an-improved-mechanical-testing-method-to-assess-bone-implant-anchorage

An Improved Mechanical Testing Method to Assess Bone-implant Anchorage

Recent advances in material science have led to a substantial increase in the topographical complexity of implant surfaces, both on a micro- and a ...

University of Toronto

Enhanced biocompatibility of titanium implants highly depends on the possibility of achieving high degrees of surface functionalization for a low immune response and/or enhanced mineralization of bioactive minerals, such as hydroxyapatite. In this respect, surface modification with Self Assembled Monolayers (SAMs) has a great potential in delivering artificial surfaces of improved biocompatibility. Herein, the effectiveness of common chemical pre-treatments, i.e. hydrogen peroxide (H(2)O(2)) and Piranha (H(2)SO(4) + H(2)O(2)), in facilitating surface decontamination and hydroxylation of titanium surfaces to promote further surface functionalization by SAMs is investigated. The quality of the octadecyltrichlorosilane (OTS) based SAM appeared to strongly depend upon the surface morphology, the density and nature of surface hydroxyl sites resulting from the oxidative pre-treatments. Contrary to common belief, no further hydroxylation of the titanium substrate was observed after the selected chemical pre-treatments, but the number of hydroxyl groups available on the surface was decreased as a result of the formation of a titanium oxide layer with a gel-type structure. Further examinations by atomic force microscopy, infrared spectroscopy and X-ray photoelectron spectroscopy also revealed that mild oxidizing conditions were sufficient to remove surface contamination without detrimental effects on surface hydroxylation state and surface roughness. Furthermore, the adsorption of the alkylsiloxane molecules forming the SAM film is believed to proceed through hydrolysis at surface acidic hydroxyl groups rather than randomly. This site dependent adsorption process has significant implications for further functionalization of titanium based implants. It also highlights the difficulty of achieving an OTS based SAM at the surface of titanium and question the quality of SAMs reported at titanium surfaces so far.

Formation of OTS self-assembled monolayers at chemically treated titanium surfaces.

This work reports a novel and reproducible route for the successful modification of the surface of titanium (Ti) with self-assembled monolayers (SAMs). By electropolishing the surface of Ti, suitable physical/chemical surface properties were obtained for adequate growth of OctadecylTrichloroSilane (OTS) based SAM. Optimum conditions to achieve a well-organized and densely packed OTS film were also determined by monitoring the effect of different parameters including time, concentration, and temperature for OTS adsorption. The optimum conditions for the formation of an OTS-SAM were found to be upon immersion of the electropolished Ti substrate in a 10mM OTS solution at 10°C for 24h. Furthermore, multiple growth regimes for the formation of OTS-SAM on electropolished Ti surface were observed. The kinetics for the self-assembly were fast at the beginning of OTS adsorption, but rapidly slowed down after 10h of immersion, i.e. during the densification process of the film at the surface of Ti. In addition, the growth behavior was found to be random as opposed to the island growth behavior usually observed with OTS at the surface of silica. The successful implementation of OTS-SAM was further investigated through the immobilization and delivery of a model drug and the OTS monolayer showed clear abilities in drug delivery with an initial burst release up to 5 days followed by a sustained release up to 26 days.

Functionalization of electropolished titanium surfaces with silane-based self-assembled monolayers and their application in drug delivery.

