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1. Archwire Materials And
Application Of Newer Materials
in Begg Appliance.
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2. Introduction

Advancements in orthodontic materials have
been progressing by leaps and bounds.

Plethora of archwires varying widely –
material, geometry, configuration,
manufacturing process and physical properties.

Lack of an ideal archwire – clinician – select
the best – for the intended use.
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3. Evolution of Archwire Materials

Availability of archwire materials – determined
mechanotherapy.

Requirements changes initial stages to finish.

Variable cross section Orthodontics,

Prior to 70’s – only gold & SS – available

Difft. Requirements met – changing cross section –
& geometry.
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4. 
Variable Modulus Orthodontics.


TMA , Nitinol etc.


Varying modulus of elasticity.
Lower moduli – initial stages and higher – finish.
Varying Transformation Temperature
Orthodontics.

NiTi archwires – super elastic & thermodynamic.

Cu NiTi & Neosentalloy.
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5. Desirable Properties of Archwire
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6. Ultimate Tensile Strength
Yield Strength
Proportional
limit
Force
(stress)
Deflection ( Strain)
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Failure Point

7. 
Spring back.( Range of Activation or Working
range)



Measure of how far a material can be deformed
without exceeding the limits of the material.
Related to Y.S
E
Higher spring back – large activations – increase
in working time of appl.
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8. 
Stiffness ( Load Deflection Rate ).

Measure of resistance to any kind of mechanical
deformation,

Proportional to Modulus of Elasticity.

Low stiffness or LDR provide

Ability to apply lower forces

A more constant force

Greater ease & accuracy in applying a given force.
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9. 
Strength.

It is the measure of the max. possible load, the
greatest force which the wire or arch arrangement
can sustain or deliver if it is loaded to the limit of
the material.

Formability.

Ability to bend a wire into desired configurations
without failure.
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10. 
Modulus of Resilience or Stored energy.



Work available to move the teeth.
Area – elastic portion of the stress- strain curve.
Bio compatibility & Environmental stability.

Resistance to corrosion and tissue tolerance to
elements in the wire.

Maintenance of desirable properties for extended
periods after manufacture.
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11. 
Poor Biohostability.

Neither actively nurture nor passively act as a
substrate for microorganisms.
Cause foul smell
 Color changes – detract from esthetics.
 Remove or build up material – compromise mech prop.


Joinability.

Permit welding and soldering
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12. 
Friction,

Excessive amount



Loss of anchorage
Less tooth movement.
Esthetics.



Color stability
Inconspicuous
Non Ferromagnetic.
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13. Classification.

Based on material constituent:

Metals.
Gold Alloys.
Stainless Steel.
Cobalt – Chromium Alloys.
Nickel- Titanium Alloys










NiTinol
Chinese Ni Ti
Japanese Ni Ti
Niobium Ti
Copper NiTi
Cv NiTi
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Metal
Non metal

14. 
Beta Ti

Alpha Ti

Non Metals.

Polymeric materials.

Composite / Coated Archwires.

Optiflex.
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15. Gold Alloys.

Pure gold – too soft for orthodontic purpose.

Initial round wire, Begg - .020 platinised gold.

Hardened – cold working or hardening heat trt.

Marginal properties & price – obsolete.
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16. Stainless Steel

Developed b/w 1903 & 1921

Harry Brearley of Sheffield, F.M. Beckett of the
U.S, Edward Maurer of Germany.

1933 – Archie Brusse presented table clinic – 1 st
Stainless Steel Appliance system.

Displaced Gold alloys.

SS wires - work horse of the orthodontic
industry for generations
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17. 
Composition.

Steels – iron based alloys – contains < 1.2% C

SS

Types.
Cr. ( 12 – 30%) + steel.

Ferritic

Martensitic.

Austenitic.
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18. 
Ferritic.


AISI series 400.


Body Centered Cubic Str.
Low sth. & not hardenable by heat trt.
Martensitic.

AISI series 400.

