Chinese Journal of Lasers, Volume. 49, Issue 10, 1002601(2022)

Progress in Preparation of Medical Functional Surfaces by Femtosecond Laser-Induced Micro/Nanostructures

Yimeng Wang1 and Yingchun Guan1,2,3,4、*
Author Affiliations
  • 1School of Mechanical Engineering and Automation, Beihang University, Beijing 100083, China
  • 2National Engineering Laboratory of Additive Manufacturing for Large Metallic Components, Beihang University, Beijing 100083, China
  • 3International Research Institute for Multidisciplinary Science, Beihang University, Beijing 100083, China
  • 4Ningbo Innovation Research Institute, Beihang University, Ningbo 315800, Zhejiang, China
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    Figures & Tables(20)
    Typical metal implant applications
    Femtosecond laser irradiating metal surface. (a) Electron lattice energy transfer[65]: (a-1) absorption, (a-2) heating,(a-3) energy transfer, (a-4) ablation; (b) mechanical stripping[70]; (c) Coulomb explosion[73]
    TTM-MD method is used to simulate the overall visual image of Al target material splashing irradiated by 100 fs laser pulse[75] (the atoms are colored according to their potential energy. Blue represents low-energy atoms in the target body, red represents gas-phase atoms. The red dot connected by the red line marks the position of the melting front)
    Finite element simulation of SERS intensity distribution in typical Au nanoparticle structure[91]
    SERS phenomenon caused by electromagnetic enhancement and chemical enhancement mechanisms. (a) Electromagnetic enhancement mechanism; (b) chemical enhancement mechanism
    Femtosecond laser processing SERS substrate[106]. (a) Schematic of manufacturing process; (b) SEM image of silver plated substrate; (c) AFM image of silver plated LIPSS surface; (d) absorption spectrum of silver plated LIPSS surface
    Enhancement mechanism of metal surface fluorescence. (a) Plasma oscillation field; (b) fluorescence radiation of SPP regulated molecules
    Microstructure and fluorescence spectra of SEF substrate[113]. (a) Femtosecond laser induced layered LIPSS; (b) fluorescence spectra under different Cu2+ concentrations; (c) linear relationship between spectral intensity and Cu2+ concentration
    Microstructure and spectral detection of double reinforced substrates[118]. (a) Morphology of SERS-SEF substrate; (b) Raman and fluorescence spectra; (c) glucose detection
    Adhesion behavior of cells on base. (a) Protein adsorption; (b) extracellular matrix protein deposition; (c) engineering adhesion
    Cell activity of MC3T3-E1 cultured on Mg-6Gd-0.6Ca alloy with different states and cell adhesion SEM and fluorescence images[137], where (a-1) represents original surface, (a-2) represents laser remelting surface, (a-3) represents laser remelting+LIPSS surface, and (a-4) represents laser remelting+micro groove surface
    Schematic of cell migration process[139]
    LIPSS regulates cells migration[142]. (a)(b) Cycle and height of LIPSS; (c)(e) cell migration behavior on original surface, laser remelting surface, laser remelting+LIPSS surface after 48 h culture; (f)(g) cell fluorescence images of laser remelting surface and laser remelting+LIPSS surface after 48 h culture
    Proliferation of MC3T3-E1 cultured for one week (significant difference when p [147]
    Interaction between microstructure and bacteria. (a) Three dimensional diagrams of interaction between bacteria and microstructure[154], where (a-1) represents bacteria contact the surface of microstructure, (a-2) represents bacteria adsorb to the surface of microstructure, and (a-3) presents rupture of the bacterial cell wall; (b) bacteria adhere to flat surface and microstructure surface[155], where L and R represent the length and radius of bacteria, respectively, h is the height of nano column, and Rp is the radius of nano column; (c) schematic of bacteria adhering to two adjacent“nano ridges”[156], where H is the height of“nano ridge”,2R is the bottom width of“nano ridge”, SA represents contact area between“nano ridge”and bacteria, SB represents the area of bacteria hanging, r0 is the distance from the boundary between SA and SB to the x-axis, and D is the distance between two adjacent“nano ridges”
    SEM images and schematics of S.aureus and E.coli static and dynamic adhesion on hydrophilic and hydrophobic aluminum substrate surfaces after 24 h culture[160]
    Adhesion of S.aureus on titanium plate after 48 h culture[162].(a)(b) Original surface; (c)(d) LIPSS surface; (e)(f) NPs surface
    SEM and CLSM images of P.aeruginosa and S.aureus cultured on micro/nano structure and original surfaces for 18 h, where live bacteria were stained red and EPS was stained green[164]
    • Table 1. Clinical application of common medical metal materials

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      Table 1. Clinical application of common medical metal materials

