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Ординатура / Хирургия / Библиотека им академика М.И. Перельмана / Книга_6019_Библиотеки_им_академика_М_И_Перельмана.pdf
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Properties Grafts Osteoconductive Osteoinductive Osteogenic Autograft + + + Allograft + +/−− DMB + +/−− Ceramics + −− Platelet gels −−+ BMA ++ BMP −−+
DBM demineralized bone matrix, BMP bone morphogenetic proteins, BMA bone marrow aspirate
Z. Buser et al.
similar fusion rates in both preclinical animal models and clinical studies. Commonly used grafting materials and their properties are summa­rized in Table 34.1.

Autograft

Autograft is considered the gold standard among graft materials in spinal fusion. It is the only material which possesses all three of the neces­sary elements for bone formation: osteogenic cells, an osteoconductive matrix, and osteoinduc­tive factors [5, 6]. Based on the harvest site, auto- graft can be divided into two main categories: iliac bone crest graft (ICBG) and local bone. Local bone is commonly harvested during decompression from the lamina, facets, or pro­cesses. With no extra harvest procedure, local bone has advantage over ICBG when it comes to harvest morbidities and complications. Local bone is a cortical graft which provides immediate mechanical stability; however, due to the small pore size, cell migration is impaired. This leads to lower rates of bone remodeling and long-term instability. On the other hand, the iliac crest is the most common and frequently used source because it has the ability to provide sufficient quantities of unicortical, bicortical, tricortical, and cancellous bone [79]. In addition, the iliac crest is easily accessible; during posterior spinal fusion procedures, a separate incision is not required [9]. Despite being regarded as the gold standard, autograft is associated with several dis­advantages. Donor site morbidity and complica-
tions such as deep infections, fracture, abdominal hernia, retroperitoneal hemorrhage, cutaneous nerve damage, blood loss, and vascular injury are well documented. In several studies, the afore­mentioned complications have been reported in up to 10% of cases [5, 7, 912]. Minor complica­tions, such as superficial infections, superficial seromas, and minor hematomas, were reported in 10–21% of patients [9, 12]. Graft volume is also a concern, with studies showing the average vol­ume harvested from the anterior iliac crest being 13 cm3 and the posterior iliac crest 30 cm3 [9]. The adequacy of these depends on the type of procedure and the number of levels included [5,
9]. Despite these limitations, autograft continues
to remain the gold standard due to its availability and proven track record. Surgeons must thor­oughly understand the types of autograft, their indications, and harvesting techniques.

Autologous Cancellous Bone

Cancellous bone has a high osteogenic potential due to the abundance of osteoblastic stem cells and osteoprogenitor cells. The trabecular struc­ture and large surface area of cancellous bone are favorable, as they provide increased osteocon­duction and promote vascular ingrowth [ Immediately after graft implantation, hemor­rhage and inflammation occur [
13]. This causes
the graft site to become rich in inflammatory cells and mesenchymal stem cells. Within 48 h of the surgical procedure, these cells produce fibrous granulation tissue. While this is occurring,
5, 9, 13].
34 Bone Grafting and Spinal Fusion Options
455
macrophages are recruited in order to remove the necrotic graft tissue [14]. Most of the graft cells do not survive; however, surface osteoblasts sur­vive and begin to produce new bone. As soon as 48 h after the surgery, host vessels along with osteoblastic and osteoclastic precursors infiltrate the trabecular surfaces of the cancellous graft. While new blood vessels begin to form through­out the graft, osteoclasts begin to resorb it. As the vascular ingrowth progresses, osteoblasts line the dead trabecular surfaces and produce osteoid. Through remodeling, which lasts several months, necrotic bone is resorbed by osteoclasts while osteoblasts form new bone [9, 13]. Thus, the incorporation of cancellous autograft occurs through simultaneous bone formation and resorp­tion [14]. Over the next 6–12 months following the grafting, newly formed osteoid is mineralized into bone and becomes fully integrated with the surrounding host bone. Integration is typically complete 1 year after the surgery [9, 13, 14].
Cancellous bone graft has been thoroughly studied to determine its clinical success. Throughout several historical studies, the rate of pseudarthrosis when using autogenous cancel­lous bone ranges from 5 to 44% [6, 7]. Herkowitz and Kurz studied the differences in clinical and radiographic results between decompressive laminectomy and decompressive laminectomy with intertransverse-process arthrodesis. The arthrodesis was performed with corticocancel­lous and cancellous bone grafts obtained from the iliac crest. Good to excellent results were found in 96% of the arthrodesis group and in 44% of the decompressive laminectomy group. Pseudarthrosis was found in 36% of the patients in the arthrodesis group, but the clinical results were significantly better in the arthrodesis group [15]. Fischgrund et al. performed a randomized study comparing posterolateral fusion with or without instrumentation with autogenous iliac crest bone graft [
16]. At a 2-year follow-up,
arthrodesis was successful in 82% of patients with instrumentation and 45% of the patients without instrumentation. However, the findings suggested that there were no significant differ­ences in the clinical outcomes [
16]. Kornblum
et al. followed up on patients from the previous
two studies in order to determine the long-term effects of pseudarthrosis and successful fusion. The clinical outcomes were good to excellent in 86% of the solid fusion group and in 56% of the pseudarthrosis group. Upon evaluating residual back and leg pain, the authors found that patients in the solid fusion group reported significantly lower pain scores in both areas as compared to the pseudarthrosis group [17]. The use of can­cellous autograft has also shown improved fusion rates and clinical outcomes in cervical spine. Song et al. studied the efficacy of a three­level anterior cervical arthrodesis with cancel­lous bone, polyether ether ketone (PEEK) cages, and plate fixation in 21 patients [18]. Solid arthrodesis, which occurred 10–14 weeks after surgery, was found in all 21 patients. Although graft site morbidity was not evaluated, SF-36 and NDI improved after surgery and at final follow-up.

