Exploring the thumbprints of Ag-hydroxyapatite composite as a surface coating bone material
for the implants
Lett, J. Anita; Sagadevan, Suresh; Paiman, Suriati; Mohammad, Faruq; Schirhagl, Romana;
Leonard, Estelle; Alshahateet, Solhe F.; Oh, Won-Chun
Published in:
Journal of Materials Research and Technology
DOI:
10.1016/j.jmrt.2020.09.037
IMPORTANT NOTE: You are advised to consult the publisher's version (publisher's PDF) if you wish to cite from
it. Please check the document version below.
Document Version
Publisher's PDF, also known as Version of record
Publication date:
2020
Link to publication in University of Groningen/UMCG research database
Citation for published version (APA):
Lett, J. A., Sagadevan, S., Paiman, S., Mohammad, F., Schirhagl, R., Leonard, E., Alshahateet, S. F., &
Oh, W-C. (2020). Exploring the thumbprints of Ag-hydroxyapatite composite as a surface coating bone
material for the implants. Journal of Materials Research and Technology, 9(6), 12824-12833.
https://doi.org/10.1016/j.jmrt.2020.09.037
Copyright
Other than for strictly personal use, it is not permitted to download or to forward/distribute the text or part of it without the consent of the author(s) and/or copyright holder(s), unless the work is under an open content license (like Creative Commons).
Take-down policy
If you believe that this document breaches copyright please contact us providing details, and we will remove access to the work immediately and investigate your claim.
Downloaded from the University of Groningen/UMCG research database (Pure): http://www.rug.nl/research/portal. For technical reasons the number of authors shown on this cover page is limited to 10 maximum.
https://www.journals.elsevier.com/journal-of-materials-research-and-technology
Availableonlineatwww.sciencedirect.com
Original
Article
Exploring
the
thumbprints
of
Ag-hydroxyapatite
composite
as
a
surface
coating
bone
material
for
the
implants
J.
Anita
Lett
a,∗,
Suresh
Sagadevan
b,∗,
Suriati
Paiman
c,
Faruq
Mohammad
d,
Romana
Schirhagl
e,
Estelle
Léonard
f,
Solhe
F.
Alshahateet
g,
Won-Chun
Oh
h,∗ aDepartmentofPhysics,SathyabamaInstituteofScienceandTechnology,Chennai,TamilNadu,IndiabNanotechnology&CatalysisResearchCentre,UniversityofMalaya,KualaLumpur50603,Malaysia cDepartmentofPhysics,FacultyofScience,UniversitiPutraMalaysia,43400Serdang,Selangor,Malaysia
dSurfactantResearchChair,DepartmentofChemistry,CollegeofScience,KingSaudUniversity,P.O.Box2455,Riyadh,KingdomofSaudi
Arabia11451
eGroningenUniversity,UniversityMedicalCenterGroningen,AntoniusDeusinglaan1,9713AWGroningen,Netherlands fESCOM,UTC,EATIMR4297,1alléeduRéseauJean-MarieBuckmaster,60200Compiègne,France
gDepartmentofChemistry,MutahUniversity,P.O.BOX7,Mutah,61710Karak,Jordan
hDepartmentofAdvancedMaterialsScienceandEngineering,HanseoUniversity,Seosan-si,Chungnam356-706,RepublicofKorea
a
r
t
i
c
l
e
i
n
f
o
Articlehistory:Received30June2020 Accepted7September2020 Availableonline21September2020
Keywords:
Polylacticacidscaffolds Silverdopedhydroxyapatite Fuseddepositionmethod Antibacterialstudies Hemocompatibility Hardnessstudy
a
b
s
t
r
a
c
t
Polylacticacid(PLA),althoughhasmanyinterestingphysicochemicalcharacteristics,the stronghydrophobicityandalackofantibacterialactivityrestrictingitswidespread appli-cationinthemedicalsector.InaviewofaddressingsomeofthelimitationsofPLA,the currentstudyaimedtotesttheantibacterialefficacyofactivemetal-dopedbioceramic/PLA compositeformedbythefuseddepositionmanufacturing(FDM)technique.Forthetesting, wepreparedpolyvinylalcohol(PVA)boundsilver-hydroxyapatite(Ag-HAp)compositeand furtherappliedasalow-temperaturecoatingontothePLAscaffolddesignedforthe appro-priatecelldevelopment,differentiation,andbio-mineralestablishment.Fromtheanalysis, werevealedthatthelargersurfaceareaofthree-dimensional(3D)printedcomposite mate-rialhavingthematrixporositymakesitaperfectbiocompatiblematerialwithnolosstoits mechanicalpotency.TheHAp/PLAandAg-HAp/PLAcompositesweretestedforthe hemo-compatibility,andantibacterialactivity(gram-positiveandgram-negativebacteria).Further, themechanicalpropertyoftheAg-HAp/PLAscaffoldwastested.Theresultsdemonstrated thattheAg-HAp/PLAcompositeoffersthebiocompatibilityandantibacterialabilityand thereforecanserveasthepotentialboneimplantmaterial.
©2020TheAuthor(s).PublishedbyElsevierB.V.Thisisanopenaccessarticleunderthe CCBY-NC-NDlicense(http://creativecommons.org/licenses/by-nc-nd/4.0/).
∗ Correspondingauthors.
