Wires in orthodontics final

WIRES IN
ORTHODONTICS
www.indiandentalacademy.com

CONTENTS
 INTRODUCTION
 PHASES OF
ARCHWIRE
DEVELOPMENT
 WROUGHT METAL
ALLOYS
 BASIC MECHANICAL
PROPERTIES
 WIRE
CHARACTERISTICS
OF CLINICAL
RELEVANCE
 GOLD ALLOYS
 STAINLESS STEEL
 Multistranded wires
 Australian Arch wires

INTRODUCTION

CONTENTS
 CHROME- COBALT
ALLOYS
 TITANIUM ALLOYS
 Alpha Titanium alloy
 Beta Titanium alloy
 Nickel Titanium alloys
 COMBINATION
WIRES
 ESTHETIC ARCH
WIRES
 COMPARISON OF
ARCHWIRES IN
ORTHODONTIC
APPLICATIONS
 CONCLUSION

PHASES OF ARCHWIRE DEVELOPMENT
(Evans and Durning - BJO 1996)
METHOD OF
FORCE DELIVERY
MATERIALS
USED
CONCEPT
PHASE I Variation in
archwire dimension
Stainless steel,
Gold
VARIABLE CROSS-
SECTIONAL
ORTHODONTICS
PHASE II Variation in archwire
material but same
dimension
Beta Titanium, Nickel
Titanium, Stainless
Steel, Cobalt chromium
VARIABLE
MODULUS
ORTHODONTICS
PHASE III Variation in archwire
properties (super
elasticity)
Superelastic Nickel
Titanium
PHASE IV Variation in structural
composition of wire
material
Thermally activated
Nickel Titanium
PHASE V Variation in archwire
material composition /
structure
Graded thermally
active Nickel Titanium
VARIABLE
TRANSFORMATION
TEMPERATURE
ORTHODONTICS

WROUGHT METAL ALLOYS
 Formation of wrought alloy wires :
 Melting
 Formation of ingot
 Rolling (Turk’s head apparatus)
 Drawing
 Wrought alloy properties and micro structure
differ from the same alloy when cast.

 Force systems of orthodontic wires are
determined by:
 appliance design and
 wire composition
 Proportional to Elastic modulus (E)
 Low forces biologically desirable
 Large elastic deflection / working range
depending on PL, YS and E

 Other important properties:
 Ductility
 Joinability : soldering, welding
 Corrosion resistance
 Cost factor

BASIC MECHANICAL
PROPERTIES
 STRESS
Force per unit area within a structure
subjected to an external force or pressure.
COMPRESSIVE STRESS
Ratio of compressive force to cross
sectional area perpendicular to the axis of
applied force

 TENSILE STRESS
Ratio of tensile force to the original cross sectional
area perpendicular to the direction of applied
force.
 SHEAR STRESS
Ratio of force to the original cross sectional area
parallel to the direction of the force applied
 FLEXURAL STRESS / BENDING STRESS
Force per unit area of a material subjected to
flexural loading

 STRAIN
Change in length per unit initial length.
 PROPORTIONAL LIMIT
Maximum stress at which stress is proportional to
strain and above which plastic deformation
occurs
 WORKING RANGE
Maximum amount of elastic strain that an
orthodontic wire can sustain before it plastically
deforms

 YIELD STRENGTH
The stress at which a test specimen exhibits a
specific amount of plastic strain
 MODULUS OF ELASTICITY / YOUNG’S
MODULUS (E)
Ratio of elastic stress to elastic strain. It represents
relative stiffness of the material.

 FLEXIBILTIY
Is a measure of the amount to which a wire
can be strained without undergoing plastic
deformation. Maximum flexibility is defined
as the flexural strain that occurs when the
material is stressed to its proportional limit.

 RESILIENCE
A relative amount of stored energy per unit volume
released on unloading of a test specimen.
 PERMANENT / PLASTIC DEFORMATION
If a material is deformed by a stress at a point
above the proportional limit then plastic or
permanent deformation occurs.

