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Roughened implant surfaces are thought to enhance osseointegration. Torque removal forces have been used as a biomechanical measure of anchorage or osseointegration in which the greater forces required to remove implants may be interpreted as an increase in the strength of osseointegration. The purpose of this study was to compare the torque resistance to removal of screw shaped titanium implants having an acid etched (HC1/H2SO4) surface (Osseotite) with implants having a machined surface. Two custom screw shaped implants, 1 acid etched and the other machined, were placed into the distal femurs of 10 adult New Zealand White rabbits. These implants were 3.25 mm in diameter x 4.00 mm in length without holes, grooves or slots to resist rotation. Following a 2 month healing period, the implants were removed under reverse torque rotation with a digital torque measuring device. Two implants with the machined surface preparation failed to achieve osseointegration. All other implants were found to be anchored to bone. Resistance to torque removal was found to be 4 x greater for the implants with the acid etched surface as compared to the implants with the machined surface. The mean torque values were 20.50 +/- 6.59 N cm and 4.95 +/- 1.61 N cm for the acid etched and machined surfaces respectively. The results of this study suggest that chemical etching of the titanium implant surface significantly increases the strength of osseointegration as determined by resistance to reverse torque rotation.
Titanium alloys are used in different industries such as biomedical, aerospace, aeronautic, chemical, and naval. Those industries have high requirements with few damage tolerances. The aim of this work was to study the corrosion behavior of titanium alloys anodizing and non-anodizing in alkaline (KOH and NaOH) solutions, exposed in 3.5%wt. NaCl and 3.5% wt. H2SO4 solutions at room temperature using cyclic potentiodynamic polarization (CPP) according to standards to obtain electrochemical parameters as the passivation range (PR), corrosion type, passive layer persistence, corrosion potential (Ecorr), and corrosion rate. The alloy Ti Beta-C anodized presented better corrosion resistance than Ti-6Al-4V in both media. The smallest corrosion rate is presented in Beta-C samples (4.72 E-8 A/cm2) and the highest corrosion rate is CP2 (1.61 E-5 A/cm2)
Yuguchi et al. 2020 applies the previous contributions to simultaneously determine zircon U-Pb age and titanium concentration in granitic samples. This will produce both age and temperature of zircon crystallization. In this zircon method, I will be focusing only on the experiments this paper ran for Ti-in-zircons. To measure titanium for thermometry, Yuguchi et al. employed two approaches. Both approaches use a quadrupole mass spectrometer equipped with a collision reaction cell. The first method used a MS/MS mass-shift mode with oxygen reaction gas which provided a consistent measurement of titanium as 48Ti16O+. The second method proceeded in no-gas mode to measure the intensity of 49Ti. The CRC, through kinetic energy discrimination (collision) or chemical reactivity (hydrogen, oxygen, helium, methane through reactions). Evaluation of titanium in an oxygen-flow CRC generates a consistent measurement of 48Ti16O+ but is not an available option of analysis at the Jackson School of Geoscience. Therefore, the second method (non-gas mode) would be best adaptable to the resources available. Titanium has five stable isotopes: 46Ti (8.25% in isotope abundance ratio), 47Ti (7.44%), 48Ti (73.72%), 49Ti (5.41%), and 50Ti (5.18%). Common interferences include bivalent ions of zirconium (92Zr++, 94Zr++, and 96Zr++). Isobaric interferences 48Ca, 50V, or 50Cr for 48Ti+ and 50Ti+. If these isobaric interferences cannot be removed, focus on 49Ti must ensue.
Initial Method looked at four sacrificial grains of unit RCC-E under parameters: 10 Hz, 25spt, 60dw, 800 mL/min of Ar&He with incremental increase in laser energy (%) of 10% (20-30-40-50%). After Initial Method, two major problems arose: spectral skew and low recorded counts of titanium and light rare earth elements. To fix these, the repetition rate was increased from 10 to 20 Hz, incrementally, and the integration time was increased from 0.01 to 0.02 s, respectively (S.P., init. = 0.2872 s, S.P., fix = 0.3772 s). Revised Test 1 had four zircons under 5, 10, 15, and 20 Hz repetition rates to understand the reduction in spectral skew with an increase in repetition rate. An increase in integration times for titanium and LREEs (0.02 s), 35μm spot, 50% laser energy were altered as well. Test 2 retained the Test 1 parameters but varied energy levels between 45% and 50%; 50% returned the best data. Final ablation parameters were 50% laser energy, 4.1 J/cm^2 fluence variation, 20 Hz repetition rate, and 25 and 35 μm spots according to zircon size. More explanation is provided underneath each Method/Test image.
The aim of this study was to establish finite element models of free fibular flapreconstruction of different types of mandibular defects. The finite models was createdfrom CT image. The finite element method was used to carry out biological analysis.Comparative analysis of the stress distribution characteristics and the displacementchanges in mandible were carried out. From the stress distribution nephogram, it couldbe concluded that the stress was mainly concentrated in the bilateral condylar neck,the anterior and posterior edges of the mandibular ramus, and the joint between theposterior end of the fibula and the mandible. The more mandibular defects that werepresent, the greater the corresponding stress on the contralateral condyle. Displacementnephogram: the inward displacement of the condyle on the affected side of a type Bdefect was more obvious than that of the normal mandible, and the most obvious in theX-axis direction, with a displacement of 1.61 mm; the BSS defect crossed the midline, andthe bilateral condyles shifted inward causing posterior displacement; the displacementresults of RBS and CRBS defects showed whether the condyle was involved in thebone defect, and the displacement changes after reconstruction were not significantlydifferent. After mandibular reconstruction, the loss of attachment muscles can causepostoperative condylar displacement, resulting in postoperative occlusal disorder,opening deviation and other complications.
The mandible, as a movable bony scaffold underlying thelower 1/3 of the face, not only maintains the facial contour, butalso is closely related to the functions of chewing, breathing andswallowing. In radical surgery for mandibular tumors, a largenumber of muscles attached to the mandible are stripped, resultingin a lack of coordination of the chewing muscles, resulting incomplications such as limited mouth opening, jaw deviation, jointclicking and disorder of occlusal relationship [1-3]. In the past,the most commonly-used repair methods were titanium plate andpersonalized prosthesis, which are prone to complications such astitanium plate exposure and fracture after long-term observation.Therefore, it was gradually replaced by free iliac or rib grafts [4,5].In 1989, Hidalgo first applied a free fibular flap for jaw defectrepair [6]. Since then, the vascularized fibular flap has become themost important method of mandibular defect repair because ithas sufficient bone length, is easy to shape, as well as having fewerdonor site complications and other advantages [7-9]. In recentyears, with the development of digital technology, the accuracy ofmandibular reconstruction is the common goal pursued by oraland maxillofacial surgeons [10-12]. Analysis of the shape andposition of the mandible after reconstruction is not only conduciveto optimizing the reconstruction plan, but also conducive to theanalysis of factors affecting accuracy, improving clinical treatmenteffects, and reducing postoperative complications. To date, therehave still been few biomechanical studies on the reconstruction ofmandibular defects with fibula flaps. The Finite Element Method(FEM) is a mathematical simulation method for mechanicalanalysis. It is widely used for biomechanical analyses of complexstructures with different shapes, loads and materials [13-15].
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