Patent Application
20200149145
Titanium and titanium alloys are widely recognized as advantageous materials for biological implants, including bone implants. Titanium-based materials have been commonly used as biological implants due to a beneficial balance between biomechanical properties and in vivo biocompatibility. Titanium-based materials are the preferred materials for a variety of implants, including dental implants, joint replacements, pacemakers and a variety of other medical applications and procedures.
Unprocessed, naturally-surfaced titanium-based implants suffer from a number of known disadvantages. First, solid commercially pure titanium and a number of titanium alloys are biomechanically incompatible, primarily due to elasticity and modulus mismatch between the implant and adjacent tissues, which may aggravate unwanted bone resorption in host tissues. Second, because titanium-based materials are bioinert, the body frequently grows a thin fibrous tissue over their surface after they are introduced into a patient. The fibrous tissue hinders osseointegration and may increase the risk of the implant loosening and bone fracture.
Modern implant producers have attempted to address these issues in a number of ways. Regarding biomechanical incompatibility, implants have been developed to improve mechanical mismatch, or reduce elastic modulus mismatch, by introducing pores in the implant via a number of known metallurgical processes. While pores reduce the modulus of the implant, careful control of the pore size and morphology is required for osseointegration, especially at the surface of the implant, to improve bone ingrowth and fatigue resistance. To address the growth of fibrous tissue, implants with surface modifications have been developed, utilizing topographical or chemical changes. Because cell surfaces naturally contain nanofeatures linked to the extracellular matrix, nanotopographical alterations to implants are important for cell adhesion and response.
Plasma-based techniques have been used for both generating surface porosity and modifying surface topology. For example, U.S. Pat. No. 6,582,470 describes modifying porous titanium surfaces by exposing the surface to a reactive plasma gas. While these techniques improve the biomechanical properties and cell adhesion, they provide little control over surface reactions and have difficulty in reliably fabricating structures smaller than about 50 nm. By providing precise porous and/or nanopatterned regions to the implant, including tailored to the specific application of the implant, biomechanical stresses may be reduced and cell adhesion increased, resulting in longer implant life, faster patient recovery times and reduced risk of implant tissue damage, complications and infections.
Conventional surface treatment of Ti surfaces for biomedical applications such as integration with bone have focused mostly on techniques that require strong chemical etchants and high-temperature processes. These approaches generally result in large toxic chemical waste streams and high-cost in manufacturing. Other approaches induce physical changes with methods such as sand-blasting or grit-blasting that result in kinetic roughening of the Ti surface with little control over the nanoscale topography, its specific dimensions, chemistry, composition and surface charge density.
Nanopatterned surfaces have been obtained mostly by bottom-up and top-down techniques on model materials given the difficulty in high-fidelity control of clinically-relevant surfaces and of complex 3D systems. Furthermore, no current nanoscale modification method exists that can control both surface chemistry and topography independently.
Thus, it can be seen from the foregoing that there remains a need in the art for surface modification of titanium-based implants, including at the nanometer level to improve biomechanical compatibility, associated functional deployment and implant lifetime and success rate, including by well controlled cellular adhesion to implant surface, morphology and behavior as well as high-fidelity control of the spatio-temporal immune-response behavior of the biomedical implant interface with the body. Tunability of the implant surface to engender specific cell and immune-system response that ultimately results in an interface that can trigger these effects over specific times and reproducibly is critically desirable.
Provided herein are methods for the controlled, independent modification of the surface of titanium-based materials and compositions generated thereby. The methods allow for the alteration of multiple surface characteristics including generation of precise nanostructures, morphology, crystallography, chemical hybridizations and chemical composition for increased biocompatibility, for example, osseointegration, osseoconduction, cell adhesion, cell proliferation, enhanced local mechanical properties (elasticity, modulus, surface texture, porosity), hydrophobicity, hydrophilicity, steric hindrance, modulating-immuno response, anti-inflammatory properties and/or anti-bacterial properties. The surface of the composition may be modified by independently controlling parameters (e.g. incident angle, fluence, flux, energy, species, etc.) of one or more directed energetic particle beams, providing more control and increased bioactivity over conventional kinetic roughing techniques.
The provided compositions are modified to increase multiple biological properties or functions, including modification of multiple properties in a single region or domain and creating multiple regions or domains with biological advantages within a single composition. The provided methods are precise, allowing for the controlled generation of specific nanostructures across multiple domains. Further, precise changes to crystallography or morphology are possible, including changes to grain structure and the generation of metastable states. The provided methods also allow for specific modification of chemical composition, for instance, accurate creation of one or more alloys different from adjacent domains or the original underlying substrate. Irradiation-driven compositional variation such as one element over another at the surface differing from the sub-surface can be tuned to specific concentrations.
In aspect, provided is a titanium-containing composition comprising: a titanium or titanium alloy substrate having a surface; wherein the surface has a plurality of nanoscale domains characterized by a surface geometry providing a selected multifunctional bioactivity; wherein each of the nanoscale domains has at least one lateral spatial dimension selected over the range of 3 nm to 1 □m and a vertical spatial dimension less than 500 nm. In a second aspect, provided is a titanium-containing composition comprising: a titanium or titanium alloy substrate having a surface; wherein the surface has a plurality of nanoscale domains characterized by a surface geometry providing a selected multifunctional bioactivity; wherein the nanoscale domains are generated by exposing the surface to one or more directed energetic particle beam characterized by one or more beam properties.
In an embodiment, for example, the selected multifunctional bioactivity is with respect to an in vivo or in vitro activity with respect to a plurality of biological or physical processes relative to a titanium or titanium alloy substrate surface not having the plurality of nanoscale domains characterized by the nanofeatured surface geometry. In embodiments, the in vivo or in vitro activity is an enhancement in cell adhesion activity, cell shape activity, cell proliferation activity, cell migration activity, cell differentiation activity, anti-bacterial activity, bactericidal activity, anti-inflammatory activity, osseointegration activity, biocorrosion activity, cell differentiation activity, immuno-modulating activity during acute or chronic inflammation or any combination of these. In an embodiment, the enhancement of in vivo or in vitro activity is equal to or greater than 100%. In an embodiment, the in vivo or in vitro activity is a decrease in an immune response, for example, a decrease in the immune response equal to or greater than 200% in a period selected from the range of 24 to 48 hours.
The wetting characteristics of a solid material is ultimately the result of surface free energy. In all forms of condensed matter, there is a significant difference in the energy distribution of surface atoms and atoms within the bulk of a material. Each atom within the bulk material is surrounded by other neighboring atoms that all exert multi-directional pulling forces that collectively balance into a net force of zero. Unlike bulk atoms, surface atoms are exposed to the environment and subject to the one-sided pulling force of their inner material atom interfaces and external contacting influences. In the conditions of an unbalanced net force, surface atoms have a higher energy state whose “excess energy” creates an internal contracting pressure designated as the surface tension or free energy. Contact angle analysis essentially accesses the equilibrium force between the surface tension of the liquid molecules and a solid material surface in terms of cohesion and adhesion energy. Cohesion free energy is defined as the free energy change per unit area in the process of bringing two like materials together to form a continuous body like the contracting forces pulling the liquid surface into a droplet. Adhesion free energy is the free energy change in the process of bringing two unlike bodies together. When the liquid surface tension exceeds the material tension, one obtains a high cohesion energy between the liquid molecules that results in a beaded liquid droplet and overall poor wetting of a material surface. A large contact angle is observed in unfavorable wetting conditions. A higher material surface tension correlates to a larger adhesion free energy, in which the material's inward attractive forces dominate the intermolecular forces of a liquid to spread and wet the surface. Naturally, a small contact angle is observed in favorable wetting conditions. Because of this, contact angle continues to be one of the accurate methods of characterizing material wettability.
The surface geometry of the titanium-based material may be altered in a variety of beneficial ways to provide the desired biocompatibility, each independently providing specific biological functions. Surface geometry may be simultaneously altered in multiple aspects over a selected surface area and selected depth, allowing for the efficient generation of compositions with enhanced bioactivity, including alterations to both inter-pore and intra-pore areas.
In an embodiment, the surface geometry is a spatial distribution of relief features, recessed features, localized regions characterized by a selected composition, phase, crystallographic texture, or any combination of these. In embodiments, the surface geometry is a periodic or semi-periodic spatial distribution of the nanoscale domains. In embodiments, the surface geometry is provided between and within pores of the substrate. In embodiments, the surface geometry is a selected topology, topography, morphology, texture or any combination of these.
In embodiments, for example, each of the nanoscale domains are characterized by a vertical spatial dimension less than or equal to 250 nm, less than or equal to 100 nm, less than or equal to 50 nm or, optionally, selected over the range of 10 nm to 250 nm, 10 nm to 100 nm or 10 nm to 50 nm. In embodiments, the nanoscale domains comprise nanowalls, nanorods, nanoplates, nanoripples or any combination thereof having lateral spatial dimensions selected over the range of 10 to 1000 nm and vertical spatial dimensions of less than or equal to 250 nm. In an embodiment, for example, the nanowalls, nanorods, nanoplates or nanoripples are inclined towards a direction oriented along a selected axis relative to the surface. In embodiments, the nanowalls, nanorods, nanoplates or nanoripples are separated from one another by a distance of less than 100 nm.
In an embodiment, for example, the nanoscale domains comprise discrete crystallographic domains. In an embodiment, the crystallographic domains are characterized as an α+β annealed alloy. In embodiments, the nanoscale domains characterized by a chemical composition different from the bulk phase of the titanium or titanium alloy substrate.
The provided surface geometries allow for specific, designed increases in biofunctionality of the modified surfaces and/or domains. The described increased bioactivity allows for the fabrication of compositions and implants that decrease bacterial growth or inflammation, improve biomechanical compatibility between the material and in situ tissue, promote functional deployment and increase implant lifetime and success rate.
In embodiments, the surface geometry provides an enhancement in vivo or in vitro activity with respect to cell adhesion proliferation activity and migration greater than or equal to 100%. In an embodiment, the surface geometry provides an enhancement in vivo or in vitro activity with respect to anti-bacterial activity and bactericidal activity greater than or equal to 100%. In embodiments, the surface geometry provides an enhancement of a selected physical property of the substrate, for example, hydrophillicity, hydrophobicity, surface free energy, surface charge density or any combination of these. In embodiments, the enhancement of selected physical property is equal to or greater than 25%.
The provided compositions and methods include a variety of titanium-based substrates or implants known as useful in medical procedures or as medical devices. The provided titanium substrate may include titanium-based materials preprocessed to have porosity or surface characteristics to further increase biofunctionality.
In embodiments, the titanium or titanium alloy substrate is a biocompatible substrate, for example, mesoporous, microporous, or nanoporous substrates. Advantageously, the described systems and methods may generate nanostructures and nanopatterns on the surface of the pore, between pores or both. In embodiments, the titanium or titanium alloy substrate comprises commercially pure titanium metal (cpTi), Ti6Al4V alloy or a combination thereof. In an embodiment, for example, the titanium or titanium alloy substrate comprises a component of a medical device. In an embodiment, the medical device is a dental implant, a joint, hip or shoulder replacement, pedicle screw, syringe, needle, scalpel, or other surgical rod, plate or spinal injury instrument device.
The energetic particle beam(s) provided herein may be individually controlled to promote specific self-assembly of nanostructures, topography and/or topography and/or to alter chemical composition, morphology or crystallography. In the embodiments utilizing multiple beams, each beam may be independently controlled by one or more beam parameters to achieve the desired biofunctionality. Given the option of multiple beams each controlled by one or more independent parameters, complex surface alterations are possible.
In an embodiment, the directed energetic particle beam is a broad beam, focused beam, asymmetric beam, reactive beam or any combination of these. In embodiments, for example, the one or more beam properties is intensity, fluence, energy, flux, incident angle, ion composition, neutral composition, ion to neutral ratio or any combinations thereof.
In an aspect, provided is a method of fabricating a bioactive titanium-containing substrate, the method comprising: i) providing the titanium or titanium alloy substrate having a substrate surface; and ii) directing a directed energetic particle beam onto the substrate surface, thereby generating a plurality of nanoscale domains on the surface; wherein the directed energetic particle beam has one or more beam properties selected to generate the plurality of nanoscale domains characterized by a surface geometry providing a selected multifunctional bioactivity. In an embodiment, the directed energetic particle beam is a broad beam, focused beam asymmetric beam or any combination of these. In embodiments, for example, the step of directing the directed energetic particle beam onto the substrate surface comprises directed irradiation synthesis (DIS), directed plasma nanosynthesis (DPNS), Direct Seeded Plasma Nanosynthesis (DSDPNS), Direct Soft Plasma Nanosynthesis (DSPNS) or any combination of these.
In an embodiment for certain applications, the step of directing the directed energetic particle beam onto the substrate surface is achieved using a method other than directed irradiation synthesis (DIS). For example, the invention, includes methods of fabricating a bioactive titanium-containing substrate wherein directed plasma nanosynthesis (DPNS), direct seeded plasma nanosynthesis (DSPNS) or any combination of these techniques is used to carry out the step of directing the directed energetic particle beam onto the substrate surface to generate a plurality of nanoscale domains characterized by a surface geometry providing a selected multifunctional bioactivity. Accordingly, one of skill in the art will readily understand that certain applications and materials of the invention are achieved using methods that do not include processing via directed irradiation synthesis (DIS).
In an aspect, provided is a method of fabricating a bioactive titanium-containing substrate, the method comprising: i) providing the titanium or titanium alloy substrate having a substrate surface; and ii) directing a first directed energetic particle beam and a second directed energy particle beam onto the substrate surface, thereby generating a plurality of nanoscale domains on the surface; wherein the first directed energetic particle beam has one or more first beam properties and the second directed energetic particle beam has one or more second beam properties; and wherein at least one of the first beam properties is different than at least one of the second beam properties and the first beam properties and the second beam properties are independently selected to generate the plurality of nanoscale domains characterized by a surface geometry providing a selected multifunctional bioactivity.
In embodiments, the one or more beam properties is intensity, fluence, energy, flux, incident angle, ion composition, neutral composition, ion to neutral ratio or any combinations thereof. In an embodiment, the directed energetic particle beam comprises one or more ions, neutrals or combinations thereof. In an embodiment, the ions are Kr ions or Ar ions. In embodiments, aid one or more beam properties comprise incident angle and the incident angle is selected from the range of 0° to 80°. In embodiments, the one or more beam properties comprise fluence and the fluence is selected from the range of 1×1016 cm−2 to 1×1019 cm−2 or optionally 1×1016 cm−2 to 1×1020 cm−2. In an embodiment, for example, the one or more beam properties comprise energy and the energy is selected from the range of 0.05 keV to 10 keV, or optionally, 0.1 keV to 10 keV. The use of energetic particle beams allows for substrate quench rates that are greater than traditional thermal and/or chemical processing methods. Quench rates may, for example, be nearly instantaneous as the directed particle beams may athermally interact with the substrate. In embodiments, the provided energetic particle beams provide a quench rate selected from the range of 1011 K/s to 1014 K/s (degrees Kelvin per second). In embodiments, for example, the substrate is quenched in less than or equal to 10 μs, or optionally, less than or equal to 1 ns.
The described compositions, systems and methods may be beneficial in any other applications in tunability of surface interfaces is desirable, such as tuning surface chemistry, topography, crystallographic structure or physical properties to support specific functions. For example, the provided compositions and methods may be utilized to achieve desired functionality in healthcare applications, aseptic processing, food and beverage production, consumer products and industrial processes.
Bioactivated titanium may be useful in a wide range of healthcare related applications, not limited to implants but expanding to a variety of medical devices. For example, bioactive titanium may be used in aseptic processing for the production of pharmaceuticals, vaccines, food and beverage or medicals devices, for example, by increasing antibacterial properties. Further, bioactive titanium can implemented in surgical instruments, dental instruments, and biosensors, including in vivo sensors and those integrated with or applied to tissues.
Surface modified titanium may also be useful in non-biological applications such as consumer products or industrial processes. For example, it may be used as a catalyst or catalyst support in a chemical reactor or processing device. Further, surface modified titanium may have enhanced heat transfer properties beneficial for use in heat exchangers, HVAC applications, insulators or other applications in which control of heat transfer is desirable.
As noted herein, the titanium compositions may be rendered anti-bacterial by the treatments described herein. On many surfaces exposed to the environment, there is the risk that a microbial biofilm may form on a surface. The compositions of the invention may be used together with any surface. The surface is not limited and includes any surface on which a microorganism may occur, particularly a surface exposed to water or moisture. Treating surfaces to avoid films of antimicrobial compounds or manufacturing with them the working surfaces of laboratories (clinical, microbiological, water analysis, food), of businesses handling fresh food (butchers, fishmongers, etc.), of hospital buildings and health centers, to mention just a few examples, guarantees the suitable hygienic conditions for development of the work and eliminates the risk of contamination and infections.
