Nouh MR. Spinal fusion-hardware construct: Basic concepts and imaging review. World J Radiol 2012; 4(5): 193-207
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Mohamed Ragab Nouh, MD, Radiology Specialist, Department of Radiology, Al-Razi Hospital, Jamal Abdulnaser street, Sulibikhate 13001, Kuwait. firstname.lastname@example.org
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World J Radiol. May 28, 2012; 4(5): 193-207 Published online May 28, 2012. doi: 10.4329/WJR.v4.i5.193
Spinal fusion-hardware construct: Basic concepts and imaging review
Mohamed Ragab Nouh
Mohamed Ragab Nouh, Department of Radiodiagnosis and Clinical Imaging, Faculty of Medicine, Alexandria University, Alexandria 21599, Egypt
Mohamed Ragab Nouh, Department of Radiology, Al-Razi Hospital, Sulibikhate 13001, Kuwait
Author contributions: Nouh MR selected the subject, reviewed the literature, wrote the paper, selected the figures and edited the whole work.
Correspondence to: Mohamed Ragab Nouh, MD, Radiology Specialist, Department of Radiology, Al-Razi Hospital, Jamal Abdulnaser street, Sulibikhate 13001, Kuwait. email@example.com
Telephone: +965-24825508 Fax: +965-24825909
Received: June 1, 2011 Revised: August 7, 2011 Accepted: August 14, 2011 Published online: May 28, 2012
The interpretation of spinal images fixed with metallic hardware forms an increasing bulk of daily practice in a busy imaging department. Radiologists are required to be familiar with the instrumentation and operative options used in spinal fixation and fusion procedures, especially in his or her institute. This is critical in evaluating the position of implants and potential complications associated with the operative approaches and spinal fixation devices used. Thus, the radiologist can play an important role in patient care and outcome. This review outlines the advantages and disadvantages of commonly used imaging methods and reports on the best yield for each modality and how to overcome the problematic issues associated with the presence of metallic hardware during imaging. Baseline radiographs are essential as they are the baseline point for evaluation of future studies should patients develop symptoms suggesting possible complications. They may justify further imaging workup with computed tomography, magnetic resonance and/or nuclear medicine studies as the evaluation of a patient with a spinal implant involves a multi-modality approach. This review describes imaging features of potential complications associated with spinal fusion surgery as well as the instrumentation used. This basic knowledge aims to help radiologists approach everyday practice in clinical imaging.
Citation: Nouh MR. Spinal fusion-hardware construct: Basic concepts and imaging review. World J Radiol 2012; 4(5): 193-207
Successful spinal fusion procedures appeared in the medical literature in the early 20th century[1,2]. The development of an integrated osseous fusion complex is essential for the long-term success of these procedures. Early surgeries relied upon extended bracing for solid fusion to occur with considerably long convalescence periods. Currently, a vast array of implants and surgical approaches are available for spinal surgeries to aid graft incorporation with early mobility and shorten postoperative recovery period[3-9]. The choice of fixation device and technique depends on the clinical problem, the anatomic location, and the surgeon’s preference[3-9].
The goal of spinal instrumentation is to maintain or correct anatomic alignment of spinal segments by sharing the loads acting on the spine, usually until solid biological fusion occurs[5-9]. Subsequent instrument failure occurs if solid bony fusion is not achieved[5-9].
Radiologists are required to be familiar with the spinal instrumentation in common use as well as those used in his/her region to promote communication with the referring physician and awareness of potential complications of such procedures. This review will highlight these procedures and the common techniques, surgical approaches, postoperative imaging features as well as common complications associated with them.
SPINAL INSTABILITY: BASIC OVERVIEW
The spine is a complex structure that transmits loads from the upper body through the pelvis into the lower extremities[3,7]. A spinal motion segment is the smallest functional unit addressing spinal biomechanics. It consists of two adjacent vertebrae, an intervertebral disc, various ligaments and apophyseal joints. Harmonic interaction of these elements as well as surrounding spinal musculature results in spinal motion segment stability during the applied forces of daily activities.
Accordingly, the American Academy of Orthopedic Surgeons has basically defined spinal instability as an abnormal response to applied loads, characterized by movement in the motion segment beyond normal constraints.
Denis’s spinal model (Table 1) is widely employed by spinal surgeons to address genuine native gross spinal stability.
In general, two of the three spinal columns must be anatomically intact for functional stability. Violation of more than one column by trauma, infection, tumor, degenerative change, or surgical approach will necessitate spinal instrumentation.
SPINAL INSTRUMENTATION: DEVICES AND SURGICAL APPROACHES
Listing different spinal instrumentation devices and surgical procedures is beyond the scope of this review. However, a general overview will be provided here.
Spinal instrumentation is commonly performed when spinal stability restoration, deformity correction, spinal-motion segment height restoration and pain relief are desired as in the management of scoliosis and other spinal deformities, spinal degenerative disease, trauma, instability, infection, and neoplasm[13-16]. A combination of both biologic (bone graft) and prosthetic (instruments) materials are usually used to form a construct that aims to maintain spinal stability in an unstable region of the spine.
