|
68
|
Amine (NH2), octyl (CH3) |
Ti6Al4V |
Mouse fibroblast L929 cells, Staphylococcus aureus, Escherichia coli
|
Hydrophobic octyl surfaces (1035 ± 38 ng cm−2) showed the maximum adsorption of bovine serum albumin (BSA) |
| Hydrophilic COOH surfaces (647 ± 38 ng cm−2) showed the maximum adsorption of fibronectin (FN) |
| Hybrid surfaces showed the maximum cell adhesion (%) and proliferation, larger nuclei area and the least cell circularity |
| Cells exhibited higher proliferation rate on all the modified surfaces as compared to unmodified Ti6Al4V, suggesting good cytocompatibility |
|
69
|
Silanization |
Silicon wafers |
Serum, saliva |
The modified materials that span a broad range of physicochemical properties, from hydrophilic to hydrophobic surfaces (water contact angles from 15° to 115°), negative to positive surface charge (zeta potentials from −120 to +40 mV at physiologic pH) |
| The chemical surface functionalities exerted a substantial effect on the total amounts of proteins adsorbed |
|
71
|
Different chemical groups (–OH, –OEG, –COOH, –NH2, and –PO3H2) |
Gold slides |
Recombinant mouse osteopontin (OPN), mouse bonemarrow mesenchymal stem cells (mBMSCs) |
The amount of adsorbed OPN was highest on SAMs-NH2 (89.01 ± 13.62 ng cm−2) and lowest on SAMs-OEG (3.39 ± 0.63 ng cm−2) |
| Cells on SAMs-COOH, SAMs-NH2, and SAMs-PO3H2 with pre-adsorbed OPN showed larger spreading, better viabilities, and higher expression levels of αv/β3 genes |
| OPN on SAMs-COOH, SAMs-NH2, and SAMs-PO3H2 exhibited higher bioactivity |
|
77
|
Thioctic acid-functionalized dendritic polyglycerol sulfate (dPGS) |
Gold-coated sensors |
Blood proteins albumin (Alb) and fibrinogen (Fib) |
Compared to non-sulfated dPG, dPGS showed enhanced protein adsorption driven by ionic interactions and enhanced cellular uptake via the formed protein corona |
| The formation of densely packed protein layers in case of Fib and a more loosely packed protein layer in case of Alb |
|
80
|
Self-assembled monolayer of phosphonates (SAMPs) |
Silicon dioxide (SiO2) |
Chondrocytes |
Chondrocytes attach to the modified surface, without substantial changes in gene expression SAMPs modification to SiO2 increased chondrocyte adhesion by 3× after 4 h and 4.5× after 24 h |
|
81
|
[(3-Aminopropyl)triethoxysilae (APTES), and octadecyltrimethoxysilane (OTS)], amino acid (histidine and leucine)-conjugated |
Poly(dimethylsiloxane) (PDMS) |
Induced pluripotent stem cells (iPSCs) |
Modified surfaces were found to be hydrophilic |
| PDMS surface chemical properties were enhanced for the differentiation of iPSCs into cardiomyocytes |
| All SAM-modified surfaces increased the number of viable iPSCs, when compared to native PDMS |
|
84
|
ω-(Ethylene glycol)2–4- and ω-(GRGDS)-, α-benzamidinobolaamphiphiles |
Gold |
MC3T3-E1 cells |
Modified surfaces can be used to reverse cell adhesion in a noninvasive manner |
| A versatile tool to study and control cell adhesion and differentiation |
|
85
|
Antimicrobial peptides (AMPs), elastin-like recombinamers (ELRs) |
Gold sputtered cover glasses |
S. aureus ATCC 25923, S. epidermidis ATCC 35984 |
The multifunctional SAMs exhibit protein anti-fouling activity |
| Strong anti-biofilm activity and cytocompatibility of these coatings was demonstrated |
|
86
|
Chitosan layer |
Polyetheretherketone (PEEK) |
MC3T3-E1, Gram-negative P. gingivalis, Gram-positive S. mutans
|
The inclusion of chitosan on the surface of PEEK-CS increased fibronectin adherence, enhancing the adhesion, proliferation, and differentiation of MC3T3-E1 subclone 14 cells substantially |
| Modified PEEK surfaces demonstrated decreased adhesion force to P. gingivalis, and less initial bacterial adhesion to P. gingivalis and S. mutans
|
