Date post: | 03-Jun-2018 |
Category: |
Documents |
Upload: | amber-williams |
View: | 221 times |
Download: | 0 times |
of 6
8/11/2019 A Tribological Study of a Series of Retrieved
1/6
A tribological study of a series of retrieved
Accord knee explants
e.EIII;;iez*, J. Fisher*, D. Dow son*, S.A. Sampath, R. Johnson* and
.
*Department of Mechanical Engineering, University of Leeds, Leeds LS2 9JT, UK;
University Departm ent of Orthopaedics and Accident Surgery, U niversity of Liverpool,
Liverpool, UK; *Knee Research U nit, Arrowepark Hospital, U pton, Wirral, Merseyside,
L49 5PE, UK;
* *DePuy International Ltd., St Anthony s Road, Leeds LSll SDT, UK
ABSTRACT
A tribological s y of a series of 27 retriev ed Accord meniscal bearing knee joints has been carried out. Ihe roughness of
the articulating sufaces of the men al and the femoral componen ts was investigated, and the penetration into the
polyethylene meniscal comp onent was determined. There was generally little damage to the highly polished metallic
femoral components. A general polishing and smoothing of the ultra high molecular weight polyethylene meniscal
compon ents was observed, although there was some subsequent deterioration of
the
olyethylene surfaces in certain cases.
h e penetration rate of thefemoral componen ts into the menisci was low, and was found to be similar to that reportedfor
other m eniscal k nee joints.
Keywords: Tribology, retrieval, knee prostheses
Med. Eng. Phys., 1994, Vol. 16, 223-228, May
INTRODUCTION
The natural kn ee offers a complex range of move-
ments with 150 of motion in flexion-extension,
rotation, and translation in the anterior-posterior
direction. In the more widely used total condylar
artificial knees this range of movem ents is achieved
by having relatively low conforming tibia1 and
femoral components . This produces high stresses in
the contact. In certain knee designs the high cyclic
contact stresses can cause sub-surface fatigue and
structural failure o f the ultra high molecular weight
polyethylene (U HM WPE) compo nent3. In some
cases inadequate
mechanical properties and
poor quality UHM WPE have been acknowledged
as accelerating factorsk7. Sub-surface fatigue can
initiate several millimetres into the UHM WPE at the
position of the maxim um shear stress, with cracks
propagating to the surface causing com plete failure
and break up of the UHMW PE component. This
type of failure has been widely described as delamin-
ation in the literature8~g. In addition structural failure
can also initiate from stress concentrations arising
from the metal tibia1 support or tray, which can lead
to the complete breaking up of the polyethylene
compo nent. It is important to emphasize that this
mode of failure and wear is not primarily a surface
wear process, as it is not caused by relative motion of
the surface asperities, and it initiates in the bulk of the
material. In some total condylar knees it has been
possible to reduce the levels of contact stress that
cause structural failure, by increasing the conformity
Correspondence and reprint requests: Dr J.L. Hailey
0 1994 Butterworth-Heinemann for BES
1350-4533/94/03223-06
of the compon ents, but this can restrict the range of
movem ents an d impose biomechanical constraints.
The meniscal bearing knee offers an alternative
approach to overcoming the desi
ated with total condylar knees
p problems associ-
.
Memscal bearing
knees achieve a wide range of motion by allowing
articulation at both the femoro-meniscal and the
tibio-meniscal surfaces. Figure 7 shows an Accord
meniscal knee. The femoro-meniscal bearing surfaces
are conforming and cylindrical in shape which gives
rise to a large area of contact on both cond yles in a
correctly aligned knee. The tibio-meniscal surfaces
are conical in shape and allow rotation of the
polyethylene meniscal comp onent with respect to the
tibial tra
.
In most components the translation of the
menisca ly omp onent is constrained by a pin through
the apex of the truncated conical surface. Thu s the
Accord meniscal knee permits flexion-extension at
the femoro-meniscal bearing surface, and rotation at
the tibio-meniscal surfaces. This allows more highly
conforming bearing surfaces to be used and it has
been postulated that reduced contact stresses may
reduce the incidence of early structural failure and
perhaps reduce the volume of wear debris generated
in the long term. The purpose of this study was to
investigate the tribological character istics of a series of
retrieved Accord meniscal knees, and in particular
focus on the condition of the UHM WPE and the
femoro-meniscal wear surfaces.
