Abstract
In three-dimensional (3D) bioprinting, the accuracy, stability, and mechanical properties of the formed structure are very important to the overall composition and internal structure of the complex organ. In traditional 3D bioprinting, low-temperature gelatinization of gelatin is often used to construct complex tissues and organs. However, the hydrosol relies too much on the concentration of gelatin and has limited formation accuracy and stability. In this study, we take advantage of the physical crosslinking of agarose at 35–40 °C to replace the single pregelatinization effect of gelatin in 3D bioprinting, and printing composite gelatin/alginate/agarose hydrogels at two temperatures, i.e., 10 °C and 24 °C, respectively. After in-depth research, we find that the structures manufactured by the pregelatinization method of agarose are significantly more accurate, more stable, and harder than those pregelatined by gelatin. We believe that this research holds the potential to be widely used in the future organ manufacturing fields with high structural accuracy and stability.
Highlights
The concept, connotation and extension of organ manufacturing were firstly defined by Professor Wang in 2003, and it is an emerging discipline combining biology, chemistry, computer, mechanics and materials to construct bioartificial organs in vitro through automatic or semi-automatic methods [1,2]
The manufacturing process is briefly described as follows: after the Adipose-derived stem cells (ASCs) cells were mixed with the gelatin–alginate–agarose solution at a density of 1 × 107 cells/mL, the mixed solution was poured into the printing needle tube for pregelatinization at a certain temperature before being printed
DisIncutshsiisonstudy, we mainly studied the role of agarose in 3D bioprinting, and used the cIhnarthacistesrtiusdtiyc,owf ethme apihnylysisctauldcireodsstlhine kroinlegooffaaggaarroosseeiant33D5–b4i0op◦Crinttoinrgep, alancde uthseedsitnhgele pcghheryealdagrrtaeiocnlgatieeztrilansitsiiwtzoiacnetroieeoffnfptehrceeitfnfpoetehfcdtygsoeailftcaagttwilencloaritnotiesn3smDliinpnbek3iriDonaptgburiiornoeftpsia,nrgiign.ae.rt.Cio,ns1oge0m.a◦CptCoo3s5mai–ntp4ed0og2s°Ce4iltae◦ttCoign,er–rleaaepltsglipanienc–ecaattltieghv–ieenalsgyai.tanerg–olasegepahrryeo--se drogels were printed at two temperatures, i.e., 10 °C and 24 °C, respectively
Summary
The concept, connotation and extension of organ manufacturing were firstly defined by Professor Wang in 2003, and it is an emerging discipline combining biology, chemistry, computer, mechanics and materials to construct bioartificial organs in vitro through automatic or semi-automatic methods [1,2]. Vat polymerization bioprinting uses photopolymerization to cure the liquid ink hosted in a vat into a volumetric construct in a layer-by-layer manner Limitations exist for this technology in organ manufacturing because it is hard to print multiple biomaterials with necessary accuracy [38–40]. The phenomenon of shear thinning is widespread in polymer fluids, which makes it difficult to control the extruded hydrogel, which in turn affects the accuracy and stability of the structure. This problem still plagues the majority of researchers. A natural polymer with great biocompatibility, is selected as the pregelatinized matrix in most of the traditional extrusion-based bioprinting technologies, because gelatin can be physically crosslinked at low temperature (e.g., 10–30 ◦C) [29–36]. We have broken through the shortcoming of the traditional gelatin-based “bioinks”, in which the sol–gel state transition process is totally dependent on temperature-sensitive gelatin
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