Posterior/posterolateral spinal fusion and instrumentation
Posterior spinal column reconstruction has been performed for decades using different combinations of plates or rods with hook/wire/pedicle screw systems to form posterior spinal construct devices for different spinal levels[3,5,7].
A posterior approach is usually used when posterior decompression is required in addition to fusion as in degenerative spinal disease. It is more common in dorsal and lumbar regions (e.g., posterior inter-lumbar body fusion or PILF) as it is easier and adequately visualizes neural elements. It avoids the high-risk of the anterior approach in these regions, while it is mostly avoided in the cervical region for cord manipulation risks at that level[3,4].
Posterior fusion uses autografts placed along decorticated facets, laminae and/or transverse processes. In PLIF, bilateral partial laminectomies are performed and are followed by diskectomy (Figure 1). Bone graft material is packed into the anterior disk space before the insertion of one or two interbody spacers; placed side by side; and packed with graft material[4,7,8,18].
Figure 1 Antero-posterior (A) and lateral digital radiographs (B) of the lumbosacral spines with posterior lumbar interbody fusion showing LV3 through LV5 levels laminectomies with fine posteriorly located bone chips (arrows) on antero-posterior view that are difficult to appreciate on lateral view.
When there is a severe loss of disk space height and when the insertion of a posterior interbody spacer might cause neurologic compromise, Trans-laminar inter-body fusion with cortical screws is used as a simple method of posterior fixation. The bone graft material is placed laterally (between transverse processes) rather than anteriorly (between vertebral bodies), for posterolateral spinal fusion[4,7,8,18].
Rods are commonly used for long segment spinal fixations e.g., in scoliosis, as they can be individually cut and molded as required to facilitate maintenance of sagittal alignment, while plates are favored for short segment fixations e.g., in traumatic and degenerative etiologies[4,6,7,18].
Anterior instrumentation and fusion
Anterior fusion procedures are indicated for discogenic pain where removal of degenerative disk material and replacement for disk height is performed along with anterior osseous fusion for immediate stability. The presence of facet joint disease contra-indicates these procedures[4,7].
Anterior instrumentation may use either rod-screw or plate-screw systems to form a spinal construct. The anterior approach is generally preferred in the cervical spine (commonly known as anterior cervical diskectomy and fusion or ACDF) because of the risk of cord manipulation associated with a posterior approach at this level. Also, implants used posteriorly in the thoracic and lumbar regions are too large imparting greater traction forces that are not needed in the smaller cervical spine[4,7].
On the contrary, in the thoracic and lumbar levels (commonly known as anterior inter-lumbar body fusion or AILF) it is less indicated owing to significant morbidity, as the procedure involves going through the chest and abdominal cavities, and delayed recovery is associated with this approach[4,7].
Inter-body grafts and implants
These are a group of materials that have compressive strength and aim mainly to preserve disc space and/or spinal motion heights in diverse indications such as degenerative disc disease, neoplastic disorder, etc. They can be biologic substances like iliac bone grafts (Figure 2) and fibular grafts in cervical regions. Femoral grafts can be used where more spinal axial loads are present as in the lumbar region. Synthetic materials such as stainless, titanium and carbon polymers can be used in threaded and solid forms (Figure 3).
Figure 2 Immediate post-operative antero-posterior (A) and lateral digital radiographs (B) of the lumbosacral spines with posterior lumbar interbody fusion showing LV4-LV5 levels laminectomies with iliac bone graft at LV4-5 disc level.
Figure 3 Antero-posterior (A) and lateral radiographs (B) of the cervical spines showing metallic markers of CV4-5 intervertebral disc spacers.
In either situation, the central cavity is typically packed with autologous bone chips, demineralized bone matrix, and/or bone morphogenetic protein to establish bony fusion. The most recent non-metallic synthetic spacers contain two radiopaque markers to enable radiographic assessment of the spacer position (Figure 4)[7,19].
Figure 4 Antero-posterior (A) and lateral digital radiographs (B) of the lumbosacral spines with posterior lumbar interbody fusion showing LV3 through SV1 levels laminectomies with 2 metallic marks denoting insertion of radiolucent intervertebral disc spacers.
Note the posterior mark is at least 2 mm anterior to posterior border of adjacent vertebral body at LV3-4 level.
Vertebral body replacement (corpectomy)
Spinal diseases of neoplastic, infective or traumatic processes may necessitate resection of one or more vertebral bodies under certain circumstances, known as corpectomy or vertebral body replacement. Maintaining the lost spinal segment height is mandatory to preserve functionality and avoid further neural related complications.
For corpectomy procedures large strut grafts are used. Femoral strut allografts are designed for use in the lumbar or thoracic spine, while fibular strut allografts or tricortical iliac crest grafts may be used in anterior cervical corpectomy. In all cases, spinal hardware fixations are added to share load-bearing and aid bony fusions.
Total disk replacement
Total disk replacement, also known as disk arthroplasty, is performed in patients where their pain is believed to be discogenic in origin with no nerve root involvement as well as absent spinal stenosis or spondylolisthesis[4,7,20].
These procedures were resorted to in an attempt to avoid the effects on adjacent motion segments and the facets following spinal arthrodesis[21,22].