MATERIALS AND METHODS
A total of 768 Accord knees Figure
7)
have been
implanted at Arrowepa rk Hospital since a clinical
8/11/2019 A Tribological Study of a Series of Retrieved
2/6
Tribological tudy
o
retrieve knee expiaat s:J.L. Hai lq et al.
Figure Photograph of the Accord meniscal bearing knee
Figure
2 Photograph of an explant which suffered from metal-to-
metal contact during articulation
trial of the knee began in 1982, of which 73 have now
been revised. The majority of these were revised for
failure of cementless fixation and infection. None of
the explants were revised for structural failure of the
UHM WPE meniscus. Twenty-seven paired meniscal
and femoral com ponents were available for examina-
tion in this study.
An initial visual examination and the clinical
history of the explants were used to determine
the modes of failure of the compo nents. Certain
mechanical modes of failure were then eliminated
from the tribological study. These included joints
where the meniscus had dislocated and led to the two
metal compo nents, the femoral compon ent and the
tibia1 tray, contacting. During articulation these two
metal compo nents maintained contact leading to the
generation of large amounts of metal w ear debris. A n
example of this type of failure is shown in Figure 2.
Sixteen of the 27 paired explants had failed in this
manner and were thus discarded from the rest of the
study, which has focused on the articulating surfaces.
The full clinical history, p atient details and regular
follow-up information
of the eleven remaining
explants (which were evaluated for wear) were
available from hospital records, and are summ arized
in Table 1. The average age of the patients was 60.0
years a nd their average weight was 71.1 kg. The
period of implantation for these compon ents ranged
from less than 1 year to over 5 ears with an average
lifetime of 33.4 months. In a dy ition to the revised
explants, four unwo rn p rostheses taken from clinical
stock prior to implantation were also evaluated as
control samples.
The articulating surfaces of the
menisci a nd femoral comp onents were characterized
by R, surface roughness measurem ents using a
Talysurf 5 machine (Rank Taylor Hobson , Leicester).
The R, was measured perpendicular to the direction
of sliding using a 0.8 mm cut off. Three readings were
obtained from each cond yle, giving a total of six
measurem ents per comp onent. The mean of these
readings was then calculated and used as the average
R, value for that particular compo nent.
The UHMW PE meniscal components were wider
than the femoral compon ents, and due to a close
fitting central locating step (see Figure 4b), the edges
of the menisci were not subjected to wear. This
resulted in the formation of a lip at the edges of
Table 1 Summ ary of clinical data, patient details and follow-up information
Case
Wear life
number (months)
Activity
capability
Age
(years)
Weight
(kgs)
Sex
Operation
side
Initial
diagnosis
Reason for
revision
I 8 A 73
72 F I. OA
I,, ST
2 9 - 62
66 F R RA
I
3 IO A 60
71 F L OA
I
4 I6 A 61
64 M L O A
I,
5 23 P 61
54 F R RA
I
6 26 G 67
79 M I* Other
I, L
7 43 G 46
73 F R RA
L, ST
8 45 G 63
61 F R RA
I, U
9 59 A 62
88 M L O A
I,, ST
IO 64 G 62 77 M R O A L
II 64 A 43
77 F L OA
L
G, good mobility; A, average mobility; P, poor mobility; OA, osteo arthritis; RA, rheumatoid arthritis; I, infection; L, loosening; ST, subsidence of
tibia; U, unstable
224 Med. Eng. Phys. 1994, Vol. 16, May
8/11/2019 A Tribological Study of a Series of Retrieved
3/6
the menisci. A Talycontor machine (Rank Taylor
Hobson, Leicester) was used to trace across the
surface o f the menisci (perpendicular to the sliding
direction) from one lip, over the worn region to the
worn area and unworn lip on the op osite side of the
comp onent. A rotating levelling ta 1 le was used to
ensure that the two unw orn lips were at the same
height, and that the menisci were orientated at
exactly 90 to the direction of sliding. This proce-
dure was repeated twice for each sample and the
average difference between the height of the unwo rn
lip and the height of the worn region was evaluated to
give the penetration depth for each polyethylene
comp onent. It should be pointed out that the
measured penetration into the menisci occurred as a
result of both creep and wear of the polyethylene.
