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FRICTION
A force resisting the relative displacement of two contacting bodies in a
direction tangent to the plane of contact is called friction.
It is the force that resists the movement of one surface past another and acts
in a direction opposite the direction of movement. Because of friction, part
of the mechanical energy intended for movement of the two bodies relative
to each other is dissipated as thermal energy
Friction may exist between:
Two solid surfaces
Solid fluid interface
Liquid/fluid layers
Types of friction
Rolling or sliding
Static or dynamic
When two surfaces in contact slide or tend to slide against each other,two components of total force arise:-
Frictional component
Normal force
Normal force:-
Perpendicular to one or both contacting surfaces and also to the
frictional component.
Fixed surface on which the block rests responds only to the weight of
the block with an upward force, perpendicular to the plane contact area.
This force is symbolized by N.
Also signifies the force pushing two surfaces together
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Frictional force :-
Parallel in the direction to the intended or actual sliding motion and
opposes the motion.
2. Static and Dynamic Friction :-
Resistance that precludes actual motion is termed static friction.
That which exists during motion is called Dynamic friction.
Both static and dynamic forms of sliding friction are of orthodontic interest.
Static friction is the component of frictional force that has to be overcome
to initiate motion
Dynamic (kinetic) friction is the component of frictional force that has to
be overcome to maintain motion .
Static frictional force is usually higher than dynamic frictional force
Frictional coefficient( )the law of friction theorized by coulomb statesthat the magnitude of the frictional force F is equal to the product of normal
force N acting perpendicular to the contact surface multiplied by frictional
coefficient
The frictional coefficient depends on the surface roughness of the
combination of the materials involved .it does not depend on the area of
contacting surfaces and varies only slightly with velocity of movement
Coefficient of static friction:
It reflects the force necessary to initiate movement.
Coefficient of Kinetic friction:-
Reflects the force necessary to perpetuate the motion.
It takes more force to initiate motion than to perpetuate it.
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LAWS OF FRICTION :
As early 17th and 18th centuries, Amontons and coulomb were formally
investigating frictional forces. From their efforts, fundamental laws of
friction evolved :-
a) Frictional force (f) is proportional to the applied normal force (N)
multiplied by the coefficient of friction () i.e f = N.
b) Frictional force (f) is independent of the apparent area of contact b/n two
sliding surfaces.
This is because all surfaces, no matter how smooth, have irregularities
that are large on a molecular scale and real contact occurs only at a limited
number of small spots at the peaks of surface irregularities
ASPERITIES :
Spots called Asperities, carry all the load b/n two surfaces. Even
under light loads,, local pressure at the asperities may cause appreciable
plastic deformation of small areas beacuse of this the true contact area is to a
considerable extent determined by the applied load and is directly
proportional to it
C) Frictional force is independent of the sliding velocity (v) i.e the so called
coulombs 3rd law.
Orthodontic tooth movement during space closure is achieved through
two types of mechanics:-
1. Friction
2. Friction free or frictionless
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Friction Mechanics (Sliding Mechanics) - It involves either :-
Moving the brackets along an archwire
Sliding the archwire through brackets and tubes.
ROLE OF FRICTION IN SLIDING MECHANICS :
Most fixed appliance techniques involve some degree of sliding
between bracket and archwire.
When sliding mechanics are used, friction occurs at the wire bracket
interface. Some of the applied force is therefore dissipated as friction and the
remainder is transferred to supporting structures of the tooth to mediate tooth
movement.
Maximum biological tissue response occurs only when the applied
force is of sufficient magnitude to adequately overcome friction and lie
within the optimum range of forces necessary for movement of the tooth
in vitro resolution of static and kinetic frictional resistance into
separate and distinct phases is arbitrary and potentially misleading because
at low velocity, such as exists in orthodontics, static and kinetic frictional
resistances are dynamically related.
The first two laws are usually obeyed in orthodontics whereas the
third usually is not.
In wire/bracket couples of stainless steel/stainless steel and NiTi/ stainless
steel, the third law is obeyed; however for Co-Cr/SS and B-Ti/SS couples,
the values of u slightly increase and markedly decrease respectively with
velocity.
