{"paper_id":"38989834-2cf4-45f5-b8fa-d43ca8974eb4","body_text":"Investigation of Calcium Carbonate Particle Coating on Nanostructured Implant Surface for Biomedical Applications | Research Square window.SnipcartSettings = { analytics: { enabled: false } }; (function() { var accessVector = localStorage.getItem('access_vector') || ''; window.dataLayer = window.dataLayer || []; if (accessVector) { window.dataLayer.push({ user: { profile: { profileInfo: { snid: accessVector } } } }); } })(); (function(w,d,s,l,i){w[l]=w[l]||[];w[l].push({'gtm.start':new Date().getTime(),event:'gtm.js'});var f=d.getElementsByTagName(s)[0],j=d.createElement(s),dl=l!='dataLayer'?'&l='+l:'';j.async=true;j.src='https://www.googletagmanager.com/gtm.js?id='+i+dl;f.parentNode.insertBefore(j,f);})(window,document,'script','dataLayer','GTM-K279D39R'); Browse Preprints In Review Journals COVID-19 Preprints AJE Video Bytes Research Tools Research Promotion AJE Professional Editing AJE Rubriq About Preprint Platform In Review Editorial Policies Our Team Advisory Board Help Center Sign In Submit a Preprint Cite Share Download PDF Article Investigation of Calcium Carbonate Particle Coating on Nanostructured Implant Surface for Biomedical Applications Yasar Kemal Erdogan This is a preprint; it has not been peer reviewed by a journal. https://doi.org/ 10.21203/rs.3.rs-7059389/v1 This work is licensed under a CC BY 4.0 License Status: Posted Version 1 posted You are reading this latest preprint version Abstract Calcium carbonate (CaCO 3 ) have a high biocompatibility and biodegradability due to their chemical similarity to human bone tissue. Electrophoretic deposition (EPD) is an advanced technique used for obtaining biomedical coatings. This research is, for the first time, to investigate the effect of voltage and duration on the CaCO 3 coatings obtained by EPD on nanostructured 316L SS surface. SEM images showed that the proportion of calcium carbonate particles in the coating increased significantly with higher applied voltages. Additionally, an increase in coating thickness ( ̴20 µm) was observed with longer deposition durations. The successful incorporation of CaCO 3 in all coatings was confirmed by SEM and XRD analysis. Also, AFM analysis confirmed that coated surface performed rougher topography and morphology. These findings suggest that bioactive CaCO 3 coated on nanostructured 316L surface is promising surface for biomedical applications. Biological sciences/Biotechnology Physical sciences/Materials science Physical sciences/Nanoscience and technology Electrophoretic Deposition Calcium carbonate Implant Morphology Figures Figure 1 Figure 2 Figure 3 Figure 4 Figure 5 Figure 6 1. INTRODUCTION The progressive aging of the global population has led to a growing clinical demand for skeletal, bone, and dental repair, as age-related conditions become increasingly prevalent 1 . Commonly used metallic materials such as titanium and its alloys, stainless steel, and cobalt-chromium alloys are widely preferred as implant materials 2 , 3 . However, their bioinert nature results in poor cellular interaction and limited osseointegration. The lack of bioactivity of surface it is still major problem in dental and orthopedic applications 4 . In addition, bioinert surface may lead to wear debris that cause inflammation and corrosion of implant 5 . The global orthopedic implants market $ 45.2 billion in 2023, is anticipated to grow to $ 71.7 billion by 2032 6 . In the U.S., approximately 11% of orthopedic implants fail within 10 years, leading to an estimated $ 15 billion in annual medical care costs. Therefore, to eliminate the drawbacks of bioinert surfaces surface modification or coating process to create bioactive surface is critical and necessary 3 , 7 . Thus, improving bioactivity of implant surface could reduce failure rates, minimizes revision surgeries, and saves billions in healthcare 8 . Many ceramic materials can be preferred as a coating material, each one have distinct properties that affecting their bioactivity, degradation rate, and osseointegration 9 , 10 . For example, hydroxyapatite (HA) is widely used for implant coatings, but its high crystallinity can sometimes lead to slow resorption and weak bonding with bone 11 . In another study showed that silver/zirconia coatings on 316L surface performed higher corrosion resistance and antibacterial behavior 12 . Calcium carbonate (CaCO₃) is important in biomedical applications due to its biocompatibility, biodegradability, and favorable chemical properties 13 . Being a naturally abundant mineral in body, mostly in bone and teeth, which makes it inherently compatible with the human body 14 . Calcium carbonate provides a faster resorption rate, allowing better integration with natural bone remodeling processes 15 . The porous nature of CaCO₃ coating could enhance cell adhesion and proliferation. Moreover, a rougher surface could improve better interaction between the implant and bone 2 . In addition, CaCO₃ coatings help prevent fibrous tissue formation around the implant, which is a common cause of failure in orthopedic 14 . It supports the attachment, proliferation, and differentiation of osteoblasts, promoting new bone growth 16 . CaCO₃ particles can assist in wound healing by providing calcium ions, which play a role in cellular processes like blood clotting and tissue repair 17 . Thus, calcium carbonate coatings on implant surfaces are increasingly being explored for biomedical applications, particularly in orthopedic and dental implants. CaCO₃ occurs naturally in three crystalline polymorphs with different properties: Calcite, Aragonite and Vaterite. Vaterite has high surface area and solubility that supports rapid calcium ion release that beneficial for cell signaling and repair. Aragonite more similarity to the natural mineral that found in bones that promote osteoblast activity. Calcite is commonly used in drug delivery and bone scaffold 18 , 19 . Electrophoretic deposition (EPD) is one of most promising method to creating homogeneous coatings on metallic implants 20 , 21 . Especially, bioceramic like bioglass, hydroxyapatite or calcium carbonate have been used coated to varying thicknesses of implant surface for bone applications 22 , 23 , 24 . In EPD, nanoparticles dispersed in alcohol are deposited as a thin layer on the metallic surface that is used as an electrode under an applied electric field 25 . The electrophoretic deposition coating depends upon several factors, such as the applied voltage, deposition time, electrolyte concentration, and the condition of the substrate 21 , 26 . For example, the electrophoretic bioactive glass coated surface enhanced mesenchymal stem cells viability, attachment, and higher proliferation compared to the bare SS substrate 9 . In other study, TiO 2 nanotubes and gentamicin coated by electrophoretic deposition on 316L SS surface enhance the cell viability, and exhibit anti-microbial behavior with reduced cytotoxicity 27 . Mahlooji et al. showed that the electrophoretic deposition of chitosan-bioactive glass coating could successfully enhance the adhesion strength, bioactivity, corrosion and cellular performance of the bare surface 28 . In literature, there are a few studies have investigated CaCO₃ coatings on only bare stainless steel implant surfaces 29 . This study, for the first time, examined and fabricated the CaCO 3 particle coated on nanostructured 316L SS surface. The aim of the present work have creating a rougher with nanostructured morphology on 316L SS surface and, coated with highly biocompatible CaCO 3 particle to create bioactive surface to biomedical applications, as shown in Fig. 1 . The results showed that applied voltage play a vital role in thickness and uniformity of CaCO 3 coating process that fabricated bioactive nanosurface can be candidate for biomedical application. 2. MATERIAL AND METHODS The vaterite and aragonite particles were obtained according to previously study of our research groups 18 . In briefly, the CaCO 3 particles were synthesis at room temperature using a precipitation reaction between calcium acetate and sodium bicarbonate. In this process, calcium acetate and sodium bicarbonate were separately dissolved in 4 ml ultrapure water at various calcium (Ca 2+ ) : carbonate (CO 3 2− ) ratios, followed by addition of 20 ml ethylene glycol to solution. After pH values of the solutions were adjusted, they were mixed with each other under magnetic agitation at 800 rpm for 15 min. Then, CaCO 3 particles formed inside the solution were washed with ethanol and deionized water, respectively, collected by centrifugation (7200 rpm, 15 min, 22°C) and dried overnight at 50°C. A 316L stainless SS foil (0.5 mm) was cut into 1×1cm 2 sized samples. Prior to electrophoretic deposition, the samples were ultrasonically cleaned in acetone, ethanol, and distilled water each for 10 min. Then, anodization process (80V for 1 min) was applied to obtained rougher nanostructured morphologies on the surface according to previous study 3031 . In order to coating process, electrophoretic deposition was used that stainless steel as cathode and platin as anode. Electrodes were connected to a power supply (Genesys 300 V/5, TDK Lambda) and the distance between the electrodes was 10 mm. The electrolyte solutions were prepared as 0.06g vaterite + 1M HCI in 60ml ethanol. During EPD process, 60V, 90V and 120V was applied for 5 min, 1 min and 1 min to vaterite coating. The coated surface morphology of the samples was characterized with scanning electron microscopy (SEM, FEI Nova Nano 430) using secondary electrons. Surface topography was examined by atomic force microscopy (AFM, Veeco Multimode V). The surface roughness values were obtained using Image Plus software. To identify coated CaCO 3 polymorphs of surface was carried out using Rigaku D/Max-2200 X-ray diffractometer with monochromatic Cu Kα radiation (λ = 1.54 Å) using a power supply of 30 mA and 40 kV. 20° to 60° diffraction angles (2θ) were scanned at a scanning rate of 2°/min. 3. RESULTS AND DISCUSSION The nanostructured surface was obtained via anodization of bare stainless-steel samples. Figure 2 a showed bare implant and nanostructured surfaces. It was created about 250nm feature sized by applied 80V for 1min, which detailed optimized in previous research 30 . The results showed that anodization process created unique nanotopography on surface. In addition, surface became more rougher, surface chemistry, hydrophobicity and surface charge changed, and surface area increased after anodization process 32 , 33 . Thus, increased surface area with negatively charged surfaces could provide higher amount of calcium deposition compared to bare surface. Figure 2 b showed that initial process of calcium carbonate coating on nanostructured surface via electrophoretic deposition under 60V for 1 min. It was observed that calcium carbonate particles interacted with the surface layer directly and began forming thin layers on nanostructured surfaces (indicated by the red arrow). However, the limited amount of calcium carbonate coated on the surface was observed due to inefficient coating duration. Therefore, both nanostructures and partial particles were observed on the surface (indicated by the white arrow). As show in Fig. 2 