At least 4 mm of residual disk height and a lack of significant endplate degeneration to provide satisfactory anchorage for the replacement device are pre-requisites. The presence of spinal instability, facet joint degeneration, osteoporosis and/or infection contraindicates total disk replacement[4,23].
The first human disk prosthesis, which consisted of a single ball bearing, was inserted in the late 1950s. Bao et al classified these devices into four categories: (1) low-friction sliding surface; (2) spring-and-hinge systems; (3) contained fluid-filled chambers; and (4) discs comprised of rubber or other elastomers.
The materials used by different manufacturers vary considerably, with many different combinations of metals and polymers.
Yang et al, showed good clinical outcome, restored cervical spine mobility and prevented accelerated adjacent cervical segments degeneration at 24-mo follow-up. Yajun et al, reported equivocal results for the treatment of lumbar degenerative disc disease compared with fusion after a 2-5-year follow-up period. Their long-term evaluation is still ongoing in the literature.
Spinal dynamic stabilization
Spinal fusion procedures reduced pain clinically, but the increased stress on the adjacent segments was a new cause of instability and pain[28-30]. Dynamic stabilization may be an alternative to fusion in some patients with low back pain originating from chronic degeneration of the lumbar spine.
The concept of dynamic stabilization relies upon altering load bearing and controlling abnormal motion. This limits the stress placed on the segment adjacent to the level of fusion and thus helps prevent progressive degeneration[31-35].
A wide variety of dynamic stabilization devices is available. These devices may be broadly grouped, according to their design, into the following categories: (1) pedicle screws and artificial ligaments; (2) inter-spinous process decompression devices; and (3) posterior element replacement systems.
Radiography is the mainstay used for the postoperative imaging of spinal fusion thanks to its wide availability, cost-effectiveness, and non-invasive nature, although computed tomography (CT) is reported to be a more accurate modality[6,36,37].
Baseline radiographs or CR images are essential for evaluating spinal construct position (Figure 5) and serve as a starting point for evaluation of future studies, should patients develop symptoms suggesting potential complications. A change in position or instrument failure is often easily appreciated on serial radiographs or CR images[6,37]. Antero-posterior (AP), lateral, oblique, and motion studies (flexion, extension, or lateral bending) images are usually adequate and varies from one institution to another.
Figure 5 Antero-posterior (A) and lateral radiographs (B) showing well positioned spinal lumbar construct with pedicular screws central within the pedicles and not violating the cortices or adjacent endplates.
In some instances, fluoroscopically positioned images may be needed to judge better alignment of the hardware or osseous structures to identify subtle changes more optimally[9,38,39].
However, the projectional nature of radiography, insensitivity to detect metastasis and to explain neurologic symptoms are drawbacks limiting its yield[4-7].
Polytomography had been used to detect subtle motion at the fusion site. Nowadays, its use is only justified when older stainless steel hardware is present that precludes adequate CT imaging[7,40].
Ultrasound is not commonly used for evaluating potential spinal complications, although detection of superficial abscesses or fluid collections can be accomplished with this technique and may help to guide their aspiration[4,6].
For many years, significant beam hardening and susceptibility artifacts seen on CT and magnetic resonance (MR), respectively, made these imaging tools a poor choice for evaluating patients with spinal metallic implants[41-43]. Patient movement often exacerbates such artifacts, however, this can be overcome with currently available high-speed multidetector CT.
However, with recent advances in CT technology; especially in the multi-detector era; as well as hardware material improvements; including materials with fewer significant artifacts such as titanium, polyethylenes and fibrocarbons; many artificial implants can be imaged with fewer artifacts preserving relevant imaging information[6,7,41,44].
CT is the modality of choice for imaging bony detail in the spine, for accurate assessment of component position, particularly for positioning of pedicle screws, evaluating both spinal and construct alignment, and degree of osseous fusion[6,7,45,46]. It can also evaluate the spinal canal, and potential post-operative complications[6,7,45,46].
Metal-induced artifacts on CT are the results of both hardware-related factors such as hardware composition, geometry (shape), as well as location and imaging technical factors including tube current (in milli-ampere-seconds, mAs); X-ray kilovolt peak (KVp); pitch; and image reconstruction algorithm (filter)[47,48].
Hardware-related factors are beyond the control of the imager. Orthopedic hardware composed of lower X-ray beam attenuation coefficients (density) materials results in fewer artifacts e.g., titanium alloys produce fewer artifacts than stainless steel alloys[47-50].
Thin body parts and thinner parts of the metallic hardware attenuate X-ray beams less than their thicker counterparts producing fewer image-degrading artifacts[47-50]. This could be of clinical application in imaging of the reconstructed cervical spine with downward traction of the shoulders while raising the arms above the head for imaging of the reconstructed dorsal and lumbar spinal regions[47-50].
On the other hand, control of the following imaging factors can significantly improve the resultant hardware images and allows accurate answering of relevant clinical questions.
X-ray kilovolt peak
Most current CT- X-ray tubes operate at 120 kilovolt peak (KVp) as a default setting. This may suffice for imaging cervical spinal hardware in thin patients. However, in chubbier patients and thicker parts such as the dorsal, lumbar and sacral spines, a higher KVp, e.g., 140 KVp can increase the ability of the X-ray beam to penetrate metal[47,51,52].
