, because the cells were restricted in their spreading by the surface structure of the material. In the last group, the number of cells on day 8 on the polymer with hydroxyapatite deposits was significantly higher than on standard tissue culture polystyrene dish, as well as on unmodified PGLA foil, which suggested that hydroxyapatite supports cell proliferation.
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