Sacrificial Mold Printing
Sacrificial Mold Printing - Related Videos
10:49
Printing Thermoresponsive Reverse Molds for the Creation of Patterned Two-component Hydrogels for 3D Cell Culture
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Cited by 60 •
2013
A bioprinter was used to create patterned hydrogels based on a sacrificial mold. The poloxamer mold was backfilled with a second hydrogel and then eluted, leaving voids which were filled with a third hydrogel. This method uses fast elution and good printability of poloxamer to generate complex architectures from biopolymers.
10:43
Rapid and Low-cost Prototyping of Medical Devices Using 3D Printed Molds for Liquid Injection Molding
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Cited by 34 •
2014
We have devised a method for low-cost and rapid prototyping of liquid elastomer rubber injection molded devices by using fused deposition modeling 3D printers for mold design and a modified desiccator as a liquid injection system.
08:31
Process of Making Three-dimensional Microstructures using Vaporization of a Sacrificial Component
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Cited by 7 •
2013
The Vaporization of a Sacrificial Component (VaSC) process is used to fabricate microvascular structures. This procedure uses sacrificial poly(lactic) acid fibers to form hollow microchannels with precise 3D geometric positioning provided by laser micromachined guide plates.
08:16
Fabrication of Custom Agarose Wells for Cell Seeding and Tissue Ring Self-assembly Using 3D-Printed Molds
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Cited by 27 •
2018
This protocol describes a platform for fabricating self-assembled tissue rings in variable sizes using a customized 3D-printed plastic mold. PDMS negatives are cured in the 3D-printed mold; then agarose is cast in the cured PDMS negatives. Cells are seeded into the resulting agarose wells where they aggregate into tissue rings.
09:50
Production and Use of Customizable Agarose Molds for Scaffold-Free Mouse Ovarian Follicle Culture
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Cited by 2 •
2025
We describe methods to culture ovarian follicles in a novel scaffold-free agarose mold that complement in vitro gametogenesis.
FAQs
The temporary structure can be removed by dissolution, melting, or mechanical extraction, and each route determines how the hollow network is released from the surrounding matrix. The removal method must suit the fugitive ink and the permanent material, because incomplete removal could obstruct channels, whereas effective removal preserves the intended internal geometry.
Channel size and connectivity determine how effectively fluids can move through a fabricated construct. Printing the temporary geometry before embedding it in a matrix allows bioengineers to control these features directly rather than relying only on surface patterning. That control supports internal transport networks designed for perfusable tissue constructs, organ-on-chip devices, and biomimetic systems.
The printed fugitive structure first occupies the future cavity or channel, while the permanent material forms around it. Once the temporary structure is removed, the previously inaccessible space becomes open and enclosed within the matrix. This sequence separates channel formation from matrix fabrication, helping produce internal architectures that are challenging to manufacture as empty spaces.
Successful removal depends on matching the temporary structure, the surrounding matrix, and the chosen extraction mechanism. A fugitive ink must be removable through dissolution, melting, or mechanical extraction without destroying the hydrogel, elastomer, or other permanent material. This compatibility affects whether the final construct retains open, connected channels with the intended geometry.
A typical workflow begins by depositing a fugitive ink in the desired three-dimensional geometry. The printed structure is then surrounded by a hydrogel, elastomer, or another matrix that becomes the permanent construct. Finally, the temporary material is dissolved, melted, or mechanically extracted, leaving the internal cavity or channel network for subsequent use.
Bioengineers would use this approach when a project requires controlled internal cavities or connected channels rather than features confined to an exposed surface. Its value is especially evident in perfusable tissue constructs, organ-on-chip devices, and biomimetic systems, where internal transport, vascularization, or tissue function depends on realistic three-dimensional architecture.
The technique can provide hollow, interconnected networks whose channel dimensions and layout are defined during printing. These structures give researchers a way to study or support transport within three-dimensional models, including perfusable tissues and organ-on-chip devices. As a result, engineered systems can represent aspects of vascularization and tissue function more realistically than models without internal pathways.