Therefore the derivation of wear rates from penetra-
tion rates should be treated with caution, particularly
when penetration depths are small.
RESULTS
The surface roughnesses of the femoral compo nents
are shown in the graph in F igure 3. Th e number of
months that the joint was im lamed for is shown on
the x-axis, and the R, (in pm
P
It was found that general1
is shown on the y-axis.
were in very good cr
the femoral compo nents
con ition and had R, values
similar to the unw orn control. The av erage R, value
for the worn femoral com ponents was 0.055~m with
a standard deviation of 0.075p.m (average R= of
0.032pm if the one anomaly, 59 months, was not
included). This corn
P
ares with an Ra of 0.02p.m for
the unwo rn contra compo nent. There was one
sample (59 months) which ha d a surface roughn ess
an order of magnitude higher than the rest of the
samples. This comp onent had been badly scored
g
robably as a result of the entrapment of cement and
one debris. One other compo nent (64 months)
showed a slightly higher R, and a slight deterioration
of the surface.
Figure 4a shows the surface roughn esses of the
meniscal compon ents. The implant lifetime is shown
on the x-axis, and the R, is shown on the y-axis. From
this graph it can be seen that there was an initial
Lifetime months)
Figure 3 Histogram of the femoral surface roughness (R,) and
implant life
Tri bologicnl tudy of retri eved nee explant s:JL. Hai lq, et al.
a
Lifetime months)
Figure 4 a Histogram of the meniscal surface roughness ( ) and
implant life. 4b, Photograph of a worn (right) and an unworn (left)
meniscus
smoothing of the surfaces followed by some deteriora-
tion in certain cases. The average R, for the worn
menisci was 1.15 pm with a standard deviation of
1.03pm (using the eight polished com ponents the
average Ra was 0.60pm, using the three bad1
damaged compon ents the average R, was
2.63pm .
r
This compares with an avera e
(standard deviation 0.23 pm
Y
value of 1.04 pm
for the unworn
samples. The Ra values for the worn co mpon ents
ranged from 0.28 pm up to 3.27pm, whereas those
for the unwo rn con trols ranged from 0.76pm up to
1.33pm. Initially the polymer surface was quite
rough due to the machining marks. Initial wear and
creep produced a smoothing or polishing of the
UHM WPE meniscal compo nents. The polishing of
the worn menisci, compa red to an unwo rn control,
can be clearly seen in the
4b, where the sample on tK
hotograph shown in F igu re
e right is the worn sample.
Subsequently in certain cases the polymer surface
became damaged and the surface roughness
increased.
F igu re 5 shows the articulating surface of Case 10
(the first of the two samples implanted for 64 months
on the graph in
F igure 4a .
This sample showed severe
surface dama
explants, an B
e compa red with that seen in the other
failure of the surface can be seen in
F igure 5. This was the worst case of the 27 explants
which were studied. The Talycontor profile showed
Med. Eng. Phys. 1994, Vol. 16, May 225
8/11/2019 A Tribological Study of a Series of Retrieved
4/6
Tri bological tudy of etr ieved nee explunt xJ.1. Hai lq et al.
Figure 5 Photograph of the meniscus from Case 10 showing surface
micro-delamination
that this surface dam age and wear occurred within
0.3 mm of the meniscal bearing surface. Similar wear
features have been seen on acetabular cups from
simulator studies which we have performed at Leeds
University *. Howev er, there was also evidence of
gross misalignment and dislocation of the poly-
ethylene meniscal compo nent, and this surface
damage could have been caused by contact with the
edge of the femoral compo nent when grossly mis-
aligned. Local surface damage at the edge of the wear
scar was noted on several of the older meniscal
compo nents and this is shown in Figure 6. This is
believed to have occurred when the femoral com-
ponent and the meniscus became slightly misaligned.