X-ray tube current: An appropriate increase in tube current setting using the tube’s larger focal spot increases the ability of the X-ray beam to penetrate metal[48-52].
Pitch: The term pitch equals table translation (in millimeters) per gantry rotation divided by beam collimation[53,54]. As the number of detector rows increases the pitch decreases and this reduces metal artifacts[53,54]. Thanks to lower pitch settings of multi-channel CT technologies, the collection of enormous data sets can be achieved. Thus, high-resolution images in axial, sagittal and coronal planes can be obtained[53,54]. Furthermore, excellent post-processing images as volume rendered (VR) and shaded-surface display (SSD) images can be reproduced[48,53,54].
Image reconstruction parameters
The use of a standard or smooth reconstruction filter is preferred, particularly in the presence of dense metallic hardware and in patients with a large body habitus. The use of wide window settings (3000-4000 HU window width, 800 window levels) facilitates visualization of structures adjacent to metal hardware and reduces the effects of metal artifacts. Gathering the small thickness slices into more thickly reformates helps to reduce metal-induced artifacts and improve signal-to-noise ratio[47,48,50,52].
Volumetric rendering techniques such as VR and SSD impress semitransparent views of bones that tend to reduce metal artifacts allowing proper assessment of metal hardware-bone relationship[47,48,50,52].
Magnetic resonance imaging
CT and plain films virtually provide all relevant diagnostic information on grafts, implants, and hardware, thus magnetic resonance imaging (MRI) was commonly reserved due to magnetic-susceptibility artifacts seen with the old stainless steel alloys[6,7,55].
However, both recent MRI advances and newer magnetically inert polymers used for the manufacture of spinal hardware elements allowed higher resolution images of clinical diagnostic value. MRI has become an integral part of evaluating the patient with painful hardware implants, where clinical findings are non-focal, and laboratory diagnosis is negative for infection[50,55-58].
MRI is sensitive for detecting fractures, pseudo-arthrosis, and infections. It depicts cancellous bone marrow well compared to cortical bone.
Metallic hardware-induced MR susceptibility artifacts are mainly the sum of local field inhomogenities (due to spin resonance differences between metal and surrounding soft-tissues) altering both phase and frequency of local spins. These result in subsequent image formation misregistration in the form of signal loss within the metallic object, distortion of the shape of the metallic object along the axes of frequency encoding and section selection as well as high signal intensity appearing around the metallic object (Figure 6A)[59-62].
Figure 6 T1W SE image (A) demonstrating magnetic resonance susceptibility artifact of metallic hardware are mainly the sum of signal loss within the metallic object and high signal intensity appearing around the metallic object caused by altered both phase and frequency of local spins leading to read-out misregistration.
This is more obtrusive on T2-gradient images (B).
As mentioned with CT, the production of metal-related artifacts in MRI is a result of both hardware-related factors such as hardware composition, geometry (shape), as well as location (orientation to the main magnetic fields) and MRI technical factors including magnetic field strength used, type of pulse sequences applied and the sequence parameters, including voxel size (determined by field of view, image matrix, and section thickness), and echo train length[62-64].
Paying attention to patient positioning, choosing adequate imaging parameters and selecting different pulse sequences will help to reduce MR susceptibility artifacts associated with the spinal hardware and optimize the clinical value of MRI in such patient groups.
Again, hardware-related factors are beyond the control of the imager. Non-ferromagnetic titanium and polycarbon-enforced implants produce fewer severe artifacts than do ferromagnetic implants made of stainless steel. Also, the larger the implant size the more obtrusive the artifact will be[47,62,65-67].
In spite of multiple components and directions of the spinal hardware, alignment of the longitudinal axis of the hardware device parallel to the direction of the main magnetic field (z-axis of the scanner), will significantly reduce the resultant artifact[47,62,66-68].
The quality of MR images is dependent on the pulse sequence parameters used. Routine techniques used in the preoperative setting cannot be employed in the postoperative setting, as the resultant metal artifact is too great, yielding non-diagnostic images.
High-field-strength magnets produce larger magnetic susceptibility artifacts as misregistration artifacts are proportional to the magnitude of the local inhomogeneity in the main magnetic field, while it is inversely proportional to the strength of the applied frequency-encoding gradient[47,68,69].
However, the increased distortion effects of a higher main magnetic field strength could be offset by higher gradient strengths. Another advantage of high-field magnets is the use of broad-band width receivers that can reduce these magnetic susceptibility artifacts[47,62].
Gradient strength depends on selected field of view and matrix size in a given pulse sequence. This implies that the smaller the voxel, the smaller the artifact. Hence, the use of a small field of view, high-resolution matrix (e.g., 256 × 256 or 512 × 512), thin section, and high gradient strength can help reduce metal-related artifacts[47,71].
Gradient recalled echo (GRE) sequences are extremely sensitive to the presence of metal due to intravoxel dephasing resulting in signal loss seen as a dark or black area around the metal on the processed images (Figure 6B). This could be reduced by shortening the echo time (TE) and decreasing voxel size to minimize intravoxel dephasing seen on GRE acquisition[47,62,64,69,72].