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If a stationary mass (M) is at equilibrium (at rest with zero velocity
V0) on a solid flat surface (S), the contact between the mass and the surface
is the result of a normal force (F) acting on the mass
The normal force F may be the net system force or the weight of
mass M. The interfacing area between mass M and surface S may be
approximated as the nominal area by the macroscopic surface area of M in
contact with S To overcome the static frictional resistance from the rest position, a
minimum pulling or shear force (f), which is parallel to the contact surface
of the nominal area, is required to move mass M at velocity V. This static
frictional resistance (fs) is equal to the normal force or load (F) multiplied by
a coefficient of static friction .Once a steady sliding motion of a constant
velocity (Vc) is achieved, then a minimum force to overcome the kinetic
frictional resistance (fk) is required to maintain velocity Vc of mass M. The
kinetic frictional resistance is equal to the normal force or load (F)
multiplied by a coefficient of kinetic friction (fk).
Static friction (occurring instantaneously up to the onset of sliding)
and kinetic friction (occurring continuously after the onset of sliding) are
two distinct phases that by definition cannot coexist. The classic Amontons-
Coulomb laws relate static and kinetic friction as follows:
1. s and k are independent of F and area;
2. s and k are materials dependent; and
3. usually k < s.
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The two distinct frictional phases (ie, fs and fk are defined by zero
velocity Vo and constant sliding velocity Vc, respectively.
The transition from zero velocity Vo to constant sliding velocity Vc
must involve an acceleration of mass M. The acceleration phase is of
particular interest when Vc approximates Vo (ie, low velocity friction).
Refinement of the Amontons-Coulomb principles is required
especially when it becomes evident that Vc approximates Vo. Apparent
deviation from the Amontons-Coulomb principles includes
Time-dependency of the static coefficient S(t) (ie, static coefficient as
a function of time) and Velocity-dependency of the kinetic coefficient K(V) (ie, kinetic
coefficient as a function of velocity).
The Stick-Slip Phenomenon
At low speeds a Stick - slip phenomenon may occur as enough
force builds up to shear the junctions and a jump occurs, then the surfaces
stick again until enough force again builds to break them.
A single stick-slip cycle involves a stick state associated with elastic
loading of the system, followed by a sudden slip corresponding to stress
relaxation.
Static Coefficient as a Function of Time {s (t)}
The static coefficient of friction varies as a function of increasing
time t before the onset of sliding.
Increases in the coefficient of static friction, as a function of stick
time vary over a wide time interval range
The longer a mass M is at rest on a flat surface S (or an archwire at
rest on a bracket) the greater the resistance to pulling force fparallel to the
contact surface of nominal area.
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Age strengthening of localized point contacts among the asperities of
mass M and surface S is correlated with experimental observation of slow
plastic deformation occurring at the stressed asperities, leading to an
increasing effective interface area as a function of time
When plastic deformation occurs at the level of the softer asperities,
the frictional force becomes a function of shear stress localized to point
contacts among surface asperities of mass M and surface S As a result,
increases in both area and shear produce a proportionate increase in f.
Assuming that the normal force F (ie, load) remains constant, the
coefficient of static friction increases as a function of timeKinetic Coefficient as a Function of Velocity
The second refinement of the Amontons-Coulomb principles is that
constancy of the kinetic frictional coefficient is dependent on maintenance
of a steady sliding velocity Vc. Different materials exhibit unique kinetic
frictional characteristics as a function of velocity
Within very low velocity ranges, most materials exhibit decreasing
coefficients of kinetic friction as the low-velocity range increases (ie,
velocity weakening).
Subsequent velocity strengthening as velocity progressively increases
beyond the low-velocity range.
At low velocity, such as occurs with in vivo tooth movement, steady
sliding instability may lead to oscillations of motion characterized by cycles
of sticking and slipping.
Stick-slip motion, as observed over a broad velocity range in frictional
sliding, can potentiate consequences resulting in noise (chatter), energy loss
(friction), surface damage (wear), and component failure (breakage).
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Stick-slip processes are caused when the frictional force does not
remain constant as a function of some other variable such as distance, time,
or velocity
Orthodontic evidence of repetitive stick-slip oscillations at the
archwire-bracket interface may be inferred from scanning electron
micrographs that reveal permanent deformation of archwires subjected to
intermittent binding and sliding at bracket surfaces.
Loss of Applied Force
Orthodontic tooth movement is dependent on the ability of the clinician to
use controlled mechanical forces to stimulate biologic responses within theperiodontium. It has been concluded that the rate of tooth movement
increases proportionally with increases in applied force up to a point, after
which additional force produces no appreciable increase in tooth movement.