The very small radii on the femoral compo nents led
to the development of high contact stresses a t the
edge contact with the meniscus. This in turn resulted
in local stru ctural failures, in the form of local severe
damage to the surface of the polyethylene.
The penetration de ths into the menisci are shown
in
Figure 7. The
imp ant life is shown on the x-axis
and the penetration (in pm) is shown on the y-axis.
There was a considerable variation in the penetration
depths of the explants, and no correlation could be
found with either wear life, patient weight, or patient
activity. It can also be seen from Figure 7 that four of
the menisci showed no detectable penetration, even
after implantation for over 5 years in one case (64
months on the graph in Figure 7). Two of the samples
were too badly deformed to obtain penetration
Figure 6 Photograph showing local structural failure of a meniscus
due to misalignment of the femoral component
i 23 26 45 59 64
Lifetime months)
Figure 7 Histogram of the meniscal penetration depth and implant
life
depths from. This was due to severe misalignment of
the meniscal compo nent and gross damage of the
polyethylene, and hence these samples were dis-
regarded from this part of the study. The average
penetration rate from the data shown in Figure 7 w as
found to be 40pmyea r-. In this study the
P
enetra-
tion depths an d the Ra values for the latera side of
both compon ents were found to be similar to those
obtained for the medial side.
DIS USSION
Recent reports13 of structural fatigue and early failure
in highly stressed nonconform ing total condylar
knees have caused considerable concern in the
surgical commu nity. This has promp ted a renewed
interest in the meniscal bearing knee w here it is
possible to increase contact area and reduce contact
stresses to levels m ore generally found in hip
prostheses. It is important to recognize that changes
in the design an d tribological cond itions in artificial
joints can cause marked changes in the wear and
failure processes in the UHM WPE compo nents. In all
polyethylene acetabular cups in hip prostheses, where
contact stresses are generally lower than in total
condylar knees, structural failure is extremely rare,
and wear particles are generated by surface wear
processes produced by asperity interactions14. In
Argenson and OConn ors long term study of
Oxford meniscal knees, surface wear and pentration
rates were reported, but no evidence of structural
failure was recorded, demonstrating the potential of
the meniscal bearing concept. In this study the
majority of the implants retrieved showed metal-to-
metal contact due to dislocation of the meniscal
compo nents. As this would have produced consider-
able metallic debris which could subsequently
damage the articulating surfaces, these prostheses
were excluded from the study.
It was shown that, in general, the surface roughness
of the femoral comp onents did not change signifi-
cantly with implantation time. Some fine scratches
running parallel to the direction of sliding w ere
visible on the surfaces of the femoral compo nents,
although these did not appear to have a significant
226 Med. Eng. Phys. 1994, Vol. 16, May
8/11/2019 A Tribological Study of a Series of Retrieved
5/6
Tri boh@al study of etri eved nee explunt s:JL. Ha y et al.
reduced stresses have been demonstrated in this
study. However,
it is necessary to
em hasise
biomechanical difficulties of ensuring sta
the
meniscal knee design.
ility in the
influence on the R, values. Since the scratches were
orientate d in the direction of sliding, it is unlikely that
they would hav e had a significant effect on the wear
of the polyethylene, compa red to scratches which
were perpendicular to the sliding direction. In hip
joints this type of scratching has been related to
increased polyethylene wear as in the hip the
scratches tend to be more random ly orientated due to
the more complex movem ents generated.
The pattern of wear and changes in the surface
to ograph of the meniscal compo nent were gener-
al y ip ly similar to those found in acetabular
cr
where surface wear processes remove
EYsethylene particles within 10pm of the surface,
an dr severe plastic deformation of the polyethylene
has been noted up to a depth of 40pm below the
surface. T he initial roughness of the pol
marks was smoothed by creep
an Jrn
er machine
counterface as
microscopic
t
erity wear (Figure 4). Subsequent1 in
certain cases
e polymer surface deteriorated. Jh is
may be due to abrasive action by third body bone
cement particles, or alternatively the onset of macro-
scopic
1
olymer w ear processes which have been
reporte in explanted acetabular cups15. One
meniscal compo nent (Case 10) showed severe surface
damage, and the depth of this severe surface damage
was up to 300pm from the articulating surface.