Such inanimate surfaces exposed to microbial contact or contamination include in particular any part of: food or drink processing, preparation, storage or dispensing machinery or equipment, air conditioning apparatus, industrial machinery, e.g. in chemical or biotechnological processing plants, storage tanks and medical or surgical equipment. Any apparatus or equipment for carrying or transporting or delivering materials, which may be exposed to water or moisture is susceptible to biofilm formation. Such surfaces will include particularly pipes (which term is used broadly herein to include any conduit or line). Representative inanimate or abiotic surfaces include, but are not limited to food processing, storage, dispensing or preparation equipment or surfaces, tanks, conveyors, floors, drains, coolers, freezers, equipment surfaces, walls, valves, belts, pipes, air conditioning conduits, cooling apparatus, food or drink dispensing lines, heat exchangers, boat hulls or any part of a boat's structure that is exposed to water, dental waterlines, oil drilling conduits, contact lenses and storage cases. As noted above, medical or surgical equipment or devices represent a particular class of surface on which a biofilm may form. This may include any kind of line, including catheters (e.g. central venous and urinary catheters), prosthetic devices e.g., heart valves, artificial joints, false teeth, dental crowns, dental caps and soft tissue implants (e.g. breast, buttock and lip implants). Any kind of implantable (or “in-dwelling”) medical device is included (e.g. stents, intrauterine devices, pacemakers, intubation tubes, prostheses or prosthetic devices, lines or catheters). An “in-dwelling” medical device may include a device in which any part of it is contained within the body, i.e. the device may be wholly or partly in-dwelling. Plastic materials with antimicrobial properties can also be used in manufacturing handles, handlebars, handgrips and armrests of public transport elements, in rails and support points in places widely used, in the manufacturing of sanitary ware for public and mass use, as well as in headphones and microphones of telephones and audio systems in public places; kitchen utensils and food transport, all with the purpose of reducing the risk of propagation of infections and diseases.
Without wishing to be bound by any particular theory, there may be discussion herein of beliefs or understandings of underlying principles relating to the devices and methods disclosed herein. It is recognized that regardless of the ultimate correctness of any mechanistic explanation or hypothesis, an embodiment of the invention can nonetheless be operative and useful.
a-c. Flat, clustered platelets and nano-ripples formed on the surface. Such structures are formed using the following DIS parameter—Gas: O, Angle: 60°, Energy: 1000 eV, Fluence: 1×1018 cgs.
a-b. SEM image displaying the drastic effect of incident angle on nanostructure formation with oxygen ion irradiations. Ti—O-13 (
a-d. SEM images displaying the drastic effect of incident angle on nanostructure formation with krypton ion irradiations. Ti—Kr-15 (
a-d. Different direction-oriented nano-walls and nano-cones formed on the surface. Such structures are formed using the following DIS parameter: Ti—Kr-17—Gas: Kr, Angle: 60°, Energy: 1000 eV, Fluence: 7.5×1017 cgs.
a-c. Large, stacked nano-cones and thin nano-walls formed on the surface. Such structures are formed using the following DIS parameter: Ti—Kr-18—Gas: Kr, Angle: 60°, Energy: 1000 eV, Fluence: 5.0×1017 cgs.
a-d. Long nano-walls and short nano-walls formed on the surface. Such structures are formed using following DIS parameters—Gas: Ar, Angle: 0°, Energy: 1000 eV, Fluence: 1×1018 cgs.
a-b. Long nano-walls and short nano-walls formed inside pores. Such structures are formed using following DIS parameters—Gas: Ar, Angle: 0°, Energy: 1000 eV, Fluence: 1×1018 cgs,
a-b. Long nano-walls and short nano-walls formed on the walls of the pores. Such structures are formed using following DIS parameters—Gas: Ar, Angle: 0°, Energy: 1000 eV, Fluence: 1×1018 cgs.
a-b. Long nano-walls and short nano-walls in a tilted view of the surface. Such structures are formed using following DIS parameters—Gas: Ar, Angle: 0°, Energy: 1000 eV, Fluence: 1×1018 cgs.
a-b. Long nano-walls and short nano-walls formed on the surface.
a-b. Long nano-walls and short nano-walls formed in the pores. Such structures are formed using following DIS parameters—Gas: Ar, Angle: 60°, Energy: 1000 eV, Fluence: 1×1018 cgs.
a. Titled view of surface Nano-cones
a-b. Nano-walls and nano-cone formed on the surface. Such structures are formed using following DIS parameters—Gas: Ar, Angle: 60°, Energy: 500 eV, Fluence: 1×1018 cgs.
a-c. Narrow and wide nano-cones formed on the surface. Such structures are formed using following DIS parameters—Gas: Ar, Angle: 60°, Energy: 750 eV, Fluence: 1×1018 cgs.
a-c. Long nano-walls and short nano-walls formed on the surface. Such structures are formed using following DIS parameters—Gas: Ar, Angle: 0°, Energy: 1000 eV, Fluence: 1×1018 cgs.
a-c. Long nano-walls and short nano-walls formed in the pores. Such structures are formed using following DIS parameters—Gas: Ar, Angle: 0°, Energy: 1000 eV, Fluence: 1×1018 cgs.
a-c. Long nano-walls and short nano-walls formed on the walls of the pores. Such structures are formed using following DIS parameters—Gas: Ar, Angle: 0°, Energy: 1000 eV, Fluence: 1×1018 cgs.
a-c. Long nano-walls and short nano-walls along with nano-cones formed on the surface. Such structures are formed using following DIS parameters—Gas: Ar, Angle: 60°, Energy: 1000 eV, Fluence: 1×1018 cgs.
In general, the terms and phrases used herein have their art-recognized meaning, which can be found by reference to standard texts, journal references and contexts known to those skilled in the art. The following definitions are provided to clarify their specific use in the context of the invention.
“Nanoscale domains,” as used herein, refers to features characterized by one or more structural, composition and/or phase properties having relatively small dimensions generated on the surface of a substrate. Nanoscale domains may refer to relief features and/or recessed features such as trenches, nanowalls, nanocones, nanoplates, nanocolumns, nanoripples, nanopillars, nanorods, nanowires, nanotubes and/or quantum dots. Nanoscale domains may refer to discrete crystalline domains, compositional domains, distributions of defects, and/or changes in bond hybridization. Nanoscale domains include self-assembled nanostructures. In embodiments, for example, nanoscale domains refer to surface depths or structures generated on a surface having dimensions of less than 1 μm, less than or 500 nm, less than 100 nanometers, or in some embodiments, less than 50 nm. In an embodiment, nanoscale domains refer to a domain in a thermally stable metastate.
“Surface geometry” refers to a plurality nanoscale domains positioned on the surface of a substrate. In embodiments, for example, nanofeatured surface geometry is a periodic or semi-periodic spatial distribution of nanoscale domains. For example, nanofeatured surface geometries include topology, topography, spatial distribution of compositions, spatial distribution of phases, spatial distribution of crystallographic orientations and/or spatial distribution of defects. Surface geometries of some aspects are useful for providing a selected multifunctional bioactivity, a selected physical property or a combination thereof.
“Selected multifunctional bioactivity” refers to an enhancement of in vivo or in vitro activity with respect to a plurality of biological or physical processes. In embodiments, for example, multifunctional bioactivity is enhanced relative to a titanium or titanium alloy substrate surface not having said plurality of nanoscale domains characterized by nanoscale surface geometry. In an embodiment, for example, a selected multifunctional bioactivity is an enhancement in cell adhesion activity, cell shape activity, cell proliferation activity, cell migration activity, cell differentiation activity, anti-bacterial activity, bactericidal activity, anti-inflammatory activity, osseoconductive activity, osseointegration activity, biocorrosion activity, cell differentiation activity, immuno-modulating activity during acute or chronic inflammation or any combination of these. In an embodiment, for example, a selected multifunctional bioactivity is a modulation in the immune response to a foreign body (e.g. the implant). In an embodiment, for example, a selected multifunctional bioactivity is an enhancement or inhibition of one or more protein interactions. Macrophage cells are powerful regulators of the foreign body response that govern the inflammatory and tissue remodeling pathways of injury resolution in implantation. In the body, foreign material is a potent stimulus that triggers the surrounding tissue to produce the various signaling molecules and growth factors of macrophage recruitment and polarization. Although type 1 and type 2 T-helper cell activity continue to be the standards of cell phenotype, the fundamental polarizing states of macrophages can be classified into the three main functions of host defense, immune regulation, and tissue repair. To characterize the macrophage polarization activated in each testing condition, an ELISA kit was used to quantify the secretion of pro-inflammatory and anti-inflammatory cytokines TNF-α and IL-10 at 24, 48, and 72 hours of surface cell culture. The 24-hour cytokine results are presented in Table 1 and
“Directed energetic particle beam,” as used herein, refers to a stream of accelerated particles. In embodiments, the directed energetic particle beam is generated from low-energy plasma. In some embodiments, directed energetic particle beam is a focused or broad ion beams capable of delivering a controlled number of ions to a precise point or area upon a substrate over a specified time. Directed energetic particle beam may include ions and additional non-ionic particles including subatomic particles or neutral atoms or molecules. In embodiments, directed energetic particle beams provide individual ions to the target location. Examples of directed energetic particle beams include focused ion beams, broad ion beams, thermal beams, plasma generated beams, optical beams and radiation beams.
“Beam property” or “beam parameter” refer to a user or computer controlled property of beam, for example, an ion beam. Beam parameter may refer to incident angle with a target substrate, fluence, energy, flux, beam composition and ion species. Beam parameters may be adjusted to provide selected interactions between the beam and the target substrate to generate specific nanostructures or enhance specific properties of the substrate. Beam parameters may be controlled by a variety of means, including adjustments to electromagnetic devices in communication with the beam, adjusting the gas or energy source used to generate the beam or physical positioning of the beam in reference to the target.
“Vertical spatial dimension” refers to a measure of the physical dimensions of a nanoscale domain perpendicular or substantially perpendicular to the planar or contoured surface of a substrate. In embodiments, vertical spatial dimension refers to a height or depth of a nanoscale domain or the mean depth of a surface modification, for example, a crystalline or compositional domain.
“Lateral spatial dimension” refers to a measure of the physical dimensions of a nanoscale domain parallel or substantially parallel to the planar or contoured surface of a substrate.
“Titanium or Titanium alloy substrate” refers to any substrate composed of titanium including commercially pure titanium and Ti6Al4V as described herein. In some embodiments, titanium alloys may refer to alloys containing titanium but in which titanium is not the primary component. In other embodiments, titanium alloys refer to alloys in which titanium represents more than 25%, or optionally 50%, of the alloy. Titanium and titanium alloys may include a titanium oxide layer, including on the surface being modified.
“Porosity” or “porous titanium” refers to substrates or titanium surfaces having individual or networked voids at or near the surface of the substrate. Porosity may be nanoscale, microscale or larger. As described herein, substrates may have porosity prior to any plasma treatment (e.g. porosity formed during substrate formation such as sintering). In some embodiments, pores may be formed, enlarged or altered by the treatment of directed plasma, including forming nanopatterns on interior pore surfaces or walls between individual pores.
“Multiplexing” refers to simultaneously modifying the target substrate in more than one way, for example, by providing two or more directed particle beams at the substrate having different properties, for example, to generate or modify at least one nanoscale domain (e.g. nanoscale features, crystalline domains, compositional domains, distributions of defects, changes in bond hybridization. In some embodiments, for example, a single directed particle beam may have one or more beam properties to generate or modify multiple nanoscale domains on the substrate. In embodiments, multiple direction particle beams are generated from the same plasma source.
The invention may be further understood by reference to the following non-limiting Examples that expand on certain aspects and embodiments of the invention.
It is recognized that medical grade titanium alloys, like commercially pure titanium (cpTi), are the best metallic biomaterials for bone replacement, primarily due to their excellent balance between biomechanical properties and in-vivo biocompatibility response. However, they have two important disadvantages: stress shielding and subsequent bone resorption due to stiffness mismatch with respect to bone, and the lack of osseointegration due to fibrous tissue around implants. Porous cpTi implants have been demonstrated to be an alternative for stress shielding and different techniques of surface modification like controlled roughness have been implemented for improvements of cpTi osseointegration. In this work we have modified samples of both rough and powder metallurgy (PM) porous cpTi by directed irradiation synthesis (DIS) with the aim of evaluating the capability to produce surface nano-patterning. These samples were tested by contact angle testing, structurally characterized by scanning electron microscopy (SEM) and atomic force microscopy (AFM), and biologically tested through the response of human aortic smooth muscle cells (HASMCs). Nano-patterning of porous+polished cpTi samples were highly successful with some samples sensitive to initial surface porosity, being more effective on the flat polished areas. In contrast, initial micro-roughness of conventional machined cpTi samples was an important obstacle to nano-patterning, allowing only influence on vertical nano-roughness, with an important smoothing effect for off-normal beam incidence. In general, DIS processing generated important improvements on both smoothing and surface free energy reflected in drastic reductions of contact angle measurements. Results presented not only have produced nano-structuring on porous Ti-based surfaces, but also produced advantageous smoothing of rough surfaces without any detrimental effect on the original biocompatibility of cpTi implants.
Bone tissue damage is typically represented by joints replacements, fractures, dental implants, and bone diseases related to osteoporosis and cancer. The broad spectrum of bone degradation issues become bone tissue problems as a public health problem, as was recognized some years ago by the World Health Organization [1]. Most of the current clinical treatments for tissue bone correspond to tissue substitution, i.e. replacements approaches for which the biomaterials are mostly of first and second generation. Using these combined biomaterials substitutes have shown reasonable success through translational and clinical levels. However, several failure statistics of current joint replacements indicate that this remains a technological challenge and warrants a multidisciplinary effort to offer new clinical alternatives with the highest in-vivo performance and reliability. To that end, some medical grade of titanium (Ti) alloys, like commercially pure Ti (cpTi), have proved to be the best biomaterials for clinical success of bone replacement due to its excellent balance between biomechanical and in-vivo biocompatibility. However, cpTi exhibits the following disadvantages that are direct consequences of being a 1st generation biomaterial [2]: 1. Biomechanical incompatibility reflected in the elastic mismatch with respect to hosting tissue, and the consequent bone resorption around the implants; 2. Being bio-inert, cpTi implants are surrounded by a thin fibrous tissue, which can often reduce osseointegration with an associated risk of loosening or fracture of bone and/or implant. Biointerface improvements are necessary to avoid the existence of the fibrous tissue or to reduce the loosening risks due to its presence.
In regards to the first problem, it is desirable to design new implants and prostheses with a lower stiffness than those currently used, which would address the stress-shielding problem without any important detrimental effect on mechanical strength. Several reported studies have focused on development of new implants with a bone-matching modulus, such as porous materials [3,4]. To that end, there are some manufacturing processes, among which are highlighted: the electron beam melting process [5], creep expansion of argon-filled pores [6], directional aqueous freeze casting [7], rapid prototyping techniques [8], laser-engineered net shaping [9], electric current activated/assisted sintering techniques [10,11], conventional and non-conventional powder metallurgy (PM) [12] and space-holder techniques [13]. From a conventional PM point of view, controlling compacting pressure, sintering temperature and time, could enable a suitable porosity for stress shielding reduction. Improvement of bone ingrowth and osseointegration requires that pore size and morphology be controlled, especially at the surface, which is also critical for the fatigue resistance of the implant. Optimum PM conditions, which ensures a desired balance between a low stiffness (reduced stress-shielding) and a high mechanical strength (fatigue resistance) have been established [14]. In regards to non-conventional PM alternatives for stress-shielding reduction, the loose sintering process (LSP), in which there is no used any compaction pressure, has emerged as an attractive route to produce porous Ti implants with high porosity and the aim of successfully replacing cancellous bone with an extraordinary low Young's modulus of around 0.5 to 1 GPa. To that end, a detailed comparison between space-holder and loose sintering techniques is available [15], in which they were able to properly optimize a suitable mechanical balance for a Ti implant used in highly porous bones.
In regards to alternatives about minimizing and/or avoiding fibrous tissue and lack of osseointegration, they are basically based on modifications of topographical and/or chemical properties of cpTi surfaces. With respect to topographical modifications, state-of-the art focuses on controlling surface kinetic roughness to improve osseointegration (i.e. by methods such as: chemical etching, sand-blasting, laser ablation, etc. . . . ). Most of these approaches have in common that a vertical parameter of roughness 5.0 microns has an important positive effect on osteoblast adhesion, and in further in-vivo osseointegration [16,17]. Despite limited success, many works can be found about surface chemistry modifications of cpTi by changing its bio-inert character to a bioactive one through different treatments: bioactive ceramic coatings like hydroxyapatite (HA) and Bioglass® [18], and thermo-chemical conversions of titanium oxide layer to a bioactive layer of sodium titanate [17]. In-vivo success of these treatments has been limited due to some functional problems such as: lack of adhesion, brittleness, phases instability, etc.