Non-vascularized Autologous Cortical Bone

In comparison to cancellous autograft, cortical autograft is less osteogenic and less biologically active [5, 7, 9]. It is also compact and resistant to remodeling and vascular invasion [7, 9]. Furthermore, cortical bone has a lower surface area which reduces the potential for new bone formation. In spite of its drawbacks, it has greater mechanical strength than cancellous bone and is therefore used to provide structural support [7, 9,
13, 19]. Resorption of the graft by osteoclasts
then occurs to allow vascular ingrowth [ In order for the cortical bone to become fully incorporated, creeping substitution occurs. During this process, which can continue over the next 6 months following the surgery, osteoclasts resorb the graft at a high rate, while osteoblasts replace it with new bone [
5, 9, 14, 21]. During
creeping substitution, the graft can sustain a 75% reduction in strength, and the risk of graft col­lapse is highest [5, 14, 19]. Structural strength is regained within 12–24 months [
5, 9], and once
healed, there is little to no remaining weakness
14, 21].
[
13, 20].
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Z. Buser et al.
In several studies the rates of fusion for the cortical autograft in anterior cervical fusions were 89% or greater [
7, 2225]. Zdeblick and
Ducker found that the use of tricortical autograft in anterior cervical fusions had an 8% nonunion after 1 year. Graft collapse was observed in 5% of patients as well [
25]. Furthermore, Wright
and Eisenstein assessed 97 patients 1 year after anterior cervical discectomy and fusion (ACDF) with tricortical iliac crest bone graft. The study noted that pseudarthrosis was found in 11% of patients who had one-level fusions and 28% of patients who had two-level fusions [26]. Samartzis et al. performed a radiographic and clinical study comparing the fusion rates between allograft and autograft in two- and three-level ACDF with anterior plate fixation [27]. Out of 80 patients in the study, 45 received autogenous tricortical iliac crest graft along with anterior plate fixation. Successful bone fusion was achieved in 100% of the autograft group and in 94% of the allograft group. Within the autograft group, approximately 94% of patients with two­level fusions had good to excellent results, while 64% of patients with three-level fusions had good to excellent results [27].

