Abstract
We developed a multi-channel cell chip containing a three-dimensional (3D) scaffold for horizontal co-culture and drug toxicity screening in multi-organ culture (human glioblastoma, cervical cancer, normal liver cells, and normal lung cells). The polydimethylsiloxane (PDMS) multi-channel cell chip (PMCCC) was based on fused deposition modeling (FDM) technology. The architecture of the PMCCC was an open-type cell chip and did not require a pump or syringe. We investigated cell proliferation and cytotoxicity by conducting 3-(4,5-dimethylthiazol-2-yl)-2,5-dphenyltetrazolium bromide (MTT) and lactate dehydrogenase (LDH) assays and analysis of oleanolic acid (OA)-treated multi-channel cell chips. The results of the MTT and LDH assays showed that OA treatment in the multi-channel cell chip of four cell lines enhanced chemoresistance of cells compared with that in the 2D culture. Furthermore, we demonstrated the feasibility of the application of our multi-channel cell chip in various analysis methods through Annexin V-fluorescein isothiocyanate/propidium iodide staining, which is not used for conventional cell chips. Taken together, the results demonstrated that the PMCCC may be used as a new 3D platform because it enables simultaneous drug screening in multiple cells by single point injection and allows analysis of various biological processes.
Highlights
We demonstrated that the cytotoxic effect of oleanolic acid (OA)
Increased drug resistance in BNL-CL2, L132, U87, and HeLa cell lines cultured on the PDMS multi-channel cell chip (PMCCC)
lactate dehydrogenase (LDH) assay results showed that BNL-CL2 (66%), L-132 (34.32%), U87 (70.76%), and HeLa cells (39.68%) cultured on the PMCCC had a lower cytotoxicity compared with the 2D plate at 300 μg/mL OA
Summary
Publisher’s Note: MDPI stays neutral with regard to jurisdictional claims in published maps and institutional affiliations. Techniques for three-dimensional (3D) scaffold fabrication include solvent casting, gas forming, salt leaching, fiber binding, and membrane lamination [1]. It is difficult to control the shape and pore size of interconnected porous structures and scaffolds [2,3,4]. A 3D organ printing system can overcome the limitations of existing methods by distributing the filaments of the material in a layer-by-layer manner to produce scaffolds with various sizes, shapes, and internal architectures [5]. The porosity of a 3D printed scaffold allows the transport of nutrients and metabolic waste, making these scaffolds suitable surfaces ideal for cell adhesion and proliferation [6,7]
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