 DUCTILITY
Relative ability of a material to deform
plastically under a tensile stress before it
fractures

 COLD WORKING / STRAIN HARDENING /
WORK HARDENING
It is the mechanical manipulation (plastic
deformation) of wire at room temperature.
- Stressing beyond PL to cause permanent
deformation
- Hardness increases
- Ductility decreases
- Dislocation of grains, altering their shape
(spaghetti)
- Modulus of elasticity remains unchanged

 ANNEALING
Controlled heating and cooling process
designed to produce desired properties in
a metal. The annealing process is
intended to soften metals, to increase their
plastic deformation potential, to stabilize
shape and increase machinability.

 3 STAGES OF ANNEALING
 Recovery
Properties of cold worked metal begin to
disappear.
Residual stresses of cold worked metal
(warping) disappear
Temperature used is lower than that used
for recrystallization
Stress relief heat treatment of orthodontic
wires reduces risk of fracture

 Recrystallization
- Significant changes in microstructure
- Deformed grains replaced by new
strain-free grains
- Original soft and ductile properties
return
- Recrystallization occurs only if metal
has been sufficiently cold worked

 Grain growth
- Grain size increases after recrystallization
- Depends on the severity of cold working

 HEAT TREATMENT
1. Solution heat treatment / softening heat
treatment
- casting placed in an electric furnace – 700
degrees C for 10 mins and then quenched
- Tensile strength, hardness, proportional limit
reduced
- Ductility increased

2. Age hardening/ hardening heat treatment
- soaking or aging the casting at a specific
temperature for a definite time before it is
water quenched
- 200 and 450 degrees C depending on
composition usually 15 – 30 mins
- YS, PL, MoR increases, ductility decreases

 SLIP PLANES
Application of shearing stresses tend to
cause lateral displacement of 2 adjacent
planes of atoms with respect to each other

SLIP PLANES

 GRAINS
A microscopic single crystal in the microstructure of a metallic material
 GRAIN BOUNDARY
It is the area where crystals meet. It is the area of mismatch in which
atoms are irregularly spaced creating a weaker non crystalline
structure. Decreases mechanical strength and increases corrosion
 LATTICE
A space lattice is defined as any arrangement of atoms in space in
which every atom is situated similarly to every other atom as a result
of primary or secondary bonds

 FCC

 BCC

WIRE CHARACTERISTICS OF
CLINICAL IMPORTANCE (Kapila and
Sachdeva AJO 1989)
 SPRINGBACK
- Working range
- Maximum elastic deflection
- Maximum flexibility
- Range of activation
- Range of deflection
- Ratio of YS to (E)
- It is a measure of how far a wire can be
deflected without causing permanent
deformation

 LOAD-DEFLECTION RATE
Force magnitude delivered by an appliance and is
proportional to the modulus of elasticity
 FORMABILITY
Ability to bend a wire into loops, coils and stops
wihout fracturing the wire

 BIOCOMATIBILITY
Includes resistance to corrosion and tissue
tolerance to elements present in the wire
 JOINABILITY
The ability to attach auxillaries by welding or
soldering when incorporating modifications to
the appliance

 FRICTION
The preferred wire material for moving a
tooth relative to the wire would be one that
produces the least amount of friction at
the bracket

GOLD ALLOYS
 Popular till 1940’s
 Noble metal
 Type IV commonly used
 Composition:
Gold 55-65%
Platinum 5-10%
Palladium 5-10%
Copper 11-18%
Nickel 1-2%

 Advantages:
Inert metal
High corrosion resistance
Good formability
 Disdavantages
Low YS and (E)
Limited springback
High cost

STAINLESS STEELS
 Accidentally discovered a few years
before FWW
 Strauss and Eduard Maurrer
 Entered dentistry in 1919 – Hauptmeyer –
Krupp’s Dental Polyclinic (‘Wipla’)
 Used as orthodontic wire in 1929