E-mails:anitalett2014@gmail.com(J.A.Lett),drsureshnano@gmail.com(S.Sagadevan),wcoh@hanseo.ac.kr(W.Oh). https://doi.org/10.1016/j.jmrt.2020.09.037
2238-7854/©2020The Author(s). PublishedbyElsevier B.V.Thisis anopen accessarticleunderthe CC BY-NC-NDlicense (http:// creativecommons.org/licenses/by-nc-nd/4.0/).
1.
Introduction
Additive manufacturing (AM), commonly known as three-dimensional (3D) printing offers a range of fascinating pathwaysforthefabricationofcompositematerialsoverother monolithicprototyping.Thus,bymakinguseofthisAM tech-nique,several biomaterialsare being fabricated like tissue engineering[1,2],softcomposites[3],ceramics[4],magnetic materials[5],anddirectbiologicalmaterialprintings[6].Based ontheapplication,thistechniquecanparticularlybehelpful inthebiomedicalsectorfortheregenerationofdefectivebone tissuescaused becauseofaccidentsorsurgicalamputation oftumors[7].Sincetheusageofsyntheticmaterialsforthe developmentofboneimplantshelpstoreconstructthebone tissueswithstrongstructuralsupportandnolosstothe inter-ferencesofbiologicaltissue[8,9].Toserveforsuchbehavior, thebiodegradablematricesareindicatedtoprovide momen-taryscaffoldswithinwhichthebonetissuescanregenerate. Amongmanydifferentpolymers,polylacticacid(PLA)offers excellentbiocompatibility,biodegradability,non-toxicity,and mechanicalstrengthandhencefindsitsusageinmany differ-entclinicalapplicationslikedrugdeliverysystems,surgical stitches,medicalimplantabledevicesetc.[10].
Fuseddeposition manufacturing (FDM) isthe most fre-quentlyusedpracticefortheconstructionofpureplasticparts withlowcosts,negligiblewastes,andsimplicitywith mate-rial switching [11,12]. PLA isone of the most encouraging syntheticpolymers thatcan be usedas asource biomate-rialintheFDMtechniqueandisduetothefactthatitcan undergo degradation in the aqueous medium and is bio-compatibleinthebiologicalsurrounding[12].Ingeneral,the mechanicalpropertiesofpurePLAscaffoldsarecomparable with the natural bone and so, it can be used for cranio-facialbonerestorationand cranial defects[10]. Conversely, thePLA hasstronghydrophobicitythat limitsitsextensive application in medicine and so there is astrong need for theidealbioimplantablescaffoldmaterialthatcanfacilitate the growth and activity of cells like cell adhesion, prolif-eration, and functional differentiation [13]. Besides that, it mustbebioactiveorbioresorbablewithadequate mechani-calpropertytoendurestressstatesthatmightappearatthe implantedsite.Inthatway,theimplantablescaffoldcanact asextracellularmatrix(ECM)fortissuerejuvenation.Inrecent worksbyAlvarez-Barretoetal.[14]fabricated Arg––Gly–Asp-modifiedPLAscaffoldstoregulatethecellcharacteristicsand progresstissuefunctioningforabetterandwell-organized tis-sueengineeringapproaches.ThedepositedCaPceramicover PLAnanofibrousscaffoldswascomparabletotheconstituents ofnaturalbone,butnotabletoachievethedesired osteoin-duction[15].Bearinginmindthatthemainconstituentsof natural bone are collagen fibers and hydroxyapatite (HAp) crystals,andinthatway,thenano-HAphasexcellent prop-ertiessuchasbiocompatibilityandbioactivitythatarecrucial forcelldevelopment[9].Consequently,theinorganic/organic compositematerialsencloseagreaterpotentialforbone tis-sueengineeringapplications.Numerousscaffoldshavebeen fabricatedbydirectlymixingthecompositeactiveadditives butleadstouncontrolledhomogeneityinthepolymermatrix [12].
Inourdaytodaylifedealswithvariousviruses,fungi,and bacteriaandthus,themanufacturedHApimplantable mate-rialshouldnotallowanyofthesemicroorganismstogrowon itssurface.ThesyntheticHApdoesnotexhibitany antibac-terialpropertyandthusitbecomesimportanttomodifyits surface with activebacteriostaticelements like Ag,Sr, Zn, Ce,Ti,etc[16,17].Asanexample,thepresenceofAgmetal withactiveantibacterialpropertycaneasilydamagethe bac-terialcellwall,aswellasbindtotheDNAandRNAofbacteria andtherebypreventingthegrowththatfinallyresultsin bac-terial annihilation [18]. Besides, the radius of Ag+ atomis
0.126nmwhichisalmostthesameastheradiusofCa2+atom (0.100nm),thereforeundersomeconditions,theAgionscan bereplacedbytheCaionsintheHApcrystallattice. There-fore,toadvancethe biomedicalandclinicaluses ofHAp,it isveryessentialtoincorporateAgionsintotheHAp’scrystal latticeandinthatview,someoftheresearchershavefocused ondevelopingHAp-basedcompositecoatings[19,20].
BytakingadvantageofthebioceramicpropertiesofHApto serveasanaturalboneandAg’santibacterialproperties,we haveincorporatedAg+ionsintotheHApcrystalstoform
Ag-HApandfurthersurfacemodifiedwithPLA scaffoldsusing PVA(polyvinylalcohol)tofinallygenerateAg-HAp/PLA scaf-fold. Thehighlightsofthe study reportedhere includethe fabricationofrequiredinterconnectedporousPLA scaffolds bytheFDMtechniqueusingappropriateCADdesign.Thus, thepreparedHAP/PLA,Ag-HAp/PLAcompositesandscaffold werecharacterizedforthemicro-structure,crystallinity, ele-mentalcomposition,mechanicalproperties,biocompatibility, andantibacterialefficacy.
