- Open Access
Preliminary results in anterior cervical discectomy and fusion with an experimental bioabsorbable cage – clinical and radiological findings in an ovine animal model
© Daentzer et al.; licensee Springer. 2013
- Received: 29 June 2013
- Accepted: 22 August 2013
- Published: 29 August 2013
Bioabsorbable implants are not widely used in spine surgery. This study investigated the clinical and radiological findings after anterior cervical discectomy and fusion (ACDF) in an ovine animal model with an experimental bioabsorbable cage consisting of magnesium and polymer (poly-ϵ-caprolactone, PCL) in comparison to a tricortical bone graft as the gold standard procedure.
Materials and Methods
24 full-grown sheep had ACDF of C3/4 and C5/6 with an experimental bioabsorbable implant (magnesium and PCL) in one level and an autologous tricortical bone graft in the second level. The sheep were divided into 4 groups (6 sheep each). After 3, 6, 12, or 24 weeks postoperatively, the cervical spines were harvested and conventional x-rays of each operated segment were conducted. The progress of interbody fusion was classified according to a three-point scoring system.
There were no operation related complications except for one intraoperative fracture of the anterior superior iliac spine and two cases of screw loosening and sinking, respectively. In particular, no vascular, neurologic, wound healing or infectious problems were observed. According to the time of follow-up, both interbody fusion devices showed similar behaviour with increasing intervertebral osseointegration and complete arthrodesis in 10 of 12 (83.3%) motion segments after 24 weeks.
The bioabsorbable magnesium-PCL cage used in this experimental animal study showed clinically no signs of incompatibility such as infectious or wound healing problems. The radiographic results regarding the osseointegration are comparable between the cage and the bone graft group.
- Animal model
- Bioabsorbable cage
- Cervical spine
- Ovine animal model
Anterior cervical discectomy and fusion (ACDF) is a standard procedure performed in patients with degenerative disc disease, disc prolapse and spinal canal stenosis. The anterior approach to the cervical spine to perform an arthrodesis was simultaneously published by Bailey and Badgley, Cloward, and Smith and Robinson (Bailey and Badgley 1960, Cloward 1958, Smith and Robinson 1958). The authors used bone dowels in cylindric- or box-shaped design, either harvested from the patient’s iliac crest or taken from human donors as allogenic material. The clinical success rate reported in literature is very high and the radiologic signs of complete bony fusion are reported to come up to 98% (Savolainen et al. 1994). There are some disadvantages of taking the bone from the iliac crest as possible complications such as infection, hematoma, fractures, and prolonged donor site pain in up to 49% of operated patients (Banwart et al. 1995). Due to the long experience with this surgical technique, this procedure is considered to be the gold standard with which all alternative therapeutic options have to be compared in regard to the clinical and radiological outcome with special interest to the fusion rate as well as to the complication rate. About 20 years ago, Kaden et al. reported the use of a titanium implant as an interbody fusion device for the cervical spine, a so-called “cage” (Kaden et al. 1993). Although the initial results are favourable, long-term effects of metallic cage devices on cervical spine motion segments are still unknown (Hacker et al. 2000, Matge 1998). Some shortcomings of metallic interbody implants, like cage migration, subsidence, adjacent level degeneration, stenotic myelopathy, and non-union have already been reported (Cabraja et al. 2012, Chen et al. 2013, Daentzer et al. 2005, Hacker et al. 2000, Majd et al. 1999, Matge 1998, Wilke et al. 2002). One further relevant disadvantage of these metallic implants is the fact, that they lead to artifacts during computed tomography (CT) and magnetic resonance imaging (MRI), complicating early detection of a metastatic recurrence and the evaluation of interbody fusion (Schulte et al. 2000). Because of their high axial compression stiffness, metallic cages may lead to stress shielding of the cancellous bone grafts inside the cage, resulting in a