c, SEM image confirmed that thin and compact layer of CaCO₃ occurred on the surface. The thin layer likely forms first as homogeneous nucleation on the surface, followed by growth of crystallites into larger, organized calcium carbonate structures. Especially, the underlying rougher nanostructured surface can guide the orientation or density of CaCO₃ deposition due to enhanced surface energy or charge. It provides a chemically favorable and structurally aligned base for oriented crystal growth of CaCO₃, ensuring strong adhesion and integration with the nanostructured surface. This layer is crucial because it bridges the nanostructure, forming a stabile layer and integrates with the surface topology. The effect of applied voltage on coating process was shown in Fig. 3 . The partial CaCO₃ coated on surface was observed after 60V applied for 1 min. When increased the applied voltage, it accelerates particle coated on the surface. The uniform thin layer on surface was observed by 90V for 1 min. Especially, uniform and thicker CaCO₃ layer was observed by 120V for min. This effect can be explained as higher voltage increases the electric field strength, which accelerates the migration of Ca²⁺ and CO₃²⁻ ions toward the implant surface. As voltage increases, the rate of deposition accelerates, resulting in thicker coatings was observed in a shorter time. This boosts local supersaturation at the electrode–solution interface, leading to faster nucleation and growth of CaCO₃ crystals. On the other hand, it can be possible fabricated thicker coated surface as increased duration by applied lower voltages. Figure 3 confirmed that a uniform and thicker surface was obtained for 5 min by applying 60V, while a partially coated surface was observed for 1 min. Figure 3 . SEM micrographs of coating Aragonite particle on nanostructured surface by applied 60V, 90V and 120V for 1 min. The right SEM imaged showed increased the coating duration to 5 min created uniform coated layer. The other crystalline polymorphs type of CaCO₃, which vaterite, coating on nanostructure surface was investigated in Fig. 3 . This figure showed that applied voltages and coating duration effect coating morphology. When 60V was applied for 5 min, a uniform and thick layer of calcium carbonate coated was observed on the surface. On the other hand, when applied voltage increased, which applied 90V for 1 min, a uniform calcium coated surface was also observed. In addition, a fully coated surface was obtained by applying 120V, even though the duration was decreased to 30 sec. These results clearly showed that applied voltages play important role in coating process. As the applied voltages increased, it provides enhanced deposition coating kinetics. Also, coating duration play critical role in process that more calcium was deposited, and thickness increased on the surface as coating duration increased. On the other hand, electrolyte pH and temperature could also influence coating process. Azari et al. showed that different temperatures revealed an increasing trend in electrophoretic mobility, suspension conductivity, and current density with temperature rise 20 . However, higher temperatures could lead to agglomeration of particles and instability of suspension. The optimal coating was found as 35 o C for the bioactive glass deposited on 316L SS 20 . XRD analysis confirmed to CaCO₃ particles on a nanostructured surface, as shown in Fig. 4 . The diffraction patterns indicated the crystalline nature of the deposited particles, confirming the presence of distinct CaCO₃ polymorphs on the surfaces. Peak intensities and positions were analyzed to determine phase composition, crystallite size, and structural characteristics. XRD spectra analysis showed characteristic peaks of vaterite at 24.9°, 26.9° and 32.7° corresponding to (110), (112) and (114) crystallographic planes and calcite at 29.4°, 35.9° and 39.5° corresponding to crystallographic planes of (104), (110) and (113), respectively 18 . These findings provide insights into the nucleation and growth mechanisms of CaCO₃ on the modified surface, which is crucial for applications in biomineralization, catalysis, and material engineering. Presence of calcite as a minor polymorph for CaCO 3 particles synthesized via solution mixing method was an expected finding due to the unstable nature of vaterite at ambient conditions and electrolyte solutions, demonstrating ease of transformation from vaterite to calcite polymorph. Figure 5 indicated the roughness profiles of sample surfaces. These figures showed that coating process created a rougher and unique nanotopography on the surfaces. The mean roughness value calculated from the AFM analysis were 1.9, 18.5, 16.7, and 17.8 nm for the NA, C60V, C90V and C120V, respectively. It was clear that the nanoroughness of surface increased upon coating process compared to bare surface. It should be noted that the surface roughness parameters could affect cell interaction and viability and stem cell differentiation 34 , 35 . Furthermore, the presence of calcium ions on the surface is highly expected to enhance osteointegration 36 . Similarly, successfully electrophoretic deposition of nanoHAp coatings on Ti6Al4V surface with higher surface roughness was obtained. It was observed that bioactive coated surface significantly enhanced osteoblast attachment and proliferation 37 . It should be considered that calcium ion on the surface could affect fibronectin and vitronectin protein adsorption due to positively charged of calcium that influence cell adhesion and proliferation 38 . Especially, Oral et al. found that ellipsoidal vaterite and spherical calcite particles exhibited higher CaCO 3 -to-Hydroxyapatite conversion and enhance osteoblast proliferation 19 . On the other, the nanostructured 316L stainless steel surface exhibited a higher Cr₂O₃ peak intensity, which enhanced corrosion resistance based on previous studies 32 . Furthermore, ceramic coatings on the nanostructured surface are expected to further improve corrosion resistance. These ceramics coated layer could also improve the corrosion resistance of implant. Similarly, Katic et al. showed that electrodeposited CaP coating provides improved corrosion resistance and protects the titanium alloy in an aggressive environment 39 . In addition, fabricated calcium coated implant surface potentially enhances osteointegration for biomedical application. In this study, a nanostructured implant surface combined with calcium carbonate was developed, highlighting the potential of this approach to enhance osseointegration for biomedical applications. The results demonstrated that the proportion of calcium carbonate particles in the coating increased significantly with higher applied voltages, and coating thickness grew with longer deposition durations. These findings suggest that this surface modification strategy may improve implant performance; however, further studies are recommended to investigate and evaluate the mechanical properties and cellular interactions more comprehensively. 4. CONCLUSIONS Calcium carbonate coating were successfully fabricated on the nanostructured 316L SS alloy using electrophoretic deposition. The results showed that applied voltages, duration, and solubility significantly influenced the coating process on surface. SEM and XRD results confirmed the successful coating of the CaCO 3 on the nanostructured 316L SS surface by applied 60V, 90V and 120V. Notably, a uniform, homogeneous, and crack-free coating was obtained at 60 V for 5 min. The results indicate the formation of calcium carbonate coating on implant surface could improve osteointegration due to biological calcium ions as a major component of bone. Overall, the CaCO 3 coating with nanostructured implant surface could have a great potential for use in orthopedic and dental applications. Declarations Author Contribution The author conducted the research and wrote the main manuscript. Acknowledgement The author would like to thank Assoc. Prof. Batur Ercan for providing research equipment, and METU/METE for SEM and XRD analysis and Ercan Research Group. The author would also like to express special thanks to Beyza Tarhan for her help during the experiments. Data Availability The datasets used and/or analyzed during the current study are available from the corresponding author on reasonable request. References Bandyopadhyay, A., Mitra, I., Goodman, S. B., Kumar, M. & Bose, S. Improving Biocompatibility for next Generation of Metallic Implants. Prog. Mater. Sci. 133 (July 2021), 101053. (2023). https://doi.org/10.1016/j.pmatsci.2022.101053 Liu, Z., Liu, X. & Ramakrishna, S. Surface Engineering of Biomaterials in Orthopedic and Dental Implants: Strategies to Improve Osteointegration, Bacteriostatic and Bactericidal Activities. Biotechnol. J. 16 (7), 1–23. https://doi.org/10.1002/biot.202000116 (2021). Florea, D. A., Albuleț, D., Grumezescu, A. M. & Andronescu, E. Surface Modification – A Step Forward to Overcome the Current Challenges in Orthopedic Industry and to Obtain an Improved Osseointegration and Antimicrobial Properties. Mater. Chem. Phys. 243 (August 2019), 122579. (2020). https://doi.org/10.1016/j.matchemphys.2019.122579 Staruch, R., Griffin, M. & Butler, P. Nanoscale Surface Modifications of Orthopaedic Implants: State of the Art and Perspectives. Open. Orthop. J. 10 (1), 920–938. https://doi.org/10.2174/1874325001610010920 (2017). Manam, N. S. et al. H. I. Study of Corrosion in Biocompatible Metals for Implants: A Review. J. Alloys Compd. 701 , 698–715. https://doi.org/10.1016/j.jallcom.2017.01.196 (2017). Mizori, R. et al. The Cost of Implant Waste in Trauma Orthopaedic Surgery and Sustainability Considerations: An Observational Study. Int. Orthop. https://doi.org/10.1007/s00264-025-06532-1 (2025). Benčina, M. et al. Enhanced Hemocompatibility and Cytocompatibility of Stainless Steel. ACS Omega . 9 (17), 19566–19577. https://doi.org/10.1021/acsomega.4c01191 (2024). Hodges, N. A., Sussman, E. M. & Stegemann, J. P. Aseptic and Septic Prosthetic Joint Loosening: Impact of Biomaterial Wear on Immune Cell Function, Inflammation, and Infection. Biomaterials 278 (January), 121127. https://doi.org/10.1016/j.biomaterials.2021.121127 (2021). Hadem, H. et al. Electrophoretic Deposition of 58S Bioactive Glass- Polymer Composite Coatings on 316L Stainless Steel: An Optimization for Corrosion, Bioactivity, and Cytocompatibility. ACS Appl. Bio Mater. 7 (5), 2966–2981. https://doi.org/10.1021/acsabm.4c00037 (2024). Rasouli, R., Barhoum, A. & Uludag, H. A. Review of Nanostructured Surfaces and Materials for Dental Implants: Surface Coating, Patterning and Functionalization for Improved Performance. Biomater. Sci. 6 (6), 1312–1338. https://doi.org/10.1039/c8bm00021b (2018). Mohandesnezhad, S., Etminanfar, M., Mahdavi, S. & Safavi, M. S. Enhanced Bioactivity of 316L Stainless Steel with Deposition of Polypyrrole/Hydroxyapatite Layered Hybrid Coating: Orthopedic Applications. Surfaces and Interfaces 28 (November 2021), 101604. (2022). https://doi.org/10.1016/j.surfin.2021.101604 Atasoy, S. et al. The Fabrication of Silver/Zirconia Coatings: Characterization, Corrosion and Antibacterial Properties. Ceram. Int. https://doi.org/https://doi.org/10.1016/j.ceramint.2025.05.276 (2025). Sokolova, V. & Epple, M. Biological and Medical Applications of Calcium Phosphate Nanoparticles. Chem. - Eur. J. 27 (27), 7471–7488. https://doi.org/10.1002/chem.202005257 (2021). Drevet, R., Fauré, J. & Benhayoune, H. Bioactive Calcium Phosphate Coatings for Bone Implant Applications: A Review. Coatings 13 (6). https://doi.org/10.3390/coatings13061091 (2023). Eliaz, N. & Metoki, N. Calcium Phosphate Bioceramics: A Review of Their History, Structure, Properties, Coating Technologies and Biomedical Applications. Mater. (Basel) . 