 CARBON STEELS
Binary alloy of Fe and C (<2.1%)
3 types
1. Ferrite – BCC- stable upto 912 deg C
2. Austenite – FCC stable b/w 912-1394
deg C
3. Martensite – BCT

 Classification of Stainless Steels (AISI):
1. Austenitic stainless steel (300 series)
Type 302, 304, 316L (implants) commonly used
FCC structure stable at very high temp above 912
degrees
Cr b/w 13-25% - PASSIVATING EFFECT
C reduced to prevent SENSTIZATION
- STABILIZATION

2. Ferritic stainless steel (400 series)
- BCC microstructure
- Cannot be hardened by heat treatment
- Not readily work hardenable
3. Martensitic stainless steel (400 series)
- Less corrosion resistant
- Used for surgical and cutting instruments

 DUPLEX STAINLESS STEEL
- Consists of micro-structure with both
Austenitic and Ferritic grains
- Contains Mo and Cr with low Ni content
- Improved toughness and ductility

 MECHANICAL PROPERTIES
- High yield strength and high modulus of
elasticity
Yield strength Elastic
Modulus
Springback
Goldberg +
Burstone
275 x 103 25,000 x 103 11.0
Kusy et al 227 x 103 28,000 x 103 8.1

- High load-deflection rate
- Low springback
- High stiffness increases resistance to
deformation
- Cold working increases strength but
reduces ductility
- Stress relief heat tratment

- Annealing can cause recrystallization
- ADVANTAGES:
- Greater springback than gold
- Excellent formability
- Higher yield strength
- Moderate cost
- Low levels of bracket/wire friction (Garner et al,
Kusy et al, kapila)

- DISADVANTAGES:
 Springback lesser than Ti based alloys
 Not as resilient as B-Ti or Nitinol
 High forces are produced that dissipates
over longer periods of time

 MULTI-STRANDED/BRAIDED
WIRES
- Flexible
- Sustain large deflections
- Apply lower forces when
deflected
- Good working range
Can be used during initial levelling
aligning
- PSEUDO-VARIABLE MODULUS
MATERIAL www.indiandentalacademy.com

ROUND
.0155”
.0175”
.0195”
.0215”
RECTANGULAR
.016 x .022
.017 x .025
.018 x .025
.019 x .025
SQUARE
.016 x .016

 Wires used during initial levelling and aligning
should be:
 Flexible – low stiffness
 Good working range
 Sustain large deflections
 Apply low forces when deflected
 High strength to withstand masticatory stresses

STUDIES
 Kusy & Stevens (Angle Orthod. 1987)
- Viable alternative to the new NiTi alloys which are
slightly expensive
- Studied the mechanical properties of triple stranded S.S.
wires and compared them with TMA and Nitinol
- Wire dimensions used
.0150
.0175
.0195
.0215

- .015 triple stranded wire had a greater
working range but delivered very light
forces than Nitinol / TMA
- .0195 triple stranded wire same stiffness
as that of .016 NiTi
- However Ti alloys were Stronger –
reduced distortion over longer spans

 Evans, Jones & Newcombe (AJO.DO 1998)
- Compared 3 commonly used orthodontic
archwires:
- .016 x .022 medium force NiTi
- .016 x .022 graded force NiTi
- .0155 multistranded S.S.
Results: no significant difference in aligning
capability b/w the 3 archwires

PRODUCT CATALOGUE
ORMCO
Force 9
(braided)
D-Rect
(braided)
Respond
(multistranded)
Triple flex
(triple stranded)www.indiandentalacademy.com

GAC International
Wildcat Tricat
Pentacat
HexacatQuadcat
Multibraided

American orthodontics – Twist (triple stranded)
CO-Ax (five strand)
Straight woven (eight- stranded
rectangular wire)
Dentaurum – Dentaflex Triple strand (round &
rectangular)
Six strand Co-axial
Eight strand (braided,
rectangular)