With orthodontic mechanotherapy, a biologic tissue response with
resultant tooth movement will occur only when the applied forces
adequately overcome the friction at the bracket wire interface.
Mechano therapy to move a tooth via a bracket relative to a wire
results in friction localized at the bracket wire interface that may prevent the
attainment of an optimal force in the supporting tissues.
The portion of the applied force lost because of the resistance to
sliding can range from 12% to 60%.
If frictional forces are high, the efficiency of the system is affected,
and the treatment time may be extended or the outcome compromised
because of little or no tooth movement and/or loss of anchorage.
The amount of frictional resistance will impact on the moment to-
force ratios of the teeth and, consequently, their centers of rotation.
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When the archwire and the bracket have clearance, classical friction
exists as the only component to the resistance to sliding.
When clearance disappears and an interference fit occurs between the
bracket and the arch wires, binding arises as a second component to the
resistance to sliding superimposed on the classical friction.
Movement of the crown mostly precedes displacement of the root
because a tipping moment is placed on the crown of the tooth
This tipping leads to increased friction from binding between the
archwire and bracket restricting movement of the entire tooth.
Friction is influenced by :-
- the nature of contacting surface ,but is independent of area of contact, this
is due to the interlocking of surface irregularities
-the extent to which asperites on the harder material plough into the surface
of the softer material
Total frictional resistance is the sum of
-Force necessary to shear all junctions
-Resistance caused by interlocking roughness
-Ploughing component of total frictional force
Orthodontic Model of friction
BETWEEN ARCHWIRE AND BRACKET
Sliding friction is generated between arch wire and bracket when
The wire guides the bracket during M-D movement of an
individual tooth.
The wire is slipped through posterior crown attachment in, e.g:-
Retraction of anterior dental segment.
Possible Components of this force are :-
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Engagement of arch wire in brackets that are out alignment.
Ligatures pressing the wire against base of slot
Active torque in rectangular wire
Bodily tooth movement in which tipping tendency is resisted by two
point contact between the bracket and archwire.
The relative magnitudes of these components of frictional force vary
according to the clinical situation
VARIABLES AFFECTING FRICTIONAL RESISTANCE DURING
TOOTH MOVEMENTA) PHYSICAL :-
1) Archwire
a. Material
b. Cross sectional shape/size.
c. Surface texture.
d. Stiffness.
2) Ligation of archwire to bracket
Ligature wires.
Elastomerics
Method of ligation : Method of tying, bracket designs to limit force of
ligation, self ligating brackets
2) Bracket
a. Material
b. Manufacturing process : Cast or sintered stainless steel.
c. Slot width and depth
d. Design of bracket : Single or twin
e. First order bend ( in - out)
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f. Second order bend (angulation)
g. Third order bend (torque
Orthodontic appliance
Interbracket distance.
Level of bracket slots between adjacent teeth.
Forces applied for retraction.
B. BIOLOGICAL
Saliva
Plaque.
Acquired pellicle.
Corrosion
With so many variables affecting frictional force, it is difficult to accurately
determine them in a clinical situation. the problem is further complicated by
wide array of brackets, wires and ligatures available that provide a multitude
of combinations for use during various stages of orthodontic treatment.
EXPERIMENTAL METHOD USED TO STUDY FRICTION :
1. SIMULATED TOOTH MOVEMENT:
Most of studies within orthodontic literature have carefully simulated
different clinical conditions b/n bracket and archwire to measure sliding
frictional resistance.2. SURFACE ROGHNESS :
Some studies have quantified surface roughness of various bracket
and archwire materials.
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Most common method of estimating surface roughness
SPECULAR REFLECTANCE involves determination of amount of light
that is reflected back from a surface.
Smooth surface :- Reflects much of light shone on it in a narrow
pattern.
Rough surface :- Scatters light and reflects it back in amore dispersed
pattern.
3. CONTACT FLATS :-
Coefficients of friction have also been evaluated using orthodonticwire held between two parallel plates (Contact flats) made of material
similar to that used in orthodontic brackets such as SS, polycrystalline
alumina or Teflon various levels of normal force were applied to plates and
wire is pulled through them to measure friction generated.
