Table 1.
Bio-Ink |
(Bio)printed Constructs |
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---|---|---|---|---|---|---|
Reference | Printing Technique | Material(s) | Cells and/or Biological Cues | Mechanical Properties | Tissue Formation | Remarks |
Cohen et al. (2006)18 | Extrusion bioprinting | Alginate | • Full thickness bovine articular chondrocytes | • Compressive modulus (unconfined) ~1.8 ± 0.1 kPa |
In vitro • Viability, ~94% • Cartilage-like tissue formation similar in printed constructs as in casted alginate or alginate beads |
• Printed meniscus and intervertebral disk shapes* • Demonstrated that viability and differentiation behavior of chondrocytes were not influenced by the printing procedure |
Schuurman et al. (2012)61 | Extrusion printing | Alginate reinforced with PCL | • C20A4 cell-line* | • Compressive modulus (unconfined) ~6000 kPa |
In vitro • Viability, ~70-90% |
• First demonstration of simultaneous deposition of thermoplastic polymer and hydrogel for the fabrication of reinforced constructs |
Cui et al. (2012)19 | Inkjet bioprinting | PEGDMA | • Full thickness human articular chondrocytes• TGF-β1 and FGF-2 in medium during culture | • Compressive modulus (unconfined) ~30-37 kPa |
In vitro • More cell proliferation and more total cartilage-like tissue formation in constructs cultured with both TGF-β1 and FGF-2 after 4 weeks of differentiation |
• Demonstrated that culturing printed constructs with both TGF-β1 and FGF-2 increases proliferation and on longer term (21 days) cartilage-like tissue formation |
Cui et al. (2012)70 | Inkjet bioprinting | PEGDMA | • Full thickness human articular chondrocytes | • Compressive modulus (unconfined) ~38-320 kPa |
Ex vivo • Viability, ~89% • Cartilage-like tissue formation increased during the first 4 weeks of culture and remained stable after (6 weeks total) • Stable construct integration in the defect after 6 weeks |
• Printing directly into defects in porcine osteochondral plugs • Demonstrated the importance of rapid gelation for maintaining initial cell distribution |
Schuurman et al. (2013)17 | Extrusion bioprinting | GelMA with hyaluronic acidPCL reinforcement* | • Full thickness equine articular chondrocytes• Hyaluronic acid | • Compressive modulus (unconfined) for gelMA constructs: ~10-175 kPa (dependent on concentration) |
In vitro • Viability, ~73-83% • Similar cartilage-like tissue formation in constructs with and without hyaluronic acid after 4 weeks differentiation |
• Addition of hyaluronic acid increased the printability |
Boere et al. (2014)64 | Extrusion printing | GelMA (cast) reinforced with pHMGCL/PCL (printed) | • Full thickness human articular chondrocytes | • Construct failure (unconfined compression) ~2.7 N (~7.7 N when covalent bonds between gelMA and pHMGCL/PCL) |
In vitro • Covalent bonds between hydrogel and reinforcement to increase construct stability and mechanical strength In vivo • Rats, subcutaneous; more collagen type II but less GAGs after 8 weeks compared to in vitro study |
• Interconnected cartilage-like tissue network after 6 weeks of differentiation |
Kundu et al. (2015)83 | Extrusion bioprinting | Alginate reinforced with PCL | • Nasal human chondrocytes• TGF-β | • Not reported |
In vitro • Viability, ~85%• More cartilage-like tissue formation in constructs with TGF-β after 4 weeks of differentiation In vivo • Immunodeficient mice, subcutaneous; moderate cartilage-like tissue formation in constructs with TGF-β after 4 weeks |
• Printed constructs with a cell and growth factor-laden bio-ink, reinforced with a printed thermoplastic polymer |
Kesti et al. (2015)84 | Extrusion bioprinting | HAMA with HA-pNIPAAM | • Full thickness bovine articular chondrocytes | • Not reported |
In vitro • Viability, low when HA-pNIPAAM remains in the culture, high when HA-pNIPAAM was eluted |
• HA-pNIPAAM supports printing and can be eluted from the final construct after printing and crosslinking |