Allograft

Allografts are harvested from cadaveric bone and are often used as bone graft extenders or substi­tutes in lumbar and cervical fusions. Allografts have good osteoconductive, very minimal osteo­inductive, and no osteogenic properties. Growth factors and cells are removed during graft pro­cessing to minimize their antigenicity. Commonly used forms of allografts are chips, strips, or demineralized bone matrix (DBM). Allografts of cortical origin provide good structural stability and are often used for interbody fusion, but the bone remodeling is slow and graft resorption is increased. Corticocancellous allografts provide minimal mechanical support at the start, but have large surface area that allows for better bone remodeling and graft resorption [28]. Based on the preparation, allografts can be fresh frozen or freeze-dried. Freeze-drying reduces immunoge-
nicity more than the freezing procedure; however, freeze-dried grafting materials have inferior mechanical properties [
29].
The main concern with the use of cadaver tissues is disease transmission, even though the preparation process is extensive. Standards for handling and preparation of bone allograft have been developed by the American Association Tissue Banking. Several cases of human immu­nodeficiency virus (HIV) and hepatitis transmis­sion with the use of frozen allograft have been reported [
30]. In all of the cases, donors and tis-
sues were not adequately tested. Furthermore, Mroz and colleagues reported that 96.5% of mus­culoskeletal allografts between 1994 and 2007 were recalled due to the poor donor screening, graft contamination, and recipient infection [31]. Additional challenges with allografts are donor age and comorbidities, in particular osteoporosis, all of which can significantly diminish the mechanical properties of the graft and contribute to lower fusion rates.
Structural allografts have been extensively used for several decades in single-level anterior cervical discectomy and fusion (ACDF) showing similar fusion rates to autograft alone [3234]. However, for multilevel ACDFs, there are mixed reports on the benefits of allograft substitutes vs. autograft [25, 27, 35]. Lumbar spine studies have reported excellent outcomes with the use of freeze-dried allografts in anterior fusion approaches [
36, 37]. Furthermore, Butterman
and coauthors found that the femoral ring allograft produced similar fusion rates as iliac crest bone graft (ICBG) and better overall out­comes than ICBG when used in anterior- posterior lumbar surgery [
38]. Figure 34.1 demonstrates a
successful lumbar posterior lateral fusion with autologous bone chips, cancellous allograft bone chips, and bone marrow aspirate.While auto­grafts have shown superior performance in poste­rior fusions, allograft graft extenders have demonstrated promising results in spine defor­mity surgeries. Combination of freeze-dried allograft and autograft demonstrated high fusion rates (92.7%–97.3%) and up to 5.9 degrees loss of correction in patients undergoing a fusion pro­cedure for the treatment of idiopathic scoliosis
34 Bone Grafting and Spinal Fusion Options
457
Fig. 34.1 (a) Patient 3 weeks postoperatively from a pos- terior lateral fusion with autologous bone chips and can­cellous allograft bone chips, as well as the use of bone marrow aspirate. (b) Postoperative image of the same
[39, 40]. Most common complications with the use of structural allografts include nonunion and fracture due to the nature of graft material and slower rates of incorporation.

Ceramics

Ceramics are osteoconductive bone substitutes without cells and growth factors and limited mechanical stability [41]. Although they have a brittle structure and reduced shear strength, ceramic grafts have very desirable characteris­tics: biodegradable, unlimited supply, non­immunogenic, and no disease transmission. Mechanical instability is compensated for with the use of internal fixation which helps with the load force resistance in the initial period after the procedure. Most commonly used ceramic scaf­folds for spinal fusion are calcium phosphates (hydroxyapatite (HA) and β-tricalcium phos- phate (β-TCP)), calcium sulfates, or a combina­tion of these materials. Both hydroxyapatite and β-TCP have pore sizes similar to cancellous bone and have prolonged resorption times. Hydroxyapatite is retained in vivo for up to a year, whereas the more porous β-TCP typically biodegrades in about 6 weeks [
42]. When
patient 8 months after surgery. Note the solid bony fusion in the lateral margins of the construct involving the trans­verse processes
implanted within the fusion space ceramic, scaf­folds support vascular ingrowth and cell migra­tion leading to new bone formation.
Hydroxyapatite and β-TCP have been used as bone graft extenders for both lumbar and cervical spine fusion [
43]. In a prospective non-
randomized cohort study, patients underwent posterior lumbar fusion with HA + local bone or ICBG [44]. At 1-year follow-up, both groups had similar fusion rates, with the average fusion mass volume being greater in the group with hydroxy­apatite chips. Similar results were reported by a few other cohort studies. On the other hand, Hsu et al. found that HA + local bone achieved only 57% fusion compared to the autograft group [
45].
Acharya and coauthors compared hydroxyapatite­bioactive glass ceramic as a substitute for auto­graft and found almost no fusion in the hydroxyapatite group at 1-year follow-up [
46].
Several studies explored the viability of HA as a graft extender or substitute in cervical fusion
43]. Both a randomized controlled trial and
[ cohort studies reported similar fusion rates in HA group (alone or with local bone) compared to autograft. However, graft fragmentation, graft settling, and instrumentation-related problems were observed more in the HA groups [
43]. On
the other hand, Yoshii T et al. reported similar
458
Z. Buser et al.
fusion rates between HA + local and autograft in ACDF with less blood loss and no graft fragmen­tation in the HA + local bone groups [
47].
As hydroxyapatite, β-TCP has also been used as graft extender in lumbar posterior fusion and ACDF. Studies focusing on posterior lumbar fusion found that combining β-TCP and local bone led to similar fusion rates, outcomes, revi­sion rates, and complications as autograft group [
4851]. In patients who underwent ACDF with a
combination of β-TCP and HA, fusion rates were significantly lower in the first 5 months compared to ICBG, reaching solid fusion at 6 months post­operatively [52]. In addition, the ceramic group had shorter operative time, shorter hospital stay, and less blood loss. It is important to note that most of the studies lacked blinded assessment of fusion and patient randomization (various spinal conditions and comorbidities).
Calcium sulfate is another ceramic graft occa­sionally used in spine fusion in combination with local bone or bone marrow aspirate. In a postero­lateral lumbar fusion study, patients who received calcium sulfate pellets mixed with local bone achieved 88% fusion rates at 1 year, compared to 100% fusion rates in the ICBG group [53]. Similarly, Chen et al. found that in single- and two-level posterolateral lumbar fusion, a mix of calcium sulfate and local bone produced similar fusion rates and bone mass compared to autoge­nous bone at 30–34 months follow-up [54]. However, when calcium sulfate was combined with bone marrow aspirate (BMA), fusion rates were significantly lower than in the ICBG group (46% vs. 91%, respectively) [
55].
Silicate-substituted calcium phosphate (SiCaP) is another form of ceramic grafting material that has been shown to contain some osteogenic properties. Two studies evaluated the potential of SiCaP in spine fusion; however, their results were contradictory. In a randomized clini­cal trial (RCT), Licina et al. observed 100% fusion rates in patients undergoing posterior lum­bar interbody fusion (PLIF) with SiCaP com­pared to 89% rate in patients who received recombinant human bone morphogenetic protein 2 (rhBMP-2) [
56]. On the other hand, Nandyala
and colleagues reported lower fusion rates (65%)
with SiCaP when compared to rhBMP-2 (92%) in minimally invasive transforaminal lumbar interbody fusion [
57].

