| Leukers et al. (2005) |
HA |
DP+ Sintered |
In vitro |
MC3T3-E1 |
7 days |
The cells proliferated deep into the structure forming close contact HA granules. |
| Williams et al. (2005) |
PCL |
SLS |
In vitro In vivo |
BMP7 transduced HGF, Mice |
4 weeks |
SLS printed PCL scaffolds enhance bone tissue in-growth. |
| Mapili et al. (2005) |
PEGDMA |
SLA |
In vitro |
Acryl-PEG-RGD |
24 h |
Heparan sulfate allows efficient cell attachment and spatial localization of growth factors. |
| Arcaute, Mann & Wicker (2006) |
PEGDMA |
SLA |
In vitro |
Human dermal fibroblasts |
24 h |
Cell viability reaches at least 87% at 2 h and 24 h following fabrication. |
| Li et al. (2007) |
epoxy resin (SL, 7560, Huntsman); CPC(scaffold) |
SLA |
In vitro |
OB |
7 days |
Negative molds were generated by SLA. Cell density increased. |
| Khalyfa et al. (2007) |
TCP/TTCP |
3DP, Sintered, polymer infiltration |
In vitro |
MC3T3-E1 |
3 weeks |
Objects with high compression strengths are obtained without sintering. Cell proliferation and osteogenic differentiation are achieved. |
| Goodridge et al. (2007) |
|
SLS |
In vivo |
Rabbit tibiae |
4 weeks |
Bone was seen to have grown into the porous structure of the laser-sintered parts. |
| Habibovic et al. (2008) |
Bioceramic |
3DP |
In vivo |
12 adult Dutch milk goats |
12 weeks |
Bone formation within the channels of both monetite and brushite, indicate osteoinductivity of the materials. |
| Lee et al. (2008) |
PPF/DEF |
SLA |
In vitro |
Fibroblasts |
1 week |
Cells were adhering to and had proliferated at the top surface of the scaffold. |
| Geffre et al. (2009) |
Polymer (NG) |
FDM |
In vivo |
Femoral condyles (animal NG) |
5 months |
Biomimetic porous design largely enhances bone ingrowth. |
| Lan et al. (2009) |
PPF/DEF |
SLA |
In vitro |
MC3T3-E1 |
2 weeks |
MC3T3 pre-osteoblast compatibility with PPF/DEF scaffolds is greatly enhanced with biomimetic apatite coating |
| Fedorovich et al. (2009) |
photosensitive hydrogel (Lutrol) |
Hydrogel extrusion, UV |
In vitro |
MSCs |
3 weeks |
MSCs embedded in photopolymerizable Lutrol-TP gels remain viable of 60% and keep potential of osteogenic differentiation. |
| Zigang et al. (2009) |
PLGA/PVA |
3DP |
In vitro |
Human Osteoblasts CRL-11372 |
3 weeks |
Expression of ALP and osteonectin remain stable whilst collagen type I and osteopontin decrease. |
| Ge et al. (2009) |
PLGA/PVA |
3DP |
In vivo |
Rabbit: 1 intra-periosteum model. 2 bone defect of Ilium. |
24 weeks |
In both models, the implanted scaffolds facilitated new bone tissue formation and maturation. |
| Duan & Wang (2010) |
Customized Ca–P/PHBV |
SLS |
In vitro |
SaOS-2, C3H10T1/2 cells |
3 weeks |
Affinity of rhBMP2 on immobilized heparin facilitated the osteogenic differentiation of C3H10T1/2 cells during the whole period. |
| Warnke et al. (2010) |
TCP, HAP |
3DP+ Sintered |
In vitro |
Primary human osteoblasts. |
1 week |
Superior biocompatibility of HAP scaffolds to BioOss@ is proved, while BioOss@ is more compatible than TCP. |
| Melchels, Feijen & Grijpma (2010) |
poly(D,L-lactide) resin |
SLA |
In vitro |
MC3T3 |
11 days |
Pre-osteoblasts showed good adherence to these photo-crosslinked networks. |