Leone - Twist (straight and preformed
round & rectangular)
Flex (straight and preformed
round)
Unitek - HI-T II Twist Flex (silver
soldered)
Unitek braided wire (8 strand)
Unitek Coxial
TP Orthodontics – CoAx, Pre-Cut CoAx (central
core wire with 5 outer strandswww.indiandentalacademy.com

 AUSTRALIAN ARCHWIRES
- A.J. Wilcock – 1940’s
- Begg technique
- PROPERTIES:
 Ultra-high tensile strength
 Highly resilient
 Zero stress relaxation
 Highly resistant to deformation

 Available in Grades
(in order of
resilience):
- Regular
- Regular plus
- Special
- Special Plus

 Higher grades were developed later over
the last 25 years:
- Premium
- Premium plus
- Supreme

 TP ORTHODONTICS:
- Standard grade – white label
- Standard plus grade – green label
- Premier grade – black label
- Premier plus grade – orange label

 JCO 1988 interview of A.J. Wilcock Jr. by
P.C. Kesling
- Wire should always be straightened to
improve resilience
- Higher grades are succeptible to fracture
therefore decreased formability
- Lower grade wires exhibit better
formability and are more ductile

 Straightening
processes:
- SPINNER
STRAIGHTENING
(Bauschinger effect)
- PULSE
STRAIGHTENING

Pulse straightened – straight lengths

 PROTOCOL FOR BENDING AUSTRALIAN
WIRE

 RECENT ADVANCES IN STAINLESS STEEL:
- Avoidance of Ni due to its allergic potential
- Mn used as alternative
MEZANIUM – SCHEU DENTAL
NONINIUM – DENTAURUM
Ni FREE – FORESTADENT
NoNi – PYRAMID ORTHODONTICS

CHROME COBALT ALLOYS
 Cobalt based alloy
 Elgin watch company (1950’s) - ELGILOY
 COMPOSITION:
COBALT 40%
Cr 20%
Ni 15%
Mo 7%
Mn 2 %
C 0.15%
Be 0.4%
Fe 15% www.indiandentalacademy.com

 TYPES:
- Blue Elgiloy (soft)
 Softest
 Can be bent easily with fingers or pliers
 Can be welded at low temperatures
 Recommended for considerable bending,
soldering or welding
 Excellent for edgewise arches, lingual arches,
retainers and removables
 Heat treatment increases resistance to
deformation

 Yellow Elgiloy (ductile)
 Relatively ductile
 More resilient than blue elgiloy
 Heat treatment increases its resilience
and springback
 Green Elgiloy (semi-resilient)
 More resilient than yellow and can be
shaped with pliers before heat treatment

 Red Elgiloy (resilient)
 Most resilient
 High spring qualities
 Careful manipulation with pliers as it withstands
only minimal working
 Heat treatment makes it extremely resilient – not
recommended
 All adjustments to be made before heat
treatment

 Non heated elgiloy wires have smaller
springback compared to stainless steel of similar
sizes except for Red Elgiloy
 Heat treatment or precipitation hardening
- 482 degrees celsius for 7-12 minutes in a dental
furnace
- Properties similar to stainless steel after heat
treatment
- Higher temp can cause annealing. So use of
temperature indication paste recommended.

 Advantages:
- Greater resistance to fatigue and distortion
- Longer function as a resilient spring
- Better corrosion resistance
- High modulus of elasticity delivers twice
the force of B-Ti and 4 times the force of
Nitinol

 Exhibits good formability before heat
treatment and better springback properties
after heat treatment
 Disadvantage:
Loss in yield strength and tensile strength if
annealed. So weld and solder with
caution.