Demineralized Bone Matrix (DBM)

In spine fusion, demineralized bone matrix (DBM) is used as graft extender or filler. DBM is produced from human cadaver allograft bone by removing the mineralized component, cells, and antigenic markers. DBMs have osteoconductive and some osteoinductive properties. The osteo­conductive matrix consists of type I collagen, glycoproteins, calcium sulfate, and debris. The osteoinductive properties of DBMs come from several growth factors that are preserved during the processing. Those growth factors include bone sialoprotein, osteopontin, and tumor growth factor beta (TGF-β) family [58]. The bone mor­phogenetic proteins (BMPs) are the most impor­tant osteogenic factors that carry out progenitor cell differentiation toward the mature osteoblast. It has been shown that with aging the levels of BMPs decrease; however, several other growth factors including TGF-β are not affected and can further extend the bone formation cascades and interactions with BMPs [59]. DBMs are pro­duced in powder form and are mixed with carri­ers (calcium sulfate, glycerol, gelatin, etc.) for easier delivery. Based on the carrier and the ratio, they come in different forms such as putty, gels, powder, and chips. Demineralized bone matrix has been extensively used in preclinical animal models and clinical trials. Rat spine fusion mod­els have demonstrated great osteoinductive vari­ability in commercially available DBMs which may reflect differences in the BMP content due to the donor variability and age [6062]. In an athy­mic rat posterolateral fusion model, Wang and coworkers demonstrated that Osteofil DBM paste had the highest fusion rates (77.8%) overall and also at the early time point, 4 weeks [62]. However, DynaGraft DBM putty did not produce any fusion within the experimental time period. Although the donor variability is a main draw­back, several other posterolateral spinal fusion animal studies have demonstrated good results
34 Bone Grafting and Spinal Fusion Options
459
with DBMs alone or in conjunction with auto­graft [6365].
Early clinical studies on DBM as bone graft extenders for posterolateral spinal fusion reported similar fusion rates to the ICBG group as well as bone mineralization [6668]. All of the studies concluded that DBM can be a successful graft extender reducing significantly the amounts of autograft needed to achieve solid fusion. It has also been found that DBM putty enriched with bone marrow is a good graft substitute for poste­rior spinal fusion with the fusion rates being com­parable to DBM + autograft or autograft alone [69]. Conversely, An and colleagues [70] prospec- tively compared the fusion rates of freeze-dried allograft-DBM composite and autograft in ACDF and found that the allograft-DBM construct resulted in a higher rate of pseudarthrosis (33% in DBM vs. 22% in autograft). Furthermore, the allograft-DBM group had a higher rate of graft collapse (2 mm and 3 mm) than the autograft alone. Several studies prospectively evaluated DBM with or without autograft packed into poly­ether ether ketone (PEEK) cages [71, 72]. Park et al. observed 97% fusion rates in ACDF patients with DBM and local autograft packed in PEEK cages, while Moon and colleagues reported fusion in 77.8% patients at 25.5 months follow-up (mean). However, in the study by Moon et al., 84% of the patients had some subsidence influ­encing regional and global alignment [72].
Apart from bone extenders, DBM was used as a delivery vehicle for growth factors and cells. In a rat posterolateral fusion (PLF) model, DBM matrix with adenovirus carrying a Nell-1 gene or LacZ (control) was implanted at L4-L5 level, and at 6 weeks postoperatively, microCT demonstrated 70% fusion rates in DBM + Nell-1 group compared to 20% in DBM + LacZ con­trol group [73].