&#x6211;&#x4EEC;&#x5BFB;&#x6C42; deconvolute &#x754C;&#x9762;&#x7A33;&#x5B9A;&#x6027;&#x7684;&#x9AA8;&#x5185;&#x690D;&#x5165;&#x7269;&#x548C;&#x9AA8;&#x7C98;&#x7ED3;&#x73B0;&#x8C61;&#x5BF9;&#x4E9A;&#x5FAE;&#x7C73;&#x5730;&#x5F62;&#x548C;&#x5FAE;&#x5730;&#x5F62;&#x7684;&#x5F71;&#x54CD;&#x3002;&#x82E5;&#x8981;&#x901A;&#x8FC7;&#x5B9E;&#x9A8C;&#x89E3;&#x51B3;&#x8FD9;&#x4E2A;&#x95EE;&#x9898;&#xFF0C;&#x6211;&#x4EEC;&#x690D;&#x5165;&#x5B9A;&#x5236;&#x949B;&#x5408;&#x91D1;&#x690D;&#x5165;&#x7269;&#x7684;&#x4E0D;&#x540C;&#x8868;&#x9762;&#x5730;&#x5F62;&#x590D;&#x6742;&#x6027;&#x5728;&#x5927;&#x9F20;&#x80A1;&#x9AA8;&#x3001; 6&#x3001; 9 &#x6216; 12 &#x5929;&#x3002;&#x4E94;&#x4E2A;&#x66F2;&#x9762;&#x88AB;&#x8680;&#x523B;&#x3001; &#x629B;&#x5149;&#x3001; &#x673A;&#x68B0;&#x52A0;&#x5DE5;&#x3001; &#x4E8C;&#x5143;&#x9178;&#x548C;&#x4E24;&#x79CD;&#x5F62;&#x5F0F;&#x7684;&#x7802;&#x783E;&#x7206;&#x7834;&#x548C;&#x9178;&#x6027;&#x8680;&#x523B; &#xFF1B;&#x6BCF;&#x4E2A;&#x8868;&#x9762;&#x7684;&#x7C7B;&#x578B;&#x4F5C;&#x4E86;&#x8FDB;&#x4E00;&#x6B65;&#x4FEE;&#x6539;&#xFF0C;&#x6C89;&#x79EF;&#x7684;&#x9499;&#x78F7;&#xFF0C;&#x4F7F;&#x603B;&#x7684; 10 &#x6750;&#x6599;&#x7EC4;&#x7EB3;&#x7C73;&#x6676; (n = 10&#xFF0C;&#x6BCF;&#x4E2A;&#x65F6;&#x95F4;&#x70B9; &#xFF1B; &#x5171; 300 &#x690D;&#x5165;&#x7269;)&#x3002;&#x727A;&#x7272;&#xFF0C;&#x6211;&#x4EEC;&#x7684;&#x5047;&#x4F53;-&#x9AA8;&#x754C;&#x9762;&#x53D7;&#x5230;&#x673A;&#x68B0;&#x7834;&#x574F;&#x6027;&#x8BD5;&#x9A8C;&#x3002;&#x6211;&#x4EEC;&#x53D1;&#x73B0;&#xFF0C;&#x751A;&#x81F3;&#x5149;&#x6ED1;&#x7684;&#x8868;&#x9762;&#xFF0C;&#x5F53;&#x4FEE;&#x6539;&#x4E0E;&#x4E9A;&#x5FAE;&#x7C73;&#x5C3A;&#x5EA6;&#x6676;&#x4F53;&#xFF0C;&#x53EF;&#x80FD;&#x662F;&#x9AA8;&#x7C98;&#x7ED3;&#x3002;&#x4F46;&#x662F;&#xFF0C;&#x901A;&#x8FC7;&#x5BF9;&#x690D;&#x5165;&#x7269;&#x9AA8;&#x8FD0;&#x52A8;&#x8D1F;&#x8377;&#x589E;&#x52A0;&#x4E0E;&#x6108;&#x5408;&#xFF0C;&#x8FD9;&#x79CD;&#x63A5;&#x53E3;&#xFF0C;&#x800C;&#x53E6;&#x4E00;&#x4E9B;&#xFF0C;&#x5931;&#x8D25;&#x65F6;&#x4E0E;&#x4E9A;&#x5FAE;&#x7C73;&#x8D8A;&#x6765;&#x8D8A; microtopographical &#x590D;&#x6742;&#x7684;&#x66F2;&#x9762;&#x4E0A;&#x53E0;&#x52A0;&#x529F;&#x80FD;&#x5B8C;&#x597D;&#x65E0;&#x635F;&#x8377;&#x8F7D;&#x4F5C;&#x7528;&#x4E0B;&#x3002;&#x6211;&#x4EEC;&#x5728;&#x8FD9;&#x91CC;&#x5C55;&#x793A;&#xFF0C;&#x66F4;&#x9AD8;&#x7684;&#x79E9;&#x5E8F;&#x3001; &#x5FAE;&#x7C73;&#x6216;&#x7C97;&#x5FAE;&#x7C73;&#xFF0C;&#x5730;&#x5F62;&#x662F;&#x8F83;&#x957F;&#x671F;&#x7684;&#x754C;&#x9762;&#x7A33;&#x5B9A;&#x6027;&#x7684;&#x5FC5;&#x8981;&#x6761;&#x4EF6;&#x3002;&#x6211;&#x4EEC;&#x663E;&#x793A;&#x6BCF;&#x4E2A;&#x8FD9;&#x4E9B;&#x5730;&#x5F62;&#x7684;&#x89C4;&#x6A21;&#x8303;&#x56F4;&#x8868;&#x793A;&#x770B;&#x5230;&#x5929;&#x7136;&#x9AA8;&#x7EC4;&#x7EC7;&#x89C4;&#x6A21;&#x8303;&#x56F4;&#x3002;&#x56E0;&#x6B64;&#xFF0C;&#x4ECE;&#x6211;&#x4EEC;&#x7684;&#x7814;&#x7A76;&#x7ED3;&#x679C;&#x7684;&#x5206;&#x6790;&#x662F;&#xFF0C;&#x53EF;&#x4EE5;&#x91C7;&#x7528;&#x751F;&#x7269;&#x76F8;&#x5173;&#x6807;&#x51C6;&#x6765;&#x8BC4;&#x4F30;&#x4E0D;&#x540C;&#x89C4;&#x6A21;&#x8303;&#x56F4;&#x79CD;&#x690D;&#x4F53;&#x8868;&#x9762;&#x5730;&#x5F62;&#x7684;&#x91CD;&#x8981;&#x6027;&#x65B0;&#x624B;&#x6BB5;&#x3002;