Surface nanostructuring of conventional biomaterials has emerged as one of the most important and effective approaches to convert them to advanced bioactive materials. This is the consequence of a nano-feature's ability to effectively have some influence on surrounding biological environment at the molecular nano-scale level. Since the cells in their natural environment are surrounded by nanoscale features linked to their extracellular matrix (ECM), the nanotopographical parameters become an important part in design of biomaterials for tissue formation and repair. Accordingly, several studies suggest that a remarkably small modification in surface nanotopography could support mesenchymal stem cell growth and development, indicating that changes in such nanotopographical features can have a direct influence in the adhesion/tension balance to permit self-renewal or targeted differentiation [19]. Biointerface topography and, in particular, nanoscale features can affect cell behavior and integrin-mediated cell adhesion, and is now evident from studies with fabricated topographical features [20]. The mechanisms that mediate cellular reaction with nanoscale surface structures are not well understood [21]. A direct result of the influence of the surface topography, or even an indirect one, may also be correlated to its ability to influence the composition, orientation, or conformation of the adsorbed ECM components [22,23].
The drawbacks of conventional nano-patterning techniques have mainly been attributed to their physical limitations in fabricating structures smaller than about 50-nm. Therefore, bottom-up techniques that rely on self-assembly, self-organization, and local patterning, have become technologies capable of pattern biocompatible surface nanostructures. Irradiation-driven systems have been explored in moderate energy regimes dominated by knock-on atom displacement regimes for semiconductor metallization microstructure control [24], engineering of nanostructured carbon [25], compositional patterning of immiscible alloys [26]. Directed Irradiation Synthesis (DIS) introduces a synthesis process that is scalable to high-volume manufacturing by virtue of its intrinsic large-area simultaneous exposure of materials surfaces and interfaces. Broad-beam ions combined with rastered focused ions and gradient ion-beam profiles are sequenced and/or combined with reactive and/or non-reactive thermal beams that control the surface topography, chemistry and structure at the micro and nano-scale [27].
There are no reported works that examine the capability of ion-beam based modification of nano-patterning rough and porous Ti (e.g. within and inside pores) with cell stimulation and tissue growth. Only a few works have addressed modification and testing on flat surfaces of TiO2 [28] in contact with rat aortic endothelial cells adhesion, and upregulation of osseospecific proteins-osteopontin and osteocalcin of human osteoprogenitor cells cultured on Ti [29]. Therefore, the aim of this work is to test the hypothesis, for the first time, that rough and porous cpTi samples can be nano-patterned in such way that the biological response of the surface can be favorably influenced. To that end, treated samples were characterized in order to establish relationships with DIS conditions, and with surface energy and structural properties as well. These new surfaces were also biologically evaluated by using human aortic smooth muscle cells (HASMCs) for cytotoxicity assessment. Overall analysis of DIS influence on initial rough and porous cpTi samples enabled qualification of the real potential of our technology for nano-patterning and generating a positive biological response.
Manufacturing of Porous and Rough cpTi Samples
The powder of cpTi (SE-JONG Materials Co. Ltd., Korea) used for the blends was manufactured by a hydrogenation/dehydrogenation process. The particle size distribution corresponded to 10, 50 and 90% passing percentages, of 9.7, 23.3 and 48.4 μm, respectively. The chemical composition of the powder used was equivalent to cpTi Grade IV according to the ASTM F67-00 Standard [30]. CpTi has an apparent density of 1.30±0.01 g/cm3 (28.8±0.1%) and a tap density of 1.77±0.04 g/cm3 (39.2±0.8%). The blends of cpTi powder were prepared using a Turbula® T2C blender for 40 min to ensure good homogenization. In order to address irradiation influence on porous cpTi samples with different porosities, here we are comparing the loose sintering technique (without any compaction pressure) with the conventional PM one via a low compaction pressure. The compacting step was carried out using an Instron 5505 universal machine to apply the pressure used of 100 MPa, according to reported optimum results [14]. The compacting loading rate was 6 kN/s, dwelling time was 2 min and unloading time was 15 s for decreasing load up to 150 N. The sintering process was performed in a Carbolyte® STF 15/75/450 ceramic furnace with a horizontal tube at 1250° C. for 2 h using high vacuum (≈5×10−5 mbar). Diameter of compaction die (8 mm) and powder mass were selected to obtain samples in which the effect of compaction pressure was minimized [14]. Surface treatment of cpTi rough samples was achieved by conventional machining of discs (diameter of 2 cm, thickness of 0.5 cm) that were provided by City of Hope of Cancer (, Duarte, Calif.).
Directed Irradiation Synthesis (DIS) of Porous and Rough cpTi Samples.
Grinding and polishing of cpTi porous samples were performed, before DIS processing. In contrast, original rough cpTi samples were irradiated as received. DIS experiments were performed at Radiation Surface Science and Engineering Laboratory (RSSEL) at School of Nuclear Engineering, Purdue University, through the facilities of Particle and Radiation Interaction with Soft and Hard Matter (PRIHSM) system, which was originally developed and set-up by Prof. Jean Paul Allain [27]. DIS conditions of different rough and porous cpTi samples appear summarized in Table 1; they were chosen after an exhaustive revision of our previous DIS nano-structuring results on metals [27, 31], as well as from some other revised works on Ti, TiO2, Cu, Au, and Ag [32-42]. Argon (Ar+) source at 1 and 0.5 keV was used to irradiate cpTi samples; several angles of incidence and fluences were also evaluated, as is shown in Table 1.
Structural and Surface Free Energy Characterization of cpTi Samples Modified by DIS
Surface free energy of irradiated samples was evaluated by contact angle testing with deionized water through a Rame-Hart Goniometer Model 500-Advanced contact angle goniomter/tensiometer with DROPimage Advanced Software. We performed the sessile method of contact angle analysis (where the sample was static and not moving after the drop was placed on it). All measurements were performed with deionized water (to not have any type of interaction with the surface). The water dropper was far enough away from the surface that the water did not touch the sample until it left the dropper. The dropper was kept at the same distance from each sample surface. The water droplets had 3 pL of water on each sample. Morphological features of samples were detailed analyzed by Scanning Electron Microscopy, SEM (Philips XL40 field emission, FEI, Hillsboro, Oreg., USA). Atomic force microscopy (AFM) was also used for detailed morphological and topographical characterization of irradiated cpTi surfaces, by using an AFM Veeco Dimension 3000 (Santa Barbara, Ca) on AC Mode using cantilever Bruker DNP-10. The scanned area was 1 μm square over samples of both titanium rough and porous samples.
Biological evaluation of cpTi samples modified by DIS.
The cells used for biological assessment of treated and un-treated samples were human aortic smooth muscle cells (HASMCs, Lifetechnology Cat # C0075C). To that end, cells morphology changes with culture time, and cytotoxicity assays test on modified surfaces via Comet Assay® testing, were performed. Changes in cells morphology in terms of culture time was observed by using optical microscopy (OM) analysis. The cell line used was the choose model to validate the potential for tissue growth and regeneration of the new surfaces. Cells were grown at 37° C. with >95% Rh and CO2 gas exchange until they were nearly confluent. HASMCs were seeded on the top of the samples for 24 hours under normal culturing conditions (37° C., 95% air, 5% CO2, 95% humidity). HASMCs with a cellular density of 5×103 live cells per cm2, and viability of 86% were cultured in a 7 well tissue culture dish in the presence of the analytes. Two samples labeled as NegCtl and PosCtl corresponded to cells growing alone and used as controls in the assay. All the samples were incubated under normal culturing conditions (37.0° C., 95% air, 5% CO2, 95% humidity) for 24 hours. Then, after 48 hours, visual inspection of HASMCs growing in the presence of the tested analytes was performed during the incubation period under bright field illumination 30 utilizing a Nikon inverted Diaphot fluorescent microscope with 10× and 20× objectives (Nikon Instruments, Melville, N.Y.). The Comet Assay® was carried out according to manufacturer's recommendations (cat. #4250-050-K, Trevigen, Inc., Gaithersburg, Md.). Finally, all the experimental measurements are presented as the mean+standard derivation, which were analyzed using Origin Pro 8.6. One-way ANOVA was performed to compare the mean of the samples, and at the 0.05 level, the population means were considered to be significantly different.
Structural Characterization of as-Received (AR) and DIS Treated cpTi Samples
Microstructure of un-irradiated cpTi, rough and porous, samples correspond to a conventional medical grade cpTi (commercial Ti) (
Surface structural modifications and nano-structuring due to DIS of porous cpTi samples are summarized in
Nano-structuring of porous cpTi samples depicted in
From the theoretical point of view, the first advances for understanding ion beam sputtering (IBS) nano-structuring was made by Sigmund [46] as he showed that local surface minima (“valleys”) should be eroded at a faster rate than local maxima (“peaks”); i.e., the sputtering rate depends on the local surface curvature, leading to a surface instability, which is the origin of the nano-structuring process. Based on this work, Bradley and Harper (BH) proposed later the first continuum model describing ripples formation [47]. In such a way, sputtering can be used to alter the surface morphology due to its dependence on the local surface curvature [48]. Depending on the irradiation conditions (angle of incidence, energy, surface curvature, etc.), it can induce either surface smoothening or roughening. These competing processes may be used to design the surface geometry important for certain applications. The velocity of erosion is therefore faster for the trough than for the crest. In the case of metals, the build-up of a regular pattern is produced by two different mechanisms, which lead to a similar surface instability: the surface curvature dependence of the ion sputtering and the presence of an extra energy barrier whenever diffusing adatoms try to descend step edges. In the case of a surface porosity mostly isolated and confined at the surface, several incidence angles can be locally experienced inside the pores for a fixed remote incident angle; this will be traduced in a curvature dependence of the surface nano-patterning. Therefore, we can speculate about a sequence of patterns inside the pores for an off-normal ion incidence like 60°; for an ideal semi-circular closed pore with a diameter of the same order of the grain size that would be: 1. Initially, a nano-rod domain region produced due to a semi-grazing incidence, which would be associated to a predominant erosive regime; 2. A second domain region would consist of a mixed pattern of rods and ripples due to its similarity with remote conditions due to 60° incidence (diffusive plus erosive regimes); 3. A nano-rippled region appears due to normal incidence conditions (diffusive regime); 4. Once again, a mixed rods+ripples zone due to occurrence of a local incidence angle similar to that off-normal remote angle. Note that some pores in
DIS on rough cpTi is performed through different incident angles, in order to test the influence on surface structuring; a low energy Ar+ion particle beam is extracted and applied to the samples with normal and off-normal incidences (0°, 45° and 75°). Images with lowest magnifications basically don't show any notorious micro-scale difference due to normal Ar+incidence with respect to untreated surface (see
A similar insensitivity to Ar+normal incidence on initially rough surfaces has been also observed on different irradiated materials, like Cu samples that were observed by Hino et al. [49]; despite they were not focused on any nano-ripple formation, the surface became rough compared with that one before the irradiation, after treatment with the incident angle of 0°. In contrast, the surfaces were observed to become smooth with an increasing of incidence angle. This is reasonably consistent with our results here, as it will be discussed later about AFM analysis of irradiated surfaces. In addition, we can consider other two factors that can avoid effective nano-rippling during Ar+normal incidence on original rough surfaces: 1. Crystalline phase is not directly exposed to broad ion beam; then, this is a clear obstacle to any atom diffusion driving force due to impacting ions; 2. Irregularities associated to roughness can clearly allow some interference phenomenon between protrusions, which will reduce any driving diffusion nano-patterning effect due to impacting ions.
Nano-scale holes observed due to normal incidence could be related with increased roughness above mentioned, which is also and indicative of highest erosive effect due to interaction between normal incidence and initially rough surface. This Ar+normal incidence capability to create controlled nano-holes were previously reported by Li et al. [50]; in their work, they were able to produce those nano-holes by using a thin insulating solid-state membrane in which those samples had big symmetry hales in counterpart of the irradiated part, in such a way that a thin neck between the big pores and the irradiated part was removed by the ion beam. Therefore, within the same line of reasoning, our nano-holes due to Ar+normal incidence on a rough cpTi samples can be the consequence of a certain kind of empty space or big pore below the some thin outer irradiated layer; as in the work of Li et al [50]. It must be noticed also that, in addition to those created circular-shape holes, it can be appreciated some embryonic or nucleated pre-holes, which appear as a depressions similar to typical nano-voids which are normally observed after ductile fracture of metals. In search of another reasonable explanation, by looking the morphology of the voids produced, another source for this specific damage can rely on supersaturating defects (displacement damage) and accumulation of implanted inert gases (Ar+) [51]. Formation of voids and bubbles during ion beam interaction with materials addresses many important issues. In fact, formation of a three-dimensional (3-D) void-lattice has demonstrated the earliest example of self-organization in material processing. This is the key concept of the “bottom-up” technology used for modern ultra-small scale device formation.
Off-normal incidence on rough cpTi samples was performed through irradiations of 45° and 75° incidence angles (see
AFM analysis has quantification the surface features due to DIS on both porous and rough cpTi (see
Surface Free Energy Evaluation of as-Received (AR) and DIS Treated cpTi Samples
The wettability is fundamental for the cellular adhesion and, consequently, for the success of osseointegration and bone tissue growth, since the blood is the first tissue that reaches the implant, and 90% of its plasma is composed by water [54], the evaluation of the surface wettability can be accomplished through the determination of contact angle. First of all, we compare the contact angle of our untreated sample with some value of Ti already reported; to that end, we used some previous works about Ar+bombardment on cpTi [55] and on Riedel [45]. From that comparison, as-received surfaces (porous, polished and rough) presented similar values of free surface energies of simply AR machined Ti6Al4V samples [45], as well as values of cpTi mirror polished [55]: our samples with 53.03±0.06, against 54.55±6.54 for Ti6Al4V and 53.46±4 for cpTi II. The contact angle measurements after irradiation of porous cpTi samples, reflected an important change with respect to control one (see Table 2); both types of porous samples (lowest and highest porosity) demonstrated important reduction of contact angle (reduced hydrophobicity) after Ar+irradiation with 60° incidence angle. In case of lowest surface porosity, contact angle was of 13.45±4.51 (reduction of 74.64%), and for highest porosity the contact angle was of 28.15±5.21 (reduction of 46.92%). It is important to notice that those reduced values of contact angle after DIS were obtained despite the initial porosity of samples, and the initial roughness of rough samples as well. Despite there are reported some works about influence of ion irradiation on contact angle, this is the first time that such a reduction is reported due to off-normal Ar+incidence on Ti. With respect to those previous works on Ti6Al4V and cpTi II, there does not appear to be any examples of measurable change on contact angle due to normal Ar+incidence on machined Ti6Al4V; with respect to effect on cpTi II, a reduction of about 62.6% due to normal incidence of 1.5 keV has been reported (compared with our value of 1 keV).
In summary, our results have shown a contact angle reduction due to DIS on both porous and rough samples; DIS nano-structuring of porous samples implied lowest contact angle for middle incidence angle of around 60 degrees; in addition, smoothing of rough samples due to normal and off-normal incidences implied also a drastic reduction of contact angles. In order to rationale this tendency, we must first try to understand the factors that determine the contact angle response of a surface and its relation with the surface free energy. The molecular interactions of water with a surface can be characterized by three mechanisms: covalent bonding, electrostatic interaction, and electromagnetic interaction [56, 57]. The amount of interaction that a liquid has with a surface can be described as a balance of free energies and the subsequent surface tension relating to each interface (solid-liquid, liquid-gas, gas-solid). To better describe wetting on real surfaces with roughness and imperfections, two models have been developed based on modifications to Young's equation; these are the Wenzel [58] and the Cassie-Baxter models [59]. The difference in these modes of analysis is based on assumptions that the liquid will react to surface irregularities in two distinct manners. In the Wenzel regime, although the surface is roughened, the liquid remains capable of complete contact with the solid beneath. In contrast, the Cassie-Baxter model assumes the roughness of the surface prevents complete contact between the liquid and solid by trapping gas between the two phases. According to these models, we can summarize that contact angle dependence about following factors: liquid properties, topographical parameters, surface chemistry, surface crystalline structure, surface crystalline defects, surface residual stress, surface micro-curvature, contact time, temperature and environmental pressure. Within this framework and by considering the relationships that we have established through our own master-diagram in
Biological Assessment of as-Received (AR) and DIS Treated cpTi Samples
As it is well recognized from biological response of biomaterials surfaces, free surface energy of biomaterials reflected in their contact angle values plays a determinant role in the biological environment response. By considering the effect of multiple surface properties in contact angle results, here we can establish important relationships with surface modifications due to ion irradiation processing of cpTi surfaces. In that context, osseointegration is one of the good examples in which, besides the roughness, the surface tension is a parameter that interferes on it [60]. It permits a higher or smaller scattering of liquid onto the metallic surface. The human blood contains about 90% of water, thus the capability of water adsorption by the surface, known like wettability, is a fundamental parameter to the success of cellular adhesion and, consequently, to the osseointegration [54]. It is commonly accepted that blood compatibility is improved when the hydrophilicity of a surface is increased (unless the surfaces are superhydrophobic) [61-63].