2.
Materials
and
methods
2.1. 3DprintingofPLAframeworks
TheCADmodelsforthePLAscaffoldsweredesignedusing CatiadesignsoftwareandfabricatedbyaCrealityEnder-3 pro-HighPrecision3DprinterbyShapetool3DTechnologyFSD machine.BeforetheFDMprocess,theSTL(Standard Tessella-tionLanguage)filecreatedbytheCADsoftwareisfragmented into thin horizontalslicesand the widthofeach layercan bedrivenaspertherequirement[21].Fig.1showstheFDM printer,printingprocess,andtheformedmaterial.
2.2. SynthesisofAg-dopedHAp
For the formationofAg-Happarticles, theprecursors used includetheanalyticalreagentgradecalciumnitrate tetrahy-drate; Ca(NO3)2·4H2O, ammonium dihydrogen phosphate;
(NH4)H2PO4, and silver nitrate; AgNO3 (Merck, Mumbai,
Maharashtra, India). During the synthesis, we first formed nano-HAp bysimplydissolvingthe calciumand phosphate solutionsabovepH10toundergotheprecipitationprocess.In thisprocess,thecommonpracticerequirestheuseofa stoi-chiometricratioofCa:Ptobe1.67andinvolvesthedropwise additionofonereagenttotheotherwithcontinuousstirring underaninertatmosphere.Thisresultsinthegenerationofa suspensionunderatmospherictemperature,whichon wash-ing,drying,andsmashingformsthenano-powderofHAp.
Fig.1–SchematicrepresentationoftheFDMprintingprocessfortheformationofPLAporousscaffolds.
For the synthesis of Ag-doped HAp, 0.45M of Ca(NO3)2·4H2O along with 0.05M of AgNO3 was first
dis-solved in distilled water and adjusted to a total volume of 250mL and kept in a conical flask. Similarly, a 250mL volumeof0.3Mof(NH4)H2PO4waspreparedseparatelyusing
distilled water and transferred toa burette. On mixing of bothsolutionsataflowrateof3mL/min,roomtemperature, andstirringfor3hresultsintheformationofamilkywhite solution(havingthestoichiometricratioof1.67).Thewhole process pH was maintained at 11 (>10) by the dropwise addition of ammonia to Ca(NO3)2·4H2O+AgNO3 solution.
Thewhite colouredsolutionwaskeptatroomtemperature overnight,followed by washing thrice with distilled water, subjectedtocalcinationat100◦Cfor3h,andfinallysintered at500◦CtoobtainAg-HApcomposite.
2.3. IncorporationofAg-HApcompositeontothe3D PLAframeworks
For the surface modification ofAg-HAp composite at low-temperatureconditions,wehaveusedPLAscaffoldsandfor effectivebonding,polyvinylalcohol(PVA)wasemployedasthe bindingagent.Forthesurfacemodificationreaction,about1g ofPVA(analyticalgrade)wasmixedto50mLofdistilledwater, stirredusingamagneticstirrerat50◦Ctoformahomogenous solution. Now,the Ag-HAp compositedispersedinethanol was added to the PVA solution, whilestirring for another 2h,andaftertheperiod,theFDMprintedPLAscaffoldswere immersedandkeptinthePVAsolutionfor24h.Attheendof theincubationperiod,boththepartswereremoved,allowedto drip-dry,andthenplacedinanairdryermaintainedat50◦Cfor oneweektoobtainthefinalproductofAg-HAp/PLAscaffold.
3.
Characteristic
techniques
3.1. Morphologicalandstructuralcharacterization Themorphologicalorganizationandsurfacenatureof sam-pleswereobservedusingthefieldemissionscanningelectron microscopy (FESEM; JMS7500F; JEOL, Tokyo, Japan) and high-resolution transmission electron microscopy (HRTEM: FEI-TECNAI G2-200kV TWIN). The energy-dispersive X-ray (EDX:X-Max,USA)analysiswitharegularunit(Oxford
Instru-ments,UK)connectedtotheFESEMinstrumentwasemployed fortheelementalmappingandcompositionofelementsinthe composite.Forthesampling,thetestingmaterialswerefirst dispersedinethanol,sonicated,andthenplacedadropof sus-pensionontothecleanedaluminumfoil,driedatatmospheric air,andwassputter-coatedwithgold(EdwardsSputterCoater S150B,London,UK).Similarly, thepowder X-raydiffraction (XRD)analysis(Bruker-D8powderdiffractometer,BrukerAXS GmbH,Karlsruhe,Germany),Fouriertransforminfrared(FTIR) spectroscopy (from Agilent Cary 630, Agilent Technologies, SantaClara,CA,USA),andX-rayphotoelectronspectroscopy (XPS;SSX-100spectrometer)havingmonochromatizedX-ray beamAlK␣radiation(operatingat1486.6eV)wereemployed fortheothercharacterizations.