Autologous Platelet Gel

Autologous platelet gels are created by concen­trating platelet-rich plasma, and they can be com­bined with autograft or allograft. They consist of platelets, platelet-derived growth factor (PDGF),
and TGF-β which promote chemotaxis and pro­liferation of mesenchymal stem cells and osteo­blasts. Although the animal studies demonstrated promising results with platelet gels in spine fusion, clinical data is inconclusive. Two retro­spective cohort studies looked at the effects of platelet gels on fusion rates in posterolateral spi­nal approach [74, 75]. Both studies found that when platelet gel was combined with autograft it failed to enhance fusion and it had lower fusion rates than autograft alone. In a transforaminal lumbar interbody fusion (TLIF) study done by Hee and colleagues, platelet gels promoted faster bone remodeling; however, there was no increase in the overall fusion rates [76]. On the other hand, Jenis et al. found similar fusion rates between (85%) and autograft supplemented with AGF (89%) in one- or two-level PLIF [77]. Autologous platelet gels have several disadvantages includ­ing blood draw and gel preparation, longer sur­gery time, and higher costs.

Bone Marrow Aspirates (BMAs)

Unfractionated bone marrow aspirate (BMA) has osteoinductive and some osteogenic characteris­tics. Due to the lack of osteoconductivity, BMA is always combined with a collagen or DBM car­rier. Several studies have evaluated the amount of osteoprogenitor cells in aspirated bone marrow samples. The colony-forming units that produce alkaline phosphatase (CFU-AP) are used to determine the number of osteoblastic progenitors
78, 79]. Muschler et al. found that the preva-
[ lence of CFU-AP was 55 per million nucleated cells. The authors also studied changes in the prevalence of osteoblastic progenitors in relation to age and gender. In women, there was a signifi­cant decrease in the number of osteoblastic pro­genitors with age. On the other hand, men showed a slight increase or no change in the number of osteoblastic progenitors with age [ sequent study, Muschler et al. determined the change in osteoblastic progenitors in relation to volume of aspirated bone marrow. As the volume of bone marrow aspirated increases, the number of osteoblastic progenitors also increases. Due to
78]. In a sub-
460
Z. Buser et al.
the increase in volume, however, the sample becomes increasingly contaminated by periph­eral blood. The authors noted a 50% decrease in the concentration of osteoblast progenitor cells when the aspirate is increased from 1 to 4 millili­ters [79]. Taghavi and colleagues retrospectively reviewed a cohort of patients undergoing instru­mented revision PLF with autograft only, BMA and autograft, and rhBMP-2 on collagen sponge [80]. In single-level fusion, all groups achieved solid fusion, but in the multilevel the BMA group had a 63.6% fusion rate, while the other two groups had 100%. Niu and coauthors compared the efficacy of BMA with different carriers in promoting fusion in single-level PLF study [55]. They found that combination of BMA and autog­enous graft had similar fusion rates to ICBG alone (85.7% vs. 90.5%, respectively). However, the calcium sulfate and BMA group achieved only 45.5% fusion compared to 90.9% with ICBG on the control side [55]. In a systematic review, Khashan et al. reported several PLF stud­ies which had similar fusion rates between BMA with a carrier and ICBG group, but the overall level of evidence was weak [81].