4. DESCRIPTIVE STUDIES :-
These have involved discussion of frictional resistance of brackets
and wires based on clinical experience and anecdotal information.
EFFECT OF BRACKET MATERIAL, DESIGN, MANUFACTURING
PROCESS ON FRICTION:-
Various Bracket materials today available are :-
1. Stainless steel - Cast Sintered
2. Ceramic brackets
Polycrystalline alumina
Single Crystalalumina (SCA) (i.e Sapphirc)
3. Zircoma brackets
4. Plastic brackets
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1. Stainless Steel Brackets :-
Most popular bracket material Stainless steel brackets are associated
with lowest frictional force values amongst the available bracket materials.
Kapila et al (1990)
Evaluated friction b/n Edgewise SS brackets and orthodontic wires of
4 alloys (SS, Co- Cr, NiTi and B-Ti)
Mean frictional forces with conventional cast stainless steel brackets
ranges between 40-336 g.
Level of frictional forces observed in :-
0.018inch SS brackets Ranged from 49g with 0.016 inch SS wires
in narrow single brackets to 336g with 0.017 x 0.025 inch B-Ti wires wide
twin brackets.
0.22 inch SS brackets Friction ranged from 40g 0.018 inch SS
wires in narrow brackets to 222g with 0.019 x 0.025 inch NiTi wires in wide
brackets.Several SS bracket wire combinations generated low levels of
frictional forces less than 100g.
SINTERED STAINLESS STEEL BRACKETS
Sintering : Process of fusing individual particles together after compacting
them under heat and pressure.
Sintering allows individual bracket to be premolded in a smooth
streamlined manner. The SS particles are compressed in a contoured smooth
rounded shape as apposed to older casting procedure in which milling or
cutting process left sharp angular brackets that were bulky and rough.
Sintered edgewise brackets
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RMO Mini Taurus. (RMO Mini Taurus Synergy
Unitek Mini Twin.)
Sintered SS brackets produce significantly lower friction than cast
stainless steel brackets overall friction of sintered SS brackets is approx 40%
- 45% less than friction of conventional cast stainless steel brackets.
2) CERAMIC BRACKETS :
With ceramic brackets, most of wire size and alloy combinations with
both 0.018 and 0.022 inch slot sizes demonstrate significantly higher fric-
tional forces than with SS brackets.
Characteristics of Ceramic Bracket Material or Slot Surface Texture:
Highly magnified views have revealed numerous generalized small
indentations in the ceramic bracket slot while the SS bracket appeared
relatively smooth.
Hardness of the material
All currently available ceramic brackets are composed of Aluminium oxide.
Aluminium oxide is extremely hard.
The rough but hard ceramic material is likely to penetrate the surface
of even a steel wire during sliding, creating a considerable resistance and
this is worse with titanium wires
The interaction of metal wire - ceramic slot interface leads to leveling
of ceramic slot. This results in drop in friction as ceramic peaks are removed
and valleys become clogged with metal
Types of Ceramic brackets :
Single Crystal alumina (SCA)
Polycrystalline alumina (PCA)
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Monocrystalline alumina :- Single crystal ceramic brackets are
derived from large single crystals of Alumina which are milled into desired
shape and dimensions by ultrasonic cutting, diamond cutting or combination
of two techniques. Because Alumina is third hardest known material, this
procedure is difficult and may explain granular and putted surface of
ceramic brackets seen in SEM.
Polycrystalline brackets - have also been observed under SEM to
possess very rough surfaces which actually scribed grooves into the archwire
Monocrystalline brackets were observed to be smoother than PCA
brackets but their frictional properties were comparable.
The most apparent difference b/n polycrystalline and single. crystal
brackets is their optical clarity. Single crystal brackets are noticeably clearer
than PCA brackets which tend to be translucent
Clinical significance :-
Combination of metal archwires and Ceramic brackets produce high
magnitudes of frictional force; therefore greater force is needed to move
teeth with ceramic brackets compared to SS brackets in sliding mechanics.
Since ceramic brackets on anterior teeth are often used in
combination with SS brackets and tubes on premolar and molar teeth,
retracting canines along archwire may result in greater loss of anchoragebecause of higher frictional force associated with Ceramic than SS
brackets.To reduce frictional resistance Ceramic brackets with smoother slot
surfaces and consisting of metallic slot surface are available.
