Wires in orthodontics /certified fixed orthodontic courses by Indian dental academy

WIRES IN
ORTHODONTICS

www.indiandentalacademy.com

INDIAN DENTAL ACADEMY
Leader in continuing dental education


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 CROSSSECTIONAL
ORTHODONTICS

PHASE II

Variation in archwire
material but same
dimension

Beta Titanium, Nickel
Titanium, Stainless
Steel, Cobalt chromium

VARIABLE
MODULUS
ORTHODONTICS

PHASE III

properties (super
elasticity)

Superelastic Nickel
Titanium

PHASE IV

Variation in structural
composition of wire
material

Thermally activated
Nickel Titanium

PHASE V

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



1.
-

HEAT TREATMENT
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):

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
1.


2.
3.
-

Ferritic stainless steel (400 series)
BCC microstructure
Cannot be hardened by heat treatment
Not readily work hardenable
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


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)

Respond
(multistranded)

D-Rect
(braided)


Triple flex
(triple stranded)

GAC International
Wildcat

Tricat
Pentacat

Quadcat

Multibraided

Hexacat

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
www.indiandentalacademy.com with 5 outer strands







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%










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 levellerRicketts

Double delta space
closure arch levellerRicketts

Bioprogressive Auxillaries - Ricketts


RETAINERS

MANDIBULAR LINGUAL
RETAINER

HAWLEY
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

COMBINATION

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 reentry 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
stress
stress
Austenitic
Martensitic
Austenitic
Active Martensitic
cold
hot
Austenitic
Martensitic
Austenitic

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)
cooled
heat

Deformed (martensitic)


SUPER ELASTICITY / PSEUDOELASTICITY
 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 CURVE


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

MECHANICAL OR
THERMALLY
STRESS INDUCED
INDUCED AT ORAL
TEMP
MARTENSITIC PHASE
TRANSFORMATION
AUSTENITIC  MARTENSITIC  AUSTENITIC







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

MEDICAL AND OTHER
APPLICATIONS OF NiTi

Brain spatulas

Surgical Tissue
spreaders

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


Thank you
Leader in continuing dental education


Wires in orthodontics /certified fixed orthodontic courses by Indian dental academy

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