In contrast to GRE sequences, use of a 180° refocusing pulse with SE and FSE sequences, enables recovery of the transverse signal lost due to static magnetic field inhomogenities and bulk susceptibility differences, to some extent[66,72].
The magnetic field inhomogenities adjacent to ferromagnetic materials causes increased dephasing per unit distance of travel in randomly diffusing spinning protons (T2-effect) augmenting signal loss on imaging the orthopedic hardware, prominently on long TE (T2-weighted) acquisition sequences. This could be overcome by using FSE images with decreased inter-echo spacing (↓TE) in the same echo-train duration i.e., increasing echo-train length, thus reducing diffusion-related signal loss during filling the K-space and improves the resultant image[62,73,74].
Variation of the regional magnetic field surrounding metallic devices or debris creates an inhomogeneous magnetic field, augmenting metal-induced signal loss and making use of frequency-selective fat saturation poor choice for depicting marrow lesions and optimizing contrast studies in patients with metallic hardware.
An alternative method for fat suppression is the use of short inversion time inversion recovery imaging which is less dependent on the homogeneity of the main magnetic field[47,61,69]. However, decreased signal-to-noise ratio with loss of tissue signal resolution and grainy appearance of final images is a compromise[52,75].
Lee et al and Potter et al described a ‘view angle tilting’ technique to decrease metallic artifacts by the application of a ‘‘compensatory gradient’’ during imaging acquisitions, to correct for inhomogeneous perturbations in the local magnetic field in the vicinity of a metallic device. This results in image blurring across the entire imaging field of view, which must be partially compensated for by imaging parameter alterations such as increased receiver bandwidth, readout gradient strength, and reduced voxel size to diminish the overall decrease in signal to noise ratio (SNR) of the resultant image.
Another MRI method for nulling metallic artifacts addressed with little SNR compromise known as single-point imaging (SPI) employs several milliseconds for signal preparation and acquisition. It acquires only the immediate free induction decay following off excitation pulses to avoid diffusion-related components of metallic artifact induction. Hence, SPI requires large gradient amplitudes and long scanning times[62,78].
Bone scintigraphy including single-photon emission CT (SPECT) can assess fusion sites (the fused segment should be “cold” after 6-12 mo) and help in infection detection in the region of metal implants; especially helpful in those cases in which MRI cannot be performed or is non-diagnostic[79-82].
Radionuclide scans may remain positive for a year or more in the region of the operative bed and instrumentation due to continued normal bony remodeling at the fusion site[4,6,9,81,82].
However, very focal intense activity may reflect the presence of non-union (pseudo-arthrosis), as opposed to more ill-defined or diffuse activity that reflects normally increased bone turnover in a fused spine. Combined technetium and labeled white blood cell studies may be useful for evaluating infection[7,9,81,82]. The accuracy of this dual radiotracer technique exceeds 90%[81,82].
Generally, bone scans are more sensitive and less specific than plain radiographs and cross-sectional imaging.
Nowadays, myelography is only justified in cases with old stainless hardware, non-diagnostic MR and unexplained neurogenic symptoms. However, after lumbar spine instrumentation, puncture of the lumbar thecal sac may be difficult due to anatomic distortion (e.g., scarring, removal of posterior elements, and addition of bone graft material) or the presence of metallic implants. Occasionally, a cervical puncture is a good alternative to the classic lumbar approach in this situation. Oblique views on conventional myelography may be needed to avoid obscuration of the relevant nerve roots by the implanted devices. It may sometimes be supplemented by MDCT myelographic evaluation.
Fluoroscopically, US or CT-guided anesthetic injections may be used to determine the source of pain around a prosthesis, e.g., a hook site, facet joint, or disc or in a suspected pseudo-arthrosis region. Relief of pain after anesthetic injection confirms the source of pain and allows for proper selection of treatment options. Aspiration of osseous, disc, or soft tissue lesions is also useful when infection is suspected[6,9]. Table 2 summarizes the different imaging techniques used for evaluation of spinal hardware as well as the main indications for their use.
Table 2 Summarizes imaging techniques and indications.
Instrument failure, infection, failed fusion
Fluoroscopic positioned spot views
Fluid collections, abscesses
Instrument position, pseudo-arthrosis, infection, fragments in spinal canal, vertebral alignment
Confirm source of pain, aspiration of pseudo-bursae or organisms for infection
CT: Computed tomography; MR: Magnetic resonance; PET: Positron emission tomography.
IMAGING FEATURES OF NON-COMPLICATED SPINAL HARDWARE AND FUSION
Inter-body grafts and implants
Inter-body fusion may be carried out with cortical bone and autogenous grafting or with inter-body fusion cages. Radiolucent disc spacers contain two radiopaque markers enabling their recognition on postoperative radiographs[3,4,6,7].
In the early postoperative period, metal cages appeared to “float” within the intervertebral space on AP plain films as morselized autografts placed within and/or around them are not visible on plain X-rays. In intact fusions, the outlines of radiolucent cages become increasingly apparent as the adjacent bone graft consolidates over time with no adjacent lucency or sclerosis[3,4,6,7].