decreased interbody bone matrix formation or non-union (Epari et al. 2005, Kandziora et al. 2001a, 2002, Kanayama et al. 2000, van Dijk et al. 2002b). At the same time, experience with carbon fiber cages as cervical spinal interbody fusion devices had been reported (Brooke et al. 1997, Shono et al. 1993). The elasticity modulus of the carbon fiber material comes near to that of cortical bone which leads to a physiologic distribution of the forces to the adjacent endplates (Shono et al. 1993). However, subsidence is an imminent risk even during the application of carbon fiber cages (Wilke et al. 2002). Because of the radiolucent properties, carbon fiber devices do not cause any artifacts during CT or MRI. But a potential risk is the wear debris of the carbon fibers which can lead to inflammatory and foreign body reactions (Parsons et al. 1985). Since the beginning of this millennium, implants of polyetheretherketone (PEEK) have been used more frequently (Cho et al. 2002). Analogous to carbon fiber material, postoperative CT and MRI can be performed without having interfering artifacts and the evaluation of fusion is not problematic. Furthermore, the elasticity modulus of PEEK is more similar to bone than that of titanium and carbon fiber material with less risk of subsidence into the vertebral endplates. Nevertheless, subsidence in cages which consist of PEEK with consecutive segmental kyphosis had been observed in several clinical studies (Cabraja et al. 2012, Chen et al. 2013, Kast et al. 2009, Lemcke et al. 2011).
In general, the clinical success rate is supposed to be independent of the selected material (bone, titanium, carbon fiber, PEEK), because the clinical success rate seems more likely to be a consequence of the indication for the surgery and of performing a sufficient decompression in case of any stenotic pathology. However, the question of the ideal fusion cage to replace the degenerated disc is still on discussion. Bioabsorbable implants could play an important role to find the optimal material for interbody fusion, but actually they have in vivo only been used in animal experiments or in a few clinical studies (Chunguang et al. 2011, Kandziora et al. 2001a, b, Lippman et al. 2004, Vaccaro et al. 2004). Relevant problems seemed to be the low primary stability with development of cracks and possible foreign body reactions with inflammatory signs which raised skepticism regarding the value of bioabsorbable implants and led to a very limited use in clinical practice (Kandziora et al. 2004).
In our preclinical study we performed ACDF in an ovine model with a newly developed bioabsorbable cage as a fusion device which consisted of a magnesium structure infiltrated with a polymer (poly-ϵ-caprolactone, PCL). This material combination was chosen after in vitro-investigation of the mechanical properties of both substances with demonstration of an adequate initial compression strength for implantation in the cervical spine (Kauth et al. 2012). The favourable characteristics of magnesium alloys are the ability to degradation, a similar elasticity modulus to bone, a stimulation effect to bone growth and good biocompatibility (Shi et al. 2010, Staiger et al. 2006, Xu et al. 2007, Zeng et al. 2008). The PCL is known for its bioabsorbability with slow degradation, and it is radiolucent and not toxic (Albertsson and Karlsson 1995, Hiljanen-Vainio et al. 1996, Kronental 1975). The idea to combine these two kinds of material as a hybrid cage was to ensure a sufficient primary stability by the magnesium skeleton and to prevent too fast degradation by infiltration of the magnesium alloy with the PCL (Kauth et al. 2012). The goal of our investigation is to show the clinical findings, complications and the radiographic results of the harvested spinal segments (3, 6, 12, and 24 weeks after surgery) and to compare the osseointegration of the magnesium-PCL implant with the autologous bone graft.
Anaesthesia and surgical procedure
Ingrowth of bone with the cage securely fixed to the vertebral bone above and below, but with a radiolucent discontinuity in the fusion mass
Arthrodesis with solid bone bridging the fusion area
All 24 animals recovered from the operation without unusual events. They came to normal ambulatory activities at the first day after the operation without any restrictions.