Kesti et al. (2015)39 | Extrusion bioprinting | Gellan with alginate | • Full thickness bovine articular chondrocytes • Hydroxyapatite particles • Cartilage extracellular matrix particles |
• Tensile modulus ~116-230 kPa |
In vitro • Viability, ~80-96% (60% in the center of large constructs) • Cartilage extracellular matrix particles increased cartilage-like tissue formation during 8 weeks of differentiation. However, constructs cultured in TGF-β3 supplemented medium contained most cartilage matrix |
• Printed ear, nose, meniscus, and vertebral disk shapes by using support structures* |
Markstedt et al. (2015)85 | Extrusion bioprinting | Nanofibrillated cellulose with alginate | • Nasal human chondrocytes | • Compressive modulus (unconfined) ~75-250 kPa (depending on the ratio of both components) |
In vitro • Viability, ~73-86% |
• Printed ear and meniscus shapes* |
Visser et al. (2015)66 | Melt electrospinning | Electrospun PCL infused with gelMA | • Human articular chondrocytes in gelMA• Hyaluronic acid• Mechanical stimulation (14 days without followed by 14 days with) | • Compressive modulus (unconfined) ~80-400 kPa for hybrid construct depending on mesh porosity• Similar stress/strain curve for gelMA reinforced with a 93% porous mesh as for native articular cartilage |
In vitro • Viability, ~73-86% • Expression of chondrogenic genes increased in mechanical stimulated constructs during 4 weeks of culture. No differences were found at protein level |
• With low content of thermoplastic polymer fibers (7%), mechanical properties could be achieved within the range of articular cartilage |
Izadifar et al. (2016)86 | Extrusion bioprinting | Alginate reinforced with PCL | • Full thickness embryonic chick chondrocytes (“rounded” and “fibroblastic” subpopulations) | • Not reported |
In vitro • Viability, ~77-85% • More proliferation and cartilage-like tissue formation in constructs with the “fibroblastic” chondrocyte subpopulation compared to the “rounded’ subpopulation |
• Printed constructs with a cell-laden bio-ink, reinforced with a printed thermoplastic polymer • Demonstrated rapid cooling of PCL strands after printing • Different chondrocyte subpopulations give differences in cartilage-like tissue formation |
Abbadessa et al. (2016)87 | Extrusion bioprinting | polyHPMA-lac-PEG | • Full thickness equine articular chondrocytes• HAMA or CSMA | • Compressive modulus (unconfined) ~13-16 kPa for all combinations |
In vitro • Viability, ~85-95% (printed) • Similar levels of cartilage-like tissue formation in polyHPMA-lac-PEG hydrogels as in fibrin controls after 4 weeks of culture (cast) |
• Incorporation of HAMA and to a lesser extent CSMA decreased the degradation rate and improved the thermosensitive profile and printability |
Mouser et al. (2016)88 | Extrusion bioprinting | gelMA with gellan gum | • Full thickness equine articular chondrocytes | • Compressive modulus (unconfined) ~2.7-186 kPa depending on concentration and ratio of gelMA and gellan gum |
In vitro • All evaluated concentrations supported cartilage-like tissue formation during 6 weeks of culture. Relatively high gellan gum concentrations compromised chondrogenesis and high total polymer concentrations hampered matrix distribution |
• Identified yield stress as dominant factor for bioprintability • Addition of gellan gum improved filament deposition, increased construct stiffness, and supported chondrogenesis |
Proof of concept study.
PCL = polycaprolactone; PEGDMA = poly(ethylene) glycol dimethacrylate; TGF = transforming growth factor; FGF = fibroblast growth factor; GelMA = gelatin-methacryloyl; pHMGCL/PCL = poly(hydroxylmethylglycolide-co-ϵ-caprolactone)/poly(ϵ-caprolactone); HAMA = methacrylated hyaluronic acid; HA-pNIPAAM = poly(N-isopropylacrylamide) grafted hyaluronan; polyHPMA-lac-PEG = polyethylene glycol midblock flanked by two poly[N-(2-hydroxypropyl) methacrylamide mono/dilactate]; CSMA = methacrylated chondroitin sulfate; PEGT-PBT = poly(ethylene glycol)-terephthalate-poly(butylene terephthalate).