Although similar surface wear patterns have been
seen in hip joint simulator studies in the laboratory,
there was also evidence of gross misalignment of this
compo nent and this severe surface damage ma
have
been caused by edge contact of the femora ly
com-
ponent. In the explants which d id not dislocate, or
show evidence of gross misalignment, gross structural
failure (characterized by delamination originating
from a depth of greater than 0.5mm into the
UHM WPE) was not found. However, the follow u
of 5 years is quite sh ort and direct comparison
wi
t
longer term follow u p studies of total condylar knees
should be approached with caution. W hen misalign-
ment of the Accord knee occurred, local stress
concentrations were formed at the edge of the
femoral co mpon ent, and local structural failure
resulted due to the abnormally high contact stresses.
The average penetration rate was also evaluated
from our data and compared with that obtained by
other workers. We calculated a penetration rate of
0.040 mm year- (4Opm ) for the Accord knee, w hich
compares well with the figure of 0.047 mm
year
obtained by Argenson and OConnor for the
Oxford m eniscal knee. In comparison Dow son et
a1.16 obtained significantly higher penetration rates
for conventional Geomedic and Freeman-Swan son
knees - 0.22 and 0.26mmyea r respectively. The
penetration rate in the meniscal knee was comparable
with that found with hip joints as shown by Dowling17
who obtained a penetration rate of 0.06 mm year- for
post mortem acetabular cups. How ever, care must be
taken when comparing penetration rates in different
types of knees and hips, as the different geometries
involved will produce different v olume
than es for
the same penetration rate. Also these volume c a anges
can include different contributions from creep and
wear. Des
mental tri
K
ite this, the authors feel that the funda-
ological
advantages of a meniscal knee
design, which include larger contact areas and
CONCLUSIONS
In conclusion, the tribological advantages of the
Accord meniscal bearing knee joint are as follows.
There was generally little damage of the articulating
surfaces. The wear and penetration rates were very
low. There was no evidence of any structural failures,
except in cases where the femoral corn
onent and the
meniscus were misaligned, and lot
ap
damage was
formed at the edge of the contact area. The p attern of
surface w ear in this knee was similar to that seen in
hips with comparable penetration rates for the two
types of joint.
In the 27 retrieved knees reported in this study
failure of the cementless fixation was the most
frequen t cause of revision. This led to instability of the
joint and edge contacts between the femoral com-
ponent and the meniscus, which due to the small radii
on the femoral compo nent led to the generation of
high contact stresses and local structural failure.
There were a number of cases where dislocation of
the meniscus which led to metal-on-metal contact
during articuation, and the potential for generation of
large quantities of metal wear debris.
AC KNOWLEDGFBIENTS
This work was funded by the Arthritis and Rheum at-
ism Council (ARC).
REFERENCES
1.
2.
3.
4.
5.
6.
7.
Walker PS. Bearing surface design in total knee replace-
ment. Eng Med 1988; 17: 149-56.
Bartel DL, Bicknell VL, W right TM. The effect of
conformity, thickness and material on stress in ultra-high
molecular weight components for total joint replacement.
JBoneJoint Surg 1986; 68-A: 1041-51.
Wright TM, Rimnac CM, Stulberg SD, Mints L, Tsao AK,
Klein RW, McCrae C. Wear of polyethylene in total joint
replacements. Clin Orthop Rel Res 1992; 276: 126-34.
Kilgus DJ, Moreland JR, Finerman GAM , Funahashi IT,
Tipton JS. Catastrophic wear of tibial polyethylene inserts.
Clin Orthop Rel Res 1992; 273: 223-31.
Mayor MB, W rona M, Collier JP, Jensen RE. The role of
polyethylene quality in the failure of tibial knee com-
ponents. Transactions of 39th Annual Meeting of Orthopaedic
Research Society, Feb. 15-18, San Francisco, 1993; 292.