Complications, time of diagnosis and consequence
Time of diagnosis after operation
Temporary signs of bronchitis
Antibiotics for 10 days
Loosening of the upper screw pair in the lower segment (C5/6, magnesium-PCL cage)
Limitation in ROM of the cervical spine to one side because of pain
Sinking of cranial screw pairs of both segments (C3/4, bone graft, and C5/6, magnesium-PCL cage)
Weakness of the legs with tendency to fall after transport to outdoor area
Analgesics and cortisone (complete recovery)
Fracture of ASIS
Acute massive diarrhea
Intraoperative fluoroscopy and directly postoperative lateral radiographs showed adequate positioning of all interbody fusion devices as well as of the plate osteosynthesis. In contrast to the Caspar plate, which showed relevant problems like screw loosening and sinking in two of three cases, the ABC2 plate worked perfectly without any signs of screw loosening or sinking or breakage at all.
After 3 weeks (n=6)
After 6 weeks (n=6)
After 12 weeks (n=6)
After 24 weeks (n=6)
For evaluation of new interbody fusion devices, an appropriate animal model has to be chosen for preclinical testing. This model should be an adequate substitute to perform in vivo and in vitro studies. In search of an implant for ACDF, previous investigations have brought out the similar properties of the ovine and the human cervical spine with regard to anatomy and biomechanics (Kandziora et al. 2001a, Wilke et al. 2000, Wilke et al. 1997). In addition to the ovine cervical spine the caprine cervical spine also has been proven to be a very good model and both species were regularly used in the past for in vivo and in vitro studies to evaluate the characteristics of fusion properties as well as to analyze the biomechanical behavior of newly developed implants or substances (Chunguang et al. 2011, Kandziora et al. 2001a, Lippman et al. 2004, Kandziora et al. 2004, Cornwall et al. 2004, Goldschlager et al. 2011, Pflugmacher et al. 2004a, b, Schreiner et al. 2007, Takahashi et al. 1999, Thomas et al. 2008, Toth et al. 1995).
The main advantage of bioabsorbable materials in contrast to current cage devices (titanium, PEEK, carbon) is the potential for degradation over a distinct period of time. After that, they do not obscure postoperative radiologic assessment of intervertebral fusion and do not prevent the evaluation of the operated segment in CT or MRI because of artifacts caused by metallic implants. The optimal implant has a stiffness comparable to that of bone, which may reduce stress shielding of the graft inside the cage, possibly resulting in an accelerated interbody fusion (Chunguang et al. 2011). During the degradation process loading is transferred gradually to the healing bone and the void inside the cage is replaced with bone (van Dijk et al. 2002aSmit et al. 2003). After solid fusion of segments, cages will be absorbed, leaving no particles and avoiding great bone defects caused by removing metallic implants in revision surgery.
There are several reports about bioabsorbable implants used for ACDF in animal models (Chunguang et al. 2011, Lippman et al. 2004, Kandziora et al. 2004, Pflugmacher et al. 2004a, Thomas et al. 2008). Only few clinical studies had inserted bioabsorbable cages for ACDF in humans (Vaccaro et al. 2004). Most of these bioabsorbable cages consist of polylactide (70/30 PLDLLA, poly(L-lactide-co-D,L-lactide), which naturally degrades to carbon dioxide and water (Vaccaro et al. 2004, Kandziora et al. 2004, van Dijk et al. 2002b, Pflugmacher et al. 2004a, Smit et al. 2003). Alternative bioabsorbable materials are PCC (polymer-calciumphosphate composite), composites of 70:30 or 85:15 PLDLLA/PGA (polyglycolic acid) or MAACP/α-TCP (multiamino acid copolymer/α-tricalcium phosphate) (Chunguang et al. 2011, Lippman et al. 2004, Kandziora et al. 2004). Although most of these studies show that solid fusion can be achieved with such cages and no serious tissue response to degradation of cages is found, some negative effects have been reported (Chunguang et al. 2011, Lippman et al. 2004, Kandziora et al. 2004, Pflugmacher et al. 2004a). These were cracks with insufficient primary stability and foreign body and inflammatory reactions with consecutive osteolysis. Therefore, bioabsorbable materials have not yet reached the status of a standard implant for ACDF.