Body Centred Tetragonal Structure.

Strength & Hardness

Corrosion Resistance & Ductility
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19. 
Austenitic.

Most corrosion resistant.

AISI 302 basic type.

18% - Cr., 8% - Ni., 0.15% C.



AISI 304 – C ltd to 0.08 %
302 & 304
18-8 SS
316 L - <0.03 % C –
implants.

Str. – Face Centered Cubic.
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20. A J Wilcock Archwires.

Early 1940’s – acquainted – Mr. Arthur J
Wilcock.- Metallurgist – Whittlesea, Victoria.

Years of research – Develop wire – objectives.

Thin tensile wire – distribute force – optimal level

Considerable period of time.

Over long distances.

Minimal loss of force intensity.

Initially 0.018 wire produced.

Dia. - progressively decreased to 0.014.
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21. 
Wilcock wires mainstay of Begg Technique.

Grades of wire used initially


Special Plus
Extra Special plus – cases resistant to bite opening.
1984 – A J Wilcock Jr. – request of Dr.
Mollenhauer of Australia – ultra high tensile
strength – round wire

Supreme grade

0.010 & 0.009
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22. 
Pulse Straightening Vs Spinner Straightening.

Spinner Straightening.

Straightening resistant materials – cold drawn
condition.

Wire pulled – rotating bronze rollers

Dis Adv.

Resultant Deformation.

Decreased Yield stress value.

Strain softened.
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23. 
Pulse Straightening.

Pulsed in a special machine.

High tensile wires – straightened.

Lower dia. wires

Yield Strength – not altered.

Surface – smoother finish.
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24. 
Types of A J Wilcock Archwires.

Regular Grade.( Pink label )

Dia – 0.012 – 0.024
Regular plus (Green label )



Dia – 0.012 – 0.020
Easily formed & excellent for general use & utlility wires.
Special grade ( Blue label )



Dia – 0.012 – 0.020.
0.016 inch – initial stages.
Special Plus ( Yellow label )


Dia – 0.012 – 0.024
Premium




( Purple label )
Dia – 0.012 – 0.020.
Ideal for bite opening .
Where high resiliency is required
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25. 
Premium Plus ( Gold label ).




Size – 0.010 – 0.018
In early trt. – alignment & levelling.
Mollenhauer recommends – 0.011 wire – high angle
cases, undue molar extrusion.
Supreme ( Biege label ).





Size 0.008 – 0.011
Unravelling crowded ant. teeth.
Boxed reciprocal torquing aux.
Mini uprighting springs.
Aligning 2nd molars towards the end of stage II.
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26. 
Substituted Titanium Alloys.

Ti – used as Structural metal – 1952 .

Became available – Orthodontics – 1970’s.

Allotropy – Crystallographic change – 885°C .

Below 885°C – HCP or α lattice.

Above 885°C – BCC or β lattice.

Addn. of Molybdenum or Columbium stabilize this str.
At room temp.
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27. 



Trends in SS Metallurgy.
Eliminate or minimize Nickel content.
Nearly Ni free SS
Steel Din 1.4456 – one of them
Composition:
15 – 18 % Cr.
3 – 4 % molybdenum.
10 – 14 % Manganese
0.9 % nitrogen – compensate for nickel.

Trade names – Menzanium, Noninium.
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28. Nickel – Titanium alloys

Developed by William F Beuhler – Naval
Ordinance laboratory – 1960.

1970 - Dr. George Andreasen recognized the
potential of this alloy.

Largely through his efforts and those of the
Unitek Company, the first nitinol alloy was
marketed to orthodontists as Nitinol™.
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29. 
Andreasen – 2 types.



Elastic Nitinol.
Thermal Nitinol.
Thermal Nitinol.




1:1 atomic ratio of Ni and Ti.
Ni – 55% , Ti – 45%
Co – 1.6% - brings TTR - 37°C.
Unique feature – Shape Memory Phenomenon.