Cytotoxicity assessment of irradiated samples was performed via Comet Assay@ testing, in search of evaluating the potential geno-toxicological effect in vitro on human aortic smooth muscle cells (HASMCs) cultured in the presence of the evaluated specimens.
By comparing with previous works about biological assessment of Ar+irradiated Ti samples, our results are in well agreement with those reports; firstly, for the case of cpTi II after normal incidence [55], they found that proliferation tests showed that irradiated surfaces allowed a significant increase in the number of cells, compared to that data obtained in untreated surfaces. Their evaluations of the biological response in vitro in the new biomaterial surface showed that the behavior of pre-osteoblasts cells MC3T3-E1 was influenced by the topography, roughness and wettability of the titanium surface submitted to the argon-ion bombardment. Secondly, with respect to biological evaluations of Ar+irradiated Ti6Al4V under normal incidence [45], it was observed that Ar+beam etching had a largely positive impact on the cellular interaction over the as-received substrates. Calcein AM staining and SEM imaging confirmed that there was an increase in early cell spreading and mobility. Most importantly with respect to our cytotoxicity results, they also found that the ion beam etched substrates had slightly lower but comparable MTT absorbance to the untreated as-received substrates, but the ALP values of the etched were higher. Biocompatibility is, at least, equal to well-known biocompatibility of conventional bio-inert cpTi surface; with respect to cell behavior parameters, by considering our improvements in nano-structuring, roughness parameters and contact angle, we can reasonably expect that cells factors like adhesion, proliferation, migration, and differentiation will be also improved with the surfaces obtained here. However, it is important to point out at this moment that our results reported here are new in the sense that is the first time is shown relationships between initial surface micro-topography of cpTi (porous, polished and rough), irradiation conditions, surface nano-structure, roughness, surface free energy and basic biocompatibility assessment; they are related not only with their behavior and adhesion, but also with their further potential to stimulate tissue growth.
Characterization of surface properties and preliminary biological evaluation of porous, polished and rough cpTi samples after low energy Ar+irradiation, has allowed us to highlight the following findings about their potential use for bone tissue growth:
1. Irradiation with Ar+ of porous, polished cpTi samples under off-normal incidence (60 degrees) produced a general nano-pattering corresponding to conditions of mixed diffusive and erosive regimes: mostly nano-rods and some curved nano-ripples. These nano-features appeared mostly with same orientation, which would indicate surface texturing of α-(hcp) phase, most probably associated to plastic strain of the surface micro-structure during polishing. Interestingly, surface porosity was not an obstacle for nano-structuring; even nano-pattering of pores inside was possible, which seems to be related with different angles that can be formed between the remote incident angle and the pore's curvature. This capability of Ar+irradiation to nano-patterning both flats and curved zones of porous cpTi implants opens, for the first time, a real opportunity to address successfully two of the most important issues of Ti implants: stress shielding by controlled bulk porosity, and improvements of osseointegration by converting the whole surface in a third generation one, by a controlled surface nano-patterning.
2. Micro-roughness of original rough cpTi samples was an enough obstacle to successfully nano-structuring after low energy Ar+irradiations with different incident angles. However, it was observed some important effects on micro and nano-topographical parameters of irradiated samples, depending on the incident angle. Normal incidence was the only condition that produced small proportion of nano-ripples; however, its most important effect was increasing of roughness and some production of circumferential-shape holes. These features are assumed to be mostly the consequence of irradiation of some thin plastic deformed layer, and/or due to creation of irradiation voids and bubbles. Small nano-ripples are due to small diffusive effect, whilst the increased roughness is most likely related with a process highly erosive. As long as off-normal angle was increased, an important smoothing effect was evident; in addition, the closest angle to grazing incidence had the strongest smoothened effect, which was appreciated from SEM analysis.
3. Detailed analysis and quantification of irradiated surfaces by AFM allowed us to confirm structural and roughness modifications due to low energy Ar+ion beams. Porous, polished cpTi samples exhibited a very smooth surface reflected in a few nano-meters parameter of nano-roughness; this is mostly a consequence of the polishing process. Interestingly, the initial smooth surface was not negatively affected by DIS nano-patterning; in contrast, it seems to generate an even smoother irradiated surface. Initial rough samples showed high roughness sensitivity to irradiation; in such a way that raised off-normal incident reduced vertical roughness parameters, due to smoothing effect above mentioned.
4. Surface free energy estimations of treated samples via contact angle testing served us to establish some relationships with structural modifications due to irradiation processing. Despite contact angle has a complex functional dependence on several factors, our results here were clearly sensitive to nano-roughness vertical parameter; therefore, the lowest nano-roughness parameter implied a lower contact angle value. Moreover, it relevant that the smoothing effect of DIS on rough samples allows similar values of porous, polished and irradiated samples, especially for the incident angle close to grazing incidence. With respect to influence of DIS nano-patterning on roughness and contact angle results, which can only be analyzed for porous, polished samples, it seems that higher nano-structuring not only implied a lower roughness, but also meant a lower contact angle, with a reduction of about 50% of initial value.
5. Preliminary biological assessment by Comet Assay® testing of both porous, polished and rough cpTi irradiated samples has shown that Ar+ions beams has not any toxicological detrimental effect on initial biocompatible surface. HASMCs morphology behavior in contact modified surface, and in terms of time, also suggests that these new surfaces will in fact improve In Vivo tissue stimulation. This can be stated from the consistency with several previous results, as well as because those important improvements observed on surface nano-structuring, controlled roughness and reduced free surface energy. In summary, phenomenological relationships and trends determined here allowed us to have a new insight about positive influence of Ar+irradiation on both porous and rough cpTi surfaces in order to not only improve osseointegration, but also to effectively promote bone tissue growth and repair.
Degradation and damage of human tissues are one of the most important public health problems that often compromise the patient's quality of life. Multi-disciplinary teams from government to academic/industrial networks routinely confront this challenge seeking to develop practical treatments and repair. For damage to bone tissue, it is widely recognized that medical grade titanium alloys, such as Ti6Al4V, is the best biomaterial for bone repair due to an optimal balance between its biomechanical and biocompatible properties. Several cases in the literature exist that test the hypothesis of using Ti6Al4V for growth stimulation of other tissues different than bone by some type of surface modification. In this work we have obtained, for the first time, high-fidelity control of surface nanostructures on medical grade Ti6Al4V by using ion-beam sputtering (IBS) resulting in control of cell shape, adhesion and proliferation. These surfaces were biologically tested through the response of human aortic smooth muscle cell (HASMC) line as a cell model. This cell line was specifically used for cytotoxic assessment through yellow tetrazolium MTT method, and for evaluating morphological and adhesion changes of cells, in contact with the new surfaces. Cell behavior indicated not only an unaltered biocompatibility of the new Ti-alloy nanostructured surfaces, but also important dramatic control of filopodia and lamellipodia activity of cells. These are good indicators of improvement of cell adhesion and proliferation. Improvements of cell attachment, especially in regards to filopodia activity, were directly related with nano-ripples structure geometry and, therefore, with incidence angle, which followed a diffusive regime during ion-beam irradiation.
One of the fundamental premises in substitutive medicine is that once a certain level of deterioration of any organ or tissue has been reached, a more effective protocol is to remove it and replace it rather than attempt to heal it. In that context, damaged tissues are currently treated from two conventional medical paradigms: 1) organ transplants and 2) tissue/organ replacement with a biomaterial; i.e. via auto-grafts or allograft routes [1]. Tissue engineering (TE) and regenerative medicine (RM) are two concepts clearly related but inherently different. While TE focuses on engineering methods to produce new tissue from a variety of cellular sources, RM focuses on the use of biomaterials for the regeneration of tissues and organs [2]. RM, in the widest sense, is concerned with the restoration of impaired function of cells, tissues, and organs either by biological replacement, e.g. with tissues cultured in-vitro, or by providing the stimulus for the body's own reparative and regenerative mechanisms [4]. Simultaneously, biomimetics and bioinspired concepts have emerged based on the principle of construction of artificial materials that attempt to imitate the tissue they are implanted in and are actively interacting with its cells [6]. The repair and substitution of bone require both non-degradable and degradable materials that should be able to integrate and form a direct bond with the tissue; such is the case for osseointegration. Within this context, pure titanium (Ti) and some of its alloys, and some bioactive bioceramics as well, are the conventional biomaterials that have shown the highest clinical success [2]. Ti is widely recognized to be the preferred biomaterial for bone replacement due to its excellent balance between biomechanical and biocompatibility response. However, titanium suffers from the intrinsic growth of a thin fibrous tissue interface [2].
Last decade has been arguably a definitive period for the role nanotechnology can play on advanced biomaterials. In that sense, surface nanostructuring of conventional 1st and 2nd generation biomaterials, has emerged as one of the most important and effective approaches to convert them to a 3rd generation biomaterial, as described herein. Meaning that as a consequence of nano-features fabricated on the biomaterial in question it imparts the function to effectively influence surrounding biological environment at a molecular nano-scale level. Several studies demonstrated different morphology configurations at the nanoscale can have a strong and direct influence over cellular behavior; indeed, it's possible to appreciate that cells prefer texturized surfaces in comparison with smooth ones, depending on cell type [6]. Biointerface topography and, in particular, nanoscale features can affect cell behavior and integrin-mediated cell adhesion, and is now evident from studies with fabricated topographical features [3]. The extent to which nanotopography influences cell behavior in-vitro remains unclear, and investigation on this phenomenon is still underway. The processes that mediate the cellular reaction with nanoscale surface structures are also not well understood [7]. For example, it is not clear if this influence derives directly from surface topography, or perhaps indirectly with surface structures possibly affecting the composition, orientation, or conformation of the adsorbed ECM (extra-cellular matrix) components [8, 9].
A few papers have reported converting Ti into a third generation biomaterial and those papers do not appear to describe modifying Ti surfaces for regenerative medicine. Most of them have shown improvements of cell adhesion due to interactions with nano-patterned surfaces, as regulators of cellular functions through focal adhesion. Results include: increased adhesion and formation of human mesenchymal stem cells [10], improvements of rat aortic endothelial cells adhesion on TiO2 [11], upregulation of osteospecific proteins—osteopontin and osteocalcin of human osteoprogenitor cells cultured on Ti [10]. Conventional processing of materials for surface nanostructuring has been dominated by the development of advanced top-down fabrication techniques that include lithography-based techniques. Some of them include focused-beam lithographies using electron or ion energetic particles and scanning probe lithographies [12, 13]. The drawbacks of these conventional techniques have mainly been attributed to their physical limitations in fabricating structures smaller than about 50-nm and also limited to the modification of a few classes of materials. Therefore, bottom-up techniques that rely on self-assembly, self-organization, and local patterning, have become emergent technologies capable of patterning biocompatible surface nanostructures. Ion beams can be used to induce patterned structures with unique topography at the nano-scale by means of sputtering and other surface-related processes [14-22]. Irradiation-driven systems have been explored in similar moderate energy regimes dominated by knock-on atom displacement regimes for semiconductor metallization microstructure control [23], engineering of nanostructured carbon [24], and compositional patterning of immiscible alloys [25]. One important limitation in current nanomanufacturing approaches is a dependence on naturally self-ordered processes that balance kinetic and thermodynamic dissipative forces in the absence of irradiation therefore requiring very high temperature processes [26]. Consequently, many of the desired biomaterial properties that require a combination of metal alloy and soft material interfaces cannot be processed with conventional bottom-up techniques. Directed Irradiation Synthesis (DIS) and Directed Plasma Nanosynthesis (DPNS) address this limitation by introducing a synthesis process that is scalable to high-volume manufacturing by virtue of its intrinsic large-area simultaneous exposure of materials surfaces and interfaces. One subset of DIS is ion-beam sputtering (IBS) and is the methodology used in the work reported here. Advanced in-situ synthesis methods have been recently developed by Allain et al. to elucidate ion-irradiation mechanisms that can manipulate surface chemistry and surface morphology to ultimately synthesize functional coatings for 3D scaffold systems [27].
The aim of the work reported here is to examine the role surface nanostructuring of Ti6Al4V by IBS can have in the stimulation of cells and tissues, other than bone, in order to provide important cues for tissue regeneration. We report a systematic study where we have successfully nanostructured medical grade Ti6Al4V and conducted detailed characterization establishing processing conditions and correlating them to surface and biomaterial properties. These new nanostructured surfaces were biologically evaluated by using human aortic smooth muscle cells (HASMCs) for proliferation and cell/surface adhesion. This analysis allowed us to determine connections with processing, structure, surface energy, and biointerface properties. Biological response of these new surfaces has also lead us, for the first time, to establish correlations between nanostructuring by IBS and cell stimulation, as well as to show the real potential of these new surfaces to favorably stimulate cells and tissues different than bone.
Ion Beam Sputtering (IBS) of Ti6Al4V Samples
Medical grade Ti6Al4V alloy (ASTM F136, F1472) samples were used for surface modification by IBS. Samples were initially prepared by grinding and polishing up to mirror finish, before exposure to irradiation processing. IBS synthesis conditions for various Ti6Al4V samples are summarized in Table 5. Conditions were selected after an exhaustive revision of our previous DIS nano-structuring results on metals [27, 28], as well as from some other revised works on Ti, TiO2, Cu, Au, and Ag [29-40]. Argon (Ar+) source at 1 keV was used to irradiate discs of Ti6Al4V; several angles of incidence and fluences were also evaluated, as shown in Table 5
Structural and Energy Characterization of IBS Modified Surfaces
Surface energy of irradiated samples was evaluated by contact angle testing with deionized water through a Rame-Hart Goniometer Model 500-Advanced contact angle goniomter/tensiometer with DROPimage Advanced Software. We performed the sessile method of contact angle analysis (where the sample was static and not moving after the drop was placed on it). All measurements were performed with deionized water (to not have any type of interaction with the surface). The water dropper was far enough away from the surface that the water did not touch the sample until it left the dropper. The dropper was kept at the same distance from each sample surface. The water droplets had ˜3 μL of water on each sample. Morphological features of samples were analyzed by Scanning Electron Microscopy, SEM (Philips XL40 field emission, FEI, Hillsboro, Oreg., USA).
Cell Morphology Via SEM
HASMCs morphology was observed using a scanning electron microscope (SEM). For this, cells were culture for 24 hours on un-irradiated and irradiated Ti6Al4V samples, and subsequently, fixed and dehydrated using 10% formalin and increasing concentrations of ethanol (30, 50, 70, 80, 90 and 100%) respectively. Finally, the samples were subjected to critical point drying and coated with gold to be observed by SEM.
Cell Proliferation Via MTT
HASMCs (ThermoFisher Scientific, MA) were seeded on the top of un-irradiated and irradiated Ti6Al4V for 24 hours under normal culturing conditions (37° C., 95% air, 5% CO2, 95% humidity) at a density of 5×103 cells/cm2. Afterward, yellow tetrazolium MTT colorimetric test was carried out and the mitochondrial activity was read at 570 nm according to the manufacturer's instructions (Sigma Aldrich, M0).
Surface Nano-Structural Characteristics of IBS Ti6Al4V Samples
Considering the microstructure of unirradiated Ti6Al4V samples after proper etching procedures, one can observe a conventional α+β mill-annealed alloy (see
In
Previous work in off-normal Ar+irradiation on Ti alloys reported by Quian et al [30] consisted of a study that used the focused ion beam (FIB) technique with relatively high-energy 30-keV Ga+ions on polished commercially pure Ti (cpTi) to induce topographical patterning. Focused Ga+ions were rastered at various FIB incidence angles over a wide range of doses and at room temperature. Results presented evidence of nanoscale ripple formation at normal incidence, which was strikingly different than well-known irradiation experiments of normal incidence bombardment of semiconductors. Examination by Quian et al. demonstrated the important role that crystallographic orientation has on pattern formation and in particular the role of surface diffusion in the intrinsic anisotropic hcp structure of titanium. In addition, contrary to prior observations of ripple structure direction dependence with incident angle, results demonstrated that regardless of the incident angle, the important factor was the crystallographic orientation of each grain for the direction and type of pattern (e.g. ripple vs dot) formed at normal and near-normal incidence. In one instance with incident angle of 30°, they also observed curved nano-ripples and fragmented rods, consistent with our irradiation protocols of Ti6Al4V alloys. Furthermore, as the incident ion-beam angle was systematically increased, the importance of the incident ion-beam direction on the type and direction of the nanopattern became stronger. However, the key difference between the work by Qian et al. and that presented here is the high-fidelity control not of the ripple structure but more importantly of the nanowall systems that ultimately plays a key role in the modulating immuno-response of macrophage phenotype and cell adhesion.