10 (4). https://doi.org/10.3390/ma10040334 (2017). Huang, Y. et al. Bone-Targeting Cell Membrane-Engineered CaCO3-Based Nanoparticles Restore Local Bone Homeostasis for Microenvironment-Responsive Osteoporosis Treatment. Chem. Eng. J. 470 (January), 144145. https://doi.org/10.1016/j.cej.2023.144145 (2023). Wang, S. et al. E. G. Acceleration of Wound Healing through Amorphous Calcium Carbonate, Stabilized with High-Energy Polyphosphate. Pharmaceutics 15 (2), 1–20. https://doi.org/10.3390/pharmaceutics15020494 (2023). Oral, Ç. M. & Ercan, B. Influence of PH on Morphology, Size and Polymorph of Room Temperature Synthesized Calcium Carbonate Particles. Powder Technol. 339 , 781–788. https://doi.org/10.1016/j.powtec.2018.08.066 (2018). Oral, Ç. M., Çalışkan, A., Kapusuz, D. & Ercan, B. Facile Control of Hydroxyapatite Particle Morphology by Utilization of Calcium Carbonate Templates at Room Temperature. Ceram. Int. 46 (13), 21319–21327. https://doi.org/10.1016/j.ceramint.2020.05.226 (2020). Azari, R. & Boccaccini, A. R. Effect of Processing Temperature on Electrophoretic Deposition (EPD)-Derived Bioactive Composite Coatings for Metallic Bone Implants. Surfaces and Interfaces 58 (November 2024), 105771. (2025). https://doi.org/10.1016/j.surfin.2025.105771 Zielinski, A. & Bartmanski, M. Electrodeposited Biocoatings, Their Properties and Fabrication Technologies: A Review ; ; Vol. 10. (2020). https://doi.org/10.3390/COATINGS10080782 Sorkhi, L., Farrokhi-Rad, M. & Shahrabi, T. Electrophoretic Deposition of Hydroxyapatite–Chitosan–Titania on Stainless Steel 316 L. Surfaces 2 (3), 458–467. https://doi.org/10.3390/surfaces2030034 (2019). Mohammadsadegh, A., Allahkaram, S. R. & Gharagozlou, M. Electrophoretic Deposition of Chitosan/Gelatin/Hydroxyapatite Nanocomposite Coatings on 316 L Stainless Steel for Biomedical Applications. Biomed. Mater. 20 (1). https://doi.org/10.1088/1748-605X/ad98d6 (2024). Safavi, M. S., Walsh, F. C., Surmeneva, M. A., Surmenev, R. A. & Khalil-Allafi, J. Electrodeposited Hydroxyapatite-Based Biocoatings: Recent Progress and Future Challenges. Coatings 11 (1), 1–62. https://doi.org/10.3390/coatings11010110 (2021). Al-Rashidy, Z. M., Farag, M. M., Ghany, N. A. A., Ibrahim, A. M. & Abdel-Fattah, W. I. Aqueous Electrophoretic Deposition and Corrosion Protection of Borate Glass Coatings on 316 L Stainless Steel for Hard Tissue Fixation. Surf. Interfaces . 7 (January), 125–133. https://doi.org/10.1016/j.surfin.2017.03.010 (2017). Mehdipour, M., Afshar, A. & Mohebali, M. Electrophoretic Deposition of Bioactive Glass Coating on 316L Stainless Steel and Electrochemical Behavior Study. Appl. Surf. Sci. 258 (24), 9832–9839. https://doi.org/10.1016/j.apsusc.2012.06.038 (2012). Gutiérrez-Mejía, F. A. et al. Electrophoretic Deposition of TiO2 Nanotubes and Antibiotics on Polyurethane Coated Stainless Steel for Improved Antibacterial Response and Cell Viability. Mater. Today Commun. 40 (March). https://doi.org/10.1016/j.mtcomm.2024.109428 (2024). Mahlooji, E., Atapour, M. & Labbaf, S. Electrophoretic Deposition of Bioactive Glass – Chitosan Nanocomposite Coatings on Ti-6Al-4V for Orthopedic Applications. Carbohydr. Polym. 226 (September), 115299. https://doi.org/10.1016/j.carbpol.2019.115299 (2019). Drevet, R. & Benhayoune, H. Electrodeposition of Calcium Phosphate Coatings on Metallic Substrates for Bone Implant Applications: A Review. Coatings 12 (4). https://doi.org/10.3390/coatings12040539 (2022). Erdogan, Y. K. & Ercan, B. Anodized Nanostructured 316L Stainless Steel Enhances Osteoblast Functions and Exhibits Anti-Fouling Properties. ACS Biomater. Sci. Eng. 9 (2), 693–704. https://doi.org/10.1021/acsbiomaterials.2c01072 (2023). Erdogan, Y. K. et al. Morphology of Nanostructured Tantalum Oxide Controls Stem Cell Differentiation and Improves Corrosion Behavior. ACS Biomater. Sci. Eng. 10 (1), 377–390. https://doi.org/10.1021/acsbiomaterials.3c01277 (2024). Erdogan, Y. K., Mutlu, P. & Ercan, B. Nanostructured 316L Stainless Steel Stent Surfaces Improve Corrosion Resistance, and Enhance Endothelization and Hemocompatibility. Adv. Mater. Interfaces 2400968 . (2025). https://doi.org/10.1002/admi.202400968 Piszczek, P. et al. Comprehensive Evaluation of the Biological Properties of Surface-Modified Titanium Alloy Implants. J. Clin. Med. 9 (2), 1–30. https://doi.org/10.3390/jcm9020342 (2020). Xia, J., Yuan, Y., Wu, H., Huang, Y. & Weitz, D. A. Decoupling the Effects of Nanopore Size and Surface Roughness on the Attachment, Spreading and Differentiation of Bone Marrow-Derived Stem Cells. Biomaterials 248 , 120014. https://doi.org/https://doi.org/10.1016/j.biomaterials.2020.120014 (2020). Gardin, C. et al. Nanostructured Modifications of Titanium Surfaces Improve Vascular Regenerative Properties of Exosomes Derived from Mesenchymal Stem Cells: Preliminary in Vitro Results. Nanomaterials 11 (12). https://doi.org/10.3390/nano11123452 (2021). Kazimierczak, P. & Przekora, A. Osteoconductive and Osteoinductive Surface Modifications of Biomaterials for Bone Regeneration: A Concise Review. Coatings 10 (10), 1–25. https://doi.org/10.3390/coatings10100971 (2020). Suntharavel Muthaiah, V. M., Rajput, M., Tripathi, A., Suwas, S. & Chatterjee, K. Electrophoretic Deposition of Nanocrystalline Calcium Phosphate Coating for Augmenting Bioactivity of Additively Manufactured Ti-6Al-4V. ACS Mater. Au . 2 (2), 132–142. https://doi.org/10.1021/acsmaterialsau.1c00043 (2022). Lee, W. H., Loo, C. Y. & Rohanizadeh, R. A. Review of Chemical Surface Modification of Bioceramics: Effects on Protein Adsorption and Cellular Response. Colloids Surf. B Biointerfaces . 122 , 823–834. https://doi.org/10.1016/j.colsurfb.2014.07.029 (2014). Katić, J., Krivačić, S., Petrović, Ž., Mikić, D. & Marciuš, M. Titanium Implant Alloy Modified by Electrochemically Deposited Functional Bioactive Calcium Phosphate Coatings. Coatings 13 (3). https://doi.org/10.3390/coatings13030640 (2023). Additional Declarations No competing interests reported. Supplementary Files SupplementaryFigure.docx Cite Share Download PDF Status: Posted Version 1 posted You are reading this latest preprint version Research Square lets you share your work early, gain feedback from the community, and start making changes to your manuscript prior to peer review in a journal. As a division of Research Square Company, we’re committed to making research communication faster, fairer, and more useful. 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Also discoverable on Platform About Our Team In Review Editorial Policies Advisory Board Help Center Resources Author Services Accessibility API Access RSS feed Manage Cookie Preferences © Research Square 2026 | ISSN 2693-5015 (online) Privacy Policy Terms of Service Do Not Sell My Personal Information {\"props\":{\"pageProps\":{\"initialData\":{\"identity\":\"rs-7059389\",\"acceptedTermsAndConditions\":true,\"allowDirectSubmit\":true,\"archivedVersions\":[],\"articleType\":\"Article\",\"associatedPublications\":[],\"authors\":[{\"id\":492756406,\"identity\":\"88a6999c-5d5c-4f45-86c0-f8aad24bace0\",\"order_by\":0,\"name\":\"Yasar Kemal Erdogan\",\"email\":\"data:image/png;base64,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\",\"orcid\":\"\",\"institution\":\"Isparta University of Applied Science\",\"correspondingAuthor\":true,\"prefix\":\"\",\"firstName\":\"Yasar\",\"middleName\":\"Kemal\",\"lastName\":\"Erdogan\",\"suffix\":\"\"}],\"badges\":[],\"createdAt\":\"2025-07-06 18:08:07\",\"currentVersionCode\":1,\"declarations\":\"\",\"doi\":\"10.21203/rs.3.rs-7059389/v1\",\"doiUrl\":\"https://doi.org/10.21203/rs.3.rs-7059389/v1\",\"draftVersion\":[],\"editorialEvents\":[],\"editorialNote\":\"\",\"failedWorkflow\":false,\"files\":[{\"id\":88014437,\"identity\":\"4dcae24c-b2c5-461b-83ce-201ecaff3747\",\"added_by\":\"auto\",\"created_at\":\"2025-07-31 12:41:15\",\"extension\":\"png\",\"order_by\":1,\"title\":\"Figure 1\",\"display\":\"\",\"copyAsset\":false,\"role\":\"figure\",\"size\":357524,\"visible\":true,\"origin\":\"\",\"legend\":\"\\u003cp\\u003eSchematic showing the experiments conducted in this study. a) Fabrication of nanostructured surface via anodization. b) Schematics of the electrodeposition of CaCO\\u003csub\\u003e3\\u003c/sub\\u003e on nanostructured 316L SS surface. c) SEM images of coated surface and characterization.\\u003c/p\\u003e\",\"description\":\"\",\"filename\":\"1.png\",\"url\":\"https://assets-eu.researchsquare.com/files/rs-7059389/v1/2052d122524c18b297ee7cb9.png\"},{\"id\":88014439,\"identity\":\"763bb316-bad6-453b-9f8b-db95d4ff9dcf\",\"added_by\":\"auto\",\"created_at\":\"2025-07-31 12:41:15\",\"extension\":\"png\",\"order_by\":2,\"title\":\"Figure 2\",\"display\":\"\",\"copyAsset\":false,\"role\":\"figure\",\"size\":670887,\"visible\":true,\"origin\":\"\",\"legend\":\"\\u003cp\\u003eSEM micrographs of a) bare and nanostructured surfaces. SEM images shows the b) initial formation of a thin layer on the surface during the coating process, and c) the bottom and side views of the CaCO₃ thin layer.\\u003c/p\\u003e\",\"description\":\"\",\"filename\":\"2.png\",\"url\":\"https://assets-eu.researchsquare.com/files/rs-7059389/v1/2a338d4aa934b31652ad909b.png\"},{\"id\":88014438,\"identity\":\"84f30232-9297-4280-ac29-21c196ca86ae\",\"added_by\":\"auto\",\"created_at\":\"2025-07-31 12:41:15\",\"extension\":\"jpg\",\"order_by\":3,\"title\":\"Figure 3\",\"display\":\"\",\"copyAsset\":false,\"role\":\"figure\",\"size\":556822,\"visible\":true,\"origin\":\"\",\"legend\":\"\\u003cp\\u003eSEM micrographs of coating Aragonite particle on nanostructured surface by applied 60V, 90V and 120V for 1 min. The right SEM imaged showed increased the coating duration to 5 min created uniform coated layer.\\u003c/p\\u003e\",\"description\":\"\",\"filename\":\"3.jpg\",\"url\":\"https://assets-eu.researchsquare.com/files/rs-7059389/v1/9157fc5e46b764005bd18393.jpg\"},{\"id\":88015418,\"identity\":\"fcb86bab-d949-48aa-a01d-0e77715b744b\",\"added_by\":\"auto\",\"created_at\":\"2025-07-31 12:57:15\",\"extension\":\"png\",\"order_by\":4,\"title\":\"Figure 4\",\"display\":\"\",\"copyAsset\":false,\"role\":\"figure\",\"size\":710057,\"visible\":true,\"origin\":\"\",\"legend\":\"\\u003cp\\u003e\\u003cstrong\\u003eFigure 3. \\u003c/strong\\u003eSEM micrographs of coating Vaterite particle on nanostructured surface by applied 60V, 90V and 120V.\\u003c/p\\u003e\",\"description\":\"\",\"filename\":\"4.png\",\"url\":\"https://assets-eu.researchsquare.com/files/rs-7059389/v1/a185af8e83ae2c25a39cb1db.png\"},{\"id\":88014651,\"identity\":\"75e2019f-1386-4e22-a9fc-87ed0add4f5b\",\"added_by\":\"auto\",\"created_at\":\"2025-07-31 12:49:15\",\"extension\":\"png\",\"order_by\":5,\"title\":\"Figure 5\",\"display\":\"\",\"copyAsset\":false,\"role\":\"figure\",\"size\":259620,\"visible\":true,\"origin\":\"\",\"legend\":\"\\u003cp\\u003e\\u003cstrong\\u003eFigure 4. \\u003c/strong\\u003eXRD pattern of coating vaterite of CaCO3 by 60V, 90V and 120V surfaces.