Capability of a wire to return to a previously manufactured
shape when it is heated through its TTR.
Martensitic Grain Structure
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30. 
Elastic Nitinol.

Alloy of Ni & Ti without Co,

Elasticity , Flexibility

Lighter continuous forces.

Austenitic Grain Structure.
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31. Classification ( Kusy )

Conventional Nitinol.

Pseudoelastic Nitinol.

Thermoelastic nitinol.

Conventional – Martensitic stabilized alloy

Passive – SME suppressed – cold working during
wire drawing - >8 – 10%.

Attractive feature – Low Stiffness.

Limitation – lack of formability.
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32. 
Pseudoelastic Nitinol.

Active.

Capable of undergoing anticipated phase
transformation.

Undergo some form of SME + Superelastic.

Two types –

Austenitic active alloy

Martensitic active alloy.
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33. 
Austenitic Active alloy.

Martensite – low stiffness phase.( E = 31 -35 GPa)

Austenite – high stiffness phase. ( E = 84 – 98 GPa)
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34. 
On loading – Austenitic alloy – Stiffness 3x,
conventional martensitic stabilised alloy.

Plateau like area – Stress induced transformation –
martensitic phase. + ve slope – stiffness
comparable to martensitic nitinol.

Deactivation – reverse occurs.

2nd Plateau – Martensite
shape to maintain force
Austenite. Changes
key attribute – Pseudoelasticity.
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35. 
Thermoelastic Nitinol.

Martensitic active alloy.

Exhibits thermally induced SME.

Transition temp.- ambient oral temperature.

Medical advances – Trt. Of Scliosis.

Desired shape set by heat.

Distortion & insertion into patient’s mouth

Appliance activated – warmth of oral cavity.

Return to its predetermined shape.
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36. www.indiandentalacademy.com

37. 
Chinese NiTi.

Developed by Dr. Tien Hua Cheng & AssociatesGeneral research institute of Non – Ferrous Metals,
Beijing, China.

Little work hardening , parent phase – austenite mech
prop. differ from Nitinol.

Burstone, Qin, Morton – compared three prop. with SS
and Nitinol.

Springback

Stiffness.

Maximum moment.
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38. 
Springback.

Diff. b/w deflection of 80º & residual deformation
after unloading.
Chinese Niti > Nitinol > SS
SS
Nitinol
NiTi
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39. 
Stiffness



Steel and Nitinol – average unloading stiffness – same
regardless of amount of activation.
Chinese Niti – lower stiffness value – value changes with
degree of activation.
Maximum moment.

Niti ( 805 gm-mm at 1º of permanent deformation)< Nitinol
( 975 gm-mm)
< SS( 1400 gm-mm)
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40. 
Applications.

Low stiffness & large deflections are needed.

No time dependent deformation in mouth.

High stiffness at small activations - adequate force
levels.

Larger cross sections – larger moments – root
movement and transalation.
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41. 
Japanese Niti

1978 – Furukawa electric company.

Fujio Miura – studied mech. Properties.


Excellent springback & Super elastic properties.
Superelasticity – Stress – fairly constant upto a
certain point of deformation - & during
rebounding. ( Stress induced martensitic
transformation. BCC HCP )
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42. 
Continous force – long period during
deactivation of the wire.

Physiologic tooth movement.

Possible to modify – force – individualized
segment of the arch wire – applying controlled
heat.
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43. 
Introduced in 1994 – Rohit Sachdeva & Suchio
Miyasaki 1994.

Major advance – Variable transformation
temperature orthodontics.

Stability of Martensite / Austenite at a given
temp. – Transformation temp. of the alloy.

Impt. marker Austenite finish temperature.Af.

Working temp. of orthodontic appliance – > Af
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44. 
Compositon.


LDR charecteristics.


Low hysteresis.
Surface.


Austenitic structure.
Elements
Ti
Ni
Cr
Cu
Rough & porous – comparable to TMA.
Alloy types.

Type I – Af = 15°C.

