augmentation of screw fixation with injectable calcium sulfate bone cement in ovariectomized rats
TRANSCRIPT
Augmentation of Screw Fixation With Injectable Calcium SulfateBone Cement in Ovariectomized Rats
Xiao-Wei Yu,y Xin-Hui Xie,y Zhi-Feng Yu, Ting-Ting Tang
Department of Orthopedic Surgery, Shanghai Ninth People’s Hospital, Shanghai Jiaotong University School of Medicine,Shanghai 200011, China
Received 27 November 2007; revised 1 May 2008; accepted 26 May 2008Published online 20 August 2008 in Wiley InterScience (www.interscience.wiley.com). DOI: 10.1002/jbm.b.31184
Abstract: The objective of this study was to determine the effect of augmenting screw
fixation with an injectable calcium sulfate cement (CSC) in the osteoporotic bone of
ovariectomized rats. The influence of the calcium sulfate (CS) on bone remodeling and screw
anchorage in osteoporotic cancellous bone was systematically investigated using histomorpho-
metric and biomechanical analyses. The femoral condyles of 55 Sprague–Dawley ovariecto-
mized rats were implanted with screw augmented with CS, while the contralateral limb
received a nonaugmented screw. At time intervals of 2, 4, 8, 12, and 16 weeks, 11 rats were
euthanized. Six pair-matched samples were used for histological analysis, while five pair-
matched samples were preserved for biomechanical testing. Histomorphometric data showed
that CS augmented screws activated cancellous bone formation, evidenced by a statistically
higher (p < 0.05) percentage of osteoid surface at 2, 4, and 8 weeks and a higher rate of bone
mineral apposition at 12 weeks compared with nonaugmented screws. The amount of the
bone–screw contact at 2, 8, and 12 weeks and of bone ingrowth on the threads at 4 and 8 weeks
was greater in the CS group than in the nonaugmented group (p < 0.05), although these
parameters increased concomitantly with time for both groups. The CS was resorbed
completely at 8 weeks without stimulating fibrous encapsulation on the screw surface. Also, the
cement significantly increased the screw pull-out force and the energy to failure at 2, 4, 8, and
12 weeks after implantation, when compared with the control group (p < 0.05). These results
imply that augmentation of screw fixation with CS may have the potential to decrease the risk
of implant failure in osteoporotic bone. ' 2008 Wiley Periodicals, Inc. J Biomed Mater Res Part B: Appl
Biomater 89B: 36–44, 2009
Keywords: calcium sulfate; augmentation; fracture fixation; osteoporosis; ovariectomy
INTRODUCTION
As the population ages, the incidence of osteoporosis will
increase dramatically, along with the risk of fracture. These
fractures can range from vertebral fractures to extremity
fractures, and include fractures of the proximal femur, hu-
merus, and distal radius.1 The treatment of osteoporotic ex-
tremity fractures has become a major challenge for the
orthopedic surgeons. Poor implant anchorage in osteopor-
otic bone requires new treatment solutions. Augmentation
with bone cements or substitutes is one strategy that may
address this challenge.2
Historically, some researchers have used PMMA to
maintain the stability of the fracture–implant construct in
osteoporotic bone.3 PMMA has good strength and stiffness,
so the initial fixation is excellent. However, it is nonde-
gradable and has no biological potential to remodel or
integrate into the surrounding bone.4 Several other disad-
vantages include the release of toxic monomers,5 thermal
necrosis during cement setting,6 and infiltration of fibrous
tissue between the PMMA and surrounding bone.5 To over-
come these disadvantages, several injectable ceramic bone
cements or substitutes made from calcium-phosphate, cal-
cium-sulfate, or bioglass have been developed. These
degradable, biocompatible, and osteoconductive ceramic
materials7–9 have been used as an augment for osteoporotic
fractures fixation in the extremities as well as for vertebral
compressive fractures in the spine.10
For many decades, calcium sulfate (CS) has been widely
used as bone graft substitute in various skeletal sites.11–15
It is more rapidly resorbed than other biomaterials, allow-
ing for an earlier ingress of osteoprogenitor cells.16 It also
mimics the mineral phase of bone and resorbs at the rate
similar to that of bone formation.17,18 CS prevents soft tis-
yBoth authors contributed equally to this work.Correspondence to: T.-T. Tang (e-mail: [email protected])Contract grant sponsor: Shanghai Shuguang Educational Funding Committee
(China)
' 2008 Wiley Periodicals, Inc.