\\u003c/p\\u003e\",\"description\":\"\",\"filename\":\"5.png\",\"url\":\"https://assets-eu.researchsquare.com/files/rs-7059389/v1/4c6263fc5e1b8718e2b323f3.png\"},{\"id\":88015419,\"identity\":\"6b66f8d2-9e68-444f-9b14-21404e8fac36\",\"added_by\":\"auto\",\"created_at\":\"2025-07-31 12:57:15\",\"extension\":\"png\",\"order_by\":6,\"title\":\"Figure 6\",\"display\":\"\",\"copyAsset\":false,\"role\":\"figure\",\"size\":425724,\"visible\":true,\"origin\":\"\",\"legend\":\"\\u003cp\\u003e\\u003cstrong\\u003eFigure 5. \\u003c/strong\\u003eAFM micrographs of control and CaCO\\u003csub\\u003e3\\u003c/sub\\u003e coated nanostructured surfaces and its roughness values.\\u003c/p\\u003e\",\"description\":\"\",\"filename\":\"6.png\",\"url\":\"https://assets-eu.researchsquare.com/files/rs-7059389/v1/5cefb200cdbbce1a7b1fccb4.png\"},{\"id\":99796773,\"identity\":\"c0f96832-3ede-43d2-a6f5-fbb62b42489a\",\"added_by\":\"auto\",\"created_at\":\"2026-01-08 13:43:32\",\"extension\":\"pdf\",\"order_by\":0,\"title\":\"\",\"display\":\"\",\"copyAsset\":false,\"role\":\"manuscript-pdf\",\"size\":3715829,\"visible\":true,\"origin\":\"\",\"legend\":\"\",\"description\":\"\",\"filename\":\"manuscript.pdf\",\"url\":\"https://assets-eu.researchsquare.com/files/rs-7059389/v1/96f17a64-f811-4e77-9ba9-b3e7e5b238b0.pdf\"},{\"id\":88014446,\"identity\":\"d06fcda7-5cef-4925-8b3c-dc0e3cdace63\",\"added_by\":\"auto\",\"created_at\":\"2025-07-31 12:41:15\",\"extension\":\"docx\",\"order_by\":1,\"title\":\"\",\"display\":\"\",\"copyAsset\":false,\"role\":\"supplement\",\"size\":843036,\"visible\":true,\"origin\":\"\",\"legend\":\"\",\"description\":\"\",\"filename\":\"SupplementaryFigure.docx\",\"url\":\"https://assets-eu.researchsquare.com/files/rs-7059389/v1/0c400b401d1fb6fd7e7c4601.docx\"}],\"financialInterests\":\"No competing interests reported.\",\"formattedTitle\":\"Investigation of Calcium Carbonate Particle Coating on Nanostructured Implant Surface for Biomedical Applications\",\"fulltext\":[{\"header\":\"1. INTRODUCTION\",\"content\":\"\\u003cp\\u003eThe progressive aging of the global population has led to a growing clinical demand for skeletal, bone, and dental repair, as age-related conditions become increasingly prevalent\\u003csup\\u003e\\u003cspan citationid=\\\"CR1\\\" class=\\\"CitationRef\\\"\\u003e1\\u003c/span\\u003e\\u003c/sup\\u003e. Commonly used metallic materials such as titanium and its alloys, stainless steel, and cobalt-chromium alloys are widely preferred as implant materials\\u003csup\\u003e\\u003cspan citationid=\\\"CR2\\\" class=\\\"CitationRef\\\"\\u003e2\\u003c/span\\u003e,\\u003cspan citationid=\\\"CR3\\\" class=\\\"CitationRef\\\"\\u003e3\\u003c/span\\u003e\\u003c/sup\\u003e. However, their bioinert nature results in poor cellular interaction and limited osseointegration. The lack of bioactivity of surface it is still major problem in dental and orthopedic applications\\u003csup\\u003e\\u003cspan citationid=\\\"CR4\\\" class=\\\"CitationRef\\\"\\u003e4\\u003c/span\\u003e\\u003c/sup\\u003e. In addition, bioinert surface may lead to wear debris that cause inflammation and corrosion of implant\\u003csup\\u003e\\u003cspan citationid=\\\"CR5\\\" class=\\\"CitationRef\\\"\\u003e5\\u003c/span\\u003e\\u003c/sup\\u003e. The global orthopedic implants market \\u003cspan\\u003e$\\u003c/span\\u003e45.2\\u0026nbsp;billion in 2023, is anticipated to grow to \\u003cspan\\u003e$\\u003c/span\\u003e71.7\\u0026nbsp;billion by 2032\\u003csup\\u003e6\\u003c/sup\\u003e. In the U.S., approximately 11% of orthopedic implants fail within 10 years, leading to an estimated \\u003cspan\\u003e$\\u003c/span\\u003e15\\u0026nbsp;billion in annual medical care costs. Therefore, to eliminate the drawbacks of bioinert surfaces surface modification or coating process to create bioactive surface is critical and necessary\\u003csup\\u003e\\u003cspan citationid=\\\"CR3\\\" class=\\\"CitationRef\\\"\\u003e3\\u003c/span\\u003e,\\u003cspan citationid=\\\"CR7\\\" class=\\\"CitationRef\\\"\\u003e7\\u003c/span\\u003e\\u003c/sup\\u003e. Thus, improving bioactivity of implant surface could reduce failure rates, minimizes revision surgeries, and saves billions in healthcare\\u003csup\\u003e\\u003cspan citationid=\\\"CR8\\\" class=\\\"CitationRef\\\"\\u003e8\\u003c/span\\u003e\\u003c/sup\\u003e. Many ceramic materials can be preferred as a coating material, each one have distinct properties that affecting their bioactivity, degradation rate, and osseointegration\\u003csup\\u003e\\u003cspan citationid=\\\"CR9\\\" class=\\\"CitationRef\\\"\\u003e9\\u003c/span\\u003e,\\u003cspan citationid=\\\"CR10\\\" class=\\\"CitationRef\\\"\\u003e10\\u003c/span\\u003e\\u003c/sup\\u003e. For example, hydroxyapatite (HA) is widely used for implant coatings, but its high crystallinity can sometimes lead to slow resorption and weak bonding with bone\\u003csup\\u003e\\u003cspan citationid=\\\"CR11\\\" class=\\\"CitationRef\\\"\\u003e11\\u003c/span\\u003e\\u003c/sup\\u003e. In another study showed that silver/zirconia coatings on 316L surface performed higher corrosion resistance and antibacterial behavior\\u003csup\\u003e\\u003cspan citationid=\\\"CR12\\\" class=\\\"CitationRef\\\"\\u003e12\\u003c/span\\u003e\\u003c/sup\\u003e.\\u003c/p\\u003e\\u003cp\\u003eCalcium carbonate (CaCO₃) is important in biomedical applications due to its biocompatibility, biodegradability, and favorable chemical properties\\u003csup\\u003e\\u003cspan citationid=\\\"CR13\\\" class=\\\"CitationRef\\\"\\u003e13\\u003c/span\\u003e\\u003c/sup\\u003e. Being a naturally abundant mineral in body, mostly in bone and teeth, which makes it inherently compatible with the human body\\u003csup\\u003e\\u003cspan citationid=\\\"CR14\\\" class=\\\"CitationRef\\\"\\u003e14\\u003c/span\\u003e\\u003c/sup\\u003e. Calcium carbonate provides a faster resorption rate, allowing better integration with natural bone remodeling processes\\u003csup\\u003e\\u003cspan citationid=\\\"CR15\\\" class=\\\"CitationRef\\\"\\u003e15\\u003c/span\\u003e\\u003c/sup\\u003e. The porous nature of CaCO₃ coating could enhance cell adhesion and proliferation. Moreover, a rougher surface could improve better interaction between the implant and bone\\u003csup\\u003e\\u003cspan citationid=\\\"CR2\\\" class=\\\"CitationRef\\\"\\u003e2\\u003c/span\\u003e\\u003c/sup\\u003e. In addition, CaCO₃ coatings help prevent fibrous tissue formation around the implant, which is a common cause of failure in orthopedic\\u003csup\\u003e\\u003cspan citationid=\\\"CR14\\\" class=\\\"CitationRef\\\"\\u003e14\\u003c/span\\u003e\\u003c/sup\\u003e. It supports the attachment, proliferation, and differentiation of osteoblasts, promoting new bone growth\\u003csup\\u003e\\u003cspan citationid=\\\"CR16\\\" class=\\\"CitationRef\\\"\\u003e16\\u003c/span\\u003e\\u003c/sup\\u003e. CaCO₃ particles can assist in wound healing by providing calcium ions, which play a role in cellular processes like blood clotting and tissue repair\\u003csup\\u003e\\u003cspan citationid=\\\"CR17\\\" class=\\\"CitationRef\\\"\\u003e17\\u003c/span\\u003e\\u003c/sup\\u003e. Thus, calcium carbonate coatings on implant surfaces are increasingly being explored for biomedical applications, particularly in orthopedic and dental implants. CaCO₃ occurs naturally in three crystalline polymorphs with different properties: Calcite, Aragonite and Vaterite. Vaterite has high surface area and solubility that supports rapid calcium ion release that beneficial for cell signaling and repair. Aragonite more similarity to the natural mineral that found in bones that promote osteoblast activity. Calcite is commonly used in drug delivery and bone scaffold\\u003csup\\u003e\\u003cspan citationid=\\\"CR18\\\" class=\\\"CitationRef\\\"\\u003e18\\u003c/span\\u003e,\\u003cspan citationid=\\\"CR19\\\" class=\\\"CitationRef\\\"\\u003e19\\u003c/span\\u003e\\u003c/sup\\u003e.\\u003c/p\\u003e\\u003cp\\u003eElectrophoretic deposition (EPD) is one of most promising method to creating homogeneous coatings on metallic implants\\u003csup\\u003e\\u003cspan citationid=\\\"CR20\\\" class=\\\"CitationRef\\\"\\u003e20\\u003c/span\\u003e,\\u003cspan citationid=\\\"CR21\\\" class=\\\"CitationRef\\\"\\u003e21\\u003c/span\\u003e\\u003c/sup\\u003e. Especially, bioceramic like bioglass, hydroxyapatite or calcium carbonate have been used coated to varying thicknesses of implant surface for bone applications\\u003csup\\u003e\\u003cspan citationid=\\\"CR22\\\" class=\\\"CitationRef\\\"\\u003e22\\u003c/span\\u003e,\\u003cspan citationid=\\\"CR23\\\" class=\\\"CitationRef\\\"\\u003e23\\u003c/span\\u003e,\\u003cspan citationid=\\\"CR24\\\" class=\\\"CitationRef\\\"\\u003e24\\u003c/span\\u003e\\u003c/sup\\u003e. In EPD, nanoparticles dispersed in alcohol are deposited as a thin layer on the metallic surface that is used as an electrode under an applied electric field\\u003csup\\u003e\\u003cspan citationid=\\\"CR25\\\" class=\\\"CitationRef\\\"\\u003e25\\u003c/span\\u003e\\u003c/sup\\u003e. The electrophoretic deposition coating depends upon several factors, such as the applied voltage, deposition time, electrolyte concentration, and the condition of the substrate\\u003csup\\u003e\\u003cspan citationid=\\\"CR21\\\" class=\\\"CitationRef\\\"\\u003e21\\u003c/span\\u003e,\\u003cspan citationid=\\\"CR26\\\" class=\\\"CitationRef\\\"\\u003e26\\u003c/span\\u003e\\u003c/sup\\u003e. For example, the electrophoretic bioactive glass coated surface enhanced mesenchymal stem cells viability, attachment, and higher proliferation compared to the bare SS substrate\\u003csup\\u003e\\u003cspan citationid=\\\"CR9\\\" class=\\\"CitationRef\\\"\\u003e9\\u003c/span\\u003e\\u003c/sup\\u003e. In other study, TiO\\u003csub\\u003e2\\u003c/sub\\u003e nanotubes and gentamicin coated by electrophoretic deposition on 316L SS surface enhance the cell viability, and exhibit anti-microbial behavior with reduced cytotoxicity\\u003csup\\u003e\\u003cspan citationid=\\\"CR27\\\" class=\\\"CitationRef\\\"\\u003e27\\u003c/span\\u003e\\u003c/sup\\u003e. Mahlooji et al. showed that the electrophoretic deposition of chitosan-bioactive glass coating could successfully enhance the adhesion strength, bioactivity, corrosion and cellular performance of the bare surface\\u003csup\\u003e\\u003cspan citationid=\\\"CR28\\\" class=\\\"CitationRef\\\"\\u003e28\\u003c/span\\u003e\\u003c/sup\\u003e.\\u003c/p\\u003e\\u003cp\\u003eIn literature, there are a few studies have investigated CaCO₃ coatings on only bare stainless steel implant surfaces\\u003csup\\u003e\\u003cspan citationid=\\\"CR29\\\" class=\\\"CitationRef\\\"\\u003e29\\u003c/span\\u003e\\u003c/sup\\u003e. This study, for the first time, examined and fabricated the CaCO\\u003csub\\u003e3\\u003c/sub\\u003e particle coated on nanostructured 316L SS surface. The aim of the present work have creating a rougher with nanostructured morphology on 316L SS surface and, coated with highly biocompatible CaCO\\u003csub\\u003e3\\u003c/sub\\u003e particle to create bioactive surface to biomedical applications, as shown in Fig.