3.2. Biocompatibilitystudies
3.2.1. MeasurementofFBSadsorptionontotheHAp samples
ThebiocompatibilityofHApandAg-HAp/PLAcompositewas assessedbytheproteinadsorptionassayandforthe analy-sis, thetesting pellets(atadimension10×1mmdia) were engrossedintrisbufferatpH7.4fora20hperiod.Then,the scaffoldswereincubatedinMinimumEssentialMedium (␣-MEM)containing10%FetalBovineSerum(FBS;syntheticcell culturemedia)for4h.Attheendoftheincubationperiod, thescaffoldswerefirstrinsedthoroughlywithanisotonictris buffer solution, and thenthe surfacewasexposed toa2% sodiumdodecyl sulfate(SDS)solutionfor24htoelude any adsorbedproteins.Thetotalcapacityofadsorbedproteinwas investigatedusingtheBCAproteinassayequipmenthaving themicroplatereader(MolecularDevicesLLC,Sunnyvale,CA, USA).
3.2.2. Hemolyticstudies
ThehemocompatibilityofHApandAg-HAp/PLAcomposite wasexamined aspertheearlierproceduredescribed byLv et al. [22]. Briefly, about 1.25mLof sterile saline was first combinedwith1mgoftestingsample(HAporAg-HAp/PLA composite powder)andinaseparatetube, 4mLvolumeof blood collected from the healthy human was dilutedwith thatof5mLsterilesalinesolution.Fromthis,20Lofdiluted blood solutionwascollectedandmixedwiththatofa test-ingsamplecontainingtubeandfurtherincubatedat37◦Cfor
30minandthenall thetubeswere incubatedfor60minat 37◦Cinashakingwaterbath.Thereleaseofhemoglobinwas determined aftercentrifugationbyphotometricanalysis of thesupernatantat540nmusingtheUVspectrophotometer (ShimadzuUV2450)andfurtherthehemolyticrate(HR)was calculatedfromtheEq.(1),
HR= [(Dt−Dnc)/(Dpc−Dnc)]×100% (1)
whereDt,Dnc,andDpccorrespondstotheabsorbancesofthe
testingsample,negativecontrol,andpositivecontrol, respec-tively.
3.3. Antibacterialstudies
Forthetesting,thesamplesweremadeintopelletsof10mm diameterand2mmthickness.Toaccomplishthestudy, ster-ilePetri-dishes(90mmdiameter)comprisingsterilenutrient agarmedium(15mL)weretaken.After24hofbacterial cul-ture,thejustpreparedbacterialinoculumswerespreadover theentiresurfaceofagarmediumthriceusingasterile cot-tonswab,tomakesurethatthebacterialcultureisthoroughly andevenlydistributedonthesurfaceofplates.Thetest sam-pleswereboredinthemediumineachplateandtheplates werepreservedatnormalroomtemperaturefor45minand furtherincubatedat37◦Cfor24h.Finally,thediameterofthe zoneofinhibition(mm)wasmeasuredat3-equidistantplaces takenfromthecenteroftheinhibitionzone,andtheaverage ofthesethreevalueswastakenasthefinal.Allprocedures wereinco-operatedintriplicate.
3.4. Hardnessstudy
For this, the compressive tests were carried out on a 10×10mmdimensionofPLA-coated HApand Ag-HAp/PLA scaffold by making use of the Universal testing machine (INSTRON5566,Germany)withamaximumcompressionload cellof10kNandacross-headspeedof1.0mm/min.
4.
Results
and
discussion
ThemineralizedAg-HAp/PLAporous scaffoldsinthis work usedalow-temperatureprocess tomodifythe PLAsurface ascomparedtotheplasma-sprayedcoatingthatrequires ele-vated temperatures. The use ofmineralized Ag-HAp along withPVA asa biocompatible binder onthe surface ofPLA porous scaffolds under physiological conditions in a more rapidand simplemethodtoemerge exquisitecrystal mor-phologyforcellgrowth.Fig.2showsthecomparisonofthe powderXRDpatternofpureHApandAg-HApcomposite,and fromthefigure,theremarkablepeaksidentifiedatthe2of 31.74,32.18, and32.89canbeindexed tothe HApmaterial and alsomatcheswell withthe JCPDScard #89-6495. The veryfeeblepeakforsilverassociatedat2 of38.1 and44.2 (JCPDScard No.4–783) are alsofound. Thesharp peaks of theHApsampleindicateitshighlycrystallinenature(5.16%); whereas,theAg-dopedsilverHAppeaksarebroadsignifying thechange(decrease)incrystallitesize(34.8nm)andhence thecrystallinity(1.95%)ofthedopedsample[23].Theaddition
Fig.2–ComparisonofthepowderXRDpatternofHApand Ag-HApnanopowder.
Table1–Comparisonofthecrystallinitydataforthe
HapbeforeandafterdopingwithAgmetal.
Sample Thecrystallitesize(nm) Crystallinity(%)
HAp 71 5.16
Ag-HAp 34.8 1.95
ofsilvernitrate(0.05Mofsilvernitratesolutionsintocalcium nitratesolution)resultsinthereplacementofCainHApwith AgionsandthusleadstothedistortionofHAplatticeresulting intheformationofamorphousnature.Weobserved signifi-cantlynodifferencefromtheXRDpattern,anditcoulddue tothepreferredorientationofdopedelements(Ag) concen-trationaslow[24];thetracequantityofmetalnitridedopant couldnotbeabletoproduceaconsiderableimpactintheXRD pattern.Sincethedopantconcentrationislow,theimpactof thepeaksintheXRDpatternisveryfeebleandhardlydetected duetothelowerinstrumentaldetectionlimit(Table1).