Bone Morphogenetic Proteins (BMPs)

In 1965, Dr. Marshall Urist performed a land­mark study in which demineralized bone implanted into the muscle of a rabbit induced bone growth in surrounding tissues [82]. Because this bone-forming activity could be extracted from the organic component of the bone, Dr. Urist theorized that some type of protein or pro­teins were responsible for these phenomena and gave it the name “bone morphogenetic protein.” With the advances in recombinant DNA and pro­tein purification techniques, isolates of the vari­ous BMPs were procured and studied for their ability to induce bone formation. They were cat­egorized into the transforming growth factor beta (TGF-B or TGF-β) superfamily based on their primary amino acid sequence [83]. Unlike the other members of the family, the BMPs are dif­ferentiation factors, inducing mesenchymal stem
cells to differentiate into bone-forming and cartilage- forming cells. The effects of BMPs occur through ligand-specific receptors found on the cell membrane. These receptors are com­plexes of type I and type II serine-threonine pro­tein kinases. Upon ligand binding to the type II receptor, transphosphorylation occurs in the type I receptor. This then leads to phosphorylation of intracellular proteins known as Smads, with eventual activation of target genes [84]. The most extensively studied BMP is the recombinant human bone morphogenetic protein 2 (rhBMP-
2). Validation studies of rhBMP-2 use in the spine showed excellent results with essentially zero complications [85, 86]. Based on these stud­ies, BMP2 was FDA-approved for anterior lum­bar interbody fusions with the use of a specific type of threaded cage (LT cages, Medtronic). Initial positive results led to widespread off-label
increased from 0.7% of all fusions in 2002 to more than 50% of primary ALIFs, 43% of PLIF/ TLIFs, and 30% of PLFs in 2007 [87]. It became known as the “most successful medical device in history,” garnering 40% of the bone graft market with annual sales approaching $900 million dol­lars in 2011 [88].
With widespread use, several complications were reported including radiculitis, cyst forma­tion, seroma formation, endplate resorption, ret­rograde ejaculation, and ectopic bone formation. Because of well-documented reports of adverse events occurring with its use in ventral cervical spine surgery, the FDA issued a Public Health Notification in July of 2008, underscoring “life­threatening complications of rhBMP-2 in cervi­cal spine surgery” [89]. A systematic review in 2010 by Mroz et al. evaluated the available litera­ture regarding site- and procedure-specific com­plication rates with rhBMP-2 [90]. They found a high percentage of resorption (44%), graft sub­sidence (25%), and cage migration (27%) in the lumbar spine. Similar results were seen in the cervical spine with resorption (43%), but higher graft subsidence (43%) was seen. The incidence of dysphagia/neck swelling and respiratory diffi­culties were found to be approximately 6%. This systematic review concluded that the complica-
34 Bone Grafting and Spinal Fusion Options
461
tions associated with the use of BMP could be “substantial.” In 2011 Carragee et al. published an article questioning the veracity and reporting bias of the initial validation studies for rhBMP-2 [91]. They found that the rate of complications was 10–50 times higher than what was reported in the validation studies, critical methodological flaws within the studies themselves, and serious deficiencies within the peer review process that evaluated these studies. Faced with controversy and questions, Medtronic turned over all data to the Yale Open Data Analysis (YODA) Project. YODA was created as a new model to evaluate industry-sponsored clinical trials, with the goal of increasing transparency, disseminating data, and increasing the benefit with mitigation of risk to patients. YODA selected two different sites to the review the data, the Oregon Health and Science University and University of York in the United Kingdom. At the Oregon Health Sciences University, Fu et al. [92] reviewed 13 randomized control trials, 31 other cohort studies, 47 inter­vention series, and 34 case series and reports. Simmonds et al. at the York University reviewed 11 randomized control trials and 43 other publi­cations [93]. Both papers commented on the methodological flaws in the validation studies, namely, a lack of blinding among physicians and patients. At the same time, both studies agreed that there were no significant differences in clini­cal outcomes between ICBG and rhBMP-2, a sig­nificantly higher risk with its use in anterior cervical fusions, and increased relative risk that did not reach significance with its use in both anterior and posterior lumbar fusions. There was a significantly increased risk of back and leg pain in the immediate postsurgical period when rhBMP-2 was used in posterolateral fusions. Fu et al. concluded that they could see no clear indi­cation for the use of rhBMP-2 as there was no significant benefit in measured clinical outcomes. They also stated that though the overall rates of cancer were low, there was an increased risk of cancer with rhBMP-2 at 24 months; however, at 48 months these differences were no longer sig­nificant. Simmons et al. concluded the use of rhBMP-2 resulted in increased fusion rates that did not translate into improved clinical outcomes
and increased back and leg pain with its use dur­ing the first 6 months. They found trends toward increases in cancer, but no significance in this regard [93]. Their differing conclusions indicate that the results are highly dependent on study selection; that if there is an increased risk of can­cer with the use of rhBMP-2, it is likely small, that rhBMP-2 should be used in caution with patients that have a history of cancer; and that future analysis incorporating more of the data can help draw more definitive conclusions.