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We sought to deconvolute the effects of sub-micron topography and microtopography on the phenomena of bone bonding and interfacial stability of endosseous implants. To address this experimentally, we implanted custom-made titanium alloy implants of varying surface topographical complexity in rat femora, for 6, 9 or 12 days. The five surfaces were polished, machined, dual acid etched, and two forms of grit blasted and acid etched; each surface type was further modified with the deposition of nanocrystals of calcium phosphate to make a total of 10 materials groups (nÂ =Â 10 for each time point; total 300 implants). At sacrifice, we subjected the bone-implant interface to a mechanical disruption test. We found that even the smoothest surfaces, when modified with sub-micron scale crystals, could be bone-bonding. However, as locomotor loading through bone to the implant increased with time of healing, such interfaces failed while others, with sub-micron features superimposed on surfaces of increasing microtopographical complexity remained intact under loading. We demonstrate here that higher order, micron or coarse-micron, topography is a requirement for longer-term interfacial stability. We show that each of these topographical scale-ranges represents a scale-range seen in natural bone tissue. Thus, what emerges from an analysis of our findings is a new means by which biologically-relevant criteria can be employed to assess the importance of implant surface topography at different scale-ranges.

The roles of different scale ranges of surface implant topography on the stability of the bone/implant interface.

Nous avons cherch&eacute; &agrave; deconvolute les effets de la topographie de la sub-micronique et microtopographie sur les ph&eacute;nom&egrave;nes d&#39;os de liaison et de la stabilit&eacute; interfaciale des implants endo-osseux. Pour y rem&eacute;dier exp&eacute;rimentalement, nous avons implant&eacute; implants en alliage titane sur mesure de la variation de surface complexit&eacute; topographique dans les f&eacute;murs de rat, pour 6, 9 ou 12 jours. Les surfaces de cinq &eacute;taient poli, usin&eacute;, double acide grav&eacute;, et deux formes de grain sabl&eacute;e et acide grav&eacute;es ; chaque type de surface a &eacute;t&eacute; modifi&eacute;e avec la d&eacute;position de nanocristaux de phosphate de calcium pour faire un total de 10 mat&eacute;riaux groupes (n = 10 pour chaque point dans le temps ; total 300 implants). Au moment du sacrifice, nous avons soumis l&#39;interface os-implant &agrave; un essai de rupture m&eacute;canique. Nous avons constat&eacute; que m&ecirc;me les surfaces lisses, lorsque modifi&eacute;s avec des cristaux d&#39;&eacute;chelle sub-micronique, pourrait &ecirc;tre l&#39;OS-collage. Cependant, comme chargement locomotrice &agrave; travers l&#39;os &agrave; l&#39;implant augmente avec le temps de gu&eacute;rison, de telles interfaces &eacute;chou&eacute;s tandis que d&#39;autres, avec sub-micronique caract&eacute;ristiques superpos&eacute;es sur des surfaces de Macrotopographie complexit&eacute; croissante rest&egrave;rent intactes sous la charge. Nous d&eacute;montrons ici plus &eacute;lev&eacute; ou cette ordonnance, micron micron grossiers, la topographie est une exigence de stabilit&eacute; interfaciale &agrave; plus long terme. Nous montrons que chacune de ces gammes-&eacute;chelle topographiques repr&eacute;sente une gamme d&#39;&eacute;chelle-vue dans le tissu osseux naturels. Ce qui ressort d&#39;une analyse de nos r&eacute;sultats est donc un moyen nouveau par lequel des crit&egrave;res pertinents sur le plan biologique peuvent &ecirc;tre utilis&eacute;es pour &eacute;valuer l&#39;importance de la topographie de surface implant &agrave; &eacute;chelle-gammes diff&eacute;rentes.

Les r&ocirc;les des diff&eacute;rents &eacute;chelle varie de surface de l&#39;implant topographie sur la stabilit&eacute; de l&#39;interface os/implant.