\\u0026nbsp;\\u003cspan refid=\\\"Fig1\\\" class=\\\"InternalRef\\\"\\u003e1\\u003c/span\\u003e. The results showed that applied voltage play a vital role in thickness and uniformity of CaCO\\u003csub\\u003e3\\u003c/sub\\u003e coating process that fabricated bioactive nanosurface can be candidate for biomedical application.\\u003c/p\\u003e\\u003cp\\u003e\\u003c/p\\u003e\"},{\"header\":\"2. MATERIAL AND METHODS\",\"content\":\"\\u003cp\\u003eThe vaterite and aragonite particles were obtained according to previously study of our research groups\\u003csup\\u003e\\u003cspan citationid=\\\"CR18\\\" class=\\\"CitationRef\\\"\\u003e18\\u003c/span\\u003e\\u003c/sup\\u003e. In briefly, the CaCO\\u003csub\\u003e3\\u003c/sub\\u003e particles were synthesis at room temperature using a precipitation reaction between calcium acetate and sodium bicarbonate. In this process, calcium acetate and sodium bicarbonate were separately dissolved in 4 ml ultrapure water at various calcium (Ca\\u003csup\\u003e2+\\u003c/sup\\u003e) : carbonate (CO\\u003csub\\u003e3\\u003c/sub\\u003e\\u003csup\\u003e2\\u0026minus;\\u003c/sup\\u003e) ratios, followed by addition of 20 ml ethylene glycol to solution. After pH values of the solutions were adjusted, they were mixed with each other under magnetic agitation at 800 rpm for 15 min. Then, CaCO\\u003csub\\u003e3\\u003c/sub\\u003e particles formed inside the solution were washed with ethanol and deionized water, respectively, collected by centrifugation (7200 rpm, 15 min, 22\\u0026deg;C) and dried overnight at 50\\u0026deg;C.\\u003c/p\\u003e\\u003cp\\u003eA 316L stainless SS foil (0.5 mm) was cut into 1\\u0026times;1cm\\u003csup\\u003e2\\u003c/sup\\u003e sized samples. Prior to electrophoretic deposition, the samples were ultrasonically cleaned in acetone, ethanol, and distilled water each for 10 min. Then, anodization process (80V for 1 min) was applied to obtained rougher nanostructured morphologies on the surface according to previous study\\u003csup\\u003e3031\\u003c/sup\\u003e. In order to coating process, electrophoretic deposition was used that stainless steel as cathode and platin as anode. Electrodes were connected to a power supply (Genesys 300 V/5, TDK Lambda) and the distance between the electrodes was 10 mm. The electrolyte solutions were prepared as 0.06g vaterite\\u0026thinsp;+\\u0026thinsp;1M HCI in 60ml ethanol. During EPD process, 60V, 90V and 120V was applied for 5 min, 1 min and 1 min to vaterite coating.\\u003c/p\\u003e\\u003cp\\u003eThe coated surface morphology of the samples was characterized with scanning electron microscopy (SEM, FEI Nova Nano 430) using secondary electrons. Surface topography was examined by atomic force microscopy (AFM, Veeco Multimode V). The surface roughness values were obtained using Image Plus software. To identify coated CaCO\\u003csub\\u003e3\\u003c/sub\\u003e polymorphs of surface was carried out using Rigaku D/Max-2200 X-ray diffractometer with monochromatic Cu Kα radiation (λ\\u0026thinsp;=\\u0026thinsp;1.54 \\u0026Aring;) using a power supply of 30 mA and 40 kV. 20\\u0026deg; to 60\\u0026deg; diffraction angles (2θ) were scanned at a scanning rate of 2\\u0026deg;/min.\\u003c/p\\u003e\"},{\"header\":\"3. RESULTS AND DISCUSSION\",\"content\":\"\\u003cp\\u003eThe nanostructured surface was obtained via anodization of bare stainless-steel samples. Figure\\u0026nbsp;\\u003cspan refid=\\\"Fig2\\\" class=\\\"InternalRef\\\"\\u003e2\\u003c/span\\u003ea showed bare implant and nanostructured surfaces. It was created about 250nm feature sized by applied 80V for 1min, which detailed optimized in previous research\\u003csup\\u003e\\u003cspan citationid=\\\"CR30\\\" class=\\\"CitationRef\\\"\\u003e30\\u003c/span\\u003e\\u003c/sup\\u003e. The results showed that anodization process created unique nanotopography on surface. In addition, surface became more rougher, surface chemistry, hydrophobicity and surface charge changed, and surface area increased after anodization process\\u003csup\\u003e\\u003cspan citationid=\\\"CR32\\\" class=\\\"CitationRef\\\"\\u003e32\\u003c/span\\u003e,\\u003cspan citationid=\\\"CR33\\\" class=\\\"CitationRef\\\"\\u003e33\\u003c/span\\u003e\\u003c/sup\\u003e. Thus, increased surface area with negatively charged surfaces could provide higher amount of calcium deposition compared to bare surface. Figure\\u0026nbsp;\\u003cspan refid=\\\"Fig2\\\" class=\\\"InternalRef\\\"\\u003e2\\u003c/span\\u003eb showed that initial process of calcium carbonate coating on nanostructured surface via electrophoretic deposition under 60V for 1 min. It was observed that calcium carbonate particles interacted with the surface layer directly and began forming thin layers on nanostructured surfaces (indicated by the red arrow). However, the limited amount of calcium carbonate coated on the surface was observed due to inefficient coating duration. Therefore, both nanostructures and partial particles were observed on the surface (indicated by the white arrow). As show in Fig.\\u0026nbsp;\\u003cspan refid=\\\"Fig2\\\" class=\\\"InternalRef\\\"\\u003e2\\u003c/span\\u003ec, SEM image confirmed that thin and compact layer of CaCO₃ occurred on the surface. The thin layer likely forms first as homogeneous nucleation on the surface, followed by growth of crystallites into larger, organized calcium carbonate structures. Especially, the underlying rougher nanostructured surface can guide the orientation or density of CaCO₃ deposition due to enhanced surface energy or charge. It provides a chemically favorable and structurally aligned base for oriented crystal growth of CaCO₃, ensuring strong adhesion and integration with the nanostructured surface. This layer is crucial because it bridges the nanostructure, forming a stabile layer and integrates with the surface topology.\\u003c/p\\u003e\\u003cp\\u003e\\u003c/p\\u003e\\u003cp\\u003eThe effect of applied voltage on coating process was shown in Fig.\\u0026nbsp;\\u003cspan refid=\\\"Fig3\\\" class=\\\"InternalRef\\\"\\u003e3\\u003c/span\\u003e. The partial CaCO₃ coated on surface was observed after 60V applied for 1 min. When increased the applied voltage, it accelerates particle coated on the surface. The uniform thin layer on surface was observed by 90V for 1 min. Especially, uniform and thicker CaCO₃ layer was observed by 120V for min. This effect can be explained as higher voltage increases the electric field strength, which accelerates the migration of Ca\\u0026sup2;⁺ and CO₃\\u0026sup2;⁻ ions toward the implant surface. As voltage increases, the rate of deposition accelerates, resulting in thicker coatings was observed in a shorter time. This boosts local supersaturation at the electrode\\u0026ndash;solution interface, leading to faster nucleation and growth of CaCO₃ crystals. On the other hand, it can be possible fabricated thicker coated surface as increased duration by applied lower voltages. Figure\\u0026nbsp;\\u003cspan refid=\\\"Fig3\\\" class=\\\"InternalRef\\\"\\u003e3\\u003c/span\\u003e confirmed that a uniform and thicker surface was obtained for 5 min by applying 60V, while a partially coated surface was observed for 1 min.\\u003c/p\\u003e\\u003cp\\u003e\\u003c/p\\u003e\\u003cp\\u003eFigure \\u003cspan refid=\\\"Fig3\\\" class=\\\"InternalRef\\\"\\u003e3\\u003c/span\\u003e. SEM micrographs of coating Aragonite particle on nanostructured surface by applied 60V, 90V and 120V for 1 min. The right SEM imaged showed increased the coating duration to 5 min created uniform coated layer.\\u003c/p\\u003e\\u003cp\\u003eThe other crystalline polymorphs type of CaCO₃, which vaterite, coating on nanostructure surface was investigated in Fig.\\u0026nbsp;\\u003cspan refid=\\\"Fig3\\\" class=\\\"InternalRef\\\"\\u003e3\\u003c/span\\u003e. This figure showed that applied voltages and coating duration effect coating morphology. When 60V was applied for 5 min, a uniform and thick layer of calcium carbonate coated was observed on the surface. On the other hand, when applied voltage increased, which applied 90V for 1 min, a uniform calcium coated surface was also observed. In addition, a fully coated surface was obtained by applying 120V, even though the duration was decreased to 30 sec. These results clearly showed that applied voltages play important role in coating process. As the applied voltages increased, it provides enhanced deposition coating kinetics. Also, coating duration play critical role in process that more calcium was deposited, and thickness increased on the surface as coating duration increased. On the other hand, electrolyte pH and temperature could also influence coating process. Azari et al. showed that different temperatures revealed an increasing trend in electrophoretic mobility, suspension conductivity, and current density with temperature rise\\u003csup\\u003e\\u003cspan citationid=\\\"CR20\\\" class=\\\"CitationRef\\\"\\u003e20\\u003c/span\\u003e\\u003c/sup\\u003e. However, higher temperatures could lead to agglomeration of particles and instability of suspension. The optimal coating was found as 35\\u003csup\\u003eo\\u003c/sup\\u003eC for the bioactive glass deposited on 316L SS\\u003csup\\u003e\\u003cspan citationid=\\\"CR20\\\" class=\\\"CitationRef\\\"\\u003e20\\u003c/span\\u003e\\u003c/sup\\u003e.\\u003c/p\\u003e\\u003cp\\u003e\\u003c/p\\u003e\\u003cp\\u003e\\u003c/p\\u003e\\u003cp\\u003eXRD analysis confirmed to CaCO₃ particles on a nanostructured surface, as shown in Fig.\\u0026nbsp;\\u003cspan refid=\\\"Fig4\\\" class=\\\"InternalRef\\\"\\u003e4\\u003c/span\\u003e. The diffraction patterns indicated the crystalline nature of the deposited particles, confirming the presence of distinct CaCO₃ polymorphs on the surfaces. Peak intensities and positions were analyzed to determine phase composition, crystallite size, and structural characteristics. XRD spectra analysis showed characteristic peaks of vaterite at 24.9\\u0026deg;, 26.9\\u0026deg; and 32.7\\u0026deg; corresponding to (110), (112) and (114) crystallographic planes and calcite at 29.4\\u0026deg;, 35.9\\u0026deg; and 39.5\\u0026deg; corresponding to crystallographic planes of (104), (110) and (113), respectively\\u003csup\\u003e\\u003cspan citationid=\\\"CR18\\\" class=\\\"CitationRef\\\"\\u003e18\\u003c/span\\u003e\\u003c/sup\\u003e. These findings provide insights into the nucleation and growth mechanisms of CaCO₃ on the modified surface, which is crucial for applications in biomineralization, catalysis, and material engineering. Presence of calcite as a minor polymorph for CaCO\\u003csub\\u003e3\\u003c/sub\\u003e particles synthesized via solution mixing method was an expected finding due to the unstable nature of vaterite at ambient conditions and electrolyte solutions, demonstrating ease of transformation from vaterite to calcite polymorph.