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Dental sg resin

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Dental SG Resin is a high-performance photopolymer resin designed for 3D printing dental applications. It is optimized for use with Formlabs 3D printers and provides accurate, high-resolution parts.

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Lab products found in correlation

Form 2, by Formlabs (2 mentions) Clear resin, by Formlabs (2 mentions) Sfh4053, by RS Components (2 mentions) Form 2 sla 3d printer, by Formlabs (2 mentions) Isopropyl alcohol, by Merck Group (1 mentions) Fibroblast media, by ScienCell (1 mentions) Anti fibronectin antibody, by Merck Group (1 mentions) Alamar blue dye, by Thermo Fisher Scientific (1 mentions) Gelatin type b from bovine skin, by Merck Group (1 mentions) Nucblue fixed cell stain readyprobes reagent, by Thermo Fisher Scientific (1 mentions) Actingreen 488 readyprobes reagent, by Thermo Fisher Scientific (1 mentions) Sodium alginate, by Merck Group (1 mentions) Form 2 printer, by Formlabs (1 mentions) Form 3, by Formlabs (1 mentions) Spinning diskmicroscope, by PerkinElmer (1 mentions) Form 2 3d printer, by Formlabs (1 mentions)

13 protocols using dental sg resin

1

In vitro maturation of COCs in biocompatible supports

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In the second experiment, mIVM culture was performed by inserting COCs within biocompatible supports placed at the bottom of the bioreactor chamber in order to recreate a protecting structure around them, similar to that of an ovarian follicle or part of it (Table 1). The supports, consisting of a ring (inner/outer radius = 5.5/7 mm) and a plain or a concave disk (outer radius 7 mm, maximum depth = 1.5 mm), were designed with Fusion 360 and fabricated at the Research Center ‘E. Piaggio’, University of Pisa, using a stereolithographic 3D printer (Form2, FormLabs) loaded with a biocompatible photo-polymeric material (Dental SG resin, Formlabs) [59 (link)]. The configurations tested were: (i) ring; (ii) concave + ring; (iii) concave + ring + plain (namely ring, concave + ring and “box” in the further text; Table 1; Figure 1). In all conditions, COCs were uploaded in the chamber after inserting the supports and adding the first 300 µL of IVM medium. Next, the chamber was then completely filled, closed, and connected to the pump as described above. The flow rate was set at 50 μL/min.
Mastrorocco A., Cacopardo L., Temerario L., Martino N.A., Tridente F., Rizzo A., Lacalandra G.M., Robbe D., Carluccio A, & Dell’Aquila M.E. (2022). Investigating and Modelling an Engineered Millifluidic In Vitro Oocyte Maturation System Reproducing the Physiological Ovary Environment in the Sheep Model. Cells, 11(22), 3611.
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2

Fabrication of Vancomycin-Loaded Bone Cement Scaffolds

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Space maintainers were fabricated as previously described [5 (link),22 (link)]. Briefly, UV-sterilized carboxymethyl cellulose (CMC, Spectrum Chemical, New Brunswick, NJ) was constituted in sterile water at 9 wt%. Scaffolds consisted of 10 wt% PLGA microparticles, 30 wt% CMC gel, and bone cement powder and bone cement liquid at 2:1 w/v ratio. Bone cement powder (84 wt% polymerized methylmethacrylate/methyl acrylate copolymer, 1 wt% benzoyl peroxide, and 15% zirconium dioxide, kindly donated by Synthasome, Inc., San Diego, CA) and PLGA were mixed prior to adding CMC. After a homogenous paste was formed, the liquid monomer (97.5 wt% methacrylate monomer, 2.5 wt% N,N-dimethyl-4-toluidine, and 75 ppm hydroquinone, Synthasome, Inc.) was added and stirred until the mixture entered a dough phase. The mixture was transferred to 3D-printed molds (Dental SG resin, FormLabs) of 1 × 2 × 0.5 cm, allowed to cure, and then vacuum dried for 48 hours. All space maintainers were sterilized via ethylene oxide Anprolene AN74i gas sterilization (Andersen Products, Haw River, NC) and allowed to degas prior to implantation. Untreated sheep are those who received blank space maintainers, while treated animals are those that received the vancomycin-loaded space maintainers.
Watson E., Smith B.T., Smoak M.M., Tatara A.M., Shah S.R., Pearce H.A., Hogan K.J., Shum J., Melville J.C., Hanna I.A., Demian N., Wenke J.C., Bennett G.N., van den Beucken J.J., Jansen J.A., Wong M.E, & Mikos A.G. (2020). Localized Mandibular Infection Affects Remote in Vivo Bioreactor Bone Generation. Biomaterials, 256, 120185.
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3