Degradable metal implants made of magnesium alloys were introduced into orthopaedic and trauma surgery in the first half of the last century and screws and plates which consisted of magnesium alloys provided stable implant materials that degraded in vivo, eliminating the need for a second operation for implant removal (Witte et al. 2005). To our knowledge the present study is the first one using an experimental cervical interbody fusion cage consisting of a magnesium alloy and a polymer. Therefore, the radiologic results cannot be directly compared with the results from previous studies. The radiographic analysis of the intervertebral implants had been made according to a three-point score described by van Dijk et al. to assess the grade of bony fusion (van Dijk et al. 2002a, b). After 24 weeks, almost all treated disc spaces (10 of 12, 83.3%) showed radiologically solid bone bridging of the fusion area meaning a successful arthrodesis. On the basis of the radiographic score, both implant types (magnesium-PCL cage and tricortical bone graft) showed very similar behavior and no obvious differences between both materials regarding the osseointegration at all four points of follow-up. As a result of this analysis we could assume that the magnesium-PCL implant has an identical fusion behavior and enhances osseointegration in the same manner as autologous bone, which is still the gold standard in ACDF. However, one limitation of the study is the exclusive evaluation of the fusion signs on the basis of standard lateral radiographs. In the publications of van Dijk et al. the motion segments were additionally cut to 5 mm thick parasagittal sections which also underwent lateral radiography (van Dijk et al. 2002a, b). Using these additional images the assessment of the fusion rate can be made more precisely, mainly in the inside of the cage device. Better imaging techniques to estimate the grade of interbody bony ingrowth would be analysis by CT scan or μ-CT, which makes it possible to determine the fraction of degraded implant material in detail. Furthermore, it was necessary to adapt the technique of fusion assessment described by van Dijk et al. to the autologous bone grafts, in which the lack of a cavity inside the bony implant has to be considered. This forms a contrast to the conditions in a “cage”, in which a fusion can actually happen by successive osseous growth through the cage (van Dijk et al. 2002a, b). However, in another report the same radiographic score was used for bone grafts and in our experience this technique proved to be appropriate also in bone grafts taken for interbody fusion because it is possible to determine the progressive building of new trabecular bone inside the bone dowel indicating increasing osseointegration (Chunguang et al. 2011).
To date, the clinical relevance of the prevertebral gas accumulation in front of the magnesium implant, which was observed after three weeks in 50% of the treated disc spaces is not clear. It is a well-known phenomenon that a certain amount of hydrogen develops as a product of magnesium corrosion during the process of degradation (Witte 2010, Witte et al. 2005, 2008). In the present study the gas constantly disappeared within week 3 to 6 after surgery, so the gas was no more seen at the 6 weeks follow-up. Clinical signs for relevant problems due to the gas like visible swelling or dysphagia did not occur.
Both types of implants (magnesium-PCL cage and bone graft) showed very similar behavior on the basis of the radiographic classification, regarding the tendency to osseointegration with no obvious difference between them to all four points of time during the follow-up period and with an almost always complete arthrodesis after 24 weeks. These findings are worth to be analyzed more exactly regarding the characteristics of the experimental magnesium-PCL implant and to allow a comprehensive statement about the in vivo and in vitro behavior of the tested bioabsorbable cage by further investigations, including μ-CT as well as biomechanical and histological analysis to obtain more information regarding the degradation, the stiffness and osseointegration parameters.
The study was financed by the Arbeitsgemeinschaft industrieller Forschungsvereinigungen (AiF) as part of the program to support “Industrial Community Research and Development (IGF)” by the German Federal Ministry of Economy and Technology (BMWi) due to an enactment of the German Bundestag through the AiF.
