Biocad software

Manufactured by RegenHU

Sourced in Switzerland

BioCAD is a software application developed by RegenHU. It is a computer-aided design (CAD) tool specifically designed for working with biological materials and processes. The software provides a digital environment for the visualization, modeling, and simulation of various biological structures and systems.

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Lab products found in correlation

3d discovery bioprinter, by RegenHU (3 mentions) 3d discovery, by RegenHU (2 mentions) 3d discovery system, by RegenHU (1 mentions) Smz1500, by Nikon (1 mentions) 3d discovery printer, by RegenHU (1 mentions) Purasorb pc 12, by Corbion (1 mentions) Stemi 508, by Zeiss (1 mentions) Paravision 6, by Bruker (1 mentions) Matlab r2020a, by MathWorks (1 mentions) Sodium dodecyl sulfate (sds), by Merck Group (1 mentions)

Close spelling variants of this product

BioCAD™ drawing software BioCAD

14 protocols using biocad software

3D Printing of PLGA/PEG Biocomposites

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A RegenHU 3D Discovery system (Switzerland) was used for 3D printing with Huber Pilot ONE temperature controller (Switzerland). PLGA/PEG particles (≤50 μm) were mixed by spatula with different carriers, cells and microparticles at 4 °C before being transferred into a sterile syringe. Mixing was performed until a homogenous colour (of the phenol-red cell culture media) was achieved as previously [30 (link)]. Syringes were placed into the printer mount and allowed to equilibrate with the printing temperature (25 °C). During printing, the pressure was manually adjusted (1–3 bar) to ensure adequate flow of material through the 20 gauge (0.61 mm) tapered syringe tip (Adhesive dispensing Ltd. UK). The print speed varied between 20 and 60 mm/s. BioCAD software (RegenHU) was used to design the lattice structure to be printed. Dissection microscope Nikon SMZ1500 was used to image the printed structures. For 3D printing of the L5 vertebra, SLS files were downloaded from: http://www.thingiverse.com/thing:781206. For L5 vertebrate; PLGA/PEG with Pluronic F-127 (PF127) 18% (with 1% Tri-acetin) 1:1.5 ratio was mixed and loaded to the printer, the printing temperature was 25 °C.

Abu Awwad H.A., Thiagarajan L., Kanczler J.M., Amer M.H., Bruce G., Lanham S., Rumney R.M., Oreffo R.O, & Dixon J.E. (2020). Genetically-programmed, mesenchymal stromal cell-laden & mechanically strong 3D bioprinted scaffolds for bone repair. Journal of Controlled Release, 325, 335-346.

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Osteochondral Plug Fabrication via 3D Printing

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Osteochondral plugs were fabricated by extrusion-based 3D printing of GMP-grade PCL (Purasorb^® PC 12, Corbion, The Netherlands) using a screw-based extruder on a 3D Discovery printer (regenHU, Switzerland). The osteochondral plug was designed on BioCAD software (regenHU) as a cylinder with 6 mm diameter, featuring a square-grid scaffold structure with six zones with different porosities. The lower zones were designed for bone osteoconduction and formed a gradient of decreasing porosity from the bottom to the top, mimicking the transition from trabecular to cortical bone. The top zone of the scaffold represented the endochondral interface and was designed as completely closed to separate the hydrogel materials for cartilage repair from the osteal anchor (Fig. 1 A). The uppermost zone in the osteochondral plug was designed for fiber reinforcement of the chondral portion (Fig. 1B), to enhance fixation of the hydrogels and to increase biomechanical resistance of the chondral layer.²⁹Before printing, the PCL was first molten in the extruder heating tank at 90°C for at least 30 min to ensure consistent material viscosity. The osteochondral plugs were then fabricated using the following printing parameters: feeding pressure of 0.5 bar, 32G extrusion nozzle, temperature of 80°C, spindle speed of 4rpm, and printing speed of 4mm/s.

Mancini I.A., Bolaños R.A., Brommer H., Castilho M., Ribeiro A., van Loon J.P., Mensinga A., van Rijen M.H., Malda J, & van Weeren R. (2017). Fixation of Hydrogel Constructs for Cartilage Repair in the Equine Model: A Challenging Issue. Tissue engineering. Part C, Methods, 23(11), 804-814.

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Bioink Printing with Cell-Friendly System

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All the formulated bioinks were printed using a cell-friendly print head (regenHU, Villaz-St-Pierre, Switzerland) controlled by an electromagnetic microvalve system and compressed air in a Class II biosafety cabinet permitting work under sterile conditions (3DDiscovery, regenHU). Printing path designs were created using BioCAD software (regenHU); a G-code file was obtained, loaded to HMI software, and launched for printing. To prevent sedimentation in the printing, a cell mixing system (regenHU) was used to print the designed constructs with a homogeneous distribution of cells and AMP particles. An optical microscope (Zeiss Stemi 508, Carl Zeiss Meditec AG, Oberkochen, Germany) in bright field mode was used to determine the state of distribution of the AMP particles in printed constructs. The print accuracy was evaluated qualitatively using a digital scanner (V550, Epson America, Inc., Long Beach, CA, USA) and the optimized feed rate and dosing distance were used for subsequent prints (Figure 10). Four-layer (10 mm × 10 mm) constructs were printed following optimized parameters (Table 1) to assess shape fidelity.