Fabrication of Microneedle Arrays

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Form 2 MN arrays were fabricated using Class I biocompatible Dental SG resin (Formlabs, Ripon, UK). Inkspire MN arrays were fabricated using white resin (Zotrax, Olsztyn, Poland). Asiga Max UV MN arrays were fabricated using PLasGRAY resin (Asiga, Alexandria, Australia). Isopropyl Alcohol was purchased from Sigma-Aldrich (St. Louis, MO, USA). Parafilm® M was purchased from Bemis Company (Neenah, WI, USA).
Mathew E., Pitzanti G., Gomes dos Santos A.L, & Lamprou D.A. (2021). Optimization of Printing Parameters for Digital Light Processing 3D Printing of Hollow Microneedle Arrays. Pharmaceutics, 13(11), 1837.
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4

Hydrogel-based Tissue Engineering Scaffold

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Sodium alginate (MW 50000 Da) and gelatin Type B from bovine skin (MW ~50,000–100,000 Da), calcium chloride analytical grade, and anti-fibronectin antibody were purchased from Sigma Aldrich (St Louis, Missouri). Human corneal keratocyte (HCK) cells and fibroblast media were purchased from ScienCell (Carlsbad, California). NucBlue fixed cell stain ready probes reagent was purchased from Invitrogen (Thermo Fischer Scientific, Massachusetts) and Actin green 488 ready probes reagent was purchased from Thermo Fischer Scientific. Live-Dead assay reagent/viability Assay Kit was purchased from Biotium Inc. Anti-rabbit Texas and FITC secondary antibodies were purchased from Santa Cruz Biotechnology. Polylactic acid (PLA) (Lulzbot TAZ 6, Colorado), SLA printer Form 2, Clear Resin, and Dental SG Resin (Formlabs) and Alamar blue dye (Invitrogen, California). Type I bovine collagen solution-Fibricol was purchased from Advanced BioMatrix.
Kutlehria S., Cong Dinh T., Bagde A., Patel N., Gebeyehu A, & Singh M. (2020). High-throughput 3D bioprinting of corneal stromal equivalents. Journal of biomedical materials research. Part B, Applied biomaterials, 108(7), 2981-2994.
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5

OK Adhesion Strength Measurement Protocol

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OK adhesion strength was quantitively measured on our surfaces following the work of Reyes and García [72 (link)] and others [73 (link)]. OKs were seeded as previously described (6 × 104 cells) and cultured for two days. The substrates were then placed vertically in 3D-printed holders (printed with Dental SG Resin, Formlabs) in a wellplate and centrifuged in culture medium at 500 g. This holder fits inside a 48-well such that disks (one disk per holder per well) are oriented perpendicular to the ground when centrifuged. The number of cells before and after centrifugation was determined by DAPI staining as previously described and OK adhesion strength was expressed as a percentage of cells remaining on the surface after centrifugation (schematic shown in Figure S10). Three fields of view (FOVs) were captured per sample (n=3). Following analyses, samples were not used for any other analysis.
Fischer N.G., Kobe A.C., Dai J., He J., Wang H., Pizarek J.A., De Jong D.A., Ye Z., Huang S, & Aparicio C. (2021). Tapping Basement Membrane Motifs: Oral Junctional Epithelium for Surface-mediated Soft Tissue Attachment to Prevent Failure of Percutaneous Devices. Acta biomaterialia, 141, 70-88.
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6

Lightweight Wireless Head/Eye Tracking

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Head and eye tracking was performed as described in Wallace et al., 2013 (link), with modifications as described below. The eye camera mount and implant were re-designed to be smaller, lighter and stronger (Figure 7A–B). The camera system body, camera holders and mounting arms were produced using a Formlabs Form2 SLA 3D printer (Formlabs Inc, USA), with Dental SG Resin (Formlabs Inc, USA) as the primary construction material. The cable used for position tracking LEDs power inputs and for data transfer and camera were custom cables (Axon Kabel GmbH, Leonberg, Germany) combined with custom-designed flexible flat cables (IBR Ringler, Bad Rappenau, Germany) for the cameras, to reduce stiffness over the last 30 cm. Eye movements were recorded at 60 Hz (camera resolution 752x480 pixels), with illumination provided by a ring of three IR-LEDs (λ=850 nm, OSRAM SFH4050 or SFH4053 @ 70mA, RS Components, Germany) surrounding the camera lens. The mouse’s head position and head rotations were tracked using seven IR-LEDs (λ = 950 nm, OSRAM SFH4043 @ 70mA, RS Components, Germany) mounted on three struts of carbon fiber that projected from the body of the camera system. The resultant total system weight was ~3 g, including effective cable weight.
Holmgren C.D., Stahr P., Wallace D.J., Voit K.M., Matheson E.J., Sawinski J., Bassetto G, & Kerr J.N. (2021). Visual pursuit behavior in mice maintains the pursued prey on the retinal region with least optic flow. eLife, 10, e70838.
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7