Landy MM , Walker PS. Wear of UHM WPE in 90
retrieved knee prostheses.
J Arthrq ty,
1988; Oct.
Suppl. 73.
Blunn GW, Joshi AB, Lilley PA, Engelbrecht E, Ryd L,
Lidgren L, Hardinge K, Nieder E, Walker PS. Poly-
ethylene wear in unicondylar knee prostheses: 106
retrieved Marm or, PCA, and St Georg tibia1 components
compared. Acta Orthop and, 1992; 63: 247.
8. Collier JP, Mayor M B, McNamara JL, Surprenant VA,
Jensen RE. Analysis of the failure of 122 polyethylene
inserts from uncemen ted tibia1 knee components. Cl in
Orthop Rel Res
1991; 273: 232-42.
9. Engh GA, Dwyer KA, Hanes CK. Polyethylene wear of
Med. Eng. Phys. 1994 Vol. 16 May 227
8/11/2019 A Tribological Study of a Series of Retrieved
6/6
Tribologicaltudy f et ri eved nee xpkmt s:J.L. Ha y
et al
metal-backed tibia1 components in total and unicompart-
mental knee prostheses. JBone Joi nt Surg 1992; 74-B: 9- 17.
10. Argenson J-N, OConnor JJ. Polyethylene wear in
meniscal knee replacement. J BoneJoi nt Surg 1992; 74-B:
228-32.
11. Johnson R, Walker CR, Harvey IA, Barry GK, Elloy MA.
Five to eight year results of the Johnson-Elloy Accord)
total knee arthroplasty. JAr t hrop lasty , 1993; 8: 27-32.
12. Dowson D, Jobbins B. Design and development of a
versatile hip joint simulator and a preliminary assessment
of wear and creep in Charnley total replacement hip
joints. Eng Med 1988; 17: 111-17.
13. Goodfellow J. Editorial, Knee prostheses - one step
forward, two steps back. JBoneJoi nt Surg 1992; 74-B: l-2.
14. Cooper JR, Dowson D, Fisher J. Macroscopic and
microscopic wear mechanisms in ultra-high molecular
weight polyethylene. Wear 1993; 162-164: 378-84.
15. Cooper JR, Dowson D, Fisher J. Birefringent studies of
polyethylene wear specimens and acetabular cups. Wear
1991; 151: 391-402.
16. Dowson D, McCullagh PJ, Wright V. An assesssment of
the relative importance of wear and creep in the overall
performance of load-bearing total replacement knee
joints. In: Willert H-G, Buchhom GH, Eyerer P, eds.
Ul tr a-H h Mok cular Weight Polyethyl ene as Biomat erial
in Or thopaedic Surgeery. Toronto: Hogrefe and Huber
Publishers 1991; 32-40.
17. Dowling JM. Wear analysis of retrieved prostheses. In:
Szycher M, ed. Bi ocompati ble Pol ymers, M et als, and Com-
posi t es. Pennsylvania: Technomic 1983; 407-425.
1994 IEEE
ULTRASONICSSYMPOSIUM
NOVEMBER~ST-~TH
1994
CANNES
RANCE
Sponso red by the IEEE Ultrasonics, Ferroelectrics Frequency Control Society
There will be a large range of topics for discussion, including:
Bio-effects and Biophysics
Hyperthermia
Medical imaging
Physical acoustics
Quantitative laser ultrasonics
Tissue characterization
Tissue motion and compliance
Ultrasonic in surgery
Abstract submission deadline: Friday April 29th, 1994
Abstrac ts to be sent to: Ultrasonics Sym posium, c/o LRW A ssociates, 1218
Balfour Drive, A rnold, M D 21012-2150, USA .
Tel: +410 647 1591 or Fax: +410 647 5136.
For further information please contact: Bernhard R. Titmann, The Pennsylvania
State University, 227 Hamm ond Building, University Park, PA 16802, USA .
Tel: +814 865 7827 or Fax: +814 863 7967.
228
Med. Eng. Phys. 1994 Vol. 16 May