Applications of Elgiloy
PENTA-MORPHIC ARCH FORMS – Dr. RICKETTS
Yellow Elgiloy – heat treated to maintain arch
form and resilience

RICKETTS UTILITY ARCH
- Blue Elgiloy (.016 x .016), unheat treated;
designed to be used without heat treating

Elgiloy Preformed
natural arches
Elgiloy Preformed
ideal arches

Maxillary anterior
torquing retractor
Double delta space
closure arch leveller-
Ricketts
Double delta space
closure arch leveller-
Ricketts

Bioprogressive Auxillaries - Ricketts

RETAINERS
HAWLEY
RETAINER
MANDIBULAR LINGUAL
RETAINER

 PRODUCTS:
ROCKY MOUNTAIN – Elgiloy
ORMCO – Azurloy
DENTAURUM – Remaloy
UNITEK – Blue Flexiloy
(16x16, 16x22,
18x25, 19x25)
LEONE - Leoloy (blue & yellow)

TITANIUM ALLOYS
 ALPHA TITANIUM
 BETA TITANIUM
 NICKEL TITANIUM

ALPHA TITANIUM
 Developed by A.J. Wilcock Jr. (JCO 1988)
 Pure titanium exists in 2 forms:
 Alpha Titanium (below 885 deg C)
 Beta Titanium (above 885 deg C)
 Crystallographic lattice arrangement differs in
both types
 Alpha Ti – closely packed hexagonal
 Beta Ti – BCC lattice arrangement

 Alpha Ti manufactured by feedback
centerless grinding technique
 COMPOSITION:
Ti – 88.9 %
Al – 7.86 %
Vanadium – 4.05 %

RECTANGULAR
SQUARE
COMBINATIONwww.indiandentalacademy.com

PROPERTIES:
 Less ductile than Beta Ti because it has
fewer slip planes due to its closely packed
hexagonal configuration.
 At oral temp (37 deg C) it has a tendency
to harden by absorbing intraoral free
hydrogen ions to form Ti hydride therefore
becoming brittle

NICKEL TITANIUM ALLOY
 Stoichiometric binary alloy of Ni and Ti
 HISTORY
 Developed by William F. Buehler – research metallurgist
in the late 1950’s
 Naval Ordinance Laboratory, Silver Springs, Maryland 
Naval Surface Weapons Centre
 Accidental discovery
 Studying metals with SME for the US Navy Polaris re-
entry vehicle’s nose cone  space research
programme.
 Nitinol  Nickel Titanium Naval Ordinance Laboratory

 1971 – introduced to orthodontics by
George Andreasen and marketed by
Unitek Corporation as Nitinol™
 Nitinol – Ni 50% and Ti 50%

 Key properties of Nitinol alloys include:
 Large forces that can be generated due to the
shape memory effect
 Excellent damping properties below the
transition temperature
 Excellent corrosion resistance
 Nonmagnetic
 High fatigue strength
 Moderate impact resistance
 Moderate heat resistance
 Biocompatible

 Applications
 Aerospace and naval applications - Nitinol fluid fittings or coupling
have are being used in military aircraft and naval craft.
 Medical Applications - Tweezers for removing foreign objects via
small incisions, anchors for tendon fixation and stents for
cardiovascular applications
 Dentistry - Orthodontic wires, which no not need to be retightened
and adjusted
 Safety devices - Safety valves/actuators to control water
temperature and fire sprinklers
 Other uses include:
 Spectacle frames
 Household appliances and deep fryers
 Vibration control in the form of engine mounts and actuators for
buildings
 Fasteners, seals, connectors and clamps
 Mobile telephone antennaes

Manufacturing Process
 Nickel and titanium are manufactured into Nickel
Titanium alloy by a process of VACCUM
INDUCTION MELTING or VACCUM ARC
MELTING in a furnace.
 Several remelts are required to improve
homogenity
 Powdered alloy  hot pressed to form wires
 Final shape  drawing or rolling
 Predetermined shapes e.g. archform obtained
by heating the alloy in moulds at 500 deg C