Abbiamo cercato di deconvolute gli effetti della topografia sub-micron e microtopography su fenomeni di osso di bonding e stabilit&agrave; interfacciale di impianti endossei. Per risolvere questo sperimentalmente, abbiamo impiantato gli impianti in lega di titanio su misura di varia complessit&agrave; superficie topografica nel femore di ratto, 6, 9 o 12 giorni. Le cinque superfici erano lucidata, lavorata, dual acido inciso, e due forme di graniglia sabbiata e acido inciso; ogni tipo di superficie &egrave; stata ulteriormente modificata con la deposizione di nanocristalli di fosfato di calcio per fare un totale di gruppi 10 materiali (n = 10 per ogni punto di tempo; totale 300 impianti). Al sacrificio, abbiamo sottoposto l&#39;interfaccia osso-impianto a una prova di rottura meccanica. Abbiamo scoperto che anche le superfici pi&ugrave; liscia, quando modificato con cristalli su scala sub-micron, potrebbe essere osso-bonding. Tuttavia, come carico dell&#39;apparato locomotore attraverso osso all&#39;impianto aumentato con il tempo di guarigione, tali interfacce non riuscite mentre altri, con sub-micron caratteristiche sovrapposte su superfici di crescente complessit&agrave; microtopographical rimasero intatte sotto carico. Qui dimostriamo che pi&ugrave; alto ordine, micron o grossolani-micron, topografia &egrave; un requisito per la stabilit&agrave; a lungo termine interfacciale. Mostriamo che ciascuno di questi intervalli di scala topografici rappresenta un intervallo di scala visto nel tessuto osseo naturale. Cos&igrave;, ci&ograve; che emerge da un&#39;analisi dei nostri risultati &egrave; un nuovo mezzo con cui biologicamente rilevanti criteri possono essere impiegati per valutare l&#39;importanza della topografia di superficie implantare a diversi intervalli di scala.

I ruoli delle gamme differenti scale di superficie implantare topografia sulla stabilit&agrave; dell&#39;interfaccia osso/impianto.

