Cell-laden microengineered gelatin methacrylate hydrogels

Nichol, Jason W.; Koshy, Sandeep T.; Bae, Hojae; Hwang, Chang Mo; Yamanlar, Seda; Khademhosseini, Ali

doi:10.1016/j.biomaterials.2010.03.064

Cited by 1,979 publications

(2,269 citation statements)

References 57 publications

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“…The 3D printing compatibility of the bioink was tested over a range of F127 concentrations (11,13, and 15 wt%) at both 5 and 6 wt% sodium alginate. Optimum printing performance was observed using 13 wt% F127 with 6 wt% sodium alginate, which produced reliably smooth prints with reproducible geometries ( Figure S1b,e, Supporting Information).…”

Section: Doi: 101002/adhm201600022mentioning

confidence: 99%

3D Bioprinting Using a Templated Porous Bioink

Armstrong

Burke

Carter

et al. 2016

Adv Healthcare Materials

159

111

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3D cell printing (bioprinting) is rapidly emerging as a key biofabrication strategy for engineering tissue constructs with physiological form and complexity. [1][2][3][4] In practice, this process involves layer-by-layer deposition of a cell-laden bioink resulting in the additive manufacture of a patterned architecture with different cell types, growth factors, or mechanical cues, which are positioned with far greater precision than can be achieved with conventional scaffold-based tissue engineering. [ 5 ] While there have been signifi cant advances in printing technology, [ 6,7 ] progress has been limited by the rate of development of bioinks that are compatible with both 3D printing and tissue engineering. [ 8 ] These materials must be able to withstand extrusion, maintain structural fi delity for long time periods, and permit adequate nutrient diffusion, all under cytocompatible conditions. Due to their intrinsic porosity and capacity for high nutrient loading, hydrogels are the most promising candidate for bioink design, [ 9 ] particularly when gelation can be externally triggered using chemical bonding, [ 10 ] photoinduced crosslinking, [ 11 ] thermal setting, [ 12 ] or shear-thinning. [ 13 ] However, integrating these factors into a system while maintaining printability, structural persistence, and cell viability, is an enduring challenge. [ 14 ] Pluronic block copolymers of poly(ethylene oxide-b-propylene oxide-b-ethylene oxide) present a possible pathway to print gelation, as they undergo a sol-gel transition upon heating near physiological temperatures. Here, elevating the temperature of these non-ionic surfactants reduces the

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Section: Doi: 101002/adhm201600022mentioning

confidence: 99%

3D Bioprinting Using a Templated Porous Bioink

Armstrong

Burke

Carter

et al. 2016

Adv Healthcare Materials

159

111

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“…Gelatin methacrylate (GelMA) was synthesized as described previously. 28 At a temperature of 65°C, type A porcine skin gelatin powder (Sigma-Aldrich, St Louis, MO, USA) was added to Dulbecco's phosphate-buffered saline solution (DPBS; Gibco, Carlsbad, CA, USA) and stirred until fully dissolved to obtain a concentration of 10% (w v -1 ). Methacrylic anhydride (Sigma-Aldrich), a photocrosslinkable monomer, 29 was added to this solution at a rate of 0.5 ml min -1 while stirring at 50°C until the target volume was reached.…”

Section: Fe 3 O 4 Nanoparticle and Gelma Synthesismentioning

confidence: 99%

Magnetically actuated cell-laden microscale hydrogels for probing strain-induced cell responses in three dimensions

Huang

Gao

et al. 2016

NPG Asia Mater

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Living cells respond to their mechanical microenvironments during development, healing, tissue remodeling and homeostasis attainment. However, this mechanosensitivity has not yet been established definitively for cells in three-dimensional (3D) culture environments, in part because of challenges associated with providing uniform and consistent 3D environments that can deliver a large range of physiological and pathophysiological strains to cells. Here, we report microscale magnetically actuated, cell-laden hydrogels (μMACs) for investigating the strain-induced cell response in 3D cultures. μMACs provide high-throughput arrays of defined 3D cellular microenvironments that undergo reversible, relatively homogeneous deformation following non-contact actuation under external magnetic fields. We present a technique that not only enables the application of these high strains (60%) to cells but also enables simplified microscopy of these specimens under tension. We apply the technique to reveal cellular strain-threshold and saturation behaviors that are substantially different from their 2D analogs, including spreading, proliferation, and differentiation. μMACs offer insights for mechanotransduction and may also provide a view of how cells respond to the extracellular matrix in a 3D manner.

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“…The combination of hydrogel bioprinting with melt extrusion has been successfully explored to design well-defined 3D constructs with improved mechanical properties, which is of special interest for load bearing tissues [80], but of limited application in soft tissues. The printing process of viscous bioinks might affect the distribution of cells throughout the construct ultimately leading to tissue heterogeneity, while highly crosslinked hydrogels may lead to excessively stiff matrices that impose severe restrictions to cell spreading, migration and proliferation [11,24,130]. Thus, it is crucial to ensure that the bioink has the appropriate rheological properties to be printed and, at the same time, is able to maintain the shape upon deposition.…”

Section: Hydrogel Bioinksmentioning

confidence: 99%

Advances in bioprinted cell-laden hydrogels for skin tissue engineering

et al. 2017

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Bioprinting technologies are powerful additive biofabrication techniques to produce cellular constructs for skin tissue engineering owing to their unique ability to precisely pattern living and non-living materials in predefined spatial locations. This unique feature, combined with the computer controlled printing and medical imaging techniques, enable researchers and clinicians to generate patient specific constructs partly replicating the intricate compositional and architectural organization of the skin. Bioprinting has been used to automatically dispense hydrogels with skin cells located in prescribed sites that promote skin formation in vitro and in vivo. Current skin bioprinting approaches mostly rely on the sequential printing of fibroblasts and keratinocytes embedded within a homogeneous hydrogel. Although such approaches have already been translated to pre-clinical scenarios, they still present limitations in terms of fully replicating the cellular and extracellular matrix (ECM) heterogeneity in native skin. The success of bioprinting for skin repair strongly depends on the design of printable bioinks capable of supporting the function of printed cells and stimulating the production of new ECM components. To better mimic the human skin, novel developments in dedicated bioprinting technologies, in the design of bioinks, as well as in the printing of vascularised constructs are necessary. This paper presents an overview regarding the use of bioprinting for skin tissue engineering applications. The operating principles of bioprinting technologies are outlined along with requirements of printed skin constructs. Finally, preclinical results are summarized and future perspectives for the field are highlighted.

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Cell-laden microengineered gelatin methacrylate hydrogels

Cited by 1,979 publications

References 57 publications

3D Bioprinting Using a Templated Porous Bioink

3D Bioprinting Using a Templated Porous Bioink

Magnetically actuated cell-laden microscale hydrogels for probing strain-induced cell responses in three dimensions

Advances in bioprinted cell-laden hydrogels for skin tissue engineering

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