\\u003c/p\\u003e\\u003cp\\u003e\\u003c/p\\u003e\\u003cp\\u003eFigure \\u003cspan refid=\\\"Fig5\\\" class=\\\"InternalRef\\\"\\u003e5\\u003c/span\\u003e indicated the roughness profiles of sample surfaces. These figures showed that coating process created a rougher and unique nanotopography on the surfaces. The mean roughness value calculated from the AFM analysis were 1.9, 18.5, 16.7, and 17.8 nm for the NA, C60V, C90V and C120V, respectively. It was clear that the nanoroughness of surface increased upon coating process compared to bare surface. It should be noted that the surface roughness parameters could affect cell interaction and viability and stem cell differentiation\\u003csup\\u003e\\u003cspan citationid=\\\"CR34\\\" class=\\\"CitationRef\\\"\\u003e34\\u003c/span\\u003e,\\u003cspan citationid=\\\"CR35\\\" class=\\\"CitationRef\\\"\\u003e35\\u003c/span\\u003e\\u003c/sup\\u003e. Furthermore, the presence of calcium ions on the surface is highly expected to enhance osteointegration\\u003csup\\u003e\\u003cspan citationid=\\\"CR36\\\" class=\\\"CitationRef\\\"\\u003e36\\u003c/span\\u003e\\u003c/sup\\u003e. Similarly, successfully electrophoretic deposition of nanoHAp coatings on Ti6Al4V surface with higher surface roughness was obtained. It was observed that bioactive coated surface significantly enhanced osteoblast attachment and proliferation\\u003csup\\u003e\\u003cspan citationid=\\\"CR37\\\" class=\\\"CitationRef\\\"\\u003e37\\u003c/span\\u003e\\u003c/sup\\u003e. It should be considered that calcium ion on the surface could affect fibronectin and vitronectin protein adsorption due to positively charged of calcium that influence cell adhesion and proliferation\\u003csup\\u003e\\u003cspan citationid=\\\"CR38\\\" class=\\\"CitationRef\\\"\\u003e38\\u003c/span\\u003e\\u003c/sup\\u003e. Especially, Oral et al. found that ellipsoidal vaterite and spherical calcite particles exhibited higher CaCO\\u003csub\\u003e3\\u003c/sub\\u003e-to-Hydroxyapatite conversion and enhance osteoblast proliferation\\u003csup\\u003e\\u003cspan citationid=\\\"CR19\\\" class=\\\"CitationRef\\\"\\u003e19\\u003c/span\\u003e\\u003c/sup\\u003e. On the other, the nanostructured 316L stainless steel surface exhibited a higher Cr₂O₃ peak intensity, which enhanced corrosion resistance based on previous studies\\u003csup\\u003e\\u003cspan citationid=\\\"CR32\\\" class=\\\"CitationRef\\\"\\u003e32\\u003c/span\\u003e\\u003c/sup\\u003e. Furthermore, ceramic coatings on the nanostructured surface are expected to further improve corrosion resistance. These ceramics coated layer could also improve the corrosion resistance of implant. Similarly, Katic et al. showed that electrodeposited CaP coating provides improved corrosion resistance and protects the titanium alloy in an aggressive environment\\u003csup\\u003e\\u003cspan citationid=\\\"CR39\\\" class=\\\"CitationRef\\\"\\u003e39\\u003c/span\\u003e\\u003c/sup\\u003e. In addition, fabricated calcium coated implant surface potentially enhances osteointegration for biomedical application. In this study, a nanostructured implant surface combined with calcium carbonate was developed, highlighting the potential of this approach to enhance osseointegration for biomedical applications. The results demonstrated that the proportion of calcium carbonate particles in the coating increased significantly with higher applied voltages, and coating thickness grew with longer deposition durations. These findings suggest that this surface modification strategy may improve implant performance; however, further studies are recommended to investigate and evaluate the mechanical properties and cellular interactions more comprehensively.\\u003c/p\\u003e\"},{\"header\":\"4. CONCLUSIONS\",\"content\":\"\\u003cp\\u003eCalcium carbonate coating were successfully fabricated on the nanostructured 316L SS alloy using electrophoretic deposition. The results showed that applied voltages, duration, and solubility significantly influenced the coating process on surface. SEM and XRD results confirmed the successful coating of the CaCO\\u003csub\\u003e3\\u003c/sub\\u003e on the nanostructured 316L SS surface by applied 60V, 90V and 120V. Notably, a uniform, homogeneous, and crack-free coating was obtained at 60 V for 5 min. The results indicate the formation of calcium carbonate coating on implant surface could improve osteointegration due to biological calcium ions as a major component of bone. Overall, the CaCO\\u003csub\\u003e3\\u003c/sub\\u003e coating with nanostructured implant surface could have a great potential for use in orthopedic and dental applications.\\u003c/p\\u003e\"},{\"header\":\"Declarations\",\"content\":\"\\u003ch2\\u003eAuthor Contribution\\u003c/h2\\u003e\\u003cp\\u003eThe author conducted the research and wrote the main manuscript.\\u003c/p\\u003e\\u003ch2\\u003eAcknowledgement\\u003c/h2\\u003e\\u003cp\\u003eThe author would like to thank Assoc. Prof. Batur Ercan for providing research equipment, and METU/METE for SEM and XRD analysis and Ercan Research Group. The author would also like to express special thanks to Beyza Tarhan for her help during the experiments.\\u003c/p\\u003e\\u003ch2\\u003eData Availability\\u003c/h2\\u003e\\u003cp\\u003eThe datasets used and/or analyzed during the current study are available from the corresponding author on reasonable request.\\u003c/p\\u003e\"},{\"header\":\"References\",\"content\":\"\\u003col\\u003e\\u003cli\\u003e\\u003cspan\\u003eBandyopadhyay, A., Mitra, I., Goodman, S. B., Kumar, M. \\u0026amp; Bose, S. Improving Biocompatibility for next Generation of Metallic Implants. \\u003cem\\u003eProg. Mater. Sci. 133\\u003c/em\\u003e (July 2021), 101053. (2023). \\u003cspan class=\\\"ExternalRef\\\"\\u003e\\u003cspan class=\\\"RefSource\\\"\\u003ehttps://doi.org/10.1016/j.pmatsci.2022.101053\\u003c/span\\u003e\\u003cspan address=\\\"10.1016/j.pmatsci.2022.101053\\\" targettype=\\\"DOI\\\" class=\\\"RefTarget\\\"\\u003e\\u003c/span\\u003e\\u003c/span\\u003e\\u003c/span\\u003e\\u003c/li\\u003e\\u003cli\\u003e\\u003cspan\\u003eLiu, Z., Liu, X. \\u0026amp; Ramakrishna, S. Surface Engineering of Biomaterials in Orthopedic and Dental Implants: Strategies to Improve Osteointegration, Bacteriostatic and Bactericidal Activities. \\u003cem\\u003eBiotechnol. J.\\u003c/em\\u003e \\u003cb\\u003e16\\u003c/b\\u003e (7), 1\\u0026ndash;23. \\u003cspan class=\\\"ExternalRef\\\"\\u003e\\u003cspan class=\\\"RefSource\\\"\\u003ehttps://doi.org/10.1002/biot.202000116\\u003c/span\\u003e\\u003cspan address=\\\"10.1002/biot.202000116\\\" targettype=\\\"DOI\\\" class=\\\"RefTarget\\\"\\u003e\\u003c/span\\u003e\\u003c/span\\u003e (2021).\\u003c/span\\u003e\\u003c/li\\u003e\\u003cli\\u003e\\u003cspan\\u003eFlorea, D. A., Albuleț, D., Grumezescu, A. M. \\u0026amp; Andronescu, E. Surface Modification \\u0026ndash; A Step Forward to Overcome the Current Challenges in Orthopedic Industry and to Obtain an Improved Osseointegration and Antimicrobial Properties. \\u003cem\\u003eMater. Chem. Phys. 243\\u003c/em\\u003e (August 2019), 122579. (2020). \\u003cspan class=\\\"ExternalRef\\\"\\u003e\\u003cspan class=\\\"RefSource\\\"\\u003ehttps://doi.org/10.1016/j.matchemphys.2019.122579\\u003c/span\\u003e\\u003cspan address=\\\"10.1016/j.matchemphys.2019.122579\\\" targettype=\\\"DOI\\\" class=\\\"RefTarget\\\"\\u003e\\u003c/span\\u003e\\u003c/span\\u003e\\u003c/span\\u003e\\u003c/li\\u003e\\u003cli\\u003e\\u003cspan\\u003eStaruch, R., Griffin, M. \\u0026amp; Butler, P. Nanoscale Surface Modifications of Orthopaedic Implants: State of the Art and Perspectives. \\u003cem\\u003eOpen. Orthop. J.\\u003c/em\\u003e \\u003cb\\u003e10\\u003c/b\\u003e (1), 920\\u0026ndash;938. \\u003cspan class=\\\"ExternalRef\\\"\\u003e\\u003cspan class=\\\"RefSource\\\"\\u003ehttps://doi.org/10.2174/1874325001610010920\\u003c/span\\u003e\\u003cspan address=\\\"10.2174/1874325001610010920\\\" targettype=\\\"DOI\\\" class=\\\"RefTarget\\\"\\u003e\\u003c/span\\u003e\\u003c/span\\u003e (2017).\\u003c/span\\u003e\\u003c/li\\u003e\\u003cli\\u003e\\u003cspan\\u003eManam, N. S. et al. H. I. Study of Corrosion in Biocompatible Metals for Implants: A Review. \\u003cem\\u003eJ. Alloys Compd.\\u003c/em\\u003e \\u003cb\\u003e701\\u003c/b\\u003e, 698\\u0026ndash;715. \\u003cspan class=\\\"ExternalRef\\\"\\u003e\\u003cspan class=\\\"RefSource\\\"\\u003ehttps://doi.org/10.1016/j.jallcom.2017.01.196\\u003c/span\\u003e\\u003cspan address=\\\"10.1016/j.jallcom.2017.01.196\\\" targettype=\\\"DOI\\\" class=\\\"RefTarget\\\"\\u003e\\u003c/span\\u003e\\u003c/span\\u003e (2017).\\u003c/span\\u003e\\u003c/li\\u003e\\u003cli\\u003e\\u003cspan\\u003eMizori, R. et al. The Cost of Implant Waste in Trauma Orthopaedic Surgery and Sustainability Considerations: An Observational Study. \\u003cem\\u003eInt. Orthop.\\u003c/em\\u003e \\u003cspan class=\\\"ExternalRef\\\"\\u003e\\u003cspan class=\\\"RefSource\\\"\\u003ehttps://doi.org/10.1007/s00264-025-06532-1\\u003c/span\\u003e\\u003cspan address=\\\"10.1007/s00264-025-06532-1\\\" targettype=\\\"DOI\\\" class=\\\"RefTarget\\\"\\u003e\\u003c/span\\u003e\\u003c/span\\u003e (2025).\\u003c/span\\u003e\\u003c/li\\u003e\\u003cli\\u003e\\u003cspan\\u003eBenčina, M. et al. Enhanced Hemocompatibility and Cytocompatibility of Stainless Steel. \\u003cem\\u003eACS Omega\\u003c/em\\u003e. \\u003cb\\u003e9\\u003c/b\\u003e (17), 19566\\u0026ndash;19577. \\u003cspan class=\\\"ExternalRef\\\"\\u003e\\u003cspan class=\\\"RefSource\\\"\\u003ehttps://doi.org/10.1021/acsomega.4c01191\\u003c/span\\u003e\\u003cspan address=\\\"10.1021/acsomega.4c01191\\\" targettype=\\\"DOI\\\" class=\\\"RefTarget\\\"\\u003e\\u003c/span\\u003e\\u003c/span\\u003e (2024).\\u003c/span\\u003e\\u003c/li\\u003e\\u003cli\\u003e\\u003cspan\\u003eHodges, N. A., Sussman, E. M. \\u0026amp; Stegemann, J. P. Aseptic and Septic Prosthetic Joint Loosening: Impact of Biomaterial Wear on Immune Cell Function, Inflammation, and Infection. \\u003cem\\u003eBiomaterials\\u003c/em\\u003e \\u003cb\\u003e278\\u003c/b\\u003e (January), 121127. \\u003cspan class=\\\"ExternalRef\\\"\\u003e\\u003cspan class=\\\"RefSource\\\"\\u003ehttps://doi.org/10.1016/j.biomaterials.2021.121127\\u003c/span\\u003e\\u003cspan address=\\\"10.1016/j.biomaterials.2021.121127\\\" targettype=\\\"DOI\\\" class=\\\"RefTarget\\\"\\u003e\\u003c/span\\u003e\\u003c/span\\u003e (2021).\\u003c/span\\u003e\\u003c/li\\u003e\\u003cli\\u003e\\u003cspan\\u003eHadem, H. et al. Electrophoretic Deposition of 58S Bioactive Glass- Polymer Composite Coatings on 316L Stainless Steel: An Optimization for Corrosion, Bioactivity, and Cytocompatibility. \\u003cem\\u003eACS Appl. Bio Mater.\\u003c/em\\u003e \\u003cb\\u003e7\\u003c/b\\u003e (5), 2966\\u0026ndash;2981. \\u003cspan class=\\\"ExternalRef\\\"\\u003e\\u003cspan class=\\\"RefSource\\\"\\u003ehttps://doi.org/10.1021/acsabm.4c00037\\u003c/span\\u003e\\u003cspan address=\\\"10.1021/acsabm.4c00037\\\" targettype=\\\"DOI\\\" class=\\\"RefTarget\\\"\\u003e\\u003c/span\\u003e\\u003c/span\\u003e (2024).\\u003c/span\\u003e\\u003c/li\\u003e\\u003cli\\u003e\\u003cspan\\u003eRasouli, R., Barhoum, A. \\u0026amp; Uludag, H. A. Review of Nanostructured Surfaces and Materials for Dental Implants: Surface Coating, Patterning and Functionalization for Improved Performance. \\u003cem\\u003eBiomater. Sci.\\u003c/em\\u003e \\u003cb\\u003e6\\u003c/b\\u003e (6), 1312\\u0026ndash;1338. \\u003cspan class=\\\"ExternalRef\\\"\\u003e\\u003cspan class=\\\"RefSource\\\"\\u003ehttps://doi.org/10.1039/c8bm00021b\\u003c/span\\u003e\\u003cspan address=\\\"10.1039/c8bm00021b\\\" targettype=\\\"DOI\\\" class=\\\"RefTarget\\\"\\u003e\\u003c/span\\u003e\\u003c/span\\u003e (2018).