36
sue invasion by acting as a space filler,19 and can be
replaced by newly formed bone that ultimately remodels
comparably to autogenous bone.20 It has also shown signifi-
cant augment pull-out strength when used for augmentation
of pedicle screw fixation in vitro.21
Generally, calcium-phosphate cement is the more com-
mon ceramic for augmenting osteoporotic fractures.
Although Leung et al. reported the temporal changes invivo of calcium phosphate cement in screw augmentation,22
to date, calcium sulfate cement (CSC) has not been eval-
uated in an osteoporotic model. Most studies found that CS
is resorbed in the body within 8 weeks.17,23 Whether this
relative rapid resorption will be followed by enhanced
osteointegration and improved stability of the fixation
implant, remains unexplored. The aim of this study is to
investigate the effect of the CS on bone remodeling and to
evaluate its effect on screw augmentation in osteoporotic
bone in vivo.
MATERIALS AND METHODS
Osteoporotic Rat Model
Fifty-five 6-month-old female Sprague–Dawley rats were
used in this study.24 Under general anesthesia, the rats
underwent bilateral ovariectomies using a dorsal approach
(OVX). Nonabsorbable suture material was used for the lig-
ature, and the bilateral ovaries were completely excised.
Finally, the wound was closed by suturing. All rats were
housed in a cage with a circadian light rhythm of 12:12 h
light/dark, 60% humidity at 218C, and were fed a normal
diet. Four months after ovariectomization, osteoporosis was
confirmed by dual X-ray absorptiometry (Hologic Discov-
ery-A; Hologic Corporation, Waltham, MA). Both the rear-
ing of these rats and the experiments were approved by the
Animal Ethics Committee of Shanghai Jiaotong University
School of Medicine (reference number: 2004-12-5).
Screw Implantation and CS Augmentation
The femoral condyles were selected as the implantation site
of the screws. Under generalized anesthesia, the bilateral
knees of the rat were prepared with a sterile technique.
Straight incisions of 1 cm were made on the lateral sides
of the knees. The fibers of the tensor fascia lata were cut
longitudinally, and the lateral condyles of the distal femurs
were exposed. A 1.2 mm (diameter) 3 5 mm (depth) hole
was drilled unicortically in the cancellous bone, parallel to
the articular surface of the femoral condyles. The hole was
subsequently washed with saline solution and dried with
gauze. Each rat received a screw augmented with CS in
one leg, while the contralateral limb received the screw
without augmentation. The implants were randomly
assigned. The CS used in the study was a commercially
available surgical grade CS hemihydrate with a high com-
pressive strength.25 This injectable paste hardens in about
10 min when mixed with water (MIIG1 X3 CSC; Wright
Medical Technology, Arlington, TN). The CS cement was
prepared according to the manufacturer’s guidelines, and
about 0.02 mL was injected into each augmented hole.26 A
fully threaded cancellous screw (Shanghai Pu Wei Medical
Appliance Co.) with a thread diameter of 1.7 mm, a core
diameter of 0.8 mm, and 6 mm in length was inserted into
the hole before the cement hardened in situ. The soft tis-
sues were closed by suturing in layers.
At each time interval of 2, 4, 8, 12, and 16 weeks after
screw implantation, 11 rats were euthanized by an abdomi-
nal overdose of barbiturates and the femora were dissected.
All rats were injected intraperitoneally with tetracycline
hydrochloride of 30 mg/kg (Sigma, St. Louis, MO) and
15 mg/kg calcein (Sigma) to label the new bone calcification
on day 12 and 2 days before euthanasia. Six pair-matched
samples were put immediately in 70% ethanol for histologi-
cal analysis, while five pair-matched samples were double
bagged and fresh frozen at 2208C for biomechanical testing.