We hereby express our thanks to Prof. Dr. med. vet. Klaus Otto (DVM) for his excellent support in planning and realization of the animal study.
- Albertsson A-C, Karlsson S: Degradable polymers for the future. Acta Polymerica 1995, 46: 114-123. 10.1002/actp.1995.010460203View ArticleGoogle Scholar
- Bailey RW, Badgley CE: Stabilization of the cervical spine by anterior fusion. J Bone Joint Surg Am 1960, 42: 565-594.Google Scholar
- Banwart JC, Asher MA, Hassanein RS: Iliac crest bone graft harvest donor site morbidity. A statistical evaluation. Spine 1995, 20: 1055-1060.Google Scholar
- Brooke NSR, Rorke AW, King AT, Gullan RW: Preliminary experience of carbon fibre prostheses for treatment of cervical spine disorders. Br J Neurosurg 1997, 11: 221-227. 10.1080/02688699746285View ArticleGoogle Scholar
- Cabraja M, Oezdemir S, Koeppen D, Kroppenstedt S: Anterior cervical discectomy and fusion: Comparison of titanium and polyetheretherketone cages. BMC Musculoskelet Disord 2012, 13: 172. 10.1186/1471-2474-13-172View ArticleGoogle Scholar
- Chen Y, Wank X, Lu X, Yang L, Yang H, Yuan W, Chen D: Comparison of titanium and polyetheretherketone (PEEK) cages in the surgical treatment of multilevel cervical spondylotic myelopathy: a prospective, randomized, control study with over 7-year follow-up. Eur Spine J 2013, 22: 1539-1546. 10.1007/s00586-013-2772-yView ArticleGoogle Scholar
- Cho D-Y, Liau W-R, Lee W-Y, Liu J-T, Chiu C-L, Sheu P-C: Preliminary experience using polyetheretherketone (PEEK) cage in the treatment of cervical disc disease. Neurosurgery 2002, 51: 1343-1350.Google Scholar
- Chunguang Z, Yueming S, Chongqi T, Hong D, Fuxing P, Yonggang Y, Hong L: Evaluation of bioabsorbable multiamino acid copolymer/α-tri-calcium phosphate interbody fusion cages in a goat model. Spine 2011, 36: E1615-E1622. 10.1097/BRS.0b013e318210ca32View ArticleGoogle Scholar
- Cloward RB: The anterior approach for removal of ruptured cervical discs. J Neurosurg 1958, 15: 602-617. 10.3171/jns.1958.15.6.0602View ArticleGoogle Scholar
- Cornwall GB, Ames CP, Crawford NR, Chamberlain RH, Rubino AM, Seim HB III, Turner AS: In vivo evaluation of bioresorbable polyactide implants for cervical graft containment in an ovine spinal fusion model. Neurosurg Focus 2004, 16: E5.View ArticleGoogle Scholar
- Daentzer D, Asamoto S, Böker D-K: HAC titanium as an implant for interbody fusion in spondylotic stenosis of the cervical spine. Six year clinical results. Orthopade 2005, 34: 234-240. 10.1007/s00132-004-0721-5View ArticleGoogle Scholar
- Epari DR, Kandziora F, Duda GN: Stress shielding in box and cylinder cervical interbody fusion cage designs. Spine 2005, 30: 908-914. 10.1097/01.brs.0000158971.74152.b6View ArticleGoogle Scholar
- Goldschlager T, Rosenfeld JV, Ghosh P, Itescu S, Blecher C, McLean C, Jenkin G: Cervical interbody fusion is enhanced by allogeneic mesenchymal precursor cells in an ovine model. Spine 2011, 36: 615-623. 10.1097/BRS.0b013e3181dfcec9View ArticleGoogle Scholar