      Type of medical materialMain clinical applicationApplication advantageMain limitationRef.
      InertStainless steelWidely used in various fields such as stomatology, fracture internal fixation instruments, and artificial jointsLow cost, good processability and mechanical propertiesThe toxicity and corrosion resistance of alloy elements are weaker than those of cobalt base alloys[21]
      Cobalt base alloyManufacturing and processing is very difficultThe mechanical properties and corrosion resistance are better than those of stainless steelThe joint replaces the trunk of the prosthesis connector[22]
      Titanium base alloySurgical implants and orthopaedic instrument productsThe density is similar to human bone, the new brand is non-toxic, light and has high strength and good biocompatibilityYoung’s modulus is higher than that of human bones and traditional alloy elements[23]
      InertAluminum base alloyHigh load componentsGood plasticity and biocompatibility,high corrosion resistance in body fluids, high alternating fatigue strength, and no receptor fluidNotch crack growth capability is high[24]
      Zirconium base alloyReplace human hard tissueHigh strength, good toughness and corrosion resistance, good biocompatibility, and appropriate elastic modulusZirconium is often used as an additive element in titanium implants, and its alloy system design for preparation needs to be further studied[25]
      DegradableMagnesium base alloyTissue and organ wound repair and functional reconstruction represented by degradable magnesium alloy vascular stentBiocompatibility, mechanical compatibility and biodegradability are favorable for cell growth, differentiation and transportationDegradation rate regulation[26]
      Zinc base alloyBone defect implantZinc is a trace element needed by human bodyThe mechanical properties and biocompatibility still need to be adjusted by the addition of alloy elements[27]
      TungstenMechanical detachable coil embolization for intracranial aneurysmsRadiation impermeability and good biocompatibilityDegraded tungsten is enriched in blood vessels and has certain thrombogenicity[28]
      Precious metalsDental implant material, artificial heart power supply (Pt), sterilization (Ag), clinical detection (Au and Ag)Unique biocompatibility, good ductility, and non-toxic to human bodyHigh cost[29]
      Other metal materialsBone plate, screw, pacemaker, etc.High strength, high hardness, high wear and corrosion resistance,high fatigue resistance, and suitable elastic modulusThe design of alloy system for preparation needs to be further studied[30]
    • Table 2. Conventional surface modification methods of biomedical metal materials

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      Table 2. Conventional surface modification methods of biomedical metal materials

      MethodObjectiveAdvantageInferiorityRef.
      Anodic oxidationForm corrosion resistant protective film, blocking the release of harmful elementsCoating micropores are conducive to cell adhesionThe prepared film is generally rough and porous,with poor protective effect. It is generally necessary to seal the hole after oxidation[38-39]
      Micro arc oxidationAdjust the dissolution rate, increase corrosion fatigue lifeNo pollution, low original surface requirements, can be completed in stages, without vacuum or low temperature conditionsHigh energy consumption and difficult processing in large area[40-41]
      Plasma sprayingImprove the ability of bone integration and endow the surface with antibacterial propertiesHigh cost performance, mature process, wide selection of raw materials, and large-scale productionThe equipment is expensive,the spraying rate is small, and the quality requirements of spraying materials are high[42-43]
      Ion implantationImprove friction and wear properties,improve antibacterial and corrosion resistance, and regulate surface physical propertiesNo change in thickness, no physical condition requirements, wide range of applicable elements and strong parameter controllabilityThe equipment is complex and damages the original matrix lattice[44-45]
      Electrochemical depositionIncrease the physiological stability, cell surface activity, and surface antibacterial properties of implantsVarious grain sizes can be obtained, the method is simple, the obtained nanocrystals have unique properties, the method has low cost and high efficiencyElectric burn, dark spot, gas stripe, crystalline attachment[46-47]
      Sol-gelIncrease biocompatibilityHomogeneous doping of multiple substances at the molecular levelThe preparation time is long, small holes and cracks are easy to appear in drying[48-49]
      Friction stir treatmentRefine surface grains and increase corrosion resistanceEliminate shrinkage porosity and shrinkage cavity defects, improve mechanical properties of materials, influence area is smallThe travel end keyhole needs to be repaired[50-51]
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    Yimeng Wang, Yingchun Guan. Progress in Preparation of Medical Functional Surfaces by Femtosecond Laser-Induced Micro/Nanostructures[J]. Chinese Journal of Lasers, 2022, 49(10): 1002601

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    Paper Information

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    Received: Nov. 30, 2021

    Accepted: Jan. 26, 2022

    Published Online: May. 12, 2022

    The Author Email: Guan Yingchun (guanyingchun@buaa.edu.cn)

    DOI:10.3788/CJL202249.1002601

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