Glossary and Properties of Nickel
Titanium alloys
 NiTi exhibits POLYMORPHISM  ALLOTROPY
 NiTi can exist in 2 crystalline structures:
 Austenitic NiTi (A NiTi)
- BCC lattice structure
- High temperature
 Martensitic NiTi (M NiTi)
- Closely packed hexagonal lattice, less
symmetrical
- Low temperature phase

 AUSTENITIC NiTi
 High temp phase
 Rigid and stiffer
 Symmetrical
 Uniform structure –
allows sound waves to
pass thru it easily
 Less dense
 MARTENSITIC NiTi
 Low temp phase
 Flexible
 Less symmetrical
 Boundaries between
regions with different
orientation reduce
vibrations which muffle
the sound
 More dense

 STABILIZED NiTi / Nitinol (Martensitic Niti)
 Introduced to orthodontics by Dr George
Andreasen in 1971 who realised its Shape
Memory potential
 However the SME effect could not be exploited
because it was suppressed during cold working
 Low stiffness compared to austenitic NiTi
 Low force per unit deactivation delivering light
continuous forces

 Martensitic NiTi with fixed composition at
room temperature
 Incapable of demonstrating changes
 Elastic properties due to inherently stable
structure
 Springy wire
 Poor formability

 AUSTENITIC NiTi
 Introduced in 1980’s
 Chinese NiTi – 1985, reported by Burstone and
developed by Tien Hua Cheng and associates at
General Research Institute for non ferrous
metals, Beijing
 Japanese NiTi – 1986 reported by Miura et al,
Furukawa Electric Company Ltd (1978).
 Active austenitic alloys  form SIM or stress
induced martensite
 Superelasticity

 ACTIVE NiTi
- Fixed composition
- Capable of undergoing changes in its crystal
structure when stress/temp is applied
 Active Austenitic
Austenitic Martensitic Austenitic
 Active Martensitic
Austenitic Martensitic Austenitic
stress stress
cold hot

 SHAPE MEMORY
 Andreasen and Morrow have explained it
as the capability of the NiTi wire to return
to a previously manufactured shape when
it is heated through its TTR

SHAPE MEMORY
NiTi
(predetermined shape  archform)
Deformed (martensitic)
cooled
heat

 SUPER ELASTICITY / PSEUDO-
ELASTICITY
 Ability to withstand elastic deformation to
very high degree when compared to other
alloys and return to its original shape
without undergoing plastic deformation

 THERMODYNAMIC PROPERTY
 Refers to the ability of an archwire to return to its
intended shape once heated through its
transition temperature.
 TRANSITION TEMP RANGE
 It is the temperature at which martensitic NiTi is
converted to austenitic NiTi
 To be of clinical value thermodynamic archwires
should have a transition temperature close to
mouth temperature

TWINNING

MARTENSITIC PHASE
TRANSFORMATION

Cell structure during Martensitic Phase
Transformation
twinning
De-twinning

POLAR BEAR WIRE CHILLER

HYSTERESIS
 Transformation from austenite to martensite do
not take place at the same temperature
 This difference is known as hysteresis
 Range for most NiTi alloys is 40 – 60 deg C
 Non linear stress/strain curve where the loading
curve differs from the unloading curve

HYSTERESIS CURVEwww.indiandentalacademy.com

FLATTER LOAD DEFLECTION CURVE FOR A- NiTi
GREATER SPRINGBACK THAN M- NiTi

 Over a considerable range of deflection,
the force produced by A-NiTi hardly varies
 Therefore an initial archwire would exert
about the same force whether it is
deflected a relatively small or large
distance.