Cell-Based Therapies

Cell-based approaches have primarily focused on the use of mesenchymal stem cells (MSCs), exploiting their potential for differentiation into various lineages and their low immunogenicity. MSCs have been tested in various animal models for spine fusion together with a carrier or as a vehicle for the delivery of growth factors [94
100]. Bone marrow stem cells (BMSCs) in par-
ticular have shown a great potential in promoting osteogenesis and have been extensively used in in vitro and in vivo models [94, 95, 97100]. However, the disadvantages of BMSC lie in their low numbers and the harvest morbidity. Because of that, the use of adipose stem cells has gained popularity, due to their fairly easy isolation, higher numbers of stem cells, and prolonged osteogenic potential [ et al. compared the potential of human bone mar­row and adipose-derived stem cells transfected with BMP2 in inducing fusion in a posterolateral rat model. They found that at 8 weeks postopera­tively animals that have received stem cells (either adipose or bone marrow) with BMP showed fusion that in most of the cases bridged the adjacent levels. Animals with stem cells alone however did not form new bone. These results are in agreement with other studies showing that pre­differentiated stem cells had a higher osteogenic potential than naïve cells. Nakajima and coau­thors reported that the successful fusion was the highest in animals that received scaffolds with osteogenic stem cells (80%), followed by autografts (66.7%) and non-differentiated stem
96, 98, 100]. Miyazaki
462
Z. Buser et al.
cells (33.3%) [99]. The clinical use of stem cells for spine fusion is being investigated in several clinical trials. Khashan et al. conducted a system­atic review evaluating the efficacy of MSC or BMA in conjunction with graft extenders for cer­vical and thoracolumbar fusions and how they compare to autograft [81]. Their review found that eligible studies had a low level of evidence and there was no clinical evidence on the use of MSC as graft extender or substitute [81]. While stem cells show great potential to be a powerful tool in spine fusions, there are also several limita­tions, starting with a decline in the number and quality of stem with age, metabolic diseases, or comorbidities such as smoking. Other obstacles are missing cell expansion protocols that will maintain a stable phenotype under GMP condi­tions and the potential for contaminations and complications.

Modulus of Elasticity

In the early stages of spine fusion, the mechani­cal loading is the key element which balances new bone formation and resorption. Various implants and instrumentation are used to lend initial mechanical support to the fusion site. To be considered suitable, those materials have to have mechanical properties similar to the host tissue (Table 34.2) [101, 102], have the right pore size for cell migration and blood vessel ingrowth, be biocompatible, and tolerate steril­ization. Polyether ether ketone (PEEK), titanium (Ti), and its alloys are the most commonly used
Table 34.2 Modulus of elasticity
Tissue or implant material Modulus (GPa) Cortical bone 12.8–17.7 Cancellous bone 0.4 Stainless steel 190 Ti-alloy 116 PEEK 8.3 HA-PEEK 9.6–10.6 PMMA 2.6 HA 95
Values adopted from Ramakrishna et al. [
102]
materials in spine fusions. PEEK cages are bio­compatible and radiolucent and their elasticity modulus is lower than the cortical bone (Table 34.2). Fusion success with PEEK cages has been demonstrated in various studies; how­ever, osteogenic cell migration and adhesion were reduced compared to Ti [101, 102]. Studies have shown that the addition of hydroxyapatite to PEEK increased osseointegration and the elasticity modulus (up to 10.6 GPa). Ti and its alloys are biocompatible, have great resistances to corrosion, have low density, and have been used in the spine field for decades [101, 102]. In contrast to PEEK, titanium has a very high elas­ticity modulus (Table 34.2) that is six- to seven­fold higher than the cortical bone which can contribute to subsidence and implant failure. Furthermore, Ti and its alloys are not radiolucent and have low osseointegration potential in their unmodified form. Various modifications have been used to improve the elasticity modulus and the in- and on-growth of osteoblasts. The most common modifications include creation of sur­face microscale roughness, thermal or chemical treatments, and HA coating [101, 102]. HA coat­ing of Ti in particular has shown good results in bone formation, providing good mechanical sta­bility, and osseointegration properties.
Other materials such as tantalum, polymethyl methacrylate (PMMA), and stainless steel have been used for spine implants. However, their elasticity modulus is very different from the auto­graft (Table 34.2) which can compromise the mechanical stability of the fusion site. The mechanical properties of the implant are not only important within the fusion site but also influence the adjacent, unfused segments and the progres­sion of intervertebral disc degeneration.