Dubey N., Ferreira J.A., Malda J., Bhaduri S.B, & Bottino M.C. (2020). Extracellular Matrix/Amorphous Magnesium Phosphate Bioink for 3D Bioprinting of Craniomaxillofacial Bone Tissue. ACS applied materials & interfaces, 12(21), 23752-23763.

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3D Bioprinting of GCB and GACB Scaffolds

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GCB and GACB scaffolds were produced using the direct-dispensing printhead (Direct Dispenser DD135N) of a 3D Discovery Bioprinter (RegenHU, Villaz-St-Pierre, Switzerland). The inks were loaded in 3 mL syringes, and conical nozzles of 0.25 mm inner diameter (G25) were used. The 3D scaffold design was generated in BioCAD software (developed by RegenHU, Switzerland) as a cylindrical model with 8 mm diameter, 1 mm distance between two neighboring filaments, 8 layers of 0–90° deposition direction, and a layer thickness which represented 75% of the nozzle diameter used. The adequate processing parameters were determined through multiple 3D printing experiments and are listed in Table 2. The 3D scaffolds were printed on a plastic sheet at room temperature and kept in the refrigerator before crosslinking.

Curti F., Serafim A., Olaret E., Dinescu S., Samoila I., Vasile B.S., Iovu H., Lungu A., Stancu I.C, & Marinescu R. (2022). Development of Biocomposite Alginate-Cuttlebone-Gelatin 3D Printing Inks Designed for Scaffolds with Bone Regeneration Potential. Marine Drugs, 20(11), 670.

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Scaffold Designs for Standardized Cell Seeding

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Two different scaffold structures are used in this study and designed using BioCAD software (RegenHU). Design 1 is round and has a porous grid structure. Design 2 is a round dense disc with only two layers and can be press-fit into 24-well-plates, especially practical for cell seeding. Using the discs (Design 2) for cell experiments allows for higher standardization of cell seeding and attachment on top of the biomaterial compared to the Design 1, which can lead to uneven cell-attachment starting point between groups. Scaffold dimensions and corresponding measurement are summarized in Table 2.

Hatt L.P., Wirth S., Ristaniemi A., Ciric D.J., Thompson K., Eglin D., Stoddart M.J, & Armiento A.R. (2023). Micro-porous PLGA/β-TCP/TPU scaffolds prepared by solvent-based 3D printing for bone tissue engineering purposes. Regenerative Biomaterials, 10, rbad084.

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3D Printing of Hydrogel Scaffolds

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Hydrogels were printed using a 3D Discovery Printer and BioCAD software (RegenHU, Villaz-St-Pierre, Switzerland). A solution of PNC was shortly mixed for 1 minute with a solution of PEG–NHS or HA–NHS, to a total concentration of 7.5–3.8 wt% PNC–PEG or 7.5–1.6 wt% PNC–HA, and transferred into a 3 or 10 mL syringe. The polymeric solutions were allowed to pre-crosslink for 30 min before starting filament deposition. A pressure of 3–4 bar was applied for pneumatic extrusion. A printing head movement speed in the x and y plane (F_xy) of 5 mm s⁻¹ and a layer height of 0.25 mm were used. Nordson EFD (Westlake, Ohio, USA) dispensing SmoothFlow tapered tips with an inner nozzle diameter of 0.25 mm was used that matched with the high solution viscosity. 3D-printing was performed using a heated plate of 37–40 °C. A red food coloring agent, Ponceau 4R, E number 124 was added to the HA–NHS solution in a concentration of 50 mL coloring agent per 1 mL HA solution to obtain additional visual contrast that allowed accurate evaluation of the porosity. Hydrogel porosity of the 3D-printed condyle shape PNC–PEG constructs was estimated after measuring the construct dimensions and weighing the construct, using the following equation:

(1 - \frac{hydorgel weight (mg)}{hydrogel volume ({mm}^{3})}) \times 100 %

Boere K.W., Blokzijl M.M., Visser J., Linssen J.E., Malda J., Hennink W.E, & Vermonden T. (2015). Biofabrication of reinforced 3D-scaffolds using two-component hydrogels. Journal of materials chemistry. B, 3(46), 9067-9078.