Histologic and Histomorphometric Analysis
The distal femurs were dehydrated in graded series of etha-
nol and finally in xylene, then infiltrated and embedded in
methylmethacrylate.22 These specimens were longitudinally
sectioned into 220-lm-thick slices parallel to the axis of
the screw, using a diamond saw (Leica SP1600; Leica
Instruments, Nussloch, Germany). The sections were hand-
ground to 50 lm and stained with Stevenel’s blue and Van
Gieson’s picro-fuchsin for histomorphometric analysis of
the bone–screw contact and bone ingrowth, and again were
ground to 20–30 lm for fluorescence microscopy. After
assessing the fluorescence microscopic images, the sections
were stained again for histomorphometric analysis of the
osteoid surface.
Four histomorphometrical parameters, as described by
Tadjoedin, Fini, and Nkenke et al., were blindly measured
as illustrated in Figure 1 by a single observer.27–29 Briefly,
the osteoid surface in the surrounding area of the screw
was determined in Eq. (1) as
Figure 1. Schematic diagram of histomorphometrical parameters(bone–screw contact perimeter, thread area, and the surrounding
area of screw).
37AUGMENTATION WITH CALCIUM SULFATE BONE CEMENT
Journal of Biomedical Materials Research Part B: Applied Biomaterials
Osteoid perimeter
Trabecular perimeter3 100 ð%Þ ð1Þ
The bone–screw contact was defined in Eq. (2) as
Bone contact with the screw surface perimeter
Screw surface perimeter3 100 ð%Þ
ð2ÞThis bone–screw contact measurement started from the
most coronal thread down to the most apical thread. The
bone ingrowth was defined in Eq. (3) as
Area of bone between the screw threads
Area between the screw threads3 100 ð%Þ ð3Þ
Finally, the bone mineral apposition rate (MAR) (lm/
day) in the surrounding area of the screw was expressed in
Eq. (4) as
Mean distance between adjacent fluorochromemarkers ðlabelsÞNumber of days ð10 daysÞ
ð4Þ
All image analysis used BioQuant OSTEO II software
(BioQuant Image Analysis Corporation, Nashville, TN).
Biomechanical Testing
The femurs were progressively thawed and rehydrated in
phosphate-buffered saline for 48 h before biomechanical
testing (Instron model 4411; Instron, Canton, MA). Each
femur was mounted in acrylic cement, and clamped as
shown in Figure 2. The screw head was grasped by a cus-
tom-made jig which connected into the actuator of the test
frame. The screw was then pulled to failure along the long
axis of the screw at a constant speed of 0.1 mm/s. During
testing, the force-displacement curve was displayed on the
monitor by using a testing software program (Series IX
software; Instron). The pull-out force (N) was determined
as the maximum point on the curve where failure occurred.
The energy to failure (J) was calculated based on the area
under the curve. Five specimens from each group were
evaluated at each time point.
Statistical Analysis
The results of both the histological analysis and the biome-
chanical test were expressed as means 6 SD. Paired t testwas used to compare histomorphometrical parameters and
biomechanical results between the CS and control groups.
All the data analyses were carried out using SAS (version
6.12; SAS Institute, Cary, NC). The level of significance
was set at p\ 0.05 (two-tailed).
RESULTS
Overall Observation
No animals encountered complications after surgery, and
all wounds healed without signs of infection. Radiographs
obtained postoperatively confirmed good placement of the
screws. There was no observed inflammation or adverse
soft tissue reaction to the CS implantation. Additionally, no
screw-loosening was observed at the surgical site in all
femurs.
Histologic Results
At 2 weeks, residual bone fragments were observed
between the bone bed and screw interface, because of oper-
ative pilot hole drilling. New woven bone was observed on
the surface in both groups. In the CS group, most of the
space surrounding each screw was filled with graft material
and appeared homogeneous [Figure 3(A)]. There was much
more void space in the control group [Figure 3(F)], and
some fibrous tissue infiltration was detected. Connective
tissue began to separate the screw from bone interface in
this group. At this time point, few fluorescent markers were
present in either group [Figure 4(A,F)]. As highlighted in
Figure 5, a higher frequency of active osteoblasts with cu-
boidal morphology was observed in the augmented speci-
mens compared with the control specimens as evidenced
by the area of osteoid matrix. These cells were more con-
centrated in areas in close proximity to the CS surface.