TheanalysisofcompositesbytheXPStechniqueis com-monly used for the surface analysis and to detect trace elements(excepthydrogen)alongwiththeiroxidationstates inanunknownmaterial.Fig.3representstheXPSsurveyand the Agelemental spectrum ofthe Ag-HAp composite.The surveyspectrumpredictsthepresenceofmajorconstituents fortheelementsofCa,P,Ag,C,and OofAg-HAp compos-ite.Fromthespectra,weobservedthepeaksatthebinding energypositionsof348eVand351eVthatcanbeattributedto theCa2p3/2andCa2p1/2,respectively[25].Similarly,theother
peaksobservedcorrespondingtothebindingenergiesof190 eV,531eV,and532.2eVcorrespondstoP2s,O1selementsof theoxygenatomsassociatedwiththephosphategroupand adsorbedwaterrespectivelyinAg-HAp [26]. Theminuscule peakfoundobviouslyat368.2and374.3eVcorrespondstoAg 3d3/2andAg3d5/2agreeswiththeliterature[23].Althoughthe
concentrationofdopantissmall,thischaracterizationgives additionalevidenceforthesuccessfuldopingofAg+intothe
HAplattices.
Figs. 4 and 5 show the SEM, TEM, elemental mapping, EDX,andSAEDpatternofthepureHAppowderandAg-HAp
Fig.3–XPSspectrumofAg-HApcompositeandAg’selementalspectrum.
compositerespectively.TheSEMimageprovidesinformation abouttheparticlesizeandtypicalshapefortheas-prepared samples(Fig.4).Itcanbeobservedfromthefiguresofboththe samples,dopedaswellaspureHApexhibitsagglomeration, andcanbeseenthatthedopingofAg+ metalhas
consider-ableinfluenceonthemorphologyofHAppowder.Wenoted fromthe morphologythatthe HApsamplespreparedfrom theAg-dopinghavemuchsmallerparticlesizeasagainstthe pureHApones.Further,theEDXspectraandtheelemental mappingconfirmsfortheuniformdistributionofAginthe
Ag-HApsamplealongwithelementsofCa,P,andO,andthereby confirmingforthesuccessfulformationofAg-HApcomposite. TheTEMmicrographofpureHAp(Fig.4)showstheparticles ofnon-uniformsizedistributionwithelongatedrod-like mor-phologywithasphericallumpofaround50nmsize,whilethe Ag-HApparticles(Fig.5)exhibitsimplesmallrod-shaped mor-phology. Thelengthofthe nanorodsvariedfrom20−30nm andthediameterwasbetween5−10nmandthedoped Ag-HApsampleisamorphousasseenintheSAEDpatternand the brightspotsdiffusetoformrings.Inoneofthesimilar
Fig.5–SEM,elementalmapping,EDX,TEM,andSAEDpatternofsynthesizedAg-HApnanopowder.
study,Chungetal.(2006)reportedforthepresenceof crys-tallinephaseofAg2OalongwiththeHApandnitratephases
andisstronglyinfluencedbyAg’sdegreeofsubstitutionandin this,theformationofAg2Onucleididnotseemtobedetected
[26].
Fig. 6 displays the stereo zoom optical images ofpure HApandAg-HAp/PLAscaffoldalong withitsEDX andSEM at different magnifications. From the figure (Fig. 6e), the scaffold-coatedHApsampleseemstobeexhibitingthehighly open-porousstructure,wherethe largeporesare intercon-nectedwitheachother.Thesizeofmacroporesdependson thePLAframework,anditiseasytocustomizethescaffolds ofdesiredshapeandsizeasitisparticularlyrequiredforsome needs.Besides,theEDXprovidedelementalanalysis(Fig.6b,f) indicatesthepresenceofallelementslikeCa,P,C,O,andan additionalelementAgforthedopedHApandthereby confirm-ingforthesuccessfulformationofAg-HAp/PLAscaffold.Also, theSEMprovidedmorphologies(Fig.6g–h)showedthatallthe coatingsarecompact,even,andcontainaggregatedgranules atthesurface,ascomparedagainstthepureHAp(Fig.6c–d). TheformationofsuchporousscaffoldsbytheHApcomposite isthemostpromisingmaterialinparticularforbonedefects, repair,andtissueregeneration.Someoftheearlierresearches onscaffoldmaterialshaveconfirmedthesamethattheporous structuresareessentialcriteriafortheconductionofessential nutrientstohelpwiththetissuegrowth[27].
