Microarrays are commonly used in literature, for their ease-of-integration within established biological and immunofluorescence assays (IFAs), the most common being sandwich enzymelinked immunosorbent assays (ELISAs). By combining microarrays and IFAs, target analytes and biomarkers are distinguishable, enhancing their applicability for diagnosing and monitoring disease in clinical and industrial settings. A variety of fabrication methods, including both non-contact and contact bioprinting techniques, are available for creating microarrays. Non-contact bioprinting techniques, such as piezoelectric, continuous inkjet, and drop-on-demand printing, offer the advantage of precise, high-speed deposition of bioinks onto substrates without direct contact. These methods are highly automated and suitable for large-scale production; however, they often face limitations when printing highly viscous bioinks or large biomolecules due to issues like nozzle clogging and reduced resolution. Additionally, non-contact systems can struggle to customize microarrays with intricate features, particularly when unique or complex patterns are required. In contrast, microcontact bioprinting (μCP), directly transfer bioinks from a patterned stamp onto the substrate, allowing for greater flexibility in feature design. μCPs can handle a wider range of bioink viscosities, including large and complex biomolecules, and offer enhanced customizability in terms of pattern geometry. However, contact bioprinting can face challenges with scalability and consistency in industrial settings due to the manual nature of the process. μCP involves the fabrication of a stamp with micron features made from elastomers that are flexible, affordable, and easily accessible. The micron features are cast utilizing a silicon mold and can be predesigned with unique and fine detailed patterns and microarrays. μCP involves the application of a bioink across the featured stamp surface, followed by physical force for direct biomolecule transfer onto substrates. The dimensions of the stamps allow microcontact printing to cover a wide surface area upon a single print, making it faster than non-contact methods such as pin or stencil printing, which often require multiple passes to print large areas. Traditionally, microcontact printing has two main limitations. It typically relies on the physical attachment of biomolecules to the surface, which reduces the robustness of the resulting microarrays. The introduction of cross-linking agents within the bioink to induce covalent attachment as well as additives to control fluid evaporation rates can be investigated in μCP for microarray development. Furthermore, the PDMS stamps used in the process can leave behind residue, leading to non-specific attachment and ultimately reducing the sensitivity in bioassays. μCP also has challenges in scalability for industry translation and is predominantly used in lab scale settings. This is mainly due to the lack of characterization and assessment of factors affecting the repeatability and reproducibility of μCP microarrays, resulting in low signal-to-noise ratios (SNRs) and high percentage coefficients of variance. We propose a fully characterized μCP protocol for repeatability and reproducibility. We developed a bioink formulation that enables covalent binding of biomolecules to the surface during microcontact printing. Additionally, we established a protocol that combines microcontact printing with fluorosilanization (FS) treatment to create a lubricant-infused surface, effectively preventing non-specific attachment. By exploring the role of surface interactions and covalent binding in biomolecule immobilization and optimizing the impact of external factors on the μCP process, we achieved SNRs exceeding 15, along with intra-assay and inter-assay %CVs below 10%. To address scalability and industrial translation, we present a proof-of-concept design that standardizes the μCP procedure, marking a significant step towards full automation for integration into industrial manufacturing lines.