&#x9AA8;&#x306E;&#x63A5;&#x5408;&#x73FE;&#x8C61;&#x3068;&#x754C;&#x9762;&#x5B89;&#x5B9A;&#x6027;&#x5185;&#x9AA8;&#x5185;&#x30A4;&#x30F3;&#x30D7;&#x30E9;&#x30F3;&#x30C8;&#x306E;&#x30B5;&#x30D6;&#x30DF;&#x30AF;&#x30ED;&#x30F3;&#x5730;&#x5F62;&#x3068;&#x5FAE;&#x5730;&#x5F62;&#x306E;&#x5F71;&#x97FF;&#x3092; deconvolute &#x3057;&#x3088;&#x3046;&#x3068;&#x601D;&#x3044;&#x307E;&#x3059;&#x3002;&#x3053;&#x308C;&#x306F;&#x5B9F;&#x9A13;&#x7684;&#x306B;&#x5BFE;&#x51E6;&#x3059;&#x308B;&#x306B;&#x306F;&#x3001;6&#x3001;9&#x3001;12 &#x65E5;&#x306E;&#x8868;&#x9762;&#x5730;&#x5F62;&#x306E;&#x8907;&#x96D1;&#x3055;&#x30E9;&#x30C3;&#x30C8;&#x5927;&#x817F;&#x9AA8;&#x306E;&#x30AB;&#x30B9;&#x30BF;&#x30E0;&#x30E1;&#x30A4;&#x30C9; &#x30C1;&#x30BF;&#x30F3;&#x5408;&#x91D1;&#x30A4;&#x30F3;&#x30D7;&#x30E9;&#x30F3;&#x30C8;&#x3092;&#x6CE8;&#x5165;&#x3057;&#x307E;&#x3057;&#x305F;&#x3002;5 &#x8868;&#x9762;&#x30A8;&#x30C3;&#x30C1;&#x30F3;&#x30B0;&#x3001;&#x7814;&#x78E8;&#x3001;&#x6A5F;&#x68B0;&#x52A0;&#x5DE5;&#x3001;&#x30C7;&#x30E5;&#x30A2;&#x30EB;&#x306E;&#x9178;&#x3068;&#x30B0;&#x30EA;&#x30C3;&#x30C8; &#x30D6;&#x30E9;&#x30B9;&#x30C8;&#x3068;&#x9178;&#x306E; 2 &#x3064;&#x306E;&#x30D5;&#x30A9;&#x30FC;&#x30E0;&#x3092;&#x30A8;&#x30C3;&#x30C1;&#x30F3;&#x30B0;&#x3057;&#x307E;&#x3059;&#x3002;&#x5404;&#x30B5;&#x30FC;&#x30D5;&#x30A7;&#x30B9; &#x30BF;&#x30A4;&#x30D7;&#x306F;&#x3055;&#x3089;&#x306B;&#x30CA;&#x30CE;&#x7D50;&#x6676;&#x6750;&#x3092; 10 &#x30B0;&#x30EB;&#x30FC;&#x30D7;&#x306E;&#x5408;&#x8A08;&#x3059;&#x308B;&#x30EA;&#x30F3;&#x9178;&#x30AB;&#x30EB;&#x30B7;&#x30A6;&#x30E0;&#x306E;&#x6C88;&#x7740;&#x308C;&#x307E;&#x3057;&#x305F; (n = 10 &#x306E;&#x5404;&#x6642;&#x9593;&#x30DD;&#x30A4;&#x30F3;&#x30C8;; 300 &#x30A4;&#x30F3;&#x30D7;&#x30E9;&#x30F3;&#x30C8;&#x306E;&#x5408;&#x8A08;&#xFF09;&#x3002;&#x72A0;&#x7272;&#x306B;&#x6A5F;&#x68B0;&#x7684;&#x7834;&#x58CA;&#x30C6;&#x30B9;&#x30C8;&#x306B;&#x30A4;&#x30F3;&#x30D7;&#x30E9;&#x30F3;&#x30C8; &#x30FB;&#x9AA8;&#x754C;&#x9762;&#x3092;&#x53D7;&#x3051;&#x307E;&#x3059;&#x3002;&#x6211;&#x3005; &#x306F;&#x30B5;&#x30D6;&#x30DF;&#x30AF;&#x30ED;&#x30F3; &#x30B9;&#x30B1;&#x30FC;&#x30EB;&#x7D50;&#x6676;&#x3092;&#x5909;&#x66F4;&#x53EF;&#x80FD;&#x6027;&#x304C;&#x3042;&#x308A;&#x307E;&#x3059;&#x9AA8;&#x63A5;&#x5408;&#x3068;&#x304D;&#x3082;&#x3001;&#x6ED1;&#x3089;&#