A well-positioned spacer will show a posterior marker located at least 2 mm anterior to the adjacent posterior vertebral body margin (Figure 4B). This imaging appearance will exclude ramp/cage protrusion into the spinal canal[3,4,6,7].
Total disk replacement
The design characteristics of these devices are variable. However, both radiography and CT are equally used for evaluation of their positioning. Ideally, the device has to be located midline between the two pedicles on AP radiographs or axial or coronal CT scans and should not penetrate adjacent end plates. With respect to AP positioning, the center of rotation should be located in the posterior half of the disk space yet it should not extend beyond the posterior vertebral body line[83-85].
Combinations of plates and/or rods with pedicle screws are interconnected for spinal instrumentation, till bony fusion ensues. Optimal screw placement is typically along the medial aspect of the pedicle and contained within the pedicle. There is no consensus on their optimal length (> 50% of its length within the vertebral body) yet it should not break through the integrity of adjacent cortices or end-plates (Figure 5). However, sacral screws may be anchored in the anterior cortex of the sacrum for additional stability[3,4,6,7].
Screw position and fracture can usually be detected on radiographs for optimal positioning (Figure 5) or inadvertent insertion (Figure 7A and B). However, CT and/or MRI will show this more clearly with the added advantage of evaluating the status of bone graft and excluding pseudo-arthrosis[3,4,6,7].
Figure 7 Antero-posterior (A) and lateral digital radiographs (B) of the lumbosacral spines showing aberrant pedicular screw violating LV3 superior endplate and protruding into LV2-3 disc, T2W (C) and T1W (D) sagittal magnetic resonance images showing aberrant pedicular screw violating LV3 superior endplate and protruding into LV2-3 disc.
Posterior fusion is characterized by autografts placed along decorticated facets and/or laminae[3,4,5,7,9].
The early postoperative radiographic appearances are quite variable, sometimes it shows large solid fusion masses, and other times, small wispy bone grafts hardly show up on plain X-ray and/or on CT, particularly if small amounts of graft were placed along the posterior elements and/or transverse processes (Figure 8)[3,6,7,9]. This gradually consolidates over several months into a solid bony fusion within 9-12 mo postoperatively, if successful fusions have ensued[3,6,7,9].
Figure 8 Fluoroscopic spot views of the lumbo-sacral spines depicting the fine bone chips used for fusion beside the short-segment hardware at LV4 and LV5 levels.
These were barley seen on radiographic films.
Anterior/antero-lateral fixation devices
These are commonly seen following ACDF procedures, scoliosis corrective surgery and/or following vertebral corpectomy at any spinal level. These devices are commonly located anteriorly spanning two to three segments in cervical regions, and are located more antero-laterally spanning longer segments in the dorsal and lumbar levels (Figure 9)[5-8,13].
Figure 9 Antero-posterior (A) and lateral radiographs (B) of the dorso-lumbar spines showing a Harrington rod spanning the upper dorsal and lumbar vertebra for correction of adolescent scoliosis.
Anterior plates are anchored to the underlying vertebral bodies with screws, which should enter the anterior cortex of each vertebral body and be seated in the posterior cortex without impinging on the cord for firm purchase of the screws to promote posterior graft material compression and enhance bony fusion. Ideally, the screws should not enter an adjacent end plate and should be at least 2 mm from the superior and inferior end plates[5-8,13].
Usually, the intervertebral disks are removed and replaced with bone graft material for anterior spinal fusion. Sometimes, these devices are supplemented with posterior fixation devices.
IMAGING FEATURES OF COMPLICATED SPINAL HARDWARE AND FUSION
Given the technical difficulties of spinal instrumentation procedures, it is recognized that complications may arise from mal-positioning of hardware, technical difficulties associated with different surgical approaches, underlying clinical circumstances as well as improper patient and/or hardware selection. Imaging plays a vital role in evaluating potential complications of spinal instrumentation procedures.
Every radiologist should have his/her systematic approach to assess the integrity of the spinal hardware, neural and vascular structures throughout the spine, including the neural foramina, thecal sac, spinal cord and cauda equina, as well as peri-spinal anatomic regions of interest.
Broadly speaking, these complications are divided into spinal hardware-related complications, bony fusion-related complications and operative procedure-related complications.
Operative procedure related complications
Operative procedure level points to potential complications. Anterior cervical spine procedures may be associated with transient nerve palsies, arterial (vertebral and carotid arteries) dissections and esophageal tears[86-90]. Bone graft extrusion and instrument subsidence have also been described.
Anterior procedures in the thoraco-lumbar spine have a higher incidence of local complications and at the bone graft donor site. Vascular injuries are also more common[91,92]. With newer techniques, such as video-arthroscopy, thoracic duct injury and injury to the long thoracic or phrenic nerves may occur.
Spinal fixation and fusion are long surgical procedures; especially with increased length of the fixed spinal segments as in scoliosis; requiring prolonged immobilization or recumbency, making patients more vulnerable to certain complications such as brachial plexus injuries, superior mesenteric artery syndrome and thrombophlebitis[9,93-95].