Quantifying Cell Adhesion Force

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The relative cell adhesion force of OKs on the samples was measured following the work of Reyes and García.52 OKs were seeded as previously described (Section 2.3). and allowed to proliferate for 2 days. The samples were then placed vertically in custom, 3D-printed holders (Figure S10A; printed with Dental SG Resin, Formlabs, USA) in a wellplate and centrifuged at 500 g in culture media. The number of cells was determined by DAPI staining, as previously described (Section 2.3.3), before and after centrifugation on separate samples (multiple FOVs per sample) and expressed as a percentage of cells remaining after centrifugation.
Fischer N.G., Moussa D.G., Skoe E.P., De Jong D.A, & Aparicio C. (2020). Keratinocyte-Specific Peptide-Based Surfaces for Hemidesmosome Upregulation and Prevention of Bacterial Colonization. ACS biomaterials science & engineering, 6(9), 4929-4939.
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8

Photocrosslinking of ELP(Tyr) Hydrogels

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The photocrosslinking solution was prepared containing 10% w/v ELP(Tyr) in pH 7.5 phosphate buffer and was mixed with various concentrations of ammonium persulfate and tris(2,2′-bipyridyl)ruthenium(II) chloride hexahydrate (Sigma-Aldrich, St. Louis, MO, USA). Molds were printed by a Formlabs FORM 2 printer with Dental SG resin (Formlabs, MA, USA). Cylindrical 14 mm diameter × 2 mm height molds were prepared for rheology. Cylindrical 20 mm diameter × 1 mm height and 8 mm diameter × 1 mm height molds were prepared for cytotoxicity assays. The crosslinking solution filled the molds and was then irradiated at a distance of 10 inches under a 24 W, 460 nm, 14 × 14 LED array for 10 min. The hydrogels were removed from the molds and stored in glass scintillation vials covered with aluminum foil.
Camp C.P., Peterson I.L., Knoff D.S., Melcher L.G., Maxwell C.J., Cohen A.T., Wertheimer A.M, & Kim M. (2020). Non-cytotoxic Dityrosine Photocrosslinked Polymeric Materials With Targeted Elastic Moduli. Frontiers in Chemistry, 8, 173.
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9

Fabrication of 3D Printed Dental Drill Guides

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In the SLA 3D printer (Form 3, Formlabs Inc., Somerville, MA, USA), the drill guides were fabricated in a proprietary biocompatible photopolymer resin material (Dental SG Resin, Formlabs Inc., Somerville, MA, USA). The STL files of the drill guides were imported into the 3D printer’s slicing software (PreForm v. 3.4.4, Formlabs Inc., Somerville, MA, USA). Depending upon the complexity of the drill guides, the guides were oriented at a 30°ߝ45° angle generating sufficient raft and support structures (Figure 1). The manufacturer’s recommended settings for the respective biocompatible resin material were selected, and the guides were printed at a layer thickness of 50 microns. After printing, the drill guides were immersed and cleaned with 90% isopropyl alcohol (IPA) solution for 20 min and left to air dry for another 10 min. The drill guides were post-cured for another 30 min in an ultraviolet (UV-A light 385 nm) lightbox following the manufacturer’s instructions. Subsequently, the manual removal of the support structures from the drill guides was performed using fine-cutting pliers.
Wegmüller L., Halbeisen F., Sharma N., Kühl S, & Thieringer F.M. (2021). Consumer vs. High-End 3D Printers for Guided Implant Surgery—An In Vitro Accuracy Assessment Study of Different 3D Printing Technologies. Journal of Clinical Medicine, 10(21), 4894.
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10

Corneal Scaffold Fabrication for Tissue Engineering

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A support apparatus, on which the stroma would be printed upon, was prepared by inscribing our corneal model within a 56 mm × 42 mm × 6 mm rectangular prism so that the scaffold would complement the anterior surface of the corneal model. This resulted in a concavity, which we will call a corneal well; it helped to maintain the ocular dimensions of the cornea during printing. The corneal well also contained a small dead volume to accommodate adding crosslinking agent after printing. These well patterns could be repeated along the rectangular prism in uniform rows to the desired number of corneas. A 6- and 12-well scaffold was initially FDM printed with PLA using a 22G nozzle. We then utilized an SLA printer Form 2 (Formlabs) for printing the support scaffold with Clear Resin (Formlabs) and Dental SG Resin. The layer height for the Clear and Dental SG Resins was 25 and 50 μm, respectively. The corneal supports were positioned at different angles with respect to the build plate to modify the tessellation pattern on the surface of the corneal wells. Aligning the support parallel to the build plate resulted in parallel concentric circles. Supports were created with a touchpoint size of 0.6 mm using the Auto-Generate tool with the PreForm software.
Kutlehria S., Cong Dinh T., Bagde A., Patel N., Gebeyehu A, & Singh M. (2020). High-throughput 3D bioprinting of corneal stromal equivalents. Journal of biomedical materials research. Part B, Applied biomaterials, 108(7), 2981-2994.
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