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ZIRCONIA BRACKETS :
Besides high friction, Ceramic brackets have very low fracture
resistance Due to their brittle nature even smallest crack or flaw can
propagate rapidly through the material.
Zirconia brackets have been offered as an alternative to ceramic
brackets since surface hardening treatments to increase fracture toughness
are available for Zirconium oxide.
Frictional coefficients of Ziconia brackets were found to be greater
than or equal to those of poly crystalline alumina brackets in both dry and
wet states (Keith et al , 1994). Surface changes consisting of wire debris and
surface damage in Zirconia brackets after sliding of archwires were also
observed.
PLASTIC BRACKETS :
In an attempt to create an esthetic bracket with lower frictional
resistance and easier debonding features than ceramics a varity of new,
ceramic reinforced plastic brackets with or without metal slot inserts have
been introduced.
Plastic brackets can deform because of compression from ligation and
thus binding of the wire, and higher frictional resistances were recorded than
stainless steel brackets. Recently introduced composite brackets with andwithout metal slots faired better in friction studies showing lower frictional
resistance than both ceramic and stainless steel brackets in one of the
studies.
EFFECT OF BRACKET WIDTH ON FRICTION
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Effect of bracket width on friction has been controversial
Some studies have found that altering bracket width made no
difference in friction (Peterson et al 1982, Andereasen et al, 1970).
Frictional resistance has been reported to increase with increase in
bracket width (Tidy 1989, Drescher et al, 1989).Whereas others found that
frictional resistance decrease as bracket width increased.
Franks and Nikolai (1980):- Related greater friction with wider
brackets to the fact that binding occurs frequently with wider brackets.
Omana et al suggested that with a narrow bracket the tooth could tip
considerably before binding could occour,and once binding occurs it was of
severe nature
Kapila et al (1990 and Ogata et al (1996) :
Suggested that with a wider bracket the elastomeric ligature used was
stretched more than with a narrower bracket which exerted a greater normal
force on the wire
Bracket slot size may not influence the frictional resistance,
Some studies suggested that frictional resistance decreased as slot
size increased from 0.018 inch to 0.022 inch because of reduced binding
probably from increased wire stiffness. And also because of the increased
play in the slot with final archwire.
ADDITIONAL DESIGN FEATURES IN BRACKETS TO REDUCE
FRICTION
Bumps on the bracket slot walls and floor which decreased surface
contact with the wires, help decreased friction in bracket wire interface.
(Ogata etal)
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Begg bracketshaveachieved low friction by virtue of an extremely
loose fit betweena round archwire and a very narrow bracket, but this is at
the cost of making full control of tooth position correspondingly more
difficult. Some brackets with an edgewise slot have incorporated shoulders
to distance the elastomeric from the archwire and,thus, reduce friction, but
this type of design also produces reduced friction at the expense of reduced
control.
EFFECT OF SECOND ORDER DEFLECTION OF FRICTION
Second order defection of wire b/n brackets held in series can have
significant effects on brackets wire friction.
Several studies have found that increasing the angulation between
bracket and wire produced greater friction.
Frank and Nikolai (1980) :- Found that frictional resistance increased in a
nonlinear manner with bracket angulation.
With brackets out of alignment archwire stiffness, strongly influences
forces normal to the points of contact and hence friction.
In a well aligned arch forces that result from archwire deflection are
not important and friction is largely independent of archwire stiffness.
Ogata et al (1986)Evaluated the effects of different bracket wire
combinations and 2nd order deflections on kinetic friction. The brackets
were offset deflecting wire in increments of 0.25 mm.
As 2nd order deflection increased frictional resistance increased for
every bracket wire combination - With lower deflections a smooth sliding
phase appeared in which friction increased in approximate a linear manner.
As deflection increased further a binding phase occured in which
friction increased at a much greater rate and was not necessarily linear.
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Binding generally occured between 0.75 and 1.00 mm of 2nd order
deflection.
The relationship between frictional resistance and second order
angulation may not be linear and may become more important as the
angulation increases. The active configuration for binding occurred between
3 to 7.
When tipping occurs the frictional resistance of nickel-titanium has
been reported to be less than stainless steel,
Because of the lower modulus of elasticity of nickel-titanium
compared with stainless steel, lower normal force that was induced by
binding occurred resulting in less resistance to sliding.
Active third order torque with rectangular wires would increase the
friction even more.