Current atomistic computational modeling by Yang et al. [reference PRB 2015 and NIMB 2014] have demonstrated the role increasing incident ion-beam angle has on ripple nanopattern formation and discovered a correlation to erosion-dominant mechanisms that increased with an increase in ion-beam incident angle. The same models also demonstrated that as the incident ion-beam angle decreased to near-normal incidence, the erosive component would decrease and atomic diffusive mechanisms would take over influence mass redistribution during irradiation and ultimately dictating pattern formation. In this case, surface anisotropy and crystallographic orientation would therefore dominate in the onset of ion-induced pattern formation. Therefore, we conclude that surface nanostructuring due to ion-beam sputtering (IBS) on Ti alloys is controlled by two mechanisms: surface and sub-surface atomic diffusion mechanism (diffusive or mass-redistribution regime), which is crystallographic orientation and surface anisotropy dependent, and an erosive mechanism (erosive regime), which is incidence-angle dependent at incident angles greater than about 30-degrees for Ti alloys. We conclude, for example, that the mixed pattern of curved nano-ripples and elongated rods is the consequence of a competition between these two mechanisms. Moreover, we discovered this morphological trend with incident ion-beam angle is dominant for the α-phase in the Ti6Al4V alloy meanwhile for the 3 (bcc) phase appears insensitive to this trend, as discussed later in this paper. The interaction and competition between the two mechanisms discussed above induces pattern formation observed in
In
At the highest incident angle (e.g. 80° incidence), a new trend in the resulting nano-pattern is obtained (see
Biological Behavior with the Nano-Structured Ti6Al4V Surfaces Synthesized by DIS
In this section an evaluation of the surface morphology modification by IBS on the Ti alloy samples is correlated to in-vitro biological testing to determine effects on cell behavior. Table 6 lists the contact angle results for samples irradiated at each listed incident ion angle measured with respect to the sample surface normal. Considering the statistics from Table 6, we note that very little change in contact angle and possibly in surface energy of the material for each irradiation condition is measured. Since the contact angles are similar, this presumes that the substrates have comparable surface free energies. However, one must be careful not to confuse strong wetting as a necessary condition for cellular adhesion. There can be other important factors and especially with inorganic systems such as metals, where intrinsic passivated oxide layers can provide for a biocompatible interface and result in positive adhesion properties for surface-cell interactions [Allain Ch. 2 Nanostructured Biointerfaces book]. With respect to these studies, no changes in adhesion in nanostructured Ti6Al4V would be expected with irradiation from surface free energy arguments. Interestingly, these results of unaltered contact angle after irradiation are consistent with that observed by Riedel et al. [48, 49], in which they performed normal Ar+etching of Ti6Al4V. The goal with these studies was to engineer surfaces on Ti6Al4V that could improve mesenchymal stem cell (MSC)-material interaction properties. The work by Riedel et al. demonstrated an overall improvement in performance of MSC interaction, though not dramatic, after ion-induced nanopatterning of the Ti alloy surfaces. The implications of these results compared to the work presented here will be discussed below.
Therefore, by considering the parameters that determine free surface energy, this unaltered contact angle results can be explained as follows: the fact that contact angle basically is unaffected due to DIS, would indicate that both experimentally observed surface nano-structure and any potential surface chemistry change are not influencing surface energy; with respect to other influencing factors like crystalline system and defects, crystallographic orientation and residual stress, are weakly affected by DIS.
Cytotoxicity assessment of samples modified by IBS consisted of in-vitro MTT colorimetric tests (see
Regarding the influence of DIS surface modification of Ti6Al4V on cell/surface interactions features, all of them are included in
Cell morphology in contact with surfaces obtained after normal irradiation incidence showed a clear influence induced by irradiation treatment. With respect to untreated surfaces (see
A comparison between structural nano-features for normal incidence and cell morphology details (higher-magnification), allow us to point out that non-uniform distribution of nano-filopodia is due to non-uniformity of those structural nano-features (some incipient nano-ripples). Also due to the partial nano-patterning obtained with normal incidence, it is difficult to establish any relationship, from both micro and nano-scales points of view. In addition, consistent with improved adhesion, HASMCs exhibited enhanced morphology on the normal irradiated Ti6Al4V compared to a polished untreated surface.
In earlier work by Riedel et al. osteoblast cultures on irradiated Ti6Al4V samples after normal incidence with Ar+[48, 49] did not result in a measurable change in cell morphology as evidenced in the work here. In addition, it was not clear if any improvement of cells attachment was observed, contrary to the current results shown in
After Ti6Al4V sample irradiation with 300 incidence angle, cell morphology kept basically the same trend as per normal incidence set of samples. All parameters previously observed from lowest magnification (lower-X) to highest magnification (higher-X) exhibited a growing tendency: increased lamellipodia activity, important increment of nano-filopodia, a highest spreading of cells, a better attachment, a better interaction between cells, and a whole better interaction with the nano-patterned surface. From nano-scale point of view, it was even easier to observe the improvements of cells/nano-structures interactions. Especially important are both the increment of number of nano-filopodia and the preferential site of binding with the surface; this latter result was typically observed in the grey phase of the surface (α-phase), which is predominantly nano-patterned in both nano-ripples and nano-rods. Interestingly, those nano-filopodia preferred to have nano-rippled grains as attachment sites, which could be related with high free surface energy available there for interactions and final binding. In this context, we can state at this point qualitatively that the more nano-ripples, the more nano-filopodia and, most likely, the better cell interactions and attachment to the bioactive surface (see
Per definition, above increased presence of filopodia can be assumed as an important indicative of potential tissue growth of the cells in contact with the studied surfaces [55]: filopodia are temporary projections of cells membranes, and they extend and contract by the reversible assembly of actin subunits into microfilaments; it is supposed that actin polymerization is at the origin of the force propelling the cell forward. Within the same mechanism, the cell surface projects a membrane process called the lamellipodium, which is supported inside by filaments that form at the leading edge, turning into networks as they blend together. The functions of filopodia include locomotion and the capturing of nutrients. Therefore, besides all evident mechanical advantages related to filopodia, their higher number would indicate a highest actin activity and, therefore, higher mobility, and also higher capability to engulf nutrients. Indeed, in conjunction with lamellipodium activity, they indicate strong stability and interaction with surface and whole biological environment. Global cell behavior here observed indicates that untreated Ti6Al4V surfaces exhibit a clearly less adhesive force. The high dorsal activity of cells attached to DIS surfaces is also an indicator of the active state of cell phenotype development that is, at the same time, an indicator of a better differentiation response of HASMCs.
Cells morphology on surface with 60° of incidence angle exhibited similar results from both micro and nano-scales points of view (see
Cells/surface interactions for 800 incidence angle, for which we are completely within erosive regime, micro and nano-scale features seem to indicate that positive interactions with surface show a tendency to decrease (see
Results obtained here about improvements of cells/surface interactions due to DIS nano-patterning of Ti6Al4V can be considered in agreement with several previous efforts about study of interactions with different kind of cells with surface nano-structures obtained by other advanced techniques [3-11]; however, results reported here are new in the sense that is the first time is shown a real relationship between ion irradiation nano-structure and some micro and nano-scale parameters of cells; they are related not only with their behavior and adhesion, but also with their further potential to stimulate tissue growth.
The influence of surface nano-structures on cells behavior has been studied by using many surfaces and cell types, such as MSC osteoblasts, fibroblasts, and some others [2]; the goal of nanostructures is to mimic the in vivo environment for cell growth and proliferation. As it can be easily verified in those works, most of those studies tried about influence of regular, periodic, nano-patterns on different aspects of cells behavior. A variety of patterns ranging from topographical to chemical have been shown to have an effect on cell adhesion, proliferation, alignment and gene expression, demonstrating that the nano-scale of the surface plays a role in determining cell behavior. Several works have shown that integrin-ligand binding is followed by the formation of focal adhesions and actin stress fibers that enhance and strengthen the cell adhesion to the surface by the recruitment of additional proteins such as the focal adhesion kinase or FAK [56]. These findings are related to relevance of filopodia presence in contact with a nano-patterned surface with respect to potential stimulus for tissue growth. A well-spread morphology, similar to that observed (see
Finally, from a comparison of the technique implemented here of Ar+ions irradiation, as well as with surface nano-structures and the interactions with HASMCs, with some above reported results, we must remark the following before to get some final conclusions: 1. Our results are consistent with those reported improvements of cells response in contact with nano-patterned surfaces; that is reflected in observed increment of filopodia activity due to interactions with surfaces here developed. This is even more important, because of the straight relationship between filopodia and actin activity, with a potential of these attached cells for stimulation of further tissue growth; 2. This is the first work in which is detailed analyzed relationships between incidence angle and nano-patterning of Ti6Al4V, as well as with cells changes on those surfaces, from micro and nan-scale levels; 3. In contrast to those methodologies of surface nano-patterning used in those previous works (mostly limited to create regular-periodic and restricted patterns), DIS technology exposed here offers unique advantages like massive surface transformation by self-organized atoms mechanisms, produced in a few seconds of irradiation, with the potential to control also any desired surface chemistry; this features become it in an advanced process far away to be the same as conventional ion etching or bombardment.
The study performed here about different nano-patterns of Ti6Al4V obtained by DIS with Ar+ with different incident angles, and their interactions with HASMCs, has allowed us to draw the following conclusions about their potential for tissue growth stimulation:
1. All incidence angles joined with rest of DIS parameters used for surface treatment by DIS of Ti6Al4V were able to produce certain surface nano-pattern, which followed three regimes depending of controlling mechanisms to produce those nano-structures: 1. Diffusive regime (normal and close to normal incidences): this was characterized by generation of incipient colonies of nano-ripples, which can be also assumed as nano-cracks colonies; these colonies are the consequence of slightly happening of a diffusive mechanism; 2. Mixed regime, diffusive+erosive (closely normal incidence up to approximately 600): erosive mechanism becomes more important as the incidence angle is increased; in consequence, it is obtained a mixed nano-structure, nano-ripples and nano-rods, in which proportion of nano-rods due to erosive regime is incrementally higher as the angle is increased; 3. Erosive regime (incidence angles of 800 and higher): prevalence of this mechanism is reflected in the predominant obtained nano-pattern of straight long nano-rods, which also appears very narrow and highly packed. The presence of these different nano-patterns attributed to those different regimes, can be assumed as an indicator of validity of the Bradley-Harper model for DIS conditions used to irradiate Ti6Al4V.
2. Both crystalline phases and crystallographic orientation of alloy grains were determinant for final nano-structure and its orientation, for each incidence angle. During diffusive and diffusive erosive regimes (0 to 60 angles), alpha-phase (hcp) grains were basically the only ones that responded to nano-structuring to DIS. Orientation of both nano-ripples and nano-rods within these grains exhibited different directions due to different crystallographic orientations of them. In contrast, during complete erosive regime (angles >80) both kinds of grains (hcp and bcc) responded in a similar manner, generating those mentioned long straight nano-rods. This crystal insensitive nano-patterning can be attributed to severe controlled damage produced during erosive regime.
3. Analysis of biological response of above DIS surfaces in contact with HASMCs showed important influence of the different nano-patterns obtained, with respect to fundamental parameters of cellular behavior. Firstly, interactions between HASMCs and the nano-patterned surfaces exhibited overall improvement of cells behavior reflected in a high cytocompatibility response, besides highest positive parameters with respect to untreated surfaces: higher surface dorsal activity (lamellipodiums); higher cytoplasm prolongations (filopodia), higher interactions between cells, and mostly a reduced vertical gap between cells and the surface, as well as high spread cells shape, and better interactions with surface nano-features; all reflected in a whole better cells attachment. However, a detailed analysis of surface nano-features influence on cells response allowed us to observe a real consistency with surface nano-patterns obtained with different angles, different regimes, especially with respect to filopodia activity: despite all irradiated angles used were able to produce important number of filopodia, the detailed analysis allowed us to establish that curved nano-ripples were the better features to stimulate presence of filopodia. In that sense, as long as the regime allow to obtaining those nano-ripples, it was evident increasing filopodia activity. Therefore, filopodia increase up to approximately 60° incidence; then, it seems to become stable and even start to decrease at an approximate 80° incidence angle. This filopodia response would indicate that their presence is directly related with prevalence of diffusive regime and, therefore, optimum angle for their presence would be between 30° and 60° incidence angles.
4. Despite evaluation of potential stimulation of tissue growth due to these nano-patterned Ti6Al4V surfaces requires further and more detailed studies, criteria of filopodia existence as indicator of potential stimulus for tissue growing can be assumed as a valid one. Per definition, filopodia consists of temporary projections of cells membranes, and they extend and contract by the reversible assembly of actin subunits into microfilaments. The functions of filopodia include locomotion and the capturing of nutrients. Within this context, besides all evident mechanical advantages related to filopodia, their higher number would indicate highest actin activity and, therefore, higher mobility, and also higher capability to engulf nutrients. Indeed, in conjunction with lamellipodium, they indicate strong stability and interaction with surface and whole biological environment. The high dorsal activity of cells attached to DIS surfaces is also an indicator of the active state of cell phenotype development that is, at the same time, an indicator of a better differentiation response of HASMCs.
5. Our work reported here has allowed us to establish, for the first time, different phenomenological relationships between incidence angle, nano-structures, and cells adhesion, which have been illustrated through using some new maps and master diagrams schemes. These phenomenological trends allowed us to have a new semi-quantitative tool for predictions of HASMCs response in terms of processing and surface properties, which will be an important insight for the current work in which our group in involved about developing of new multifunctional surface by DIS for proper cells stimulation for further tissue growth and repair.
6. The most important result here is that specific phenotypic behavior can be correlated to the ion-irradiation induced type of pattern morphology. In the work by Riebel et al. the irradiation-induced patterns in Ti-based alloys did not lead to a significant effect on cell-surface interaction for mesenchymal cells although cell spreading was evidenced. However, in our work nearly identical irradiation treatment of the same Ti-based alloy results in significant effects on cellular behavior (in this case endothelial cells types) even though no apparent changes are made to the contact angle properties in either experiment. This is consistent with the hypothesis that cell spreading is correlated to both a cell's ability to spread based on its phenotypic behavior and the elasto-mechanical interactions with protrusions from 2D surfaces.
The following is a description of some aspects of the method to generate the compositions of matter and surfaces along with specific functions elicited by the same. A conceptual connection to the surface to be claimed can be illustrated as in Scheme 1:
The wide scope and variety of surface structures can be synthesized by either DIS or DPNS, depending on desired function or exemplary embodiments of structure and function. For example, to elicit an immune-modulated response for macrophage phenotype that have anti-inflammatory osseoconductive properties, an exemplary embodiment of these structures would be made of medical-grade Ti alloy exposed to a particular fluence, angle of incidence, energy and species in the energetic particle beams from either DIS or DPNS methods. We organize by surfaces having structures defined with: topography, microstructure and surface composition.
1. Nanotopography:
Based on the different experimental parameters, an array of different nanostructures can be induced. The nanostructures were obtained as function of energetic particle species, fluence and incident angle with respect to the surface normal. For reasons of organization structures are organized by principal particle-beam gas species.
Microstructure needs to be defined in anatase and rutile phases.