- Hacker RJ, Cauthen JC, Gilbert TJ, Griffith SL: A prospective randomized multicenter clinical evaluation of an anterior cervical fusion cage. Spine 2000, 30: 2646-2655.View ArticleGoogle Scholar
- Hiljanen-Vainio M, Karjalainen T, Seppälä J: Biodegradable lactone copolymers. I. Characterization and mechanical behavior of ϵ-caprolactone and lactide copolymers. J Appl Polym Sci 1996, 59: 1281-1288. 10.1002/(SICI)1097-4628(19960222)59:8<1281::AID-APP11>3.0.CO;2-9View ArticleGoogle Scholar
- Kaden B, Swamy S, Schmitz HJ, Reddemann H, Fuhrmann G, Gross U: Titanium implant as an alternative possibility in fusion of the cervical vertebrae – initial clinical experiences. Zentralbl Neurochir 1993, 54: 166-170.Google Scholar
- Kanayama M, Cunningham BW, Haggerty CJ, Abumi K, Kaneda K, McAfee PC: In vitro biomechanical investigation of the stability and stress-shielding effect of lumbar interbody fusion devices. J Neurosurg 2000, 93: 259-265.Google Scholar
- Kandziora F, Pflugmacher R, Schäfer J, Born C, Duda G, Haas NP, Mittlmeier T: Biomechanical comparison of cervical spine interbody fusion cages. Spine 2001, 26: 1850-1857. 10.1097/00007632-200109010-00007View ArticleGoogle Scholar
- Kandziora F, Pflugmacher R, Scholz M, Eindorf T, Schnake KJ, Haas NP: Bioabsorbable interbody cages in a sheep cervical spine fusion model. Spine 2004, 29: 1845-1855. 10.1097/01.brs.0000137060.79732.78View ArticleGoogle Scholar
- Kandziora F, Pflugmacher R, Scholz M, Schnake K, Lucke M, Schröder R, Mittlmeier T: Comparison between sheep and human cervical spines. An anatomic, radiographic, bone mineral density, and biomechanical study. Spine 2001, 26: 1028-1037. 10.1097/00007632-200105010-00008View ArticleGoogle Scholar
- Kandziora F, Schollmeier G, Scholz M, Schaefer J, Scholz A, Schmidmaier G, Schröder R, Bail H, Duda G, Mittlmeier T, Haas NP: Influence of cage design of interbody fusion in a sheep cervical spine model. J Neurosurg 2002, 96: 321-332.Google Scholar
- Kast E, Derakhshani S, Bothmann M, Oberle J: Subsidence after anterior cervical interbody fusion. A randomized prospective clinical trial. Neurosurg Rev 2009, 32: 207-214. 10.1007/s10143-008-0168-yView ArticleGoogle Scholar
- Kauth T, Hopmann C, Kujat B, Bach FW, Welke B, Hurschler C, Kalla K, Daentzer D: Mechanical testing of an absorbable hybrid fusion cage for the cervical spine. Biomed Tech 2012, 57: 353-358.View ArticleGoogle Scholar
- Kronenthal RL: Biodegradable polymers in medicine and surgery. Polym Sci Tech 1975, 8: 119-137.Google Scholar
- Lemcke J, Al-Zain F, Meier U, Suess O: Polyetheretherketone (PEEK) spacers for anterior cervical fusion: A retrospective comparative effectiveness clinical trial. Open Orthop J 2011, 5: 348-353. 10.2174/1874325001105010348View ArticleGoogle Scholar
- Lippman CR, Hajjar M, Abshire B, Martin G, Engelman RW, Cahill DW: Cervical spine fusion with bioabsorbable cages. Neurosurg Focus 2004, 16: E4.View ArticleGoogle Scholar
- Majd ME, Vadhva M, Holt RT: Anterior cervical reconstruction using titanium cages with anterior plating. Spine 1999, 24: 1604-1610. 10.1097/00007632-199908010-00016View ArticleGoogle Scholar