x304B;&#x306A;&#x8868;&#x9762;&#x3092;&#x767A;&#x898B;&#x3057;&#x307E;&#x3057;&#x305F;&#x3002;&#x7652;&#x3057;&#x3001;&#x4ED6;&#x306E;&#x4EBA;&#x304C;&#x5931;&#x6557;&#x3057;&#x305F;&#x3053;&#x306E;&#x3088;&#x3046;&#x306A;&#x30A4;&#x30F3;&#x30BF;&#x30FC;&#x30D5;&#x30A7;&#x30A4;&#x30B9;&#x306E;&#x6642;&#x9593;&#x3068;&#x9AA8;&#x3001;&#x30A4;&#x30F3;&#x30D7;&#x30E9;&#x30F3;&#x30C8;&#x306B;&#x904B;&#x52D5;&#x8CA0;&#x8377;&#x304C;&#x5897;&#x52A0;&#x3059;&#x308B;&#x306B;&#x3064;&#x308C;&#x3066;&#x3057;&#x304B;&#x3057;&#x3001;&#x30B5;&#x30D6;&#x30DF;&#x30AF;&#x30ED;&#x30F3;&#x306E;&#x5730;&#x5185;&#x306E;&#x8907;&#x96D1;&#x5316;&#x306E;&#x8868;&#x9762;&#x306B;&#x30B9;&#x30FC;&#x30D1;&#x30FC;&#x30A4;&#x30F3; &#x30DD;&#x30FC;&#x30BA;&#x6A5F;&#x80FD;&#x304C;&#x52A0;&#x305D;&#x306E;&#x307E;&#x307E;&#x6B8B;&#x3063;&#x305F;&#x3002;&#x6211;&#x3005; &#x306F;&#x3053;&#x3053;&#x3067;&#x305D;&#x306E;&#x9AD8;&#x3044;&#x9806;&#x5E8F;&#x3001;&#x30DF;&#x30AF;&#x30ED;&#x30F3;&#x307E;&#x305F;&#x306F;&#x7C97;&#x30DF;&#x30AF;&#x30ED;&#x30F3;&#x3092;&#x793A;&#x3059;&#x5730;&#x5F62;&#x3067;&#x3042;&#x308B;&#x9577;&#x671F;&#x7684;&#x306A;&#x754C;&#x9762;&#x5B89;&#x5B9A;&#x6027;&#x306E;&#x305F;&#x3081;&#x306E;&#x8981;&#x4EF6;&#x3002;&#x79C1;&#x9054;&#x306F;&#x3053;&#x308C;&#x3089;&#x306E;&#x5730;&#x5F62;&#x306E;&#x30B9;&#x30B1;&#x30FC;&#x30EB;&#x7BC4;&#x56F2;&#x306E;&#x81EA;&#x7136;&#x306A;&#x751F;&#x4F53;&#x7D44;&#x7E54;&#x306B;&#x898B;&#x3089;&#x308C;&#x308B;&#x30B9;&#x30B1;&#x30FC;&#x30EB;&#x7BC4;&#x56F2;&#x3092;&#x8868;&#x3059;&#x3053;&#x3068;&#x3092;&#x793A;&#x3057;&#x307E;&#x3059;&#x3002;&#x3057;&#x305F;&#x304C;&#x3063;&#x3066;&#x3001;&#x3069;&#x306E;&#x3088;&#x3046;&#x306A;&#x6211;&#x3005; &#x306E;&#x8ABF;&#x67FB;&#x7D50;&#x679C;&#x306E;&#x5206;&#x6790;&#x304B;&#x3089;&#x51FA;&#x3066;&#x304F;&#x308B;&#x751F;&#x7269;&#x5B66;&#x7684;&#x306B;&#x95A2;&#x9023;&#x3059;&#x308B;&#x57FA;&#x6E96;&#x306B;&#x3088;&#x3063;&#x3066;&#x5225;&#x306E;&#x5C3A;&#x5EA6;&#x7BC4;&#x56F2;&#x3067;&#x30A4;&#x30F3;&#x30D7;&#x30E9;&#x30F3;&#x30C8;&#x8868;&#x9762;&#x5F62;&#x72B6;&#x306E;&#x91CD;&#x8981;&#x6027;&#x3092;&#x8A55;&#x4FA1;&#x3059;&#x308B;&#x305F;&#x3081;&#x306B;&#x7528;&#x3044;&#x308B;&#x3053;&#x3068;&#x304C;&#x3067;&#x304D;&#x308B;&#x65B0;&#x3057;&#x3044;&#x624B;&#x6BB5;&#x3067;&#x3059;&#x3002;