STRESS-STRAIN CURVE
FOR SUPERELASTICITY

LOADING AND UNLOADING CURVE FOR A-NiTi

ACTIVATION-REACTIVATION TO UNLOADING FORCE
CHARACTERISTICS

SHAPE MEMORY SUPER ELASTICITY
MARTENSITIC PHASE
TRANSFORMATION
AUSTENITIC  MARTENSITIC  AUSTENITIC
MECHANICAL OR
STRESS INDUCED
THERMALLY
INDUCED AT ORAL
TEMP

 It is difficult to bend A-NiTi wires because they
do not udergo plastic deformation easily.
 But it can be shaped and properties altered if
their temp is elevated
 The superelastic properties of only a section of a
wire can be changed by heat Rx
 The properties of A-Niti have quickly made it the
preferred material for ortho applications where a
long range of activation with relatively constant
force is needed.

COPPER NiTi
 Introduced in 1994 by
Dr. Rohit Sachdeva
 Quarternary alloy
 Nickel
 Titanium
 Copper
 Chromium
 New generation NiTi
with both superelastic
and shape memory
properties

 Advantages of Cu-NiTi over traditional NiTi
alloys:
 More resistant to permanent deformation and
exhibits better springback
 Smaller loading force for the same degree of
deformation
 More consistent forces which are active longer
within the optimal tooth moving range

 Presence of Cu helps to :
 Lower the stress required to deform martensitic
phase
 Decreases hysteresis therefore it does not lose
its recovery load
 Enhances thermal reactive properties of NiTi
 Creates a consistent unloading force which
closely approximates loading forces

 Uses both stress induced and temperature
dependent martensitic transformation
 To exploit superelasticity to its fullest potential
the working temp of the ortho appliance should
be greater than the Af temp
 Differential between Af temp and mouth temp
determines the force generated
 Af temp can be controlled by altering the
composition, thermomechanical treatment and
manufacturing process

 Classified into 4 types based on the Af temp:
 Type I – Af 15 deg C
- not used frequently as it generates very high forces
- clinical indications are few
 Type II – Af 27 deg C
- generates higher forces when compared to Types III and
IV
- in patients with average or higher pain threshold
- normal periodontal health
- where rapid tooth movt is required and the force system
generated is constant

 Type III – Af 35 deg C
- generatesforces in mid range
- patients with low to normal pain threshold
- periodontium is normal to slightly
compromised
- when relatively low forces are desired

 Type IV – Af 40 deg C
- generate tooth moving forces only when mouth
temp exceeds 40 deg C
- for patients who are very sensitive to pain
- compromised periodontal health
- for patients who have long intervals between
appointments or poor co-operation

 ADVANTAGES:
- constant and sustained unloading forces
- decreased hysteresis  equal activation and
deactivation forces
- provides precise transformation temp
- easier to engage into the slot  20% less
loading force than NiTi
- decrease of force is less than NiTi alloys
therefore it continues to work as teeth near their
intended positions

GRADED THERMODYNAMIC
NICKEL TITANIUM ARCHWIRES
 Bioforce Sentalloy
 GAC International
 Unique property of
variable transformation
temperature within the
same archwire
 Graded force delivery
within the same aligning
archwire
 Lighter forces of 80g
anteriorly
 Heavier force of 300g
posteriorly www.indiandentalacademy.com

MEDICAL AND OTHER
APPLICATIONS OF NiTi
Surgical Tissue
spreaders
Brain spatulas
Laser cut tubings
and sheets
Coronary probes

NiTi Products
 ORMCO
- NiTi
- Reverse curve NiTi
- Turbo
- A+ Align wire
- Align SE 200
- Align XF

 3M Unitek
- Nitinol (stabilised martensitic)
- Nitinol SE
- Nitinol Heat Activated

 Rocky Mountain Orthodontics
- Orthonol ( stabilised martensitic)
- Orthonol Super Elastic Nickel-Titanium
- Orthonol Reverse Vector
- Thermanol (heat activated NiTi)

 Masel Orthodontics
- Elastinol
- Bendible Masel Alloy
- Onyx Ultra

 GAC International
- Sentalloy
- Neosentalloy
- Bioforce Sentalloy
- Retranol
- Sentalloy open and closed coil springs

Wires in orthodontics final

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