1.1 Parameter: Gas (Kr)
a) Parallel Nano-walls (Kr): an array of (parallel) wall like structures having a height of 3 to 250 nm, with a length ranging from 10 to 40 nm, said ridge composed primarily of titanium alloy (
b) Nano-cones (Kr): Structures which resemble sharp-like cones. These pointed sharp regions are inclined towards the incident beam direction (
c) Nano-ripples (Kr): In the midst of nano-pillar and nano-cones, we also observe nanoripples as shown in
1.2 Parameter: Gas (Ar)
a) Nano-walls (Ar): An array of (parallel) wall like structures having a height of 3 to 100 nm, with a length ranging from 10 to 40 nm, said ridge composed primarily of titanium alloy (
b) Nano-cones (Ar): Structures which resemble sharpe-like cones. These pointed sharp regions are inclined towards the incident beam direction (
Round-plate formation (Ar): The structures resemble round plate formation (
1.3 Parameter: Fluence 7.5×1017 cgs (Ar)
a) Nano-walls (Ar): An array of (parallel) long and short wall like structures having a height of 3 to 100 nm preferably, with a length ranging from 10 to 40 nm, said ridge composed primarily of titanium alloy (
b) Nano-cones (Ar): Structures consist of very narrow and wide cones (
1.4 Parameter: Fluence 5×1017 cgs (Ar)
a) Nano-walls (Ar): An array of (parallel) long and short wall like structures having a height of 3 to 100 nm preferably, with a length ranging from 10 to 40 nm, said ridge composed primarily of titanium alloy (
b) Nano-cones (Ar): Structures consist of very narrow and wide cones (
1.5 Parameter: Fluence 2.5×1017 cgs (Ar)
a) Nano-walls (Ar): The surface consists of smooth and nanostructured surface composed primarily of titanium alloy (
b) Nano-cones (Ar): The surface consists of smooth and nanostructured surface. Structures consist of very narrow and wide cones (
1.6 Parameter: Fluence 1×1017 cgs (Ar)
a) Nano-walls (Ar): The surface consists of fine nanostructures which are seen at specific regions on the surface. Due to their fine nature we cannot measure their dimensions. These structures are composed primarily of titanium alloy (
b) Nano-cones (Ar): Structures consist of cones which are non-uniform on the surface (
1.7 Angles 0° to 80° (Ar)
Surface structural modifications and nanostructuring due to DIS of Ti6Al4V are summarized in
In
At the highest incident angle (e.g. 80° incidence), a new trend in the resulting nano-pattern is obtained (see
2. Crystallographic structure:
Considering the microstructure of unirradiated Ti6Al4V samples after proper etching procedures, one can observe a conventional α+β mill-annealed alloy (see
Intrinsic to the DIS modification is its ability to only modify the first few 100's of nm and therefore not affect the optimized mechanical properties mentioned described above. The first observation relates to the effect normal incidence has on the modified surface. At normal incidence an organized dot-like structure formed alongside “broken” nanoscale ripples on the original grains is observed. Comparison with the original surface microstructure, the self-organized dot-like structures appear concentrated in the a phase (grains and Widmanstatten plates), whilst the more irregular damage seems to be preferentially located within P phase matrix. Furthermore, the nanostructures at normal incidence appear to have some preferential growth depending on grain orientation. However, normal incidence and low energy processes in some types of materials (e.g. Si) have resulted in the smoothening of the surface. Evidence for a resistance to patterning is found in the normal incidence case as well as more oblique angles for certain grains. This could be evidence of a balance between mass redistribution mechanisms that drive adatoms on the surface to recombine with irradiation-driven surface vacancies leading to smooth surfaces. The fact that smooth surfaces only occur under certain grain orientations suggests that there is also a structure-driven relaxation mechanism coupled to the irradiation-driven mechanisms that lead to self-organized nanostructures. At normal incidence, the features produced by ion sputtering reflect the surface symmetry and are aligned along energy preferred crystallographic orientation and enhanced surface recombination, which can lead to partial nano-dot and nano-ripple formation or in some cases complete smoothening of the surface. Comparing to this work we find resistance to nanopatterning along specific grain orientation or microstructure phases.
Moreover, we discovered this morphological trend with incident ion-beam angle is dominant for the α-phase in the Ti6Al4V alloy meanwhile for the P (bcc) phase appears insensitive to this trend. The interaction and competition between the two mechanisms discussed above induces pattern formation observed in
In
3. Surface Chemistry:
3.1 Parameter: Fluence 1×1018 cgs (Ar)_02
The survey scans for Ti alloy samples treated with a fluence of 1×1018 cgs for Ar irradiation at 60° is displayed in
3.3 Parameter: Fluence 7.5×1017 cgs (Ar)_10
The survey scans for Ti alloy samples treated with a fluence of 7.5×1017 cgs for Ar irradiation at 60° is displayed in
3.4 Parameter: Fluence 5×1017 cgs (Ar)_09
The survey scans for Ti alloy samples treated with a fluence of 5×1017 cgs for Ar irradiation at 60° is displayed in
3.5 Parameter: Fluence 2.5×1017 cgs (Ar)_08
The survey scans for Ti alloy samples treated with a fluence of 2.5×1017 cgs for Ar irradiation at 60° is displayed in
3.6 Parameter: Fluence 1×1017 cgs (Ar)_07
The survey scans for Ti alloy samples treated with a fluence of 1×1017 cgs for Ar irradiation at 600 is displayed in
Described a modified powder metallurgy (PM) porous cpTi (commercially-pure) material that is transformed by directed plasma nanosynthesis (DPNS) with the aim to provide three primary bioactive functions: a) enhanced soft tissue and bone tissue integration, b) anti-bacterial interfaces and c) ultra-hydrophilic properties within porous structures enabling enhanced protein and drug adhesion. We demonstrate the nano-structuring capability of DPNS on intra-porous and inter-porous surfaces without any detrimental effect on the original biocompatibility of porous cpTi.
The provided materials are designed for integration with bone or soft tissue (e.g. ligament, tendon, vascular, gum, etc. . . . ). The degree of tissue integration is dependent on the nanostructure design in-between pores and within pores of cpTi. In some embodiments, the invention provides methods capable of inducing nanostructure formation within and between Ti-based nano to microscale pores. Porosity serves two purposes: 1) to provide anchors for cell adhesion and 2) to provide protein/drug payload delivery. Control of surface chemistry and porosity is important in many biomedical application areas including: biosensors, drug delivery, tissue engineering, cell culturing and wound healing. Most methods to control porosity and surface chemistry is limited by chemical-based processes that when produced at industrial scales translate in significant toxic waste, which can result in about 30-40% of total fabrication costs. This has the potential to disrupt this cost by providing for a non-chemical method of fabrication with DPNS providing for nanostructure control of surfaces within and in-between pores. The application for this nanostructured porous cpTi material include: joint replacements, hip and shoulder fractures, dental implants, and bone diseases related like osteoporosis and cancer.
Most current clinical treatments for bone tissue regeneration correspond to tissue substitution, i.e. replacement approach for which the biomaterials are both biocompatible and bioactive. Although there have been some clinical successes with conventional materials, several failure statistics of current joint replacements indicate that are challenged by the bioinert nature of most of these materials including Ti-based biomaterials. Some medical grade titanium (Ti) alloys, like commercially pure Ti (cpTi), have proved to be the best biomaterials for clinical success of bone replacement due to its excellent balance between biomechanical and in vivo biocompatibility. However, cpTi exhibits the following disadvantages that are direct consequences of being a 1st generation biomaterial: 1) Biomechanical incompatibility reflected in the elastic mismatch with respect to hosting tissue, and the consequent bone resorption around the implants; 2) Being bio-inert, cpTi implants are surrounded by a thin fibrous tissue, which can often reduce osseointegration with an associated risk of loosening or fracture of bone and/or implant; improvement of the biointerface is necessary to avoid the existence of the fibrous tissue or to reduce the loosening risks due to its presence.
In regards to first problem, it is desirable to design new implants and prostheses with a lower stiffness than those currently used, which would allow the stress-shielding problem to be solved or reduced without any significant detrimental effect on mechanical strength. Several reported studies have dedicated to development of new implants with a bone-matching modulus, such as porous materials; to that end, there are some manufacturing processes, among which include: the electron beam melting process, creep expansion of argon-filled pores, directional aqueous freeze casting, rapid prototyping techniques, laser-engineered net shaping, electric current activated/assisted sintering techniques, conventional and non-conventional powder metallurgy (PM) and space-holder techniques. From a conventional PM point of view, controlling compacting pressure, sintering temperature and time, could help reach a suitable porosity to reduce stress shielding. Improvement of bone ingrowth and osseointegration requires that pores size and morphology be controlled, especially in the surface, which is also important for the fatigue resistance of the implant. In regards to non-conventional PM alternatives for stress-shielding reduction, loose sintering process, without compaction pressure, has emerged as an attractive route to produce porous Ti implants with a high porosity, with the aim of successfully replacing cancellous bone with an extraordinary low Young's modulus of around 0.5 to 1 GPa. To that end, we have recently published a detailed comparison between space-holder and loose sintering techniques, in which they were able to properly optimize a suitable mechanical balance for a Ti implant for highly porous bones.
In regards to alternative biomaterials to minimize and/or avoid fibrous tissue formation and lack of osseointegration, they are basically based on modifications of topographical and/or chemical properties of cpTi surfaces. Surface nanostructuring of conventional biomaterials has emerged as one of the most important and effective manners to convert them in advanced biomaterials; this is the consequence of nano-features capability to effectively have some influence on surrounding biological environment at molecular nano-scale level. Since the cells in their natural environment are surrounded by nanoscale features linked to their extracellular matrix (ECM), the nanotopographical parameters become an important part in design of biomaterials for tissue formation and repair. Accordingly, several studies suggest that a remarkably small modification in surface nanotopography could result in mesenchymal stem cell growth and development, indicating that changes in such nanotopographical features had a direct influence in the adhesion/tension balance to permit self-renewal or targeted differentiation. Biointerface topography and, in particular, nanoscale features can affect cell behavior and integrin-mediated cell adhesion, and is now evident from studies with fabricated topographical features. The processes that mediate the cellular reaction with nanoscale surface structures are not well understood and may be addressed; a direct result of the influence of the surface topography, or even indirect one, when the surface structure affects the composition, orientation, or conformation of the adsorbed ECM components.
The drawbacks of conventional nano-patterning techniques have mainly been attributed to their physical limitations in fabricating structures smaller than about 50-nm. Therefore, bottom-up techniques that rely on self-assembly, self-organization, and local patterning, have become technologies capable of pattern biocompatible surface nanostructures. Irradiation-driven systems have been explored in moderate energy regimes dominated by knock-on atom displacement regimes for semiconductor metallization microstructure control, engineering of nanostructured carbon, and compositional patterning of immiscible alloys. Directed plasma nanosynthesis (DPNS) introduces a synthesis process that is scalable to high-volume manufacturing by virtue of its intrinsic large-area simultaneous exposure of materials surfaces and interfaces.
There are no reported works on ion and plasma-induced irradiation nano-patterning with intra-porous and inter-porous surface modification of porous Ti with applications to cell stimulation and tissue growth. The methodology with DPNS can target specific regions in, around and in-between pores that enable specific tailored functionalities from drug delivery to soft issue integration enabling a highly versatile and tunable biomaterial for advanced biosensing and protein/drug adhesion/delivery applications.
Provided is a new biomaterial that introduced multiple functions to porous cpTi-based biomaterials. Also provided is a method or process of fabrication using DPNS to induce nanostructures in-between and inside pores. This process not only introduces nanostructuring as described above but also can refine pore size.
Described is a process and arrangement to generate patterned structures and unique topography at the nanoscale in-between and inside pores while eliminating the shortcomings of conventional chemical-based approaches. Besides reducing significantly toxic chemical waste processes the use of DPNS on nanostructuring porous cpTi biomaterials avoids costly high-temperature cycles necessary in conventional surface modification techniques.
Structural characterization of as-received (AR) and DPNS-treated cpTi samples
Surface structural modifications and nano-structuring due to DPNS of porous cpTi samples are summarized in
Nano-structuring of porous cpTi samples depicted in
AFM analysis has allowed us a to quantify the surface features due to DPNS on porous rough cpTi (see
Surface Free Energy Evaluation of as-Received (AR) and DPNS-Treated cpTi Samples
The wettability is fundamental for the cellular adhesion and, consequently, for the success of osseointegration and bone tissue growth, since the blood is the first tissue that reaches the implant, and 90% of its plasma is composed by water, the evaluation of the surface wettability can be accomplished through the determination of contact angle. The contact angle measurements after irradiation of porous cpTi samples reflected an important change with respect to control one (see Table 13); both kind of porous samples (lowest and highest porosity) showed important reduction of contact angle (reduced hydrophobicity) after Ar+irradiation with 60° incidence angle. In case of lowest surface porosity, contact angle was of 13.45±4.51 (reduction of 74.64%), and for highest porosity the contact angle was of 28.15±5.21 (reduction of 46.92%). It is important to notice that those reduced values of contact angle after DPNS were obtained despite the initial porosity of samples and the initial roughness of rough samples as well. Despite there are reported some works about influence of ion irradiation on contact angle, this is the first time that such a reduction is reported due to off-normal Ar+incidence on Ti.
Biological Assessment of as-Received (AR) and DPNS-Treated cpTi Samples
As it is well recognized from biological response of biomaterials surfaces, free surface energy of biomaterials reflected in their contact angle values plays a determinant role in the biological environment response. By considering the effect of multiple surface properties in contact angle results, here we can establish important relationships with surface modifications due to ion irradiation processing of cpTi surfaces. In that context, osseointegration is one of the good examples in which, besides the roughness, the surface tension is a parameter that interferes on it. It permits a higher or smaller scattering of liquid onto the metallic surface. The human blood contains about 90% of water, thus the capability of water adsorption by the surface, known like wettability, is a fundamental parameter to the success of cellular adhesion and, consequently, to the osseointegration. It is commonly accepted that blood compatibility is improved when the hydrophilicity of a surface is increased (unless the surfaces are superhydrophobic).
Cytotoxicity assessment of irradiated samples was performed via Comet Assay@ testing, in search of evaluating the potential geno-toxicological effect in vitro on human aortic smooth muscle cells (HASMCs) cultured in the presence of the evaluated specimens.
Biocompatibility is, at least, equal to well-known biocompatibility of conventional bio-inert cpTi surface; with respect to cell behavior parameters, by considering our improvements in nano-structuring, roughness parameters and contact angle, we can reasonably expect that cells factors like adhesion, proliferation, migration, and differentiation will be also improved with the surfaces obtained here. However, it is important to point out at this moment that our results reported here are new in the sense that is the first time is shown relationships between initial surface micro-topography of porous cpTi, irradiation conditions, surface nano-structure, roughness, surface free energy and basic biocompatibility assessment; they are related not only with their behavior and adhesion, but also with their further potential to stimulate tissue growth.
DPNS of Porous and Rough cpTi Samples.
Experiments were performed at Radiation Surface Science and Engineering Laboratory (RSSEL) at the University of Illinois at Urbana Champaign, which is originally developed and designed by Prof. Jean Paul Allain (
Manufacturing of Porous cpTi Samples
The powder of cpTi (SE-JONG Materials Co. Ltd., Korea) used for the blends was manufactured by a hydrogenation/dehydrogenation process. The particle size distribution corresponded to 10, 50 and 90% passing percentages, of 9.7, 23.3 and 48.4 μm, respectively. The chemical composition of the powder used was equivalent to cpTi Grade IV according to the ASTM F67-00 Standard. CpTi has an apparent density of 1.30±0.01 g/cm3 (28.8±0.1%) and a tap density of 1.77±0.04 g/cm3 (39.2±0.8%). The blends of cpTi powder were prepared using a Turbula® T2C blender for 40 min to ensure good homogenization. In order to address irradiation influence on porous cpTi samples with different porosities, here we are comparing the loose sintering technique (without any compaction pressure) with the conventional PM one via a low compaction pressure. The compacting step was carried out using an Instron 5505 universal machine to apply the pressure used of 100 MPa. The compacting loading rate was 6 kN/s, dwelling time was 2 min and unloading time was 15 s for decreasing load up to 150 N. The sintering process was performed in a Carbolyte® STF 15/75/450 ceramic furnace with a horizontal tube at 1250° C. for 2 h using high vacuum (=5×105 mbar). Diameter of compaction die (8 mm) and powder mass were selected to obtain samples in which the effect of compaction pressure was minimized. Structural and surface free energy characterization of cpTi samples modified by DPNS
Surface free energy of irradiated samples was evaluated by contact angle testing with deionized water through a Rame-Hart Goniometer Model 500-Advanced contact angle goniomter/tensiometer with DROPimage Advanced Software. We performed the sessile method of contact angle analysis (where the sample was static and not moving after the drop was placed on it). All measurements were performed with deionized water (to not have any type of interaction with the surface). The water dropper was far enough away from the surface that the water did not touch the sample until it left the dropper. The dropper was kept at the same distance from each sample surface. The water droplets had ˜3 μL of water on each sample. Morphological features of samples were detailed analyzed by Scanning Electron Microscopy, SEM (Philips XL40 field emission, FEI, Hillsboro, Oreg., USA). Atomic force microscopy (AFM) was also used for detailed morphological and topographical characterization of irradiated cpTi surfaces, by using an AFM Veeco Dimension 3000 (Santa Barbara, Ca) on AC Mode using cantilever Bruker DNP-10. The scanned area was 1 μm square over samples of both titanium rough and porous samples.
Biological Evaluation of cpTi Samples Modified by DPNS.