&#x30ED;&#x30FC;&#x30EB;&#x8868;&#x9762;&#x306E;&#x7570;&#x306A;&#x308B;&#x30B9;&#x30B1;&#x30FC;&#x30EB;&#x7BC4;&#x56F2;&#x306E;&#x9AA8;/&#x30A4;&#x30F3;&#x30D7;&#x30E9;&#x30F3;&#x30C8; &#x30A4;&#x30F3;&#x30BF; &#x30D5;&#x30A7;&#x30FC;&#x30B9;&#x306E;&#x5B89;&#x5B9A;&#x6027;&#x306B;&#x95A2;&#x3059;&#x308B;&#x5730;&#x5F62;&#x3092;&#x30A4;&#x30F3;&#x30D7;&#x30E9;&#x30F3;&#x30C8;&#x3057;&#x307E;&#x3059;&#x3002;

&#xC6B0;&#xB9AC; &#xBF08; &#xACB0;&#xD569; &#xD604;&#xC0C1;&#xACFC; endosseous &#xC784; &#xD50C; &#xB780; &#xD2B8;&#xC758; &#xACC4;&#xBA74; &#xC548;&#xC815;&#xC131;&#xC5D0; &#xB9C8;&#xC774;&#xD06C;&#xB860; &#xC9C0;&#xD615; &#xAE30;&#xBCF5;&#xC774; &#xD6A8;&#xACFC; deconvolute &#xD558;&#xACE0;&#xC790; &#xD588;&#xB2E4;. &#xC2E4;&#xD5D8;&#xC801;&#xC73C;&#xB85C; &#xC774;&#xAC83;&#xC744; &#xD574;&#xACB0; &#xD558;&#xAE30; &#xC704;&#xD574; &#xC6B0;&#xB9AC;&#xAC00; &#xC8FC;&#xBB38; &#xD488; &#xD2F0;&#xD0C0;&#xB284; &#xD569;&#xAE08; &#xD45C;&#xBA74; &#xC9C0;&#xD615; &#xBCF5;&#xC7A1;&#xC131; &#xC950; femora, 6, 9 &#xB610;&#xB294; 12 &#xC77C;&#xC5D0; &#xB300; &#xD55C; &#xB2E4;&#xC591; &#xD55C; &#xC784; &#xD50C; &#xB780; &#xD2B8; &#xC774;&#xC2DD;. 5 &#xD45C;&#xBA74; &#xAD11;&#xD0DD;, &#xAC00;&#xACF5;, &#xC774;&#xC911; &#xC0B0; &#xC131; &#xC5D0;&#xCE6D;, &#xADF8;&#xB9AC;&#xACE0; &#xBAA8;&#xB798; &#xC794;&#xD574;&#xC640; &#xC0B0; &#xC131; &#xB450; &#xAC00;&#xC9C0; &#xD615;&#xD0DC;&#xC758; &#xC5D0;&#xCE6D;; &#xAC01; &#xD45C;&#xBA74; &#xC720;&#xD615; &#xCD94;&#xAC00; 10 &#xC790;&#xB8CC; &#xADF8;&#xB8F9;&#xC758; &#xCD1D; &#xC218; &#xC788;&#xB3C4;&#xB85D; &#xC778;&#xC0B0; &#xCE7C;&#xC298;&#xC758; &#xBC29;&#xD638;&#xC758; &#xC99D; &#xCC29;&#xC73C;&#xB85C; &#xBC14;&#xB00C;&#xC5C8;&#xC2B5;&#xB2C8;&#xB2E4; (n = 10 &#xAC01; &#xC2DC;&#xAC04; &#xC9C0;&#xC810;&#xC5D0; &#xB300; &#xD55C;, &#xCD1D; 300 &#xC784; &#xD50C; &#xB780; &#xD2B8;). &#xD76C;&#xC0DD;, &#xAE30;&#xACC4;&#xC801; &#xC7A5;&#xC560; &#xD14C;&#xC2A4;&#xD2B8;&#xC5D0; &#xBF08; &#xC774;&#xC2DD; &#xC778;&#xD130;&#xD398;&#xC774;&#xC2A4; &#xB300;&#xC0C1;&#xC774; &#xC6B0;&#xB9AC;. &#xC6B0;&#xB9AC;&#xB294; &#xC2EC;&#xC9C0;&#xC5B4; &#xAC00;&#xC7A5; &#xB9E4;&#xB044;&#xB7EC;&#xC6B4; &#xD45C;&#xBA74;, &#xB9C8;&#xC774;&#xD06C;&#xB860; &#xADDC;&#xBAA8; &#xACB0;&#xC815;&#xC744; &#xC218;&#xC815;, &#xBF08; &#xACB0;&#xD569; &#xB420; &#xC218; &#xC788;&#xB294; &#xB54C; &#xBC1C;&#xACAC;. &#xADF8;&#xB7EC;&#xB098;, &#xCE58;&#xC720;, &#xBC18;&#xBA74;&#xC5D0; &#xB2E4;&#xB978;, &#xC2E4;&#xD328; &#xAC19;&#xC740; &#xC778;&#xD130;&#xD398;&#xC774;&#xC2A4;&#xC758; &#xC2DC;&#xAC04;&#xACFC; &#xBF08;&#xC5D0; &#xC784; &#xD50C; &#xB780; &#xD2B8;&#xB97C; &#xD1B5;&#xD574; &#xC6B4;&#xC804; &#xB85C;&#xB4DC; &#xC99D;&#xAC00; &#xB9C8;&#xC774;&#xD06C;&#xB860;&#xACFC; &#xAE30;&#xB2A5; microtopographical &#xBCF5;&#xC7A1;&#xC131;&#xC774; &#xC99D;&#xAC00;&#xC758; &#xD45C;&#xBA74;&#xC5D0; &#xACB9;&#xCCD0; &#xADF8;&#xB300;&#xB85C; &#xB0A8;&#xC544; &#xB85C;&#xB4DC;&#xC5D0;&#xC11C;. &#xC6B0;&#xB9AC;&#xAC00; &#xBCF4;&#xC5EC; &#xC5EC;&#xAE30;&#xB294; &#xB192;&#xC740; &#xC21C;&#xC11C;, &#xB9C8;&#xC774;&#xD06C;&#xB860; &#xB610;&#xB294; &#xBBF8;&#xD06C;&#xB860;&#xC774; &#xAC70;&#xCE5C; &#xC9C0;&#xD615; &#xC7A5;&#xAE30; &#xACC4;&#xBA74; &#xC548;&#xC815;&#xC131;&#xC5D0; &#xB300; &#xD55C; &#xC694;&#xAD6C; &#xC0AC;&#xD56D;&#xC785;&#xB2C8;&#xB2E4;. &#xC6B0;&#xB9AC;&#xAC00; &#xBCF4;&#xC5EC; &#xAC01; &#xC774;&#xB7EC;&#xD55C; &#xC9C0;&#xD615; &#xC2A4;&#xCF00;&#xC77C; &#xBC94;&#xC704; &#xADDC;&#xBAA8; &#xBC94;&#xC704; &#xC790;&#xC5F0; &#xBF08; &#xC870;&#xC9C1;&#xC5D0;&#xC11C; &#xBCFC; &#xC218;&#xB97C; &#xB098;&#xD0C0;&#xB0C5;&#xB2C8;&#xB2E4;. &#xB530;&#xB77C;&#xC11C;, &#xC0C8;&#xB85C;&#xC6B4; &#xC758;&#xBBF8;&#xB97C; &#xC0DD;&#xBB3C;&#xD559;&#xC801;&#xC73C;&#xB85C; &#xAD00;&#xB828; &#xAE30;&#xC900;&#xC744; &#xB2E4;&#xB978; &#xC2A4;&#xCF00;&#xC77C; &#xBC94;&#xC704;&#xC5D0;&#xC11C; &#xC784; &#xD50C; &#xB780; &#xD2B8; &#xD45C;&#xBA74; &#xC9C0;&#xD615;&#xC758; &#xC911;&#xC694;&#xC131;&#xC744; &#xD3C9;&#xAC00; &#xD558;&#xAE30; &#xC704;&#xD574; &#xCC44;&#xD0DD; &#xB420; &#xC218; &#xC788;&#xB2E4;&#xB294; &#xC6B0;&#xB9AC;&#xC758; &#xC5F0;&#xAD6C; &#xACB0;&#xACFC;&#xC758; &#xBD84;&#xC11D;&#xC5D0;&#xC11C; &#xB098;&#xC628;&#xB2E4;.