Surgical Technique Autologous Iliac Crest Harvesting

Anterior

The anterior approach to the iliac crest is used for anterior reconstructive procedures. Cancellous or corticocancellous grafts can be obtained with this
34 Bone Grafting and Spinal Fusion Options
463
method. This approach may be preferable during a procedure in which the patient is already supine, but a disadvantage is the lower volume of obtain­able bone. Harvesting from the anterior iliac crest should be used only if less than 20–30 cc of the bone is required. The patient is positioned supine with a bump under the ipsilateral gluteal region to accentuate the anterior superior iliac spine (ASIS). The incision is made parallel to the hip and a wide area should be sterilely draped. At least 3 cm of the ASIS needs to be kept intact to avoid injury to the insertion of the sartorius mus­cle and inguinal ligament. The lateral femoral cutaneous nerve may have an anomalous course in this region and should be avoided. The integ­rity of the ASIS should not be compromised, or a stress fracture can result from the forces of the sartorius and rectus femoris musculature.
A 3–6 cm curved incision is placed 3–4 cm lateral to the ASIS. The incision, which runs superiorly and posteriorly, is made over or just below the crest to minimize postoperative pain. The fascia should be opened carefully to facili­tate proper closure at the end of the procedure. Inadequate fascial closure increases the risk of hernia. The periosteum is incised and elevated from the ilium, thus exposing cortical bone which can be perforated with a Rongeur or osteotome. The iliac tubercle, located 5 cm posteriorly from the ASIS, contains a large amount of cancellous bone for harvesting. Once the cortex at the brim of the ilium has been violated, curettes are used to remove the inner graft material. An osteotome is used to enter the iliac crest obliquely, thus sep­arating the inner and outer tables from a central graft, which provides a block of bone up to 10 by 8 cm in size. The muscle and periosteum are left attached to the outer ridge of the iliac crest. Wire or sutures are used to reapproximate the inner and outer ilium. Tricortical grafts require more dissection. A 6 cm incision is followed by sub­periosteal dissection of the inner and outer tables of the ilium. Bone graft is harvested at least 3 cm posteriorly from the ASIS by using parallel saw blades to enter the tables of the ilium. An oscillat­ing saw is preferable to an osteotome because of weakening of the remaining iliac crest that may
occur with osteotomes. The peritoneal cavity, which lies medially, should not be violated. Careless dissection of the iliacus from the inner wall can injure the iliohypogastric and ilioingui­nal nerves, femoral nerve, deep circumflex iliac artery, and iliolumbar arteries. Once the iliac crest is fully exposed, the size of the graft should be measured carefully in all three dimensions. The graft is fashioned with a reciprocating sagittal saw. Final removal of the bone may require the use of osteotomies to free the bone from attach­ments in the inferomedial region. Hemostasis of the exposed bony surfaces may be achieved using several techniques which include bone wax or other hemostatic agents. If necessary, a drain may be left in place to avoid formation of a seroma.

Posterior

For posterior procedures, onlay graft material may be needed to supplement the fusion con­struct. Dorsal spinal surgeries do not require structural graft because dorsal instrumentation is typically implanted. The advantage of dorsal iliac crest grafts is the large volume of available bone. Two approaches are available: the bone can either be harvested through the midline lumbar incision that has been made for the current spinal decom­pression, or a separate incision can be made lat­eral to the surgical site. If graft is to be harvested from the midline lumbar incision, a fascial inci­sion is made approximately 6 cm laterally from the site of decompression. Dissection risks injury to the superior cluneal nerves, which exit from the lumbodorsal fascia and course as close as 6 cm lateral to the PSIS. The fascia over the PSIS is incised and elevated from the ilium with elec­trocautery and a Cobb elevator. Dissection should be at least 4 cm lateral to the PSIS to avoid iatro­genic injury to the sacroiliac joint and neurovas­cular structures exiting from the greater sciatic notch. Externally, the sciatic nerve, superior glu­teal nerve, and branches of the superior gluteal artery travel cephalad after exiting the greater sciatic notch. Internally, the superior gluteal artery and the ureter are of concern. An opening