Type II – Af = 27 °C.
Type III – Af = 35 °C.
Type IV – Af = 40°C


Wt%
42.99
49.87
0.5
5.64
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45. 
Type I – high force levels – not used clinically.

Type II – Highest force & best used.


Normal periodontal health.


Average or higher pain threshold.
Rapid tooth movement required.
Type III wire
Low to normal threshold.

Slightly compromised periodontium.

Relatively low forces required.
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46. 
Type IV –

Sensitive to pain.

Compromised periodontal conditions.

Tooth movement – deliberately slowed down.

Beneficial – initial rectangular wire.
Advantages.

Low hysteresis – more constant force levels.

Difft. Types – match archwire force levels – specific
early treatment requirements & goals.
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47. 
CV NiTi.

Copper free NiTi.

In the same types as CuNiTi.

Similar mechanical properties.

Slower recovery pattern.
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48. Beta – Titanium Alloys.
Charles J Burstone – 1980 ( TMA).
Composition.



Titanium79%
Molybdenum – 11%
Zirconium –
6%
Tin –
4%

Addition of elements - molybdenum or
columbium, a titanium-based alloy can
maintain its beta structure even when cooled to
room temperature.
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49. 
Advantages.





Force levels less than half of stainless steel.
Highly ductile – complicated configurations –
formed.
Weldable.
Good spring back.
Disadvantage.

Rough surface – High friction.
Ion implantation – Burstone – 1995.
 Elements or compounds – ionised and accelerated – to a
target. N & O ions from a plasma
 Ti oxide and nitride formed

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50. Alpha Titanium Alloy:


AJ Wilcock Jr. – 1988 – near α phase Titanium
alloy – Orthodontic purpose.
Composition.
Titanium – 90%.
Aluminium – 6%
Vanadium – 4%

Crystal structure. – Closely packed hexagonal
lattice (HCP).


Only one active slip plane along its base.
BCC – two slip planes ( β Titanium ).
Less ductile than TMA
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51. 
Near α phase Ti alloy – certain amount β phase retained at room temp.

Stiffer with passage of time

Absorption of H+ ions – surface layer – titanium
hydride.

Weldable

Dimensions available.


.016 x .022 and .018 x .022.
Rectangular finishing wires.
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52. 


Non metallic archwires.
Esthetic arch wires – Optiflex
Unidirectional Fiber Reinforced Polymeric
archwire – ( UFRP ) – Composite Archwires.
Manufacture.


Photopultrusion
Pultrusion - The process of manufacturing
components having continuous lengths and a
constant cross-sectional shape, such as in
archwires.
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53. 
UFRP compared to NiTi.



Elastic until failure occurs.
Resilience and springback are comparable.
Parlene : poly ( chloro – p- xylylene) – coating

Risk of glass fiber release during clinical use
eliminated.
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54. 
Applications of newer materials in Begg
technique.
Stage I :



Pulse straightened SS wires and Super elastic NiTi
wires – replaced multi loop archwires.
0.010 or 0.011 supreme PS wires – MAA. Better
root control in early stages of trt.
0.014 premium plus – in high angle cases to prevent
undue molar extrusion.
End of stage II

0.011 – alignment of 2nd molars
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55. 
Stage III :
Mini uprighting springs – 0.008 – 0.010 supreme
P.S wires.

Finishing :
Stiff Rectangular 0.018 x 0.022 α Titanium wires
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56. Conclusion

Recent advances in material science and
technology has resulted in an array of newer
archwire materials, opening new vistas in
Orthodontic treatment. Materials with widely
diverging properties are on the market today
and their usage has profound implications on
the appliance mechanics.
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57. As Kusy points out, composites will increasingly
encroach the use of metals, ceramics and
polymers as functional and esthetically
pleasing appliances become popular. The
orthodontist therefore has to clearly outline
the phases of treatment and select the
archwire most suited for attaining specific
goals for treatment.
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58. www.indiandentalacademy.com
Leader in continuing dental education
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