\\u003c/span\\u003e\\u003c/li\\u003e\\u003cli\\u003e\\u003cspan\\u003eMohandesnezhad, S., Etminanfar, M., Mahdavi, S. \\u0026amp; Safavi, M. S. Enhanced Bioactivity of 316L Stainless Steel with Deposition of Polypyrrole/Hydroxyapatite Layered Hybrid Coating: Orthopedic Applications. \\u003cem\\u003eSurfaces and Interfaces 28\\u003c/em\\u003e (November 2021), 101604. (2022). \\u003cspan class=\\\"ExternalRef\\\"\\u003e\\u003cspan class=\\\"RefSource\\\"\\u003ehttps://doi.org/10.1016/j.surfin.2021.101604\\u003c/span\\u003e\\u003cspan address=\\\"10.1016/j.surfin.2021.101604\\\" targettype=\\\"DOI\\\" class=\\\"RefTarget\\\"\\u003e\\u003c/span\\u003e\\u003c/span\\u003e\\u003c/span\\u003e\\u003c/li\\u003e\\u003cli\\u003e\\u003cspan\\u003eAtasoy, S. et al. The Fabrication of Silver/Zirconia Coatings: Characterization, Corrosion and Antibacterial Properties. \\u003cem\\u003eCeram. Int.\\u003c/em\\u003e \\u003cspan class=\\\"ExternalRef\\\"\\u003e\\u003cspan class=\\\"RefSource\\\"\\u003ehttps://doi.org/https://doi.org/10.1016/j.ceramint.2025.05.276\\u003c/span\\u003e\\u003cspan address=\\\"10.1016/j.ceramint.2025.05.276\\\" targettype=\\\"DOI\\\" class=\\\"RefTarget\\\"\\u003e\\u003c/span\\u003e\\u003c/span\\u003e (2025).\\u003c/span\\u003e\\u003c/li\\u003e\\u003cli\\u003e\\u003cspan\\u003eSokolova, V. \\u0026amp; Epple, M. Biological and Medical Applications of Calcium Phosphate Nanoparticles. \\u003cem\\u003eChem. - Eur. J.\\u003c/em\\u003e \\u003cb\\u003e27\\u003c/b\\u003e (27), 7471\\u0026ndash;7488. \\u003cspan class=\\\"ExternalRef\\\"\\u003e\\u003cspan class=\\\"RefSource\\\"\\u003ehttps://doi.org/10.1002/chem.202005257\\u003c/span\\u003e\\u003cspan address=\\\"10.1002/chem.202005257\\\" targettype=\\\"DOI\\\" class=\\\"RefTarget\\\"\\u003e\\u003c/span\\u003e\\u003c/span\\u003e (2021).\\u003c/span\\u003e\\u003c/li\\u003e\\u003cli\\u003e\\u003cspan\\u003eDrevet, R., Faur\\u0026eacute;, J. \\u0026amp; Benhayoune, H. Bioactive Calcium Phosphate Coatings for Bone Implant Applications: A Review. \\u003cem\\u003eCoatings\\u003c/em\\u003e \\u003cb\\u003e13\\u003c/b\\u003e (6). \\u003cspan class=\\\"ExternalRef\\\"\\u003e\\u003cspan class=\\\"RefSource\\\"\\u003ehttps://doi.org/10.3390/coatings13061091\\u003c/span\\u003e\\u003cspan address=\\\"10.3390/coatings13061091\\\" targettype=\\\"DOI\\\" class=\\\"RefTarget\\\"\\u003e\\u003c/span\\u003e\\u003c/span\\u003e (2023).\\u003c/span\\u003e\\u003c/li\\u003e\\u003cli\\u003e\\u003cspan\\u003eEliaz, N. \\u0026amp; Metoki, N. Calcium Phosphate Bioceramics: A Review of Their History, Structure, Properties, Coating Technologies and Biomedical Applications. \\u003cem\\u003eMater. (Basel)\\u003c/em\\u003e. \\u003cb\\u003e10\\u003c/b\\u003e (4). \\u003cspan class=\\\"ExternalRef\\\"\\u003e\\u003cspan class=\\\"RefSource\\\"\\u003ehttps://doi.org/10.3390/ma10040334\\u003c/span\\u003e\\u003cspan address=\\\"10.3390/ma10040334\\\" targettype=\\\"DOI\\\" class=\\\"RefTarget\\\"\\u003e\\u003c/span\\u003e\\u003c/span\\u003e (2017).\\u003c/span\\u003e\\u003c/li\\u003e\\u003cli\\u003e\\u003cspan\\u003eHuang, Y. et al. Bone-Targeting Cell Membrane-Engineered CaCO3-Based Nanoparticles Restore Local Bone Homeostasis for Microenvironment-Responsive Osteoporosis Treatment. \\u003cem\\u003eChem. Eng. J.\\u003c/em\\u003e \\u003cb\\u003e470\\u003c/b\\u003e (January), 144145. \\u003cspan class=\\\"ExternalRef\\\"\\u003e\\u003cspan class=\\\"RefSource\\\"\\u003ehttps://doi.org/10.1016/j.cej.2023.144145\\u003c/span\\u003e\\u003cspan address=\\\"10.1016/j.cej.2023.144145\\\" targettype=\\\"DOI\\\" class=\\\"RefTarget\\\"\\u003e\\u003c/span\\u003e\\u003c/span\\u003e (2023).\\u003c/span\\u003e\\u003c/li\\u003e\\u003cli\\u003e\\u003cspan\\u003eWang, S. et al. E. G. Acceleration of Wound Healing through Amorphous Calcium Carbonate, Stabilized with High-Energy Polyphosphate. \\u003cem\\u003ePharmaceutics\\u003c/em\\u003e \\u003cb\\u003e15\\u003c/b\\u003e (2), 1\\u0026ndash;20. \\u003cspan class=\\\"ExternalRef\\\"\\u003e\\u003cspan class=\\\"RefSource\\\"\\u003ehttps://doi.org/10.3390/pharmaceutics15020494\\u003c/span\\u003e\\u003cspan address=\\\"10.3390/pharmaceutics15020494\\\" targettype=\\\"DOI\\\" class=\\\"RefTarget\\\"\\u003e\\u003c/span\\u003e\\u003c/span\\u003e (2023).\\u003c/span\\u003e\\u003c/li\\u003e\\u003cli\\u003e\\u003cspan\\u003eOral, \\u0026Ccedil;. M. \\u0026amp; Ercan, B. Influence of PH on Morphology, Size and Polymorph of Room Temperature Synthesized Calcium Carbonate Particles. \\u003cem\\u003ePowder Technol.\\u003c/em\\u003e \\u003cb\\u003e339\\u003c/b\\u003e, 781\\u0026ndash;788. \\u003cspan class=\\\"ExternalRef\\\"\\u003e\\u003cspan class=\\\"RefSource\\\"\\u003ehttps://doi.org/10.1016/j.powtec.2018.08.066\\u003c/span\\u003e\\u003cspan address=\\\"10.1016/j.powtec.2018.08.066\\\" targettype=\\\"DOI\\\" class=\\\"RefTarget\\\"\\u003e\\u003c/span\\u003e\\u003c/span\\u003e (2018).\\u003c/span\\u003e\\u003c/li\\u003e\\u003cli\\u003e\\u003cspan\\u003eOral, \\u0026Ccedil;. M., \\u0026Ccedil;alışkan, A., Kapusuz, D. \\u0026amp; Ercan, B. Facile Control of Hydroxyapatite Particle Morphology by Utilization of Calcium Carbonate Templates at Room Temperature. \\u003cem\\u003eCeram. Int.\\u003c/em\\u003e \\u003cb\\u003e46\\u003c/b\\u003e (13), 21319\\u0026ndash;21327. \\u003cspan class=\\\"ExternalRef\\\"\\u003e\\u003cspan class=\\\"RefSource\\\"\\u003ehttps://doi.org/10.1016/j.ceramint.2020.05.226\\u003c/span\\u003e\\u003cspan address=\\\"10.1016/j.ceramint.2020.05.226\\\" targettype=\\\"DOI\\\" class=\\\"RefTarget\\\"\\u003e\\u003c/span\\u003e\\u003c/span\\u003e (2020).\\u003c/span\\u003e\\u003c/li\\u003e\\u003cli\\u003e\\u003cspan\\u003eAzari, R. \\u0026amp; Boccaccini, A. R. Effect of Processing Temperature on Electrophoretic Deposition (EPD)-Derived Bioactive Composite Coatings for Metallic Bone Implants. \\u003cem\\u003eSurfaces and Interfaces 58\\u003c/em\\u003e (November 2024), 105771. (2025). \\u003cspan class=\\\"ExternalRef\\\"\\u003e\\u003cspan class=\\\"RefSource\\\"\\u003ehttps://doi.org/10.1016/j.surfin.2025.105771\\u003c/span\\u003e\\u003cspan address=\\\"10.1016/j.surfin.2025.105771\\\" targettype=\\\"DOI\\\" class=\\\"RefTarget\\\"\\u003e\\u003c/span\\u003e\\u003c/span\\u003e\\u003c/span\\u003e\\u003c/li\\u003e\\u003cli\\u003e\\u003cspan\\u003eZielinski, A. \\u0026amp; Bartmanski, M. \\u003cem\\u003eElectrodeposited Biocoatings, Their Properties and Fabrication Technologies: A Review\\u003c/em\\u003e; ; Vol. 10. (2020). \\u003cspan class=\\\"ExternalRef\\\"\\u003e\\u003cspan class=\\\"RefSource\\\"\\u003ehttps://doi.org/10.3390/COATINGS10080782\\u003c/span\\u003e\\u003cspan address=\\\"10.3390/COATINGS10080782\\\" targettype=\\\"DOI\\\" class=\\\"RefTarget\\\"\\u003e\\u003c/span\\u003e\\u003c/span\\u003e\\u003c/span\\u003e\\u003c/li\\u003e\\u003cli\\u003e\\u003cspan\\u003eSorkhi, L., Farrokhi-Rad, M. \\u0026amp; Shahrabi, T. Electrophoretic Deposition of Hydroxyapatite\\u0026ndash;Chitosan\\u0026ndash;Titania on Stainless Steel 316 L. \\u003cem\\u003eSurfaces\\u003c/em\\u003e \\u003cb\\u003e2\\u003c/b\\u003e (3), 458\\u0026ndash;467. \\u003cspan class=\\\"ExternalRef\\\"\\u003e\\u003cspan class=\\\"RefSource\\\"\\u003ehttps://doi.org/10.3390/surfaces2030034\\u003c/span\\u003e\\u003cspan address=\\\"10.3390/surfaces2030034\\\" targettype=\\\"DOI\\\" class=\\\"RefTarget\\\"\\u003e\\u003c/span\\u003e\\u003c/span\\u003e (2019).\\u003c/span\\u003e\\u003c/li\\u003e\\u003cli\\u003e\\u003cspan\\u003eMohammadsadegh, A., Allahkaram, S. R. \\u0026amp; Gharagozlou, M. Electrophoretic Deposition of Chitosan/Gelatin/Hydroxyapatite Nanocomposite Coatings on 316 L Stainless Steel for Biomedical Applications. \\u003cem\\u003eBiomed. Mater.\\u003c/em\\u003e \\u003cb\\u003e20\\u003c/b\\u003e (1). \\u003cspan class=\\\"ExternalRef\\\"\\u003e\\u003cspan class=\\\"RefSource\\\"\\u003ehttps://doi.org/10.1088/1748-605X/ad98d6\\u003c/span\\u003e\\u003cspan address=\\\"10.1088/1748-605X/ad98d6\\\" targettype=\\\"DOI\\\" class=\\\"RefTarget\\\"\\u003e\\u003c/span\\u003e\\u003c/span\\u003e (2024).\\u003c/span\\u003e\\u003c/li\\u003e\\u003cli\\u003e\\u003cspan\\u003eSafavi, M. S., Walsh, F. C., Surmeneva, M. A., Surmenev, R. A. \\u0026amp; Khalil-Allafi, J. Electrodeposited Hydroxyapatite-Based Biocoatings: Recent Progress and Future Challenges. \\u003cem\\u003eCoatings\\u003c/em\\u003e \\u003cb\\u003e11\\u003c/b\\u003e (1), 1\\u0026ndash;62. \\u003cspan class=\\\"ExternalRef\\\"\\u003e\\u003cspan class=\\\"RefSource\\\"\\u003ehttps://doi.org/10.3390/coatings11010110\\u003c/span\\u003e\\u003cspan address=\\\"10.3390/coatings11010110\\\" targettype=\\\"DOI\\\" class=\\\"RefTarget\\\"\\u003e\\u003c/span\\u003e\\u003c/span\\u003e (2021).\\u003c/span\\u003e\\u003c/li\\u003e\\u003cli\\u003e\\u003cspan\\u003eAl-Rashidy, Z. M., Farag, M. M., Ghany, N. A. A., Ibrahim, A. M. \\u0026amp; Abdel-Fattah, W. I. Aqueous Electrophoretic Deposition and Corrosion Protection of Borate Glass Coatings on 316 L Stainless Steel for Hard Tissue Fixation. \\u003cem\\u003eSurf. Interfaces\\u003c/em\\u003e. \\u003cb\\u003e7\\u003c/b\\u003e (January), 125\\u0026ndash;133. \\u003cspan class=\\\"ExternalRef\\\"\\u003e\\u003cspan class=\\\"RefSource\\\"\\u003ehttps://doi.org/10.1016/j.surfin.2017.03.010\\u003c/span\\u003e\\u003cspan address=\\\"10.1016/j.surfin.2017.03.010\\\" targettype=\\\"DOI\\\" class=\\\"RefTarget\\\"\\u003e\\u003c/span\\u003e\\u003c/span\\u003e (2017).\\u003c/span\\u003e\\u003c/li\\u003e\\u003cli\\u003e\\u003cspan\\u003eMehdipour, M., Afshar, A. \\u0026amp; Mohebali, M. Electrophoretic Deposition of Bioactive Glass Coating on 316L Stainless Steel and Electrochemical Behavior Study. \\u003cem\\u003eAppl. Surf. Sci.\\u003c/em\\u003e \\u003cb\\u003e258\\u003c/b\\u003e (24), 9832\\u0026ndash;9839. \\u003cspan class=\\\"ExternalRef\\\"\\u003e\\u003cspan class=\\\"RefSource\\\"\\u003ehttps://doi.org/10.1016/j.apsusc.2012.06.038\\u003c/span\\u003e\\u003cspan address=\\\"10.1016/j.apsusc.2012.06.038\\\" targettype=\\\"DOI\\\" class=\\\"RefTarget\\\"\\u003e\\u003c/span\\u003e\\u003c/span\\u003e (2012).\\u003c/span\\u003e\\u003c/li\\u003e\\u003cli\\u003e\\u003cspan\\u003eGuti\\u0026eacute;rrez-Mej\\u0026iacute;a, F. A. et al. Electrophoretic Deposition of TiO2 Nanotubes and Antibiotics on Polyurethane Coated Stainless Steel for Improved Antibacterial Response and Cell Viability. \\u003cem\\u003eMater. Today Commun.\\u003c/em\\u003e \\u003cb\\u003e40\\u003c/b\\u003e (March). \\u003cspan class=\\\"ExternalRef\\\"\\u003e\\u003cspan class=\\\"RefSource\\\"\\u003ehttps://doi.org/10.1016/j.mtcomm.2024.109428\\u003c/span\\u003e\\u003cspan address=\\\"10.1016/j.mtcomm.2024.109428\\\" targettype=\\\"DOI\\\" class=\\\"RefTarget\\\"\\u003e\\u003c/span\\u003e\\u003c/span\\u003e (2024).\\u003c/span\\u003e\\u003c/li\\u003e\\u003cli\\u003e\\u003cspan\\u003eMahlooji, E., Atapour, M. \\u0026amp; Labbaf, S. Electrophoretic Deposition of Bioactive Glass \\u0026ndash; Chitosan Nanocomposite Coatings on Ti-6Al-4V for Orthopedic Applications. \\u003cem\\u003eCarbohydr. Polym.\\u003c/em\\u003e \\u003cb\\u003e226\\u003c/b\\u003e (September), 115299. \\u003cspan class=\\\"ExternalRef\\\"\\u003e\\u003cspan class=\\\"RefSource\\\"\\u003ehttps://doi.org/10.1016/j.carbpol.2019.115299\\u003c/span\\u003e\\u003cspan address=\\\"10.1016/j.carbpol.2019.115299\\\" targettype=\\\"DOI\\\" class=\\\"RefTarget\\\"\\u003e\\u003c/span\\u003e\\u003c/span\\u003e (2019).