- Matge G: Anterior interbody fusion with the BAK-cage in cervical spondylosis. Acta Neurochir 1998, 140: 1-8. 10.1007/s007010050049View ArticleGoogle Scholar
- Michaeli W, Pfannschmidt L-O: Microporous resorbable implants produced by the CESP process. Advanced Eng Materials 1999, 1: 206-208. 10.1002/(SICI)1527-2648(199912)1:3/4<206::AID-ADEM206>3.0.CO;2-AView ArticleGoogle Scholar
- Parsons JR, Bhayani S, Alexander H, Weiss AB: Carbon fiber debris within the synovial joint. A time-dependent mechanical and histologic study. Clin Orthop Relat Res 1985, 196: 69-76.Google Scholar
- Pflugmacher R, Eindorf T, Scholz M, Gumnior S, Krall C, Schleicher P, Haas NP, Kandziora F: Biodegradable cage. Osteointegration in spondylodesis of the sheep cervical spine. Chirurg 2004, 75: 1003-1012. 10.1007/s00104-004-0884-yView ArticleGoogle Scholar
- Pflugmacher R, Schleicher P, Gumnior S, Turan O, Scholz M, Eindorf T, Haas NP, Kandziora F: Biomechanical comparison of bioabsorbable cervical spine interbody fusion cages. Spine 2004, 29: 1717-1722. 10.1097/01.BRS.0000134565.17078.4CView ArticleGoogle Scholar
- Savolainen S, Usenius JP, Hernesniemi J: Iliac crest versus artificial bone grafts in 250 cervical fusions. Acta Neurochir 1994, 129: 54-57. 10.1007/BF01400873View ArticleGoogle Scholar
- Schreiner U, Scheller G, Chen C, Schwarz M: Introduction of a new intervertebral spacer for cervical fusion: results of a controlled animal study. Z Orthop Unfall 2007, 145: 736-743. 10.1055/s-2007-965798Google Scholar
- Schulte M, Schultheiss M, Hartwig E, Wilke HJ, Wolf S, Sokiranski R, Fleiter T, Kinzl L, Claes L: Vertebral body replacement with a bioglass-polyurethane composite in spine metastases – clinical, radiological and biomechanical results. Eur Spine J 2000, 9: 437-444. 10.1007/s005860000162View ArticleGoogle Scholar
- Shi Z, Liu M, Atrens A: Measurement of the corrosion rate of magnesium alloys using Tafel extrapolation. Corros Sci 2010, 52: 579-588. 10.1016/j.corsci.2009.10.016View ArticleGoogle Scholar
- Shono Y, McAfee PC, Cunningham BW, Brantigan JW: A biomechanical analysis of decompression and reconstruction methods in the cervical spine. Emphasis on a carbon fiber composite cage. J Bone Joint Surg Am 1993, 75: 1674-1684.Google Scholar
- Smit TH, Muller R, van Dijk M, Wuisman PI: Changes in bone architecture during spinal fusion: Three years follow-up and the role of cage stiffness. Spine 2003, 28: 1802-1808. 10.1097/01.BRS.0000083285.09184.7AView ArticleGoogle Scholar
- Smith GW, Robinson RA: The treatment of certain cervical spine disorders by anterior removal of the intervertebral disc and interbody fusion. J Bone Joint Surg Am 1958, 40: 607-623.Google Scholar
- Staiger MP, Pietak AM, Huadmai J, Dias G: Magnesium and its alloys as orthopedic biomaterials: A review. Biomaterials 2006, 27: 1728-1734. 10.1016/j.biomaterials.2005.10.003View ArticleGoogle Scholar
- Takahashi T, Tominaga T, Watabe N, Yokobori AT, Sasada H, Yoshimoto T: Use of porous hydroxyapatite graft containing recombinant human bone morphogenetic protein-2 for cervical fusion in a caprine model. J Neurosurg (Spine 2) 1999, 90: 224-230. 10.3171/spi.1999.90.2.0224View ArticleGoogle Scholar