Similarly, greater friction with larger rectangular wires results from
the possible introduction of torque because an 0.021x 0.025 wire has 3.9
of play compared with an 0.018 x0.025 wire that has 14.8 of play when
engaged into an 0.022 bracket slot
EFFECT OF ARCH WIRE
WIRE ALLOY:-
The role of wire alloy in frictional characteristics of sliding
mechanics has been extensively studied.
Most studies have found SS wires to be associated with the least
amount of friction and Beta titanium with the most. from lowest to highest
friction SS, Co - Cr, NiTi and B-Ti.
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Frank and Nikolai (1980) :- Found that SS wires had less friction
than nickel titanium at non binding angulations, but as the angulation
increased and binding was present reverse was true.
SURFACE TEXTURE :-
Specular reflectance studies have shown that SS wires have the
smoothest surface followed by Co-Cr, B-Ti and NiTi wires in order of
increasing surface roughness.
Since B-Titanium had the most friction but was not the roughest Kusy
and Whitly concluded that one cannot use surface roughness as an indicator
of frictional characteristics in sliding mechanics.
NiTi has greater surface roughness Beta Ti has greater frictional
resistance.
As the titanium content of an alloy increased its surface reactivity increases
and surface chemistry is a major influence on frictional behaviour.
-Ti at 80% Titanium has higher coefficient of friction than NiTi at
50% titanium. There is enough titanium reactivity for wire to COLD
WELD itself to steel bracket and therefore -Ti wire exhibits more of stick
slip phenomenon.
ION IMPLANTATION :-
Alteration of the surface of titanium wires by implantation of ions
into the surface.
Gas ions (Nitrogen and Oxygen) are implanted in to the wire surfaceresulting in a surface that is extremely hard.
Ion implantation produces no interface b/n the coating and the wire
neither does it alter the dimensions of the wire.
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Burstone and Farzin Demonstrated that ion implanted -Ti wires
produced about the same level friction as SS wires.
Braided arch wires
Berger (1990) Studied friction produced by 0.0175 inch braided
archwire in a 0.022 slot and found very high friction levels.
1.5 times compared to 0.018 inch round SS wire with elastomeric
ligation. 5 times with stainless steel ligation.
This can be attributed to interwoven pattern and irregular surface of
Braided arch wire.
Mechanical interlocking of the archwires with the edges of the
bracket slot increase friction as the wire moves relative to the bracket.
Efforts to reduce friction with teflon coating are being made
WIRE SIZE
Several studies have found that an increase in wire size is to be
associated with increased bracket wire friction .
The main reason for the increase in friction as the wire size increased
can be attributed to an increase in the stiffness of the wire.Wires of greater
stiffness will create a greater normal force with binding of the archwire with
the edges of the bracket.
Rectangular wires produce more friction than round wires. At
nonbinding angulations the contact area between bracket and archwire is
important factor in friction and would therefore expect more friction with
rectangular wire. (Nanda)
Placement of a rectangular wire can dramatically increase the friction
because of the concomitant increase in wire stiffness.(tidy)
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At greater angulation of the bracket, the determining factor is the
point at which the wire contacts the edge of the bracket
With round wires bracket slot can bite into the wire at one point
,causing an indentation in the wire
With rectangular wire the force is distributed over a large area i.e the
entire faciolingual dimension of the wire, resulting in less pressure and
therefore less resistance to movement
Frank and Nikolai (1980)Found that an 0.020 inch wire was
associated with more friction than 0.017 x 0.025 inch wire.
ROLE OF WIRE STIFFNESS AND CLEARENCE
Mechanically speaking orthodontic archwires are elastic beams
supported at either one or both ends.
Wire stiffness depends upon :-
Diameter or cross section of the wire
Length of beam.
e.g. Doubling length of cantilever beam decreases stiffness by 8 times.
By altering inter-bracket distance stiffness of wire can be altered.
During canine retraction in a premolar extraction case the increased inter-
bracket span of the unsupported wire over the extraction site decreases the
stiffness of wire.
Retraction force therefore has a greater chance of deflecting the wire
resulting in buckling. To prevent such deflections of the wire that may
increases friction and chances of bracket binding, diameter of wire should be
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increased to compensate for decrease in stiffness when inter bracket span is
greater than normal.
Another reason for not using flexible small size archwires during
sliding canine retraction is that flexible small size archwires can deflect as
canine crown tips distally which can lead to incisor extrusion.