Itiswellrecognizedthatuponimplantation,the adsorp-tion ofessentialnutrients and proteinstakes place onthe biomaterial’sexteriorsurfaceandthisoccursbythe regula-tionofdiversebiologicalproceedingslikebiocompatibility,cell adhesion,immuneresponses,andassociatedblood coagula-tion [28]. Sincethe proteinadsorptionis avibrant process
and is also strongly influenced by the nature of the pro-teinlayersavailableatthesurfaceofbiomaterial,inaddition tothetopographical/textural/pore-sizecharacteristicsofthe biomaterial. The mentioned biomaterial characteristics, in general,decideswhichproteinsarecapabletobindoverthe material[29].Italsoassiststherestriction/adsorptionof cer-tainproteinswithinthedeformitiesofmaterial’ssurfaceand observedthatthetypeofadsorbedproteinatthesurfaceis simplyaffectedbythecharacteristicsoftheunderlying mate-rial,forexample,theporousscaffold’sphysicalandchemical propertiesrestrictitsadsorptioncapacity[30].Takinginto con-sideration these facts, the ␣-MEM with 10% FBS was used to assess the adsorptioncapacityofprotein ontothe pure HApandAg-HAp/PLAcomposites.AsshowninFig.7,thetotal amountofproteinthatgotadsorbedontothesurfacesofthe twomaterialsaredifferentandisattributedtothechanges inthemorphologiesandconstituents.TheAg-HAp/PLA sam-plesupportedthesignificantlyhighproteinadsorptionthan thatofcorrespondingpureHApduetotheavailabilityof addi-tionalAgconstituentand PLAscaffolds thatinfluencesthe crystallinityandporosity.Also,thesurfaceoftheAg-HAp/PLA sampleisunevenandimpregnatedwiththeactiveelement thatsupportsmoreproteinadsorption.However,weseethat the pure HAp materialhas protein adsorption capacity to some extent,but this can bedraggedtoa significant level bymeansofincorporatingtheAgmetalandwithscaffolds, andtherebyshiftingtothepromisinglevels.Furtherstudies havetobeperformedtoenlightenitsbiocompatibilityasa promisingscaffoldingbiomaterial.
Hemolysisisavitalaspecttoevaluatethe biocompatibil-ity ofmaterialand the hemolyticassaysare carriedout to investigate the interaction ofnanoparticles withthe outer
Fig.6–(a,e)Opticalimages,(b,f)EDXspectrums,SEMimagesat100m(c,g),and5m(d,h)ofpureHApandAg-HAp/PLA scaffoldrespectively.
Fig.7–FBSadsorptionontothesurfacesofpureHApand Ag-HAp/PLAcomposite.
membranesoftheredbloodcellbyaccessingthedischarged hemoglobin [31]. Since the HAp particles interrelate with manycopiouscellularsystemsinourbody,whilstafewof these interactions can perhapslead to defective cells and kindleplateletactivation,coagulation,andthrombus devel-opment[32,33].Fig.8showsthehemolyticassaycomparison ofHApandAg-HAp/PLAcomposite.AspertheASTMF 756-00guidelines,anysamplewithhemolysisratelessthan2% isconsideredtobenon-hemolytic,andbasedonthis,bothof ourHApcontainingsamplesareconsideredtobethesuitable materialsforbiomedicalapplications. Fromthe testing,we foundthatthehemolysisrateofAg-HAp/PLAcompositefound tobe0.8%greaterthanpureHAp,andstillbeconsideredas non-hemolyticasbothofthesample’svaluesarelessthan2%. Itcanalsobeseenthatthehemolysisratioisstronglyaffected
Fig.8–HemolyticassaycomparisonofpureHApand Ag-HAp/PLAcomposite.
bytheconcentrationofdopantanditsdegreeofcrystallinity, withthe latterhavingamoredominatingrole towardsthe hemolysis[34].
The antimicrobial activity tests were conducted for the pure HAp and Ag-HAp/PLAcomposite against the bacteria E. coli (gram-negative) and S. aureus(gram-positive), where theanalysisofresultsindicatedtheAg-dopedcompositehas higherinhibitionofbacterialgrowthasagainsttheun-doped ones.Also,withintheAg-dopedcomposite,E.colidisplayed more zone ofinhibition (3mm) in comparisonwith gram-positivebacteria(2mm)andthereby signifyingthestronger abilityofS.aureusbacteriatofightagainstthetoxicresponses ofthecomposite(Fig.9).Also,theobservationofno antibacte-rialactivityforthepureHApsampleandisduetotheabsence ofstrongerantibacterialagentAginthesample.However,the observeddifferenceofactivityfortheAg-HAp/PLAcomposite amongE.coliandS.aureusmaybeduetothedifferencesin thecellwallresponsesagainsttheAgmetal.SinceE.colihasa
Fig.9–AntibacterialassayofpureHApandAg-HAp/PLAcompositeagainstGram-positivebacteria(S.aureus)and Gram-negative(E.coli).
comparativelythinnercellwall(itsassociatedcharacteristics) andtheantioxidantenzymes(catalase)ofS.aureusprovided thesensitivityandstrongeroxidantresistance(respectively) againstthetestedAg-HAp/PLAcomposite[19].
Boneformsthe skeletonsystemofthebody andsoany basic biomechanical requirements of the implanted scaf-foldingbiomaterialincludeadequate bending,compression strength,appropriatetoequalizethestrengthofaparticular implantsite.Themechanicalcharacteristicsofnaturalboneto alargerdegreeofextentfluctuateconcerningage.Numerous researchershavereportedthatthereactionofthehosttothe implantedmaterialismainlydrivenbythemechanicalaswell asbiologicalcharacteristics[35].Researchershaveconducted studiesbycombiningpolymerswithceramicstoovercomethe restrictionsofpolymerstoimproveitshydrophobicbehavior aswellascell adhesionproperties.Inthat view,the incor-poration of PLA polymer for the implant applications has theadditionaladvantageofdecomposingthepolymeritself intocarbon dioxide,water,etcandinthatway,thereisno needtoremovefrom thebody [36]. Thestress-strain anal-ysisofthe fabricated PLAscaffold (Fig. 10) byFDMproved
Fig.10–Thestress-strainanalysisofAg-HAp/PLAscaffold.
tohaveabendingstrengthofapproximately125MPa, com-parable to the strength of cortical bone and so, it can be used for the load-bearing applications. The coating of the scaffold withbiocompatible materialimproves its biocom-patibility as demonstrated byhemolytic assay and protein adsorptionstudies.Therefore,thecustom-madescaffoldsto meettherequirementsofindividualswithdesiredshapescan bepreparedbytheFDMtechniquewithceramicpolymer com-positecoatingtomeetthestrengthcompatiblewiththatof corticalbone.