- Thomas KA, Toth JM, Crawford NR, Seim HB III, Shi LL, Harris MB, Turner AS: Bioresorbable polyactide interbody implants in an ovine anterior cervical discectomy and fusion model. Three-year results. Spine 2008, 33: 734-742. 10.1097/BRS.0b013e3181695716View ArticleGoogle Scholar
- Toth JM, An HS, Lim T-H, Ran Y, Weiss NG, Lundberg WR, Xu R-M, Lynch KL: Evaluation of porous biphasic calcium phosphate ceramics for anterior cervical interbody fusion in a caprine model. Spine 1995, 20: 2203-2210. 10.1097/00007632-199510001-00005View ArticleGoogle Scholar
- Vaccaro AR, Robbins MM, Madigan L, Albert TJ, Smith W, Hilibrand AS: Early findings in a pilot study of anterior cervical fusion in which bioabsorbable interbody spacers were used. Neurosurg Focus 2004, 16: E7.View ArticleGoogle Scholar
- van Dijk M, Smit TH, Burger EH, Wuisman PI: Bioabsorbable poly-L-lactid acid cages for lumbar interbody fusion. Three-year follow-up radiographic, histologic, and histomorphometric analysis in goats. Spine 2002, 27: 2706-2714. 10.1097/00007632-200212010-00010View ArticleGoogle Scholar
- van Dijk M, Smit TH, Sugihara S, Burger EH, Wuisman PI: The effect of cage stiffness on the rate of lumbar interbody fusion. An in vivo model using poly(L-lactid acid) and titanium cages. Spine 2002, 27: 682-688. 10.1097/00007632-200204010-00003View ArticleGoogle Scholar
- Wilke H-J, Kettler A, Claes L: Stabilizing effect and subsidence tendency of three different cages and bone cement for the fusion of cervical spine segments. Orthopade 2002, 31: 472-480. 10.1007/s00132-001-0288-3View ArticleGoogle Scholar
- Wilke HJ, Kettler A, Goetz C, Claes LE: Are sheep spines a valid biomechanical model for human spines? Spine 2000, 22: 2762-2770.View ArticleGoogle Scholar
- Wilke HJ, Kettler A, Wenger KH, Claes LE: Anatomy of the sheep spine and its comparison to the human spine. Anat Rec 1997, 247: 542-555. 10.1002/(SICI)1097-0185(199704)247:4<542::AID-AR13>3.0.CO;2-PView ArticleGoogle Scholar
- Witte F: The history of biodegradable magnesium implants: A review. Acta Biomater 2010, 6: 1680-1692. 10.1016/j.actbio.2010.02.028View ArticleGoogle Scholar
- Witte F, Hort N, Vogt C, Cohen S, Kainer KU, Willumeit R, Feyerabend F: Degradable biomaterials based on magnesium corrosion. Current opinion in solid state and materials science 2008, 12: 63-72. 10.1016/j.cossms.2009.04.001View ArticleGoogle Scholar
- Witte F, Kaese V, Haferkamp H, Switzer E, Meyer-Lindenberg A, Wirth CJ, Windhagen H: In vivo corrosion of four magnesium alloys and the associated bone response. Biomaterials 2005, 26: 3557-3563. 10.1016/j.biomaterials.2004.09.049View ArticleGoogle Scholar
- Xu L, Yu G, Zhang E, Pan F, Yang K: In vivo corrosion of Mg-Mn-Zn alloy for bone implant application. J Biomed Mater Res 2007, 83: 703-711.View ArticleGoogle Scholar
- Zeng R, Dietzel W, Witte F, Hort N, Blawert C: Progress and challenge for magnesium alloys as biomaterials. Advanced Biomaterials 2008, 10: B3-B14.Google Scholar
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