At 4 weeks, bone was observed in closer proximity to
the screw surface than in 2 week specimens. While the
bone in both groups exhibited spongy architecture, the
bone present in the augmented group was more mature
[Figure 3(B,G)]. The diffuse presence of fluorescent
markers for new bone calcification near the screw surface
showed an evidence of continued remodeling [Figure
4(B,G)]. In the experimental group, CS presence had
Figure 2. Biomechanical testing configurations showing that the
screw was pulling out to failure along the long axis of the screw at
a constant speed of 0.1 mm/s. [Color figure can be viewed in theonline issue, which is available at www.interscience.wiley.com.]
38 YU ET AL.
Journal of Biomedical Materials Research Part B: Applied Biomaterials
decreased from previous time points and abundant new
immature woven bone was found in the spaces between the
CS [Figure 6(A)]. There was an evidence of direct bone
apposition without fibrous encapsulation on screw surfaces
in the experimental group; however, the control group
screw surfaces were marked by fibrous tissue apposition
[Figure 6(B)].
At 8 weeks, increased areas of woven bone with greater
surface apposition to screw surfaces were observed in both
groups compared with the previous time points [Figure
Figure 3. Representative photomicrographs of six sections in each group showing the cancellous
bone around the screw, starting with the most apical thread to the third thread, augmented with
(A–E) and without (F–J) CSC at 2, 4, 8, 12, and 16 weeks after implantation from the same animal.
White arrows, CSC; black arrows, fibrous tissue (Stevenel’s blue and Van Gieson’s picro-fuchsinstaining; 350). [Color figure can be viewed in the online issue, which is available at www.interscience.
wiley.com.]
Figure 4. Fluorochrome-marked cancellous bone demonstrating bone deposited adjacent to the
screw augmented with (A–E) and without (F–J) CSC at 2, 4, 8, 12, and 16 weeks after implantation,tetracycline (yellow) and calcein (green) is shown, as arrows indicated (350). [Color figure can be
viewed in the online issue, which is available at www.interscience.wiley.com.]
39AUGMENTATION WITH CALCIUM SULFATE BONE CEMENT
Journal of Biomedical Materials Research Part B: Applied Biomaterials
3(C,H)]. In the experimental group, CS was no longer
observed in the sections. Higher concentrations of fluores-
cent markers were present indicating intense remodeling
[Figure 4(C,H)].
At 12 weeks, thicker, more mineralized, mature bone
was observed in the surrounding area of the screw in both
groups when compared with previous time points [Figure
3(D,I)]. In the CS group, a greater presence of properly
aligned and mature bone along the screw surface was
observed compared with the control group [Figure 3(D)].
In some screw threads, the new bone completely filled the
thread area. The osteointegration of the control group was
improved over previous time points, with a reduction in fi-
brous tissue and increased contact between the screw and
bone surfaces [Figure 3(I)].
Finally, at 16 weeks more mature bone was apparent in
both groups, with no visible difference in appearance
[Figure 3(E,J)].
Histomorphometric Results
Histomorphometric data indicated that the osteoid surface
surrounding the screws in the CS group was significantly
higher than that in control group at 2, 4, and 8 weeks
Figure 5. At 2 weeks, numerous active osteoblasts with cuboidal morphology were observed, as
evidenced by the area of osteoid in close proximity to the CS group (A). Meanwhile, much more
void space was observed in the control group, with fibrous tissue infiltration detected (B). CSC, cal-cium sulfate cement; NB, new bone; FT, fibrous tissue (Stevenel’s blue and Van Gieson’s picro-
fuchsin staining; 3100). [Color figure can be viewed in the online issue, which is available at
www.interscience.wiley.com.]
Figure 6. At 4 weeks, new bone, predominantly in the form of early woven bone, was being depos-
ited in contact with the screw in the CS group (A), while fibrous tissue infiltration was observed
around the screw in the control group (B). CSC, calcium sulfate cement; NB, new bone; FT, fibroustissue; S, screw (Stevenel’s blue and Van Gieson’s picro-fuchsin staining; 3100). [Color figure can
be viewed in the online issue, which is available at www.interscience.wiley.com.]