&#xD45C;&#xBA74;&#xC758; &#xB2E4;&#xB978; &#xC2A4;&#xCF00;&#xC77C; &#xBC94;&#xC704; &#xC5ED;&#xD560; &#xBF08;/&#xC784; &#xD50C; &#xB780; &#xD2B8; &#xC778;&#xD130;&#xD398;&#xC774;&#xC2A4;&#xC758; &#xC548;&#xC815;&#xC131;&#xC5D0; &#xC9C0;&#xD615; &#xC784; &#xD50C; &#xB780; &#xD2B8;.

Intentamos deconvolucionar los efectos de la topograf&iacute;a de sub-micrones y microtopograf&iacute;a sobre los fen&oacute;menos del hueso de la vinculaci&oacute;n y interfacial estabilidad de los implantes intra&oacute;seos. Para abordar este experimental, hemos implantado implantes de aleaci&oacute;n de titanio por encargo de diversa complejidad topogr&aacute;fica superficie en f&eacute;mures de rata, 6, 9 o 12 d&iacute;as. Las cinco superficies fueron &aacute;cido pulido, trabajado a m&aacute;quina, doble grabado al agua fuerte, y dos formas de arena arruinado y &aacute;cido grabado; cada tipo de superficie m&aacute;s se modific&oacute; con la deposici&oacute;n de nanocristales de fosfato de calcio para hacer un total de 10 materiales grupos (n = 10 para cada momento; total 300 implantes). Sacrificio, nos sometieron la interfase hueso-implante a una prueba de la interrupci&oacute;n mec&aacute;nica. Encontramos que incluso las superficies m&aacute;s suaves, cuando modificado con cristales de escala submicr&oacute;nica, podr&iacute;a ser la Uni&oacute;n de hueso. Sin embargo, como carga locomotor a trav&eacute;s del hueso al implante aumenta con el tiempo de curaci&oacute;n, esas interfaces falladas mientras otros, con sub-micrones caracter&iacute;sticas superpuestas sobre superficies de creciente complejidad microtopographical permanecieron intactas bajo carga. Aqu&iacute; demostramos que mayor orden, micrones o grueso micrones, topograf&iacute;a es un requisito para la estabilidad a largo plazo de interfacial. Mostramos que cada una de estas gamas-escala topogr&aacute;ficas representa un rango de la escala en tejido &oacute;seo natural. As&iacute;, lo que surge de un an&aacute;lisis de los resultados es un nuevo medio por el cual biol&oacute;gicamente relevantes criterios pueden ser empleados para evaluar la importancia de la topograf&iacute;a de superficie de implante en diferentes intervalos de escala.

Los papeles de las gamas de diversa escala de superficie de implantaci&oacute;n de topograf&iacute;a en la estabilidad de la interfase hueso/implante.

We sought to explore the biological mechanisms by which endosseous implant surface topography contributes to bone anchorage. To address this experimentally, we implanted five groups of custom-made commercially pure titanium implants of varying surface topographical complexity in rat femora for 9 days; subjected them to mechanical testing; and then examined the interfacial bone matrix by electron microscopy. The five implant surfaces were prepared by combinations of dual acid etching and grit blasting the titanium substrates and, in some cases, modifying the created surfaces with the deposition of nanocrystals of calcium phosphate, which resulted in 10 samples per group. In parallel, we cultured rat bone marrow cells on surrogate implants constructed from polymer resin coated with the same calcium phosphate nanocrystals, and monitored the deposition of bone sialoprotein by transmission electron immunohisto-micrography. We found that implant samples modified with sub-micron scale crystals were bone-bonding, as described by the interdigitation of a mineralized cement line matrix with the underlying implant surface. The in vitro assay showed that bone sialoprotein could be deposited in the interstices between, and undercuts below, the nanocrystals. In addition, when mineralized, the cement line matrix globules occupied micron-sized pits in the implant surfaces, and in part obliterated them, creating an additional form of anchorage. Our results also showed that collagen, elaborated by the osteogenic cells, wrapped around the coarse-micron features, and became mineralized in the normal course of bone formation. This provided a mechanism by which coarse-micron implant features contributed to a functional interface, which we have previously described, that is capable of resisting the mechanical loading that increases as peri-implant bone matures. Thus, our findings provide mechanistic explanations for the biologically-relevant criteria that can be employed to assess the importance of implant surface topography at different scale-ranges.

Elnaz Ajami

Institute of Biomaterials and Biomedical Engineering

University of Toronto

An Improved Mechanical Testing Method to Assess Bone-implant Anchorage

Elnaz Ajami

.css-o250i3{font-size:18px;font-family:Open Sans,sans-serif;line-height:21.6px;}Institute of Biomaterials and Biomedical Engineering

University of Toronto

An Improved Mechanical Testing Method to Assess Bone-implant Anchorage

Institute of Biomaterials and Biomedical Engineering