5.
Conclusion
Thismanuscriptemphasizesasimpleandeffectivewayto amendthesyntheticbio-inertPLApolymerscaffold(prepared byFDMtechnique)toabiocompatiblescaffoldbysuccessfully coatingthesurfacebyAg-HAp/PLAscaffoldbysimpledip coat-ing.TheXRDdiffractogramrevealsthatthereisanincrease incrystallinitywithareductionincrystallitesizeasHApis dopedwithsilver.TheXPSstudiesonAg-HApconfirmedthe incorporationofAgonthecrystalstructureHAp,eventhough theconcentrationofAgdidnotproducevisiblediffractgram producedbyXRD.Thesuccessfulformationofthe compos-itewasconfirmedbytheEDXanalysis,whilethemorphology studies providedthe shapesandsizesoftheparticles.The antibacterialactivityofthecompositepowdershowedgreater inhibitionefficiencytowardsE.colibetterthanS.aureus organ-isms.TheinvitrohemocompatibilitytestoftheAg-HAp/PLA compositeshowedlessthan2%ofhemolyticactivityand con-sideredtobegoodcompatibilitywithhumanblood.Theinvitro proteinadsorptiontestoftheAg-HAp/PLAcompositeshowed moderateadsorptionofFBSonthesurfacenecessaryfor vari-ousnutrientstransport.Finally,thehardnesstestconfirmsthe scaffoldbendingstrengthiscompatiblewiththecorticalbone. Overall,basedonthecumulativeanalysisofinvitro biologi-calandhardnesstests,itcanbesuggestedthatthefabricated nanocompositecoatedAg-HAp/PLAscaffoldmay serveasa potentialpolymericbiomaterialforbonetissueregeneration applications.
Conflict
of
interest
Theauthorsdeclarenoconflictsofinterest.
Acknowledgments
This work was financially supported by the University of MalayaResearchGrant(RU001-2019,RU001-2020). TheKing SaudUniversityauthorisgratefultotheDeanshipof Scien-tificResearch,KingSaudUniversityforfundingthroughthe ViceDeanshipofScientificResearchChairs..
r
e
f
e
r
e
n
c
e
s
[1] LeeM,DunnJCY,WuBM.Scaffoldfabricationbyindirect three-dimensionalprinting.Biomaterials2005;26:4281–9. [2] ShenH,NiuY,HuX,YangF,WangS,WuD.Abiomimetic3D
microtubule-orientatedpoly(lactide-co-glycolide)scaffold withinterconnectedporesfortissueengineering.JMater ChemB2015;3:4417–25.
[3] FrølichS,WeaverJC,DeanMN,BirkedalH.Uncovering nature’sdesignstrategiesthroughparametricmodelling, multi-material3Dprinting,andmechanicaltesting.AdvEng Mater2017;19:1600848,8pp.
[4] PredoiD,IconaruSL,PredoiMV,Motelica-HeinoM,Guegan R,ButonN.Evaluationofantibacterialactivityofzinc-doped hydroxyapatitecolloidsanddispersionstabilityusing ultrasounds.Nanomaterials2019;9:515,22pp.
[5] ZhuW,LiJ,LeongYJ,RozenI,QuX,DongR,etal.3D-printed artificialmicrofish.AdvMater2015;27:4411–7.
[6] MironovV,PrestwichG,ForgacsG,etal.Tissueengineering byself-assemblyandbioprintingoflivingcells.
Biofabrication2010;2:022001.
[7] BrydoneAS,MeekD,MaclaineS.Bonegrafting,orthopaedic biomaterials,andtheclinicalneedforboneengineering. ProcInstMechEngH2010;224:1329–43.
[8] IconaruSL,ProdanAM,ButonN,PredoiD.Structural characterizationandantifungalstudiesofzinc-doped hydroxyapatitecoatings.Molecules2017;22:604,13pp. [9] CiobanuCS,IconaruSL,CoustumerPL,PredoiD.Vibrational
investigationsofsilver-dopedhydroxyapatitewith antibacterialproperties.JSpectrosc2013:471061,5pp. [10]TofailSAM,KoumoulosEP,BandyopadhyayA,BoseS,
O’DonoghueL,CharitidisC.Additivemanufacturing: scientificandtechnologicalchallenges,marketuptakeand opportunities.MaterToday2018;21:22–3.
[11]BoseS,KeD,SahasrabudheH,BandyopadhyayA.Additive manufacturingofbiomaterials.ProgMaterSci
2018;93:45–111.
[12]KalitaSJ,BoseS,HosickHL,BandyopadhyayA.Development ofcontrolledporositypolymer-ceramicscaffoldsviaFDM. MaterSciEngC2003;23:611–20.
[13]LettJA,SundareswariM,RavichandranK.Porous hydroxyapatitescaffoldsfororthopedicanddental applications—theroleofbinders.MaterTodayProc 2016;3(6):1672–7.