\\u003c/span\\u003e\\u003c/li\\u003e\\u003cli\\u003e\\u003cspan\\u003eDrevet, R. \\u0026amp; Benhayoune, H. Electrodeposition of Calcium Phosphate Coatings on Metallic Substrates for Bone Implant Applications: A Review. \\u003cem\\u003eCoatings\\u003c/em\\u003e \\u003cb\\u003e12\\u003c/b\\u003e (4). \\u003cspan class=\\\"ExternalRef\\\"\\u003e\\u003cspan class=\\\"RefSource\\\"\\u003ehttps://doi.org/10.3390/coatings12040539\\u003c/span\\u003e\\u003cspan address=\\\"10.3390/coatings12040539\\\" targettype=\\\"DOI\\\" class=\\\"RefTarget\\\"\\u003e\\u003c/span\\u003e\\u003c/span\\u003e (2022).\\u003c/span\\u003e\\u003c/li\\u003e\\u003cli\\u003e\\u003cspan\\u003eErdogan, Y. K. \\u0026amp; Ercan, B. Anodized Nanostructured 316L Stainless Steel Enhances Osteoblast Functions and Exhibits Anti-Fouling Properties. \\u003cem\\u003eACS Biomater. Sci. Eng.\\u003c/em\\u003e \\u003cb\\u003e9\\u003c/b\\u003e (2), 693\\u0026ndash;704. \\u003cspan class=\\\"ExternalRef\\\"\\u003e\\u003cspan class=\\\"RefSource\\\"\\u003ehttps://doi.org/10.1021/acsbiomaterials.2c01072\\u003c/span\\u003e\\u003cspan address=\\\"10.1021/acsbiomaterials.2c01072\\\" targettype=\\\"DOI\\\" class=\\\"RefTarget\\\"\\u003e\\u003c/span\\u003e\\u003c/span\\u003e (2023).\\u003c/span\\u003e\\u003c/li\\u003e\\u003cli\\u003e\\u003cspan\\u003eErdogan, Y. K. et al. Morphology of Nanostructured Tantalum Oxide Controls Stem Cell Differentiation and Improves Corrosion Behavior. \\u003cem\\u003eACS Biomater. Sci. Eng.\\u003c/em\\u003e \\u003cb\\u003e10\\u003c/b\\u003e (1), 377\\u0026ndash;390. \\u003cspan class=\\\"ExternalRef\\\"\\u003e\\u003cspan class=\\\"RefSource\\\"\\u003ehttps://doi.org/10.1021/acsbiomaterials.3c01277\\u003c/span\\u003e\\u003cspan address=\\\"10.1021/acsbiomaterials.3c01277\\\" targettype=\\\"DOI\\\" class=\\\"RefTarget\\\"\\u003e\\u003c/span\\u003e\\u003c/span\\u003e (2024).\\u003c/span\\u003e\\u003c/li\\u003e\\u003cli\\u003e\\u003cspan\\u003eErdogan, Y. K., Mutlu, P. \\u0026amp; Ercan, B. Nanostructured 316L Stainless Steel Stent Surfaces Improve Corrosion Resistance, and Enhance Endothelization and Hemocompatibility. \\u003cem\\u003eAdv. Mater. Interfaces 2400968\\u003c/em\\u003e. (2025). \\u003cspan class=\\\"ExternalRef\\\"\\u003e\\u003cspan class=\\\"RefSource\\\"\\u003ehttps://doi.org/10.1002/admi.202400968\\u003c/span\\u003e\\u003cspan address=\\\"10.1002/admi.202400968\\\" targettype=\\\"DOI\\\" class=\\\"RefTarget\\\"\\u003e\\u003c/span\\u003e\\u003c/span\\u003e\\u003c/span\\u003e\\u003c/li\\u003e\\u003cli\\u003e\\u003cspan\\u003ePiszczek, P. et al. Comprehensive Evaluation of the Biological Properties of Surface-Modified Titanium Alloy Implants. \\u003cem\\u003eJ. Clin. Med.\\u003c/em\\u003e \\u003cb\\u003e9\\u003c/b\\u003e (2), 1\\u0026ndash;30. \\u003cspan class=\\\"ExternalRef\\\"\\u003e\\u003cspan class=\\\"RefSource\\\"\\u003ehttps://doi.org/10.3390/jcm9020342\\u003c/span\\u003e\\u003cspan address=\\\"10.3390/jcm9020342\\\" targettype=\\\"DOI\\\" class=\\\"RefTarget\\\"\\u003e\\u003c/span\\u003e\\u003c/span\\u003e (2020).\\u003c/span\\u003e\\u003c/li\\u003e\\u003cli\\u003e\\u003cspan\\u003eXia, J., Yuan, Y., Wu, H., Huang, Y. \\u0026amp; Weitz, D. A. Decoupling the Effects of Nanopore Size and Surface Roughness on the Attachment, Spreading and Differentiation of Bone Marrow-Derived Stem Cells. \\u003cem\\u003eBiomaterials\\u003c/em\\u003e \\u003cb\\u003e248\\u003c/b\\u003e, 120014. \\u003cspan class=\\\"ExternalRef\\\"\\u003e\\u003cspan class=\\\"RefSource\\\"\\u003ehttps://doi.org/https://doi.org/10.1016/j.biomaterials.2020.120014\\u003c/span\\u003e\\u003cspan address=\\\"10.1016/j.biomaterials.2020.120014\\\" targettype=\\\"DOI\\\" class=\\\"RefTarget\\\"\\u003e\\u003c/span\\u003e\\u003c/span\\u003e (2020).\\u003c/span\\u003e\\u003c/li\\u003e\\u003cli\\u003e\\u003cspan\\u003eGardin, C. et al. Nanostructured Modifications of Titanium Surfaces Improve Vascular Regenerative Properties of Exosomes Derived from Mesenchymal Stem Cells: Preliminary in Vitro Results. \\u003cem\\u003eNanomaterials\\u003c/em\\u003e \\u003cb\\u003e11\\u003c/b\\u003e (12). \\u003cspan class=\\\"ExternalRef\\\"\\u003e\\u003cspan class=\\\"RefSource\\\"\\u003ehttps://doi.org/10.3390/nano11123452\\u003c/span\\u003e\\u003cspan address=\\\"10.3390/nano11123452\\\" targettype=\\\"DOI\\\" class=\\\"RefTarget\\\"\\u003e\\u003c/span\\u003e\\u003c/span\\u003e (2021).\\u003c/span\\u003e\\u003c/li\\u003e\\u003cli\\u003e\\u003cspan\\u003eKazimierczak, P. \\u0026amp; Przekora, A. Osteoconductive and Osteoinductive Surface Modifications of Biomaterials for Bone Regeneration: A Concise Review. \\u003cem\\u003eCoatings\\u003c/em\\u003e \\u003cb\\u003e10\\u003c/b\\u003e (10), 1\\u0026ndash;25. \\u003cspan class=\\\"ExternalRef\\\"\\u003e\\u003cspan class=\\\"RefSource\\\"\\u003ehttps://doi.org/10.3390/coatings10100971\\u003c/span\\u003e\\u003cspan address=\\\"10.3390/coatings10100971\\\" targettype=\\\"DOI\\\" class=\\\"RefTarget\\\"\\u003e\\u003c/span\\u003e\\u003c/span\\u003e (2020).\\u003c/span\\u003e\\u003c/li\\u003e\\u003cli\\u003e\\u003cspan\\u003eSuntharavel Muthaiah, V. M., Rajput, M., Tripathi, A., Suwas, S. \\u0026amp; Chatterjee, K. Electrophoretic Deposition of Nanocrystalline Calcium Phosphate Coating for Augmenting Bioactivity of Additively Manufactured Ti-6Al-4V. \\u003cem\\u003eACS Mater. Au\\u003c/em\\u003e. \\u003cb\\u003e2\\u003c/b\\u003e (2), 132\\u0026ndash;142. \\u003cspan class=\\\"ExternalRef\\\"\\u003e\\u003cspan class=\\\"RefSource\\\"\\u003ehttps://doi.org/10.1021/acsmaterialsau.1c00043\\u003c/span\\u003e\\u003cspan address=\\\"10.1021/acsmaterialsau.1c00043\\\" targettype=\\\"DOI\\\" class=\\\"RefTarget\\\"\\u003e\\u003c/span\\u003e\\u003c/span\\u003e (2022).\\u003c/span\\u003e\\u003c/li\\u003e\\u003cli\\u003e\\u003cspan\\u003eLee, W. H., Loo, C. Y. \\u0026amp; Rohanizadeh, R. A. Review of Chemical Surface Modification of Bioceramics: Effects on Protein Adsorption and Cellular Response. \\u003cem\\u003eColloids Surf. B Biointerfaces\\u003c/em\\u003e. \\u003cb\\u003e122\\u003c/b\\u003e, 823\\u0026ndash;834. \\u003cspan class=\\\"ExternalRef\\\"\\u003e\\u003cspan class=\\\"RefSource\\\"\\u003ehttps://doi.org/10.1016/j.colsurfb.2014.07.029\\u003c/span\\u003e\\u003cspan address=\\\"10.1016/j.colsurfb.2014.07.029\\\" targettype=\\\"DOI\\\" class=\\\"RefTarget\\\"\\u003e\\u003c/span\\u003e\\u003c/span\\u003e (2014).\\u003c/span\\u003e\\u003c/li\\u003e\\u003cli\\u003e\\u003cspan\\u003eKatić, J., Krivačić, S., Petrović, Ž., Mikić, D. \\u0026amp; Marciuš, M. Titanium Implant Alloy Modified by Electrochemically Deposited Functional Bioactive Calcium Phosphate Coatings. \\u003cem\\u003eCoatings\\u003c/em\\u003e \\u003cb\\u003e13\\u003c/b\\u003e (3). \\u003cspan class=\\\"ExternalRef\\\"\\u003e\\u003cspan class=\\\"RefSource\\\"\\u003ehttps://doi.org/10.3390/coatings13030640\\u003c/span\\u003e\\u003cspan address=\\\"10.3390/coatings13030640\\\" targettype=\\\"DOI\\\" class=\\\"RefTarget\\\"\\u003e\\u003c/span\\u003e\\u003c/span\\u003e (2023).\\u003c/span\\u003e\\u003c/li\\u003e\\u003c/ol\\u003e\"}],\"fulltextSource\":\"\",\"fullText\":\"\",\"funders\":[],\"hasAdminPriorityOnWorkflow\":false,\"hasManuscriptDocX\":true,\"hasOptedInToPreprint\":true,\"hasPassedJournalQc\":\"\",\"hasAnyPriority\":false,\"hideJournal\":true,\"highlight\":\"\",\"institution\":\"\",\"isAcceptedByJournal\":false,\"isAuthorSuppliedPdf\":false,\"isDeskRejected\":\"\",\"isHiddenFromSearch\":false,\"isInQc\":false,\"isInWorkflow\":false,\"isPdf\":false,\"isPdfUpToDate\":true,\"isWithdrawnOrRetracted\":false,\"journal\":{\"display\":true,\"email\":\"info@researchsquare.com\",\"identity\":\"researchsquare\",\"isNatureJournal\":false,\"hasQc\":true,\"allowDirectSubmit\":true,\"externalIdentity\":\"\",\"sideBox\":\"\",\"snPcode\":\"\",\"submissionUrl\":\"/submission\",\"title\":\"Research Square\",\"twitterHandle\":\"researchsquare\",\"acdcEnabled\":true,\"dfaEnabled\":false,\"editorialSystem\":\"\",\"reportingPortfolio\":\"\",\"inReviewEnabled\":false,\"inReviewRevisionsEnabled\":true},\"keywords\":\"Electrophoretic Deposition, Calcium carbonate, Implant, Morphology\",\"lastPublishedDoi\":\"10.21203/rs.3.rs-7059389/v1\",\"lastPublishedDoiUrl\":\"https://doi.org/10.21203/rs.3.rs-7059389/v1\",\"license\":{\"name\":\"CC BY 4.0\",\"url\":\"https://creativecommons.org/licenses/by/4.0/\"},\"manuscriptAbstract\":\"\\u003cp\\u003eCalcium carbonate (CaCO\\u003csub\\u003e3\\u003c/sub\\u003e) have a high biocompatibility and biodegradability due to their chemical similarity to human bone tissue. Electrophoretic deposition (EPD) is an advanced technique used for obtaining biomedical coatings. This research is, for the first time, to investigate the effect of voltage and duration on the CaCO\\u003csub\\u003e3\\u003c/sub\\u003e coatings obtained by EPD on nanostructured 316L SS surface. SEM images showed that the proportion of calcium carbonate particles in the coating increased significantly with higher applied voltages. Additionally, an increase in coating thickness ( ̴20 \\u0026micro;m) was observed with longer deposition durations. The successful incorporation of CaCO\\u003csub\\u003e3\\u003c/sub\\u003e in all coatings was confirmed by SEM and XRD analysis. Also, AFM analysis confirmed that coated surface performed rougher topography and morphology. These findings suggest that bioactive CaCO\\u003csub\\u003e3\\u003c/sub\\u003e coated on nanostructured 316L surface is promising surface for biomedical applications.\\u003c/p\\u003e\",\"manuscriptTitle\":\"Investigation of Calcium Carbonate Particle Coating on Nanostructured Implant Surface for Biomedical Applications\",\"msid\":\"\",\"msnumber\":\"\",\"nonDraftVersions\":[{\"code\":1,\"date\":\"2025-07-31 12:41:10\",\"doi\":\"10.21203/rs.3.rs-7059389/v1\",\"editorialEvents\":[{\"type\":\"communityComments\",\"content\":0}],\"status\":\"published\",\"journal\":{\"display\":true,\"email\":\"info@researchsquare.com\",\"identity\":\"researchsquare\",\"isNatureJournal\":false,\"hasQc\":true,\"allowDirectSubmit\":true,\"externalIdentity\":\"\",\"sideBox\":\"\",\"snPcode\":\"\",\"submissionUrl\":\"/submission\",\"title\":\"Research Square\",\"twitterHandle\":\"researchsquare\",\"acdcEnabled\":true,\"dfaEnabled\":false,\"editorialSystem\":\"\",\"reportingPortfolio\":\"\",\"inReviewEnabled\":false,\"inReviewRevisionsEnabled\":true}}],\"origin\":\"\",\"ownerIdentity\":\"b67a40b9-57c8-4a9e-b2ab-6dd490359fd9\",\"owner\":[],\"postedDate\":\"July 31st, 2025\",\"published\":true,\"recentEditorialEvents\":[],\"rejectedJournal\":[],\"revision\":\"\",\"amendment\":\"\",\"status\":\"posted\",\"subjectAreas\":[{\"id\":52324093,\"name\":\"Biological sciences/Biotechnology\"},{\"id\":52324094,\"name\":\"Physical sciences/Materials science\"},{\"id\":52324095,\"name\":\"Physical sciences/Nanoscience and technology\"}],\"tags\":[],\"updatedAt\":\"2026-01-07T11:54:31+00:00\",\"versionOfRecord\":[],\"versionCreatedAt\":\"2025-07-31 12:41:10\",\"video\":\"\",\"vorDoi\":\"\",\"vorDoiUrl\":\"\",\"workflowStages\":[]},\"version\":\"v1\",\"identity\":\"rs-7059389\",\"journalConfig\":\"researchsquare\"},\"__N_SSP\":true},\"page\":\"/article/[identity]/[[...version]]\",\"query\":{\"redirect\":\"/article/rs-7059389\",\"identity\":\"rs-7059389\",\"version\":[\"v1\"]},\"buildId\":\"8U1c8b4HqxoKbykW_rLl7\",\"isFallback\":false,\"isExperimentalCompile\":false,\"dynamicIds\":[84888],\"gssp\":true,\"scriptLoader\":[]}","source_license":"CC-BY-4.0","license_restricted":false}