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Bioink Extrusion-based 3D Printing

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To evaluate bioinks shape fidelity, the extrusion-based 3D printing of GelMA or GelMA-LAP (1wt%) bioinks was performed using a 3D Discovery bioprinter (RegenHU, Villaz-Saint-Pierre, Switzerland). Pre-polymer solutions were fabricated at elevated temperatures and loaded into a 3D Discovery bioprinter and protected from light. Computer aided design models were created using the BIOCAD software (3DDiscoverGS, RegenHU, Villaz-Saint-Pierre, Switzerland). The bioinks were extruded using a computer-aided syringe dispenser with a 20-gauge needle, a feed rate of 3 mm/s and pressure of 10 bar. Constructs were printed within a 6 well plate and irradiated for 5 min with visible light using the same Ru/SPS photoinitiator concentrations as described above.

Man K., Barroso I.A., Brunet M.Y., Peacock B., Federici A.S., Hoey D.A, & Cox S.C. (2022). Controlled Release of Epigenetically-Enhanced Extracellular Vesicles from a GelMA/Nanoclay Composite Hydrogel to Promote Bone Repair. International Journal of Molecular Sciences, 23(2), 832.

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3D Bioprinting Workflow with Multimodal Visualization

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The 3D Discovery was controlled by the HMI (Human Machine Interface) Software (regenHU 3D Discovery 8.23.9.38, regenHU, Villaz-St-Pierre, Switzerland). Scaffold design and G code generation was done using the BioCAD software (regenHU, Villaz-St-Pierre, Switzerland). MRI was operated with ParaVision 6.0.1 (Bruker BioSpin MRI GmbH). Data processing and plotting was performed with MATLAB R2020a (The MathWorks, Inc., Natick, United States). ImageJ software [National Institutes of Health (NIH), Bethesda, MD] was used for conversion of pseudo color z-stacks to NIftI file format as described in (Stefani et al., 2018 (link)). VR visualization of the MRI data was done using the Software ConfocalVR 3.2 (Immersive Science LLC, Newcastle, WA, United States) (Stefani et al., 2018 (link)). The video was recorded using NVIDIA^® GeForce^® Experience™ Version 3.23.0.74 and put together using DaVinci Resolve 17 (Blackmagic Design Pty. Ltd., Port Melbourne, Australia). Single frame isolation (taking snap shots) was also performed using DaVinci Resolve 17 (Blackmagic Design Pty. Ltd., Port Melbourne, Australia).

Gretzinger S., Schmieg B., Guthausen G, & Hubbuch J. (2022). Virtual Reality as Tool for Bioprinting Quality Inspection: A Proof of Principle. Frontiers in Bioengineering and Biotechnology, 10, 895842.

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3D Printing of Polymeric Scaffold Structures

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An extrusion-based 3D printing system (3D Discovery, regenHU, Switzerland) equipped with a screw-driven printing head and a 330 µm nozzle was selected for the fabrication of both PCL and PEU scaffolds. Adopting a methodology previously published by our group, rectangular prisms measuring 20 mm (length) × 20 mm (width) × 4 mm (height) were initially designed using BioCAD software (regenHU, Switzerland) and subsequently printed employing an optimised set of parameters (Table 1). The internal pore geometry (quadrangular) was defined by keeping a constant filament distance of 830 µm and alternating the deposition angle of adjacent layers between 0° and 90°. The obtained scaffolds were then cut into smaller specimens and used for further analyses.

Moxon S.R., Ferreira M.J., dos Santos P., Popa B., Gloria A., Katsarava R., Tugushi D., Serra A.C., Hooper N.M., Kimber S.J., Fonseca A.C, & Domingos M.A. (2020). A Preliminary Evaluation of the Pro-Chondrogenic Potential of 3D-Bioprinted Poly(ester Urea) Scaffolds. Polymers, 12(7), 1478.

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3D Bioprinted Scaffold Fabrication

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A multiheaded 3D Discovery
bioprinter (RegenHU, Switzerland) was used to print the scaffolds.
A high precision plunger dispenser was used at a constant volume flow
rate of 1.5 μL/s using a stainless-steel needle with an inner
diameter of 0.41 mm, at 10 mm/s printing speed. The G-code for square
scaffolds was produced using BIOCAD software (RegenHU, Switzerland)
with 0.8 mm spacing. In situ UV-crosslinking was performed after the
deposition of each layer using the light curing cartridge at 365 nm
(500 mW).

García-Astrain C., Henriksen-Lacey M., Lenzi E., Renero-Lecuna C., Langer J., Piñeiro P., Molina-Martínez B., Plou J., Jimenez de Aberasturi D, & Liz-Marzán L.M. (2024). A Scaffold-Assisted 3D Cancer Cell Model for Surface-Enhanced Raman Scattering-Based Real-Time Sensing and Imaging. ACS Nano, 18(17), 11257-11269.

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