CROSS SECTIONAL DIMENSION IN DIRECTION OF BENDING
0.017 x 0.022 inch wire placed edgewise is more springy in vertical
dimension than when placed in ribbon mode
Drescher et al (1989) Stated that vertical dimension of the wire was an
important factor in frictional resistance
NATURE OF END SUPPORTS OF A BEAM
Rigidly supported beam at both ends has stiffness 4 times as
compared to cantilever beam.Therefore During sliding space closure the
wire therefore should be tied into the supporting brackets tightly to increase
stiffness.
e.g. During canine retraction premolar and lateral incisor brackets should be
tied tightly to the archwire
CLEARANCE OF ARCH WIRE :-
Adequate clearence should be provided between bracket and wire to
prevent binding. Clearance or play in 2nd order i.e tipping depends upon slot
size, Bracket width, Archwire size
3RD ORDER PLAY IN RECTANGULAR ARCH WIRES.
In 0.018 slot 16.7 for 0.016 x 0.016 wire 4.5 for 0.017 x 0.025
wire.
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0.022 27.4 for 0.016 x 0.022 inchwire.
2 for 0.0215 x 0.028 wire.
EFFECT OF LIGATION TECHNIQUE ON FRICTION:-
The normal force exerted by ligature has a significant influence in
determining the frictional resistance developed within an orthodontic
appliance.
Ligation technique signifies the force that pulls the wire into the
bracket.
Elastomeric modules:
Affected by the oral environment.
Demonstrate stress relaxation with time
Stainless steel ligatures:
Can be tied either too tight or too lose.
Properties of an ideal ligation system
Be secure and robust;
Ensure fullbracket engagement of the archwire;
Exhibit low friction betweenbracket and archwire;
Be quick and easy to use;
Permit highfriction when desired;
Permit easy attachment of elastic chain;
Assist good oral hygiene;
Be comfortable for the patient
Edwards et al (1995) : Compared the effect of 4 ligation techniques.
E modules tied conventionally and in figure 8 pattern.
Stainless steel ligatures.
Teflon coated ligatures.
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Static frictional resistance greatest in figure of 8 emodules ; -
No significant differences between frictional resistance offered by
conventionally tied E-modules and steel ligature.teflon coated ligatures
produce lowest friction.
Shivapuja et al (1994) : E-modules produced greater frictional resistance as
compared to steel ligature ties. This combined with rapid rate of decay for
these E-modules and their predliction for harboring large quality of plaque
suggests little merit in their use especially in sliding mechanics
NEW SLICK ELASTOMERIC MODULE SYSTEM :
A new slick elastomeric module system incorporating metafasixtechnology (TP orthodontics) has recently been introduced claims to
combine ease of use with low friction.
The new slick E - modules reduced friction by upto 60% compared
with their regular counterparts when tied normally.
BRACKET DESIGNS LIMITING FORCE OF LIGATION:
Three brackets were introduced to restrict the amount of force placed
on wire by the ligature.
American friction free bracket (Am. Orthod)
GAC shoulder bracket (GAC central I slip NI)
RMO synergy bracket (RMO)
These brackets generated lower mean frictional forces at 2nd order
deflections of 0.00 & 0.25 mm than conventionally ligated brackets.
E.g. Synergy bracket:
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Includes 6 wings 3 on each side of bracket slot. The lateral wings
may be included in ligation for correction of rotation of teeth but only center
wings may be ligated during sliding mechanics to reduce force of ligation.
SELF LIGATING BRACKETS:
Orthodontic brackets are now available that possess the feature of self
ligation. First Edgewise self ligating bracket Russelhock (1946).
SELF LIGATING BRACKET SYSTEMS : LIGATIONS SYSTEM
* Edgelok bracket (Ormco) 1972 Sliding cap
* Speed bracket (Strite industries) - 1980 Spring clip
* Activa bracket (A company) - 1986 Lever arm.
Damon 1994 vertical slide
Berger (1990) Compared between speed bracket and stainless steel bracket
revealed that friction with self ligating bracket was between 12% and 23%
that of stainless steel bracket irrespective of wire shape and ligation
technique.
The unique anatomic characteristic associated with speed bracket -
highly resilient and flexible spring clip was determined to be causative factor
in critically lowering level of applied force.