| Detsch et al. (2011) |
HA, TCP, HA/TCP |
3DP |
In vitro |
RAW 264.7 cell line |
|
21 days The results show that osteoclast-like cells were able to resorb calcium phosphate surfaces consisting of granules. |
| Torres et al. (2011) |
b-TCP powder |
3DP |
In vivo |
Rabbit calvaria vertical bone augmentation |
8 weeks |
Synthetic onlay blocks achieve vertical bone augmentations as as high as 4.0 mm. |
| Rath et al. (2012) |
biphasic calcium phosphate (BCP) |
3DP + Sintered |
In vitro |
OB BMSC |
3 weeks, 6 weeks |
Application of a bioreactor system increases the proliferation and differentiation potential |
| Blanquer, Sharifi & Grijpma (2012) |
PDLLA 3-FAME/NVP |
SLA |
In vitro |
MC3T3 |
NG |
Mouse preosteoblasts readily attach and spread onto porous structures with the well-defined gyroid architectures by SLA. |
| Korpela et al. (2013) |
PCL/bioactive glass(BAG), PLA |
FDM |
In vitro |
Fibroblasts |
2 weeks |
FDM printed PLA has better cell friendly surface than PCL and PCL/BAG. |
| Luangphakdy et al. (2013) |
PLGA TCP PPF HA TyrPC MCA |
3DP VS SLA VS PL VS CM |
In vivo |
Canine Femoral Multi-Defect Model |
4 weeks |
TyrPCPL/TCP and PPF4SLA/HAPLGA Dip are better in biocompatibility than PLGA and PLCL scaffolds. MCA remains the best. |
| Wang et al. (2013) |
biogenic polyphosphate (bio-polyP) and biogenic silica (bio-silica) |
SFF/ indirect 3DP/ direct 3DP |
In vitro |
SaOS-2 cells, RAW 264.7 cells |
10 days |
Bio-silica ans bio-polyP increase release of BMP2 while bio-polyP inhibits osteoclasts activity. |
| Van Bael et al. (2013) |
PCL |
SLS |
In vitro |
hPDCs |
2 weeks |
The double protein coating increased cell metabolic activity and cell differentiation |
|
Feng et al. (2014a),Feng et al. (2014b)
|
β-TCP |
SLS |
In vitro |
MG-63 |
5 days, 4 weeks |
The mechanical and biological properties of the scaffolds were improved by doping of zinc oxide (ZnO). |
|
Feng et al. (2014a),Feng et al. (2014b)
|
nano-HAP |
SLS(NTSS) |
In vitro |
MG-63 |
5 days |
Cells adhered and spread well on the scaffolds. A bone-like apatite layer formed. |
|
Temple et al. (2014a),Temple et al. (2014b)
|
PCL |
FDM |
In vitro |
hASCs |
18 days |
ASCs seeded on the PCL scaffold are successfully induced in to both vascular and osteogenic differentiation. |
| Shim et al. (2014) |
PCL/PLGA |
FDM |
In vitro in vivo |
hTMSCs Rabbit radius defect |
4 weeks 8 weeks |
PCL/PLGA/collagen released rhBMP2 over one month in vitro, induced the osteogenic differentiation of hTMSCs in vitro and accelerated the new bone formation in the 20-mm rabbit radius defect. |
| Inzana et al. (2014) |
Calcium phosphonate powder CPS |
3DP |
In vitro In vivo |
C3H/10T1/2 cells, Murine critical size femoral defect. |
9 weeks |
3D printed CPS are enhanced through alternative binder solution formulations. Tween improve the flexural strength of CPS.Implants are osteoconductive. |
| Pati et al. (2015) |
PCL/PLGA ECM |
FDM |
In vitro In vivo |
hTMSCs, Rat calvarial defect. |
8 weeks |
The differentiation and mineralization may be augmented by combined effect of cell-laid extracellular matrix, exogenous osteogenic factors, and flow-induced shear stress |