[14]Alvarez-BarretoJF,LandyB,VanGordonS,PlaceL,DeAngelis PL,SikavitsasVI.Enhancedosteoblasticdifferentiationof mesenchymalstemcellsseededinRGD-functionalizedPLLA scaffoldsandculturedinaflowperfusionbioreactor.JTissue EngRegenMed2011;5(6):464–75.
[15]HeC,XiaoG,JinX,SunC,MaPX.Electrodepositionon nanofibrouspolymerscaffolds:rapidmineralization,tunable
calciumphosphatecompositionandtopography.AdvFunct Mater2010;20(20):3568–76.
[16]PredoiD,IconaruSL,PredoiMV.Dextran-coatedzinc-doped hydroxyapatiteforbiomedicalapplications.Polymers 2019;11:886,16pp.
[17]YuanQ,WuJ,QinC,XuA,ZhangZ,LinY,etal.One-pot synthesisandcharacterizationofZn-dopedhydroxyapatite nanocomposites.MaterChemPhys2017;199:122–30. [18]JadalannagariS,DeshmukhK,RamananSR,KowshikM.
Antimicrobialactivityofhemocompatiblesilverdoped hydroxyapatitenanoparticlessynthesizedbymodified sol-geltechnique.ApplNanosci2014;4:133–41.
[19]FieldingGA,RoyM,BandyopadhyayA,BoseS.Antibacterial andbiologicalcharacteristicsofsilvercontainingand strontiumdopedplasmasprayedhydroxyapatitecoatings. ActaBiomater2012;8:3144–52.
[20]RoyM,FieldingGA,BeyenalH,BandyopadhyayA,BoseS. Mechanical,invitroantimicrobial,andbiologicalproperties ofplasma-sprayedsilver-dopedhydroxyapatitecoating.ACS ApplMaterInterf2012;4:1341–9.
[21]GibsonI,RosenDW,StuckerB.Additivemanufacturing technologies:rapidprototypingtodirectdigital manufacturing.2nded.NewYork:Springer;2010.
[22]LvY,ChenX,WangQ,etal.Synthesisandcharacterization ofchitosan-basedbiomaterialsmodifiedwithdifferent activegroupsandtheirrelationshipwithcytotoxicity.J WuhanUnivTechnolMaterSciEdit2007;22:
695–700.
[23]WilliamsonGK,HallWH.X-raylinebroadeningfromfiled aluminiumandwolfram.ActaMetall1953;1:22–31.
[24]CiobanuCS,IconaruSL,ChisriucSC,CostescuA,Coustumer PL,PredoiD.Synthesisandantimicrobialactivityof silver-dopedhydroxyapatitenanoparticles.BiomedResInt 2013;2013:916218,10pp.
[25]GeM,GeK,GaoF,etal.Biomimeticmineralized strontium-dopedhydroxyapatiteonporouspoly(l-lactic acid)scaffoldsforbonedefectrepair.IntJNanomed Nanosurg2018;13:1707–21.
[26]ChungRJ,MingFH,HuangCW,PerngLH,WenHW,ChinTS. Antimicrobialeffectsandhumangingivalbiocompatibility ofhydroxyapatitesol-gelcoatings.JBiomedMaterResB ApplBiomater2006;76:169–78.
[27]StanicV,JanackovicD,DimitrijevicS,etal.Synthesisof antimicrobialmonophasesilver-dopedhydroxyapatite nanopowdersforbonetissueengineering.ApplSurfSci 2011;257:4510–8.
[28]TanJ,SaltzmanWM.Biomaterialswithhierarchically definedmicro-andnanoscalestructure.Biomaterials 2004;25(17):3593–601.
[29]HorbettTA.Biomaterials:interfacialphenomenaand applications.In:CooperSL,PeppasNA,HoffmanAS,Ratner BD,editors.Advancesinchemistryseries.WashingtonDC: AmericanChemicalSociety;1982.
[30]VromanL,AdamsAL,FischerGC,MunozPC,StandfordM. In:CooperSL,PeppasNA,HoffmanAS,RatnerBD,editors. Biomaterials:interfacialphenomenaandapplications. WashingtonDC:AmericanChemicalSociety;1982. [31]LordMS,FossM,BesenbacherF.Influenceofnanoscale
surfacetopographyonproteinadsorptionandcellular response.NanoToday2010;5:66–78.
[32]XiaW,LiJ,WangL,HuangD,ZuoY,YubaoL.Therelease propertiesofsilverionsfromAg-nHA/TiO2/PA66 antimicrobialcompositescaffolds.BiomedMater 2010;5:044105.
[33]QuanR,YangD,WuX,WangH,MiaoX,LiW.Invitro biocompatibilityofgradedhydroxyapatite-zirconia compositebioceramic.JMaterSciMaterMed2008;19: 183–7.
[34]WiessnerJ,MandelG,HalversonP,MandelN.Theeffectof hydroxyapatitecrystallinityonhemolysis.CalcifTissueInt 1988;42:210–9.
[35]ZhangT,ZhouS,GaoX,YangZ,SunL,ZhangD.A multi-scalemethodformodellingdegradationof
bioresorbablepolyesters.ActaBiomater2017;50: 462–75.
[36]GibsonLJ,AshbyMF,HarleyBA.Cellularmaterialsinnature andmedicine.Cambridge,UK:CambridgeUniversityPress; 2010.