Stress and displacement patterns in the craniofacial skeleton with rapid maxillary expansion-a finite element method study.

BACKGROUND: Rapid maxillary expansion (RME), indicated in the treatment of maxillary deficiency directs high forces to maxillary basal bone and to other adjacent skeletal bones. The aim of this study is to (i) evaluate stress distribution along craniofacial sutures and (ii) study the displacement of various craniofacial structures with rapid maxillary expansion therapy by using a Finite Element model. METHODS: An analytical model was developed from a dried human skull of a 12 year old male. CT scan images of the skull were taken in axial direction parallel to the F-H plane at 1 mm interval, processed using Mimics software, required portion of the skull was exported into stereo-lithography model. ANSYS software was used to solve the mathematical equation. Contour plots of the displacement and stresses were obtained from the results of the analysis performed. RESULTS: At Node 47005, maximum X-displacement was 5.073 mm corresponding to the incisal edge of the upper central incisor. At Node 3971, maximum negative Y-displacement was -0.86 mm which corresponds to the anterior zygomatic arch, indicating posterior movement of craniofacial complex. At Node 32324, maximum negative Z-displacement was -0.92 mm representing the anterior and deepest convex portion of the nasal septum; indicating downward displacement of structures medial to the area of force application. CONCLUSIONS: Pyramidal displacement of maxilla was evident. Apex of pyramid faced the nasal bone and base was located on the oral side. Posterosuperior part of nasal cavity moved minimally in lateral direction and width of nasal cavity at the floor of the nose increased, there was downward and forward movement of maxilla with a tendency toward posterior rotation. Maximum von Mises stresses were found along midpalatal, pterygomaxillary, nasomaxillary and frontomaxillary sutures.

Effects of clinical use and sterilization on surface topography and surface roughness of three commonly used types of orthodontic archwires.

AIM: To evaluate the changes in surface topography and roughness of stainless steel (SS), nickel-titanium and beta-titanium (ß-Ti) archwires after clinical use and sterilization. SETTINGS AND DESIGN: Thirty wires each of SS, nitinol, and ß-Ti (3M Unitek) were tested in as received, as received and autoclaved, and clinically retrieved then autoclaved conditions. MATERIALS AND METHODS: A sterilization protocol of 134°C for 18 min was performed using an autoclave. Surface topography of specimens from each subgroup was examined using an environmental scanning electron microscope (ESEM model Quanta 200, The Netherlands) at ×100, ×1000, and ×2500 magnifications. Surface roughness was measured using arithmetic mean roughness (Ra) values obtained from optical profilometric scanning (Taylor Hobson, Leicester, UK). STATISTICAL ANALYSIS: Data were analyzed by one-way analysis of variance and Tukey's post-hoc procedures. RESULTS: Scanning electron microscope images revealed an increase in surface irregularities in SS and nitinol wires after clinical use. There was a significant increase in Ra values of SS orthodontic wires after intra-oral exposure (P = 0.0002). CONCLUSION: Surface roughness of SS wires increased significantly after clinical use. Autoclave sterilization did not affect considerably on surface characteristics of any archwire.

An indigenously designed apparatus for measuring orthodontic force.

AIM: An indigenous apparatus is designed to measure the orthodontic force delivered from elastomeric chains and compare this force with values obtained from the Instron universal testing machine. MATERIAL AND METHODS: An indigenously designed apparatus is developed to evaluate forces delivered by various orthodontic auxiliaries. The apparatus consists of a flat steel platform, movable arm, and a mounted screw gauge arm. Orthodontic brackets can be attached to these arms. An electric circuit is connected, to the movable arm, which will estimate the forces exerted between brackets with elastomeric chain. The circuit is connected to the signal conditioner which will display the reading. Elastomeric chain with four links is attached to the arms. The movable arm is adjusted to create orthodontic forces and calibrated on the digital displayer. Twenty Elastomeric chains are used and forces are calibrated with the indigenously designed apparatus. The values of the force is compared with the forces calibrated with Instron universal testing machine to compare the efficacy of the indigenous apparatus. RESULTS: The force values obtained from activation of elastomeric chain segments, in the Instron universal testing machine and the indigenous apparatus were in the range of 100 to 150 grams, initially at 1mm activation then, took a steep rise to 300 to 350 grams at 5mm activation and then, had a gradual increase for the remaining 5mm activation, reaching 400 to 450 grams. CONCLUSION: The Indigenous apparatus can be considered efficient in measuring tensile force generated by orthodontic auxiliaries.

Frictional characteristics of the newer orthodontic elastomeric ligatures.

INTRODUCTION: Elastomeric ligatures reduce chairside time but increase friction. Polymeric coatings and 45° angulations have been introduced to the ligature modules to combat its disadvantages and reduce friction. This in vitro study compared the frictional characteristics of six different types of the most commonly used elastomeric modules. MATERIALS AND METHODS: Thecoefficient of friction for six ligation methods: the non-coated Mini Stix† and coated Super Slick Mini Stix (TP Orthodontics), 45° angulated but non-coated Alastik Easy-To-Tie (3M Unitek) elastomerics and non-angulated non-coated Alastik QuiK-StiK FNx01 , 0.110'- and 0.120'-diameter elastomerics (Reliance Orthodontics) were measured in dry conditions utilizing a jig according to the protocol of Tidy. RESULTS: A significant difference was observed between the various types of elastomeric ligatures (P<.01). Among the six types of elastomeric ligatures, the 45° angulated elastomeric ligatures produced the least friction, followed by the coated Super Slick elastomers. No difference in the friction was noted when the diameter of the elastomeric ligatures was varied. CONCLUSIONS: Polymeric surface coatings and introduction of angulations into elastomeric ligatures reduce the friction during sliding; however, the diameter of the ligature made no difference to sliding friction.