Medical complications are also common. Genitourinary infections occur in 20% and deep venous thrombosis in 25% of patients. These problems are more common in patients who have post-traumatic paralysis or prolonged hospitalization. Gastrointestinal hemorrhage may be as high as 40% in patients receiving steroid therapy.
The acute onset of neurologic symptoms in the immediate postoperative setting should arouse clinical suspicion about the possible formation of a hematoma, a surgical emergency that requires urgent surgical decompression[3,9].
Postoperative infections may occur in the immediate post-operative period or present latently several months after surgery. Infection may involve any tissue in the postoperative bed[96,97]. It may be the result of implantation at the time of surgery or occur later due to hematogenous spread and/or wound contamination[96,97].
Staphylococcus epidermidis and Propionibacterium acnes are the main organisms associated with implant infections.
Patients often present with pain, hotness, skin redness and swelling at the operative site with sinus formation draining deep collections in some cases.
Superficial soft-tissue infections are easy to diagnose clinically. MRI may depict fluid collections, abscess formation and intense enhancement following the administration of IV gadolinium-based agents (Figure 10)[3,6,7,96,97].
Figure 10 Sagittal T2W SE image (A), axial T1 pre-contrast (B) and post-contrast SE MR images (C) in a post-operative patient showing localized encysted collection within the operative bed with appreciable contrast enhancement of the encysted collection following IV gadolinium administration representing a post-operative infection with abscess formation.
CT-guided aspiration may be useful for isolating the offending organism for culturing and sensitivity tests aiding proper antibiotic selection. Implant withdrawal may be performed first if solid fusion was achieved in latent infections[3,6,7,96,97].
Spinal hardware-related complications
It should be remembered that the instrumentation used in fusion surgery is not designed to replace the bony elements of the spine, but to stabilize them as the fusion mass consolidates and takes over as the primary source of support. Any factor that retards fusion will subject the implant to abnormally high loads for longer periods and ultimately fail when it exceeds its loading capabilities[3,4,6,7,9,18,37].
Improper selection of implants may be the cause of failure, as the chosen construct may not withstand the physiologic loads imparted on it for a given patient and clinical scenario. Patients noncompliant with postoperative spinal precautions (avoiding heavy lifting, excessive bending or twisting of the trunk, or exposure to high impact activities) are liable to have their implants fail. Trauma is a common cause of immediate hardware failure[6,7,37].
Associated medical conditions may predispose to hardware failure e.g., patients with metabolic bone disease or severe osteopenia may not be appropriate candidates, as their poor bone quality is associated with cutout or loosening of hardware (Figure 11)[3,4,6,7,96,98]. Morbid obesity adds to the technical difficulty of spine surgery and exerts greater stresses on instrumentation. Also, smoking increases the rate of pseudo-arthrosis development after fusion.
Figure 11 T2W SE (A) and T1W (B) sagittal magnetic resonance images showing multiple vertebral body collapse targeting LV1, DV11 and DV8 levels in osteoporotic patient predisposing to hardware failure.
Hardware failure occurs when an implant breaks, or the device becomes largely dissociated from the underlying bone. The findings in these cases include rod migration or dislodgement, rod breakage, hook cutout or disengagement, wire breakage, screw cutout and failure (Figure 12).
Figure 12 Antero-posterior (A) and lateral digital radiographs (B) of the lumbosacral spines with short-segment posterior fixation spanning LV5 and SV1 levels with fracture of left lower pedicular screw of the construct representing hardware failure.
A precedent to hardware failure is aseptic loosening where instability due to pseudo-arthrosis and/or infection is thought to be an etiologic factor[3,4,6,7,9,18]. It is believed that particulate debris, produced by component wear, attracts and activates tissue phagocytes with repeated but unsuccessful attempts of phagocytosis to non-digestible metal particles damaging adjacent bone and cartilage by this enzymatic release resulting in osteolysis[100-102].
Based on their worldwide use and the vital structures adjacent to their insertion sites, pedicle screw complications are widely discussed in the literature. In a large series, Lonstein et al reported screw fractures in 0.5%, penetration of the anterior cortex in 2.8%, pedicle fractures in 0.6%-2.7%, dural tears in 1%, and nerve root irritation in 1% (this was related to medial or inferior screw placement).
Loosening of pedicle screws appear as a rim of lucency around the screw threads (or any hardware) especially when the lucency exceeds 2 mm or increases in size on X-ray (Figure 13) and/or CT imaging follow-up[3,6,7,9]. Loose screws will often gradually retract and may eventually be expelled from the bone entirely with eventual hardware failure.
Figure 13 Antero-posterior digital radiographs of the lumbosacral spines with posterior lumbar interbody fusion showing LV3 through SV1 levels laminectomies with peri-screw lucenecy seen around the last screws representing aseptic loosening.
Complications may arise from medial or lateral deviation of a screw or from its penetration of the anterior cortex of the vertebral body[3,6,7,9]. When aseptic loosening is shown on imaging studies, the radiologist should look for associated failed fusion and/or infection[3,6,7,9].
Similar complications may arise from mal-positioning of anterior cervical plates and screws, which may penetrate the adjacent disk space, foramen transversarium, spinal cord, or nerve roots. Inadvertent mal-positioning of cervical screws within adjacent disc material predisposes for aseptic loosening of the hardware and a high risk of vertebral body fracture as the disc material can not hold the screws.