The cells used for biological assessment of treated and un-treated samples were human aortic smooth muscle cells (HASMCs, Lifetechnology Cat # C0075C). To that end, cells morphology changes with culture time, and cytotoxicity assays test on modified surfaces via Comet Assay® testing, were performed. Changes in cells morphology in terms of culture time was observed by using optical microscopy (OM) analysis. The cell line used was the choose model to validate the potential for tissue growth and regeneration of the new surfaces. Cells were grown at 37° C. with >95% Rh and CO2 gas exchange until they were nearly confluent. HASMCs were seeded on the top of the samples for 24 hours under normal culturing conditions (37° C., 95% air, 5% C02, 95% humidity). HASMCs with a cellular density of 5×103 live cells per cm2, and viability of 86% were cultured in a 7 well tissue culture dish in the presence of the analytes. Two samples labeled as NegCtl and PosCtl corresponded to cells growing alone and used as controls in the assay. All the samples were incubated under normal culturing conditions (37.0° C., 95% air, 5% C02, 95% humidity) for 24 hours. Then, after 48 hours, visual inspection of HASMCs growing in the presence of the tested analytes was performed during the incubation period under bright field illumination utilizing a Nikon inverted Diaphot fluorescent microscope with 1× and 20× objectives (Nikon Instruments, Melville, N.Y.). The Comet Assay® was carried out according to manufacturer's recommendations (cat. #4250-050-K, Trevigen, Inc., Gaithersburg, Md.). Finally, all the experimental measurements are presented as the mean+standard derivation, which were analyzed using Origin Pro 8.6. One-way ANOVA was performed to compare the mean of the samples, and at the 0.05 level, the population means were considered to be significantly different.
Based on the different experimental parameters, an array of different nanostructures can be induced on porous Ti. The nanostructures were obtained as function of angles and energy. Using directed irradiated synthesis, along with the surface these nanostructures can also be grown inside pores as well as along the pore walls
Fluence (cm−2)=1.00E+18
Energy (eV)=1000
Surface Nano-walls (Ar): An array of (parallel) wall like structures having a height of 10 to 100 nm preferably, with a length ranging from 10 to 40 nm, said ridge composed primarily of Ti (
Inside Pore Nano-walls (Ar): Inside the pores, an array of (parallel) wall like structures having a height of 10 to 100 nm preferably, with a length ranging from 10 to 40 nm, said ridge composed primarily of Ti (
Walls of Pore Nano-walls (Ar): Along the walls of pores, an array of (parallel) wall like structures having a height of 3 to 100 nm preferably, with a length ranging from 10 to 40 nm, said ridge composed primarily of porous Ti (
Tilted view of surface Nano-walls (Ar): When the sample is tilted at a particular angle under scanning electron microscope, an array of (parallel) wall like structures having a height of 10 to 100 nm preferably, with a length ranging from 10 to 40 nm, said ridge composed primarily of porous Ti (
Fluence (cm−2)=1.00E+18
Energy (eV)=1000
Surface Nano-walls and nano-cones (Ar): On the surface, we observe 2 different kind of nanostructures: 1) an array of (parallel) wall like structures having a height of 3 to 100 nm preferably, with a length ranging from 10 to 40 nm, said ridge composed primarily of Ti (
Pore Nano-walls and nano-cones (Ar): Inside the pores, we observe nano walls as well sharp nanocones. Nano-walls: an array of (parallel) wall like structures having a height of 10 to 100 nm preferably, with a length ranging from 10 to 40 nm. Nano cones: The dimension of these cones are in the range of 2 to 50 nm preferably, with a length ranging from 10 to 40 nm said ridge composed primarily of porous Ti (
Tilted view of surface Nano-walls and nano-cones (Ar): When the sample is titled under the scanning electron microscope, an array of (parallel) wall like structures having a height of 3 to 100 nm preferably, with a length ranging from 10 to 40 nm, said ridge composed primarily of Ti (
3. Sample: 50% Ti_Ar_07
Fluence (cm−2)=1.00E+18
Energy (eV)=500
Surface nano-walls and nano-cones (Ar): At incidence energy of 500 eV, we see small nano cones and nano walls. The dimension of nano cones are in the range of 2 to 50 nm preferably, with a length ranging from 2 to 40 nm. In case of nano walls an array of (parallel) wall like structures having a height of 3 to 50 nm preferably, with a length ranging from 10 to 40 nm, said ridge composed primarily of Ti. Such structures are formed using following DIS parameters—Gas: Ar, Angle: 60°, Energy: 500 eV, Fluence: 1×1018 cgs (See
Fluence (cm−2)=1.00E+18
Energy (eV)=750
Surface Nano-cones (Ar): Structures which resemble like sharp cones. These pointed sharp regions are inclined towards the incident beam direction (
Pore Nano-cones (Ar): Inside the pores, nano cones can seen with dimensions of height of 3 to 100 nm preferably, with a length ranging from 10 to 40 nm, said ridge composed primarily of Ti (
Fluence (cm−2)=1.00E+18
Energy (eV)=1000
Surface Nano-walls (Ar): An array of (parallel) wall like structures having a height of 3 to 60 nm preferably, with a length ranging from 10 to 40 nm, said ridge composed primarily of Ti (
Pore Nano-walls (Ar): an array of (parallel) wall like structures having a height of 3 to 100 nm preferably, with a length ranging from 10 to 40 nm, said ridge composed primarily of Ti (
Wall of Pore Nano-walls (Ar): an array of (parallel) wall like structures having a height of 3 to 100 nm preferably, with a length ranging from 10 to 40 nm, said ridge composed primarily of porous Ti (
Fluence (cm−2)=1.00E+18
Energy (eV)=1000
Surface Nano-walls and nano-cones (Ar): On the surface, we observe 2 different kind of nanostructures: 1) an array of (parallel) wall like structures having a height of 3 to 100 nm preferably, with a length ranging from 10 to 40 nm, said ridge composed primarily of Ti (
Preliminary biological assessment by Comet Assay® testing of porous cpTi irradiated samples has shown that Ar+ions beams has no toxicological detrimental effect on initial biocompatible surface. HASMCs morphology behavior in contact modified surface, and in terms of time, also suggests that these new surfaces will in fact improve in Vivo tissue stimulation. This can be stated from the consistency with several previous results, as well as because those important improvements observed on surface nano-structuring, controlled roughness and reduced free surface energy. In summary, phenomenological relationships and trends determined here allowed us to have a new insight about positive influence of Ar+irradiation on porous cpTi surfaces in order to not only improve osseointegration, but also to effectively promote bone tissue growth and repair.
Provided is both a method and material structure transformed by subject method to elicit specific bioactive surface functions. In this invention directed irradiation synthesis (DIS) is used combining a sequenced asymmetric ion-beam that can be combined with a thermal-particle beam to induce surface nanostructures on medical grade Ti6Al4V. The material structures are introduced and vary in morphology and topology. The nanostructure morphology and topology has a correlated dependence on the crystallographic grains of the Ti alloy material. The nanostructure morphology, surface chemistry and topology are controlled independently by incident angle, fluence, energy and species. The ratio of ion to thermal particle flux can also influence morphology and/or topology. The nanostructure morphology and surface morphology in turn can control cell shape directing desired cell lines into specific phenotype behavior. Three primary bioactive properties are induced: 1) cell shape, 2) cell adhesion and proliferation and 3) bactericidal and anti-bacterial physical surface structures. Thus there is an enhancement of cell integration in bone tissue, for example, with a more favorable healing time range. Combining these new properties with the favored intrinsic biomechanical properties of Ti-based alloys makes for a beneficial biomaterials system.
The provided compositions and methods have implications for tissue engineering in endovascular and bone integration applications including as an advanced biointerface for bone implants and stent materials for vascular reconstruction. Other applications include implants for spinal cord injury.
Titanium and its alloys is widely recognized to be the preferred biomaterial for bone replacement due to its excellent balance between biomechanical and biocompatibility response. However, titanium suffers from the intrinsic growth of a thin fibrous tissue interface.
By transforming the surface of Ti-based biomaterials implants can provide for fast tissue reconstruction by enhancing tissue integration in a time scale that prevents immune-system response to the foreign body biomaterial. Meaning that as a consequence of nanofeatures fabricated on the biomaterial in question it imparts the function to effectively influence surrounding biological environment at a molecular nanoscale level. Several studies demonstrated different morphology configurations at the nanoscale can have a strong and direct influence over cellular behavior; indeed, it is possible to appreciate that cells prefer texturized surfaces in comparison with smooth ones. Biointerface topography and, in particular, nanoscale features can affect cell behavior and integrin-mediated cell adhesion, and is now evident from studies with fabricated topographical features. The extent to which nanotopography influences cell behavior in-vitro remains unclear, and investigation on this phenomenon is still underway. The processes that mediate the cellular reaction with nanoscale surface structures are also not well understood. For example, it is not clear if this influence derives directly from surface topography, or perhaps indirectly with surface structures possibly affecting the composition, orientation, or conformation of the adsorbed ECM (extra-cellular matrix) components. However, current practice is to simply increase the surface roughness of an implant material in the effort to elicit a more favorable cellular response. The compositions and methods to fabricate the same enable a high-fidelity control of cellular behavior that would in principle influence such mechanisms as: cell proliferation, cell differentiation and cell adhesion and migration.
Directed irradiation synthesis (DIS) and directed plasma nanosynthesis (DPNS) address this limitation by introducing a synthesis process that is scalable to high-volume manufacturing by virtue of its intrinsic large-area simultaneous exposure of materials surfaces and interfaces. One subset of DIS is ion-beam sputtering (IBS) and is the methodology used in the work reported here. Advanced in-situ synthesis methods have been recently developed by Allain et al. to elucidate ion-irradiation mechanisms that can manipulate surface chemistry and surface morphology to ultimately synthesize functional coatings for 3D scaffold systems. We vary a limited number of parameters that introduce a specific morphology with a specific cell shape response as demonstrated with HASMC biological assay tests shown below.
A few papers have reported converting Ti into a third generation biomaterial, but few address the modification of Ti-based material surfaces for regenerative medicine applications. For example, the latest technologies involving Ti-based implant systems only address enhancements to the surface roughness or vaguely the surface chemistry but with very little control of either and certainly not of both independently. Most of them have shown improvements of cell adhesion due to interactions with nano-patterned surfaces, as regulators of cellular functions through focal adhesion. Results include: increased adhesion and formation of human mesenchymal stem cells, improvements of rat aortic endothelial cells adhesion on TiO2, upregulation of osteospecific proteins-osteopontin and osteocalcin of human osteoprogenitor cells cultured on Ti. However, nowhere in prior art is there a systematic independent high-fidelity (e.g. structure shape, size, sequence, extent) control of morphology and surface chemistry. This can only be achieved by processing with DIS and/or DPNS approaches pioneered in Prof. Allain's group.
Conventional processing of materials for surface nanostructuring has been dominated by the development of advanced top-down fabrication techniques that include lithography-based techniques. Some of them include focused-beam lithographies using electron or ion energetic particles and scanning probe lithographies. The drawbacks of these conventional techniques have mainly been attributed to their physical limitations in fabricating structures smaller than about 50-nm and also limited to the modification of a few classes of materials Prior art in surface processing is constrained to the use of these lithography-dependent patterning approaches that limits scalability and versatility, which drive industrial scalability strategies. One important limitation in current nanomanufacturing approaches is a dependence on naturally self-ordered processes that balance kinetic and thermodynamic dissipative forces in the absence of irradiation therefore requiring very high temperature processes. Consequently, many of the desired biomaterial properties that require a combination of metal alloy and soft material interfaces cannot be processed with conventional bottom-up techniques or techniques that rely on chemical processes to induce a surface variation.
Directed irradiation synthesis (DIS) and directed plasma nanosynthesis (DPNS) address this limitation by introducing a synthesis process that is scalable to high-volume manufacturing by virtue of its intrinsic large-area simultaneous exposure of materials surfaces and interfaces. One subset of DIS is ion-beam sputtering (IBS) and is the methodology used in the work reported here. Advanced in-situ synthesis methods have been recently developed by Allain et al. to elucidate ion-irradiation mechanisms that can manipulate surface chemistry and surface morphology to ultimately synthesize functional coatings for 3D scaffold systems.
Provided is a new process which produces different nanostructures such as: nanoripples and nanorods depending on the incidence angle of ions. The interactions between the cells and the nanopatterned surfaces exhibited overall improvement of cells behavior and in particular cell shape control and hydrophilic properties.
Further, described is an enhanced bioactive interface for Ti-based systems and a process and arrangement to generate patterned structures and unique topography at the nanoscale while eliminating the shortcomings of the prior approaches related to high-volume manufacturing resulting in a process that is scalable to by virtue of its intrinsic large-area simultaneous exposure of materials surfaces and interfaces. In a first embodiment, a method for fabricating structures on substrate having a substrate surface includes providing a set of control parameters to an ion beam source and thermal source corresponding to a desired nanostructure topology. The method also includes forming a plurality of nanostructures in a first surface area of the substrate by exposing the substrate surface to an ion beam from the ion beam source and thermal energy from the thermal source. The ion beam has a first area of effect on the substrate surface, and the thermal energy has a second area of effect on the substrate surface. Each of the first area and the second area includes the first surface area. In other words, the coincident beams under the set of control parameters produce a plurality of microstructures or nanostructures.
In particular, the technology as described in the present disclosure has important ramifications for biomaterials which are important for introducing design pathways tuning bioactive properties used in multiple applications for biocompatibility and bio-surface material adaptability.
DIS conditions of different cpTi samples appear summarized in Table 16 for systems where the fluence and incident particle energy is kept constant and the incident angle is varied.
Surface structural modifications and nano-structuring due to DIS of commercially pure titanium (cpTi) samples are summarized in
Variation of Incident Ion Particle Fluence
Although high-fidelity control of Ti-based nanostructures is already attained by varying the incident angle we also observe that varying the fluence will result in further control of surface morphology that can be tailored depending on the cellular response needed. Table 17 summarizes the reduced to practice parameters with “oblique incidence at 60-degrees”. In another application of this approach the significantly increased surface-to-volume area also enables the use for peptide attachment and biosensing properties.
Biological Assessment of as-Received (AR) and DIS Treated cpTi Samples
As it is well recognized from biological response of biomaterials surfaces, free surface energy of biomaterials reflected in their contact angle values plays a determinant role in the biological environment response. By considering the effect of multiple surface properties in contact angle results, here we can establish important relationships with surface modifications due to ion irradiation processing of cpTi surfaces. In that context, osseointegration is one of the good examples in which, besides the roughness, the surface tension is a parameter that interferes on it. It permits a higher or smaller scattering of liquid onto the metallic surface. The human blood contains about 90% of water, thus the capability of water adsorption by the surface, known like wettability, is a fundamental parameter to the success of cellular adhesion and, consequently, to the osseointegration. It is commonly accepted that blood compatibility is improved when the hydrophilicity of a surface is increased (unless the surfaces are superhydrophobic) (
Cytotoxicity assessment of irradiated samples was performed via Comet Assay® testing, in search of evaluating the potential geno-toxicological effect in vitro on human aortic smooth muscle cells (HASMCs) cultured in the presence of the evaluated specimens (
Biocompatibility is, at least, equal to well-known biocompatibility of conventional bio-inert cpTi surface; with respect to cell behavior parameters, by considering our improvements in nano-structuring, roughness parameters and contact angle, we can reasonably expect that cells factors like adhesion, proliferation, migration, and differentiation will be also improved with the surfaces obtained here. However, it is important to point out at this moment that our results reported here are new in the sense that is the first time is shown relationships between initial surface micro-topography of cpTi, irradiation conditions, surface nano-structure, roughness, surface free energy and basic biocompatibility assessment; they are related not only with their behavior and adhesion, but also with their further potential to stimulate tissue growth.
Directed irradiation synthesis (DIS) of porous and rough cpTi samples.
Grinding and polishing of cpTi samples were performed, before DIS processing. DIS experiments were performed at Radiation Surface Science and Engineering Laboratory (RSSEL) at the University of Illinois at Urbana Champaign, which is originally developed and set-up by Prof. Jean Paul Allain (
Structural and Surface Free Energy Characterization of cpTi Samples Modified by DIS.
Surface free energy of irradiated samples was evaluated by contact angle testing with deionized water through a Rame-Hart Goniometer Model 500-Advanced contact angle goniomter/tensiometer with DROPimage Advanced Software. We performed the sessile method of contact angle analysis (where the sample was static and not moving after the drop was placed on it). All measurements were performed with deionized water (to not have any type of interaction with the surface). The water dropper was far enough away from the surface that the water did not touch the sample until it left the dropper. The dropper was kept at the same distance from each sample surface. The water droplets had ˜3 μL of water on each sample. Morphological features of samples were detailed analyzed by Scanning Electron Microscopy (SEM).
Biological Evaluation of cpTi Samples Modified by DIS.