40 YU ET AL.
Journal of Biomedical Materials Research Part B: Applied Biomaterials
(Figure 7). In addition, the bone-screw contact of the CS
group was significantly superior to that of the control group
at 2, 8, and 12 weeks (Figure 8). Bone ingrowth of the CS
group was also significantly higher than that of the control
group but only on 4 and 8 weeks (Figure 9). Although all
CS group’s MAR values of the newly formed bone in the
surrounding area of the screw experimental groups was
greater than the control group except at week 2 (which
could not be determined because of lack of fluorescent
markers), a significant difference was only exhibited at the
12 weeks time point (Figure 10).
Biomechanical Testing Results
There were three major failure modes observed in the pull-
out testing of the CS group. At 2 weeks, failure occurred at
the cement–cancellous bone interface. At 4 weeks, fracture
of the CS cement was observed. At 8 weeks, the cancellous
bone itself failed, with residual bone strongly attached to
the screw surface. In contrast, there were only two major
modes of failure in the control group. At 2 weeks, fixation
failure happened at screw–cancellous bone interface with
little bone–screw interference. But after 8 weeks, failure
mode of control group was similar to that of the CS group.
The screw pull-out force of the CS group was signifi-
cantly higher than the control, at all time points except the
16 weeks time point (Figure 11). Most notably, at week 2,
the pull-out force of the control group was only half of the
CS group value. Similarly, the energy to failure in the CS
group was significantly higher than the control, at all time
points except at 16 weeks (Figure 12).
DISCUSSION
This investigation was designed to evaluate the effects of
screw augmentation with injectable CSC in osteoporotic
fracture fixation. In this study, we augmented screw fixa-
tion in vivo using OVX aged rat model. The model is still
reliable for postmenopausal osteoporosis after 8 months
postovariectomization, as confirmed by earlier studies.30
The increase in screw pull-out force and the energy to fail-
Figure 7. Comparison of the osteoid surface of the CS and control
groups. Differences were significant at 2, 4, and 8 weeks (p\ 0.05).
Figure 8. Comparison of the bone–screw contact of the CS andcontrol groups. Differences were significant at 2, 8, and 12 weeks (p
\ 0.05).
Figure 9. Comparison of the bone ingrowth of the CS and control
groups. Differences were significant at 4 and 8 weeks (p\ 0.05).
Figure 10. Comparison of the bone mineral apposition of the CSand control groups. Differences were significant at 12 weeks (p \0.05).
41AUGMENTATION WITH CALCIUM SULFATE BONE CEMENT
Journal of Biomedical Materials Research Part B: Applied Biomaterials
ure after cement augmentation showed the cement to be
highly biocompatible and osteoconductive.
In the control groups, higher quantities of fibrous tissue
were observed. It is postulated that the fibrous tissue layer
resulted from excessive micromotion at the implant-bone
interface. Such tissue hampers bony ingrowth at the screw–
bone interface, making this interface the weak point during
biomechanical pull-out testing. Micromotion may stimulate
precursor cells differentiation into fibroblasts rather than
osteoblasts, hindering the revascularization process.22 As
reported by Fini et al., impairments in bone–screw contact,
bony ingrowth, and extent of bone mineralization are res-
ponsible for poor implant stability in osteoporotic bone.28
We also observed increased osteoid levels at early time
points in the control group. This may be due to the effect
of localized trauma caused by the drilling of the pilot hole,
implantation of the screw, and/or the influence of implant
loading on the tissue.31
Our results showed that the CS provided significant rein-
forcement of screw fixation in early time points, because
little bony ingrowth and bone–implant contact were pres-
ent. As indicated through the biomechanical pull out
testing, there were different failure modes between two
groups. During the earliest postoperative phases, fixation of
the CS implant depended solely on mechanical interface of
the CS and surrounding cancellous bone. The CS-bone
interface was the mechanically weak point because the CS-
metal bond is quite strong. In contrast, the interface
between the screw threads and cancellous bone was the
mechanically weak point in the control group. It is theor-
ized that the thorough infiltration of CSC into the surr-
ounding cancellous bone creates a composite structure
improving interfacial shear strength through increased sur-
face area contact. Moreover, it may serve as conduit for
bony ingrowth by physically halting soft connective tissue
proliferation.32 At 4 weeks, new bone formation occurred
at the expense of the CS resorption making the degraded
CS surface the mechanically weak point. Even so,
increased levels of new bone ingrowth and bone–screw
contact within the CS group offered significantly greater
pullout force and energy absorption values compared with
the control group. Additionally, the abundant immature wo-
ven bone formed around the CS at 4 weeks had begun
to demonstrate a more mature trabecular alignment at
8 weeks; most likely due to the load bearing of the animal.