Adjacent level ossification development (ALOD) was described as a long-term sequel to anterior cervical plating[3,6,9,104-106]. Park et al showed the likelihood of ALOD with anterior cervical plate margin placement within 5 mm of the adjacent disk space. He concluded that any adjacent-level ossification within the first 12 mo postoperatively resulted in the likelihood of progression to advanced ossification by 24 mo in a later study.
Spinal bone graft-related complications
Serial radiographs may be used to assess fusion using the widely accepted Ray’s criteria for solid fusion recognition (Table 3).
Table 3 Ray’s criteria for evaluation of spinal bony fusion.
Ray’s criteria for radiographic assessment of bridging osseous fusion
Less than 3 degrees of inter-segmental position change on lateral flexion and extension views
No lucent area around the implant
Minimal loss of disk height
No fracture of the device, graft, or vertebra
No sclerotic changes in the graft or adjacent vertebra
Visible bone formation in or about the graft material
A cardinal rule of hardware is that it bears a load or stress and will eventually fail unless the body fuses or heals at the site. Hence, bone grafting is used in conjunction with most spinal instrumentation procedures till solid bone graft fusion ensues within 6-9 mo and can be identified on imaging[3-9].
Subtle or low-grade instability at the fusion site results in pseudo-arthrosis or fibrous union. Pseudo-arthrosis is defined as failure of attempted spinal fusion to achieve solid bony arthrodesis by 1 year after surgery[3-9].
Pseudo-arthrosis varies widely in its incidence and etiology, being higher for ALIF (4%-68%) than the PLIF (3%-25%) and ACDF (3%-46%)[108-114]. Smoking, long-term use of non-steroidal anti-inflammatory drugs and underlying conditions such as scoliosis and osteoporosis are common risk factors for its development[108-114].
Pseudo-arthrosis or fibrous union itself may be a source of pain generation and its early recognition is critical to prevent instrument failure and allow early repair[40,93]. Mature pseudo-arthrosis appears as a clearly linear lucency across the graft material with sclerosis on its margin on radiographic films[3,6,7,9,40,108]. The same imaging findings are seen on MDCT examinations with its high-resolution and multi-planar capabilities. In addition, CT may allow precise definition of cortical margins and residual graft material[3,6,7,9,40]. With newer titanium and cobalt-chromium implants MRI can depict focal high signal intensity in the region of pseudo-articulation on T2-weighted images and bands of low intensity on T1-weighted images. Reactive marrow changes and enhancement with gadolinium due to abnormal motion may also be seen[3,6,7,9].
In the early stages of pseudo-arthrosis with equivocal radiographic examination, increased radiotracer uptake is expected at sites of motion 6-9 mo after operation as mentioned earlier. SPECT of the spine showed value in detecting painful pseudo-arthrosis in patients after spinal fusion surgeries.
Fluoroscopically, US or CT-guided anesthetic injections are recommended by some groups to prove or disprove pseudo-arthrosis as the source of pain. A combination of buffered 1% lidocaine and 0.25% bupivacaine can be used for diagnostic injections. Bupivacaine is longer acting and allows for patient testing to determine the degree of pain relief[3,9].
Long-term sequelae of fusion
Successful spinal fusion permanently alters the mechanics of vertebral segments at adjacent levels resulting in accelerated degenerative changes in the vertebrae, ligaments, and intervertebral disks[3,7,9,28,29]. These degenerative changes are termed junctional failure or adjacent segment disease[3,7,9,28,29,115-117].
This was recognized in some series as early as 3 mo post-fusion and as late as 13 years[117,118].
Junctional failure is commonly seen in the lumbar region compared with other regions, with an increased number of fused segments and with residual sagittal deformities on early postoperative upright radiographs[117,119,120].
Increasing disc height loss, degeneration, disc bulge and/or protrusions as well as progressive facet arthropathies are common and predictive for evolving junctional failure on different imaging modalities with the emphasis on comparing serial examination for accurate judgment. Micro-trauma to the intervertebral disks at adjacent levels of fusion can be a source for pain, although the disc is morphologically intact on MRI and/or myelographic examinations[3,117,119,120].
Adjacent vertebral body fractures and collapse have been reported especially in osteoporotic cases[117,121].
In conclusion, radiologists are required to be familiar with the instrumentation and operative options used in spinal fixation and fusion procedures to properly assess outcome, as it forms an increasing bulk of daily practice in a busy imaging department. The goal of spinal instrumentation is to maintain or correct anatomic alignment of spinal segments by sharing the loads acting on the spine, usually until a solid biological fusion occurs.
Familiarity with the different forms of instrumentation, fusion approaches and expected results is critical in evaluating the position of implants and potential complications associated with the operative approaches and spinal fixation devices used. Thus, the radiologist can play an important role in patient care and outcome.
Baseline radiographs are essential as the baseline point for evaluation of future studies should patients develop symptoms suggesting possible complications. They may justify further imaging workup with CT, MR and/or nuclear medicine studies, as evaluation of a patient with a