Shivapuja et al (1994)
Self ligating brackets displayed significantly lower level of friction
both static and dynamic as compared to conventional ligating system.
Significantly less chair side time was required for archwire removal
and insertion with self ligating system as compared to conventional ligating
systems.
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Kapur found dramatically lower frictionwith both stainless steel and
nickel-titanium wires for Damonbrackets compared to conventional brackets
Advantages of self ligating system
More certain fullarchwire engagement;
Low friction between bracket and archwire;
Less chairside assistance;
Faster archwire removal and ligation
Gac in ovation bracket similar in design to speed bracket with sliding
spring clip.
The clip places a diagonally
directed lingual force on the wire, which
does not contribute to any third order interaction between the wire corners
and the walls of the bracket slot, which is the origin of torquing force
This increasesthe slop between the rectangular wire and theslot, and also
reduces the moment arm of the torquing mechanism.
Activa bracket with clip Clip retaining groove is visible on the
gingival surface.
With low friction, the net tooth-moving forces are more predictably
low and the reciprocal forces correspondingly smaller.
Lower net forces deflect archwires less and, therefore, facilitate
release of binding forces between wire and bracket, enhancingsliding of
brackets along a wire.
BIOLOGICAL FACTORS:
I. Effect of saliva on kinetic friction:
It has been suggested that saliva substitute serves as an excellent
lubricant in sliding of the bracket along the wire.
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BAKER ET AL (1987):
Using an artificial saliva substitute found a 15% - 19% reduction in friction.
KUSY ET AL (1991):
Found that saliva could have lubricious as well as Adhesive
behaviour depending on which archwire bracket combination was under
consideration
SS WIRES: Showed an adhesive behaviour with saliva and a
resultant increased in coefficient of friction in wet state.
-TI wires: In wet state kinetic coefficients of friction were 50% ofthe values in dry state.when sliding through SS brackets, the titanium rich
oxide layer in -Ti archwire breaks down, reacts, adheres and breaks away
,resulting in a stick-slip phenomenon.
Hypothesis: Saliva probably acts by preventing solid to solid contact.
CLINICAL SIGNIFICANCE:
In an adult patient: H/O of Xerostomia or decreased salivary, Oral
radiation therapy, Anticholinergic medication.
- Should be noted as possible factors in varying force levels necessary to
move teeth.
Surface Characteristics Affecting Friction
Most metals are subject to oxidation and an associated oxide layer
growth. Friction between specific sliding metallic surfaces significantly
decreases with proportionate increases in oxide layer thickness, although
sliding characteristics in the presence of an oxide layer vary from material to
material.
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Bioflims may reduce the coefficient of friction by producing a
boundary lubrication effect through salivary protein adsorption and plaque
accumulation.
CLINICAL SIGNIFICANCE OF FRICTION
Based on information gathered from studies of friction several points of
clinical significance can be identified.
An appreciation of magnitude of friction is crucial for the
orthodontist who employs sliding mechanics during treatment - With best of
wire bracket combinations atleast 40g of friction must be included in force
applied to initiate tooth movement. New bracket designs and manufacturing techniques have been
introduced to decreased the amount of friction generated between wire and
bracket slot.
- Sintered SS brackets.
- Bracket designs limiting force of ligation
Self ligating brackets
Clinicians using esthetic tooth colored brackets - important to know
the level of friction generated by these brackets before initiating tooth
movement
Selection of wire shapes and sizes:
e.g.: 0.018 inch SS steel best choice for canine retraction in 0.022 slot.
- If overall torque control is required:
0.016x 0.022 inch - 0.018 slot.
0.019x0.025 inch - 0.022 slot.
Archwire can also be thinned down in region distal to canine so as to further
facilitate movement. Care must be taken not to over reduce the wire
dimensions which could decreased strength of wire
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Complete leveling of arch - important factor in reducing friction
during tooth movement. e.g.: Space closure using 0.019 x 0.025 wire in
0.022 slot.
Before starting space closure rectangular wires need to be place for at least 1
month.
- To ensure proper leveling and freedom from posterior torque pressure.
Sliding mechanics can proceed smoothly
- To optimize use of sliding mechanic sufficient time must be allowed for
distal root movement to occur.
- A common mistake is to change the E-chain too often thus maintaininghigh force levels and a M/F ratio that produces distal tipping only.