Carter et al. discussed that the amount of regenerated bone
should create a biomechanical balance where the stiffness
of the composite (residual bone graft 1 newly formed
bone construct) equals the physiological properties of the
adjacent bone tissue.33 Fini et al. also found that bony
ingrowth of the bone–screw interface was enhanced by the
presence of an osteoconductive biomaterial compared with
a bone–screw interface alone.28 Both the screw pull-out
force and energy to failure increased little in CS group at
4 weeks, which may suggest that immature woven bone is
the biomechanically weak link in the screw–cement–bone
system when cement begins to resorb. From then on, bio-
mechanical stability rose again concomitantly with time
because of the qualitative gain of new bone surrounding
the screw.
In this study, CS was found to activate new bone forma-
tion. At 2 weeks, large numbers of actively proliferating
osteoblasts and osteoid secretion were found at the surface
of cancellous bone, which allowed direct osteoblastic appo-
sition and led to faster and more abundant bone formation.
This activation suggests that CS may have a simulative
effect on the individual activity of osteoblasts, and was
effective in bone regeneration as evidenced by the results
of other authors.23,34,35 The MAR results revealed that CS
may increase cancellous bone turnover, especially at
12 weeks, which indicated that the increased concentration
of calcium ions may stimulate bone mineralization.23 Some
authors suggest that the bony response may be related to
the local acidity and subsequent demineralization of adja-
cent bone and release of matrix bound BMPs resulting in a
stimulatory effect.34
Figure 11. Comparison of the screw pull-out force of the CS and
control groups. Differences were significant at 2, 4, 8, and 12 weeks
(p\ 0.05).
Figure 12. Comparison of the energy to failure of the CS and con-trol groups. Differences were significant at 2, 4, 8, and 12 weeks (p
\ 0.05).
42 YU ET AL.
Journal of Biomedical Materials Research Part B: Applied Biomaterials
In earlier studies, other authors found that it took more
than 12 weeks for CS to disappear completely.36,37 In the
present study, CS was resorbed completely at 8 weeks,
which was similar to other studies, and most likely due to
the small volume of implanted cement surrounding screw.23
At 2 weeks, the cement appeared homogeneous and dense,
and then disintegrated into granules surrounded by new wo-
ven bone at 4 weeks, and finally disappeared at 8 weeks.
This suggests that CS was resorbed mainly by chemical
dissolution at first; then by osteoclast-mediated degradation,
as suggested by Sidqui et al.38
We also found that interconnectivity between adjacent
bone trabeculae was better in the CS group than in the con-
trol group, which implies that this biomaterial is conducive
to reestablishing the three-dimensional pattern that was lost
with osteoporosis. Further experiments are needed to quan-
tify this phenomenon and determine whether the newly
restored interconnectivity has some mechanical signifi-
cance. Also, a dynamic fatigue test should be conducted
because CS has relatively low shear strength, brittleness,
and susceptible to fatigue failure.
CONCLUSION
In summary, the CS used in the study was highly biocom-
patible and had a favorable effect on the osteogenic poten-
tial in osteoporotic bone. Though the pull-out force, the
energy to failure, bone ingrowth, and bone–screw contact
values were not significantly different after 16 weeks for
the two groups; a screw augmented with CS could stimu-
late new bone formation and withstand more load than a
nonaugmented screw in the first 12 weeks. Thus this con-
struct could provide a temporary support during a critical
period of fracture healing which may be applicable in the
treatment of osteoporotic fracture in humans.
The authors are deeply indebted to Shuang-Yan Zhang for thetechnical assistance in processing undecalcified sections, De-ZhiWang (Orthopaedic Research Lab/Center of Metabolic Bone Dis-ease Lab, University of Alabama at Birmingham) for the valuablesuggestions about histomorphometric analysis, and Ren-Guo Xie(Department of Hand Surgery, Affiliated Hospital of Nantong Uni-versity) for the biomechanical measurements.
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