The cells used for biological assessment of treated and un-treated samples were human aortic smooth muscle cells (HASMCs, Lifetechnology Cat # C0075C). To that end, cells morphology changes with culture time, and cytotoxicity assays test on modified surfaces via Comet Assay@ testing, were performed. Changes in cells morphology in terms of culture time was observed by using optical microscopy (OM) analysis. The cell line used was the choose model to validate the potential for tissue growth and regeneration of the new surfaces. Cells were grown at 37° C. with >95% Rh and C02 gas exchange until they were nearly confluent. HASMCs were seeded on the top of the samples for 24 hours under normal culturing conditions (37° C., 95% air, 5% C02, 95% humidity).
Preliminary biological assessment by Comet Assay® testing of cpTi irradiated samples has shown that Ar+ions beams has no toxicological detrimental effect on initial biocompatible surface. HASMCs morphology behavior in contact modified surface, and in terms of time, also suggests that these new surfaces will in fact improve in vivo tissue stimulation. In summary, phenomenological relationships and trends determined here allowed us to have a new insight about positive influence of Ar+irradiation on both porous and rough cpTi surfaces in order to not only improve osseointegration, but also to effectively promote bone tissue growth and repair. Furthermore, DIS and DPNS exposures with other species such as Kr+, Ne+ and O2+ have also enabled the formation of specific nanostructures and chemistries pertinent to this invention. Cell adhesion, proliferation and cell-shape morphology have all responded with increased levels of activity by over 50% and some cases over 100%. More importantly, the tunability and high-fidelity modulation of the immuno response of macrophage phenotypes suggest enhanced osseointegration an osseoconduction.
Titanium is widely used to produce implants because direct contact occurs between bones and implant surfaces. Titanium has excellent biocompatibility, superior corrosion resistant as well as durable in physiologic mediums. Moreover, it is easily prepared in many different shapes and textures without affecting its biocompatibility. Despite these advantages, some problems of titanium in hard tissue applications are still controversial. The implant fixation to the bone remains an aspect to be improved through alternatives for reducing the stress-shielding phenomenon, which is a consequence of the mismatch between Young's modulus values (titanium is 110 GPa and cortical bone around 20-30 GPa); this difference has been identified as one of the major reasons for implant loosening and bone resorption. Furthermore, it has been suggested that when bone loss is excessive, it can compromise the long-term clinical performance of the prosthesis. This may also be responsible for implant migration, aseptic loosening, fractures around the prosthesis, and can imply technical problems during revision surgery.
Solving the stress-shielding problem requires the development of new implants and prosthesis with a lower stiffness than conventional designs, without any critical detrimental effect on the mechanical strength. Within the effort to obtain implants with a better stiffness match with the cortical bone, there are several important advances already reported. One of those explored routes to obtain porous titanium is the space-holder technique, which is a modification of conventional powder metallurgy. This technique consists of mixing the metal powder with a special additive to be removed before sintering. We have prepared porous Ti using NaCl and NH4HCO3 as space holder material, with 30, 40, 50, 60 and 70 vol. % concentration (NaCl) and 50% (NH4HCO3).
Porous titanium is considered a promising biomaterial for various applications in orthopedics including bone substitution and total joint replacement surgeries. Using the space holder technique, it is now possible to manufacture porous titanium with mechanical properties in the range of the mechanical properties of bone. Open porous biomaterials have large surface area that could be modified using bio-functionalizing surface treatment techniques for improved performance of the implant. The surface of biomedical materials is often treated using surface engineering techniques to improve the (biological) performance of the materials. Since titanium is bio-inert, surface treatments and coatings are often applied to improve their bioactivity. Surface nanostructuring of conventional biomaterials has emerged as one of the most important and effective manners to convert them in advanced biomaterials; this is the consequence of nano-features capability to effectively have some influence on surrounding biological environment at molecular nano-scale level. Since the cells in their natural environment are surrounded by nanoscale features linked to their extracellular matrix (ECM), the nanotopographical parameters become an essential part in design of biomaterials for tissue formation and repair. Accordingly, several studies suggest that a remarkably small modification in surface nanotopography could result permissive for mesenchymal stem cell growth and development, indicating that changes in such nanotopographical features had a direct influence in the adhesion/tension balance to permit self-renewal or targeted differentiation. Biointerface topography and, in particular, nanoscale features can affect cell behavior and integrin-mediated cell adhesion, and is now evident from studies with fabricated topographical features.
Introduced herein is directed irradiation synthesis (DIS) as a process that can pattern porous Ti samples not only on the surface but also inside the pores and pore walls. Broad-beam ions combined with rastered focused ions and gradient ion-beam profiles are sequenced and/or combined with reactive and/or non-reactive thermal beams that control the surface topography, chemistry and structure at the micro and nano-scale. In this work, we show that porous cpTi samples can be nano-patterned inside and outside the pores in such a way that the biological response of the surface can be favorably influenced. To that end, treated samples were detailed characterized in order to establish relationships with DIS conditions, and with surface energy and structural properties as well. These new surfaces were also biologically evaluated by using human aortic smooth muscle cells (HASMCs) for cytotoxicity assessment. Overall analysis of DIS influence on porous cpTi samples allowed identifying the real potential of our technology for nano-patterning and generates a positive biological response.
Medical devices, which are design to be implanted in living tissues, have to fit perfectly in the tissue defect. There, they will get in contact to host cells and body fluids at the same time, therefore, these biomaterials must have an optimum design of their surface which should promote and facilitate tissue integration. Among the minimum requirements, biocompatibility and non-toxicity, biomaterials should be developed in a controlled manner in order to promote a reduction of bacteria attachment, a reduction or delay of immune response and enhancement of mesenchymal and osteoblast cells adhesion and differentiation.
During the past few years, the surface modification of dental implants has grown and developed new strategies to enhance the surface properties in order to achieve faster osseointegration and a reduce bacteria attachment. In general terms, the survival rates of dental implants are high, however, there is still implants failure of around 2% and 5% after one month and one year respectively. Implant rejection still occurs and therefore, the main focus of the research society is in the development of new strategies to achieve a suitable surface modification of dental implants which decrease the percentage failure.
Many efforts have been centered on the simulation of the bone matrix chemistry using an active coating with biomacromolecules such collagen or ceramics such hydroxyapatite which supports chemical cues to promotes a proper osseointegration. However, dental implants are going to contact with other tissues, not only hard bone, they have to adjust to soft tissue healing. Regarding dental implants environment, the surface has to induce a faster sealing in soft tissue to avoid bacterial colonization and post infections. The different types of tissue in which medical devices are facing made harder the smart design from a native tissue point of view.
This one reason why surface technology has been developing many strategies in order to create bioactive surfaces which can respond specifically in each context. Plasma-based techniques have shown an attractive method to modify the surface of dental implants developing topography and chemistry changes to respond to different environment. In that sense, the developed features at the nano-scale order can mimic the nanofeatures found in native ECM and interact with cytoplasmatic prolongations such filopodia and lamellipodia in the same order. Surface topography as well physicochemical properties have shown to be key factors of the biological responses affecting fundamental processes, such as the protein adsorption and cell adhesion, proliferation and differentiation.
On the other hand, surface modifications techniques have to take into account the complex structures used in the biomedical field such dental implants or catheters. Many of these surface technologies work in limited conditions using 2D substrates or at small-scale, therefore, some of these technologies are not suitable for the biomedical industry.
In this context, DPNS can produce the surface modification of 3D complex structures and in addition, can be the easy scaleable to the industry level, solving the previous limitations. Furthermore, it achieves nanofeatures in a homogeneous form for the whole surface which will enhance cells interaction and subsequently, implants osseointegration. DPNS becomes a powerful tool capable to effectively modify 3D complex structures as it is shown in the next figures.
Here, it is presented a clear example of how DPNS can modify any 3D material. As it is observed in
In these images, it is possible to confirm DPNS as a powerful technology to achieve the modification of complicated geometries with different planes, angles, and topographies.
In addition, these complex structures usually are in the biomedical market with some previous modifications produced by other technologies.
In
Commercially pure titanium (cpTi) and its medical grade alloy (Ti6Al4V) are some of the most used biomaterials for bone implants fabrication. This is attributed to their high biocompatibility, the good balance of mechanical properties and their osteointegration capability. However, since Ti is a first generation biomaterial (bioinert) it allows the formation of a fibrous tissue around the implants. In order to prevent the failure associated to this fibrous capsule, several surface modification techniques of Ti have been developed: most of them are focused on topographical and top-down chemical changes like thermal plasma spray and electrochemical methods, using HA and Bioglass®. There are not reports about development one-step and bottom-up chemical conversion coatings on Ti, in order to produce bioactive surfaces, but also with nanofeatures which can offer antibiofouling properties. The general hypothesis in the work presented here is that a new phosphating treatment of Ti not only can produce a bioactive layer of calcium phosphate, but also that layer can be the matrix to trap other elements like Silver nanoparticles, Zn, or antimicrobials which will give antimicrobial properties, all in a one-step and bottom-up process. To test the hypothesis, we have used some homemade and commercial solutions: two phosphating solutions (solution A with 2.4 g/L ZnO, 2.8 g/L CaCl, 2% v/v ortho-phosphoric acid H3PO4 in distilled water, and solution B with 16 ml/L of H3PO4, 1.2 g/L ZnO, 16 g/L NaNO2 in distilled water), and two commercial solutions (Oxifos® and Oxifos Zn®). Polished and cleaned Ti6Al4V samples were treated by immersion in these solutions, and then were characterized by SEM.
Experimental Procedure
1. Pre-Phosphating Preparation of Samples
Ti6Al4V samples are initially polished (240, 320, 400, 600, 800 and 1200 of SiC abrasive papers, and cloth disc with aluminum suspension until mirror finishing) and cleaned with water and neutral soap. Then, the samples are de-oxidized in a mix of HF and HNO3 during 5 minutes.
2. Preparation of Phosphating Solution
The better phosphating solution from the previous studies (Solution A) is prepared with 2.4 g/L ZnO, 2.8 g/L CaCl, 2% v/v H3PO4 in distilled water, and heated at 75° C., during samples immersion.
3. Phosphating Process
The prepared samples are immersed in solution A at 75° C., during 20 minutes, then washed and dried at room temperature. Some samples are already treated in this manner. Some others have to be polished and phosphated in these conditions, cause they were brought non polished from Group BAMR, UdeA.
4. DIS Procedures.
Unphosphated samples were be irradiated in the optimal conditions described in Table 19. They were selected from initial studies performed in our group using Ti6Al4V surfaces and Mg foams studies. These parameters were adjusted to avoid the delamination or cracking effect and to obtain a specific nano-patterning or an improved surface chemistry.
With respect to phosphate samples, being a ceramic layer, we must consider some previous experiences that Prof. Allain has had irradiating ceramic surfaces, with the purpose to avoid layer cracking, produce some nano-pattering or even an improved surface chemistry for the further testing of bioactivity by immersion in SBF.
Irradiation procedures were carried out at different energies, flux, fluence, incidence angles and times in order to depassivate the titanium alloy and induce diffusion of Aluminum content to the surface of the samples before being immersed in SBF. These procedures can also be used to modify the topography, mechanical properties and chemistry of the surface to obtain the proper bone environment to enhance bone formation and improve bioactivity on the surface of Ti6Al4V.
Results are provided in
All references throughout this application, for example patent documents including issued or granted patents or equivalents; patent application publications; and non-patent literature documents or other source material; are hereby incorporated by reference herein in their entireties, as though individually incorporated by reference, to the extent each reference is at least partially not inconsistent with the disclosure in this application (for example, a reference that is partially inconsistent is incorporated by reference except for the partially inconsistent portion of the reference).
The terms and expressions which have been employed herein are used as terms of description and not of limitation, and there is no intention in the use of such terms and expressions of excluding any equivalents of the features shown and described or portions thereof, but it is recognized that various modifications are possible within the scope of the invention claimed. Thus, it should be understood that although the present invention has been specifically disclosed by preferred embodiments, exemplary embodiments and optional features, modification and variation of the concepts herein disclosed may be resorted to by those skilled in the art, and that such modifications and variations are considered to be within the scope of this invention as defined by the appended claims. The specific embodiments provided herein are examples of useful embodiments of the present invention and it will be apparent to one skilled in the art that the present invention may be carried out using a large number of variations of the devices, device components, methods steps set forth in the present description. As will be obvious to one of skill in the art, methods and devices useful for the present methods can include a large number of optional composition and processing elements and steps.
When a group of substituents is disclosed herein, it is understood that all individual members of that group and all subgroups, including any isomers, enantiomers, and diastereomers of the group members, are disclosed separately. When a Markush group or other grouping is used herein, all individual members of the group and all combinations and subcombinations possible of the group are intended to be individually included in the disclosure. When a compound is described herein such that a particular isomer, enantiomer or diastereomer of the compound is not specified, for example, in a formula or in a chemical name, that description is intended to include each isomers and enantiomer of the compound described individual or in any combination. Additionally, unless otherwise specified, all isotopic variants of compounds disclosed herein are intended to be encompassed by the disclosure. For example, it will be understood that any one or more hydrogens in a molecule disclosed can be replaced with deuterium or tritium. Isotopic variants of a molecule are generally useful as standards in assays for the molecule and in chemical and biological research related to the molecule or its use. Methods for making such isotopic variants are known in the art. Specific names of compounds are intended to be exemplary, as it is known that one of ordinary skill in the art can name the same compounds differently.
Many of the molecules disclosed herein contain one or more ionizable groups [groups from which a proton can be removed (e.g., —COOH) or added (e.g., amines) or which can be quaternized (e.g., amines)]. All possible ionic forms of such molecules and salts thereof are intended to be included individually in the disclosure herein. With regard to salts of the compounds herein, one of ordinary skill in the art can select from among a wide variety of available counterions those that are appropriate for preparation of salts of this invention for a given application. In specific applications, the selection of a given anion or cation for preparation of a salt may result in increased or decreased solubility of that salt.
Every formulation or combination of components described or exemplified herein can be used to practice the invention, unless otherwise stated.
Whenever a range is given in the specification, for example, a temperature range, a time range, or a composition or concentration range, all intermediate ranges and subranges, as well as all individual values included in the ranges given are intended to be included in the disclosure. It will be understood that any subranges or individual values in a range or subrange that are included in the description herein can be excluded from the claims herein.
All patents and publications mentioned in the specification are indicative of the levels of skill of those skilled in the art to which the invention pertains. References cited herein are incorporated by reference herein in their entirety to indicate the state of the art as of their publication or filing date and it is intended that this information can be employed herein, if needed, to exclude specific embodiments that are in the prior art. For example, when composition of matter are claimed, it should be understood that compounds known and available in the art prior to Applicant's invention, including compounds for which an enabling disclosure is provided in the references cited herein, are not intended to be included in the composition of matter claims herein.
As used herein, “comprising” is synonymous with “including,” “containing,” or “characterized by,” and is inclusive or open-ended and does not exclude additional, unrecited elements or method steps. As used herein, “consisting of” excludes any element, step, or ingredient not specified in the claim element. As used herein, “consisting essentially of” does not exclude materials or steps that do not materially affect the basic and novel characteristics of the claim. In each instance herein any of the terms “comprising”, “consisting essentially of” and “consisting of” may be replaced with either of the other two terms. The invention illustratively described herein suitably may be practiced in the absence of any element or elements, limitation or limitations which is not specifically disclosed herein.
One of ordinary skill in the art will appreciate that starting materials, biological materials, reagents, synthetic methods, purification methods, analytical methods, assay methods, and biological methods other than those specifically exemplified can be employed in the practice of the invention without resort to undue experimentation. All art-known functional equivalents, of any such materials and methods are intended to be included in this invention. The terms and expressions which have been employed are used as terms of description and not of limitation, and there is no intention that in the use of such terms and expressions of excluding any equivalents of the features shown and described or portions thereof, but it is recognized that various modifications are possible within the scope of the invention claimed. Thus, it should be understood that although the present invention has been specifically disclosed by preferred embodiments and optional features, modification and variation of the concepts herein disclosed may be resorted to by those skilled in the art, and that such modifications and variations are considered to be within the scope of this invention as defined by the appended claims.
This application claims the benefit of and priority to U.S. Provisional Application No. 62/483,105, filed Apr. 7, 2017; U.S. Provisional Application No. 62/483,074, filed Apr. 7, 2017; U.S. Provisional Application No. 62/556,120, filed Sep. 8, 2017 and U.S. Provisional Application No. 62/556,048, filed Sep. 8, 2017, which are each hereby incorporated in their entirety to the extent not inconsistent herewith.
| Number | Date | Country | |
|---|---|---|---|
| 62483105 | Apr 2017 | US | |
| 62483074 | Apr 2017 | US | |
| 62556048 | Sep 2017 | US | |
| 62556120 | Sep 2017 | US |
| Number | Date | Country | |
|---|---|---|---|
| Parent | PCT/US18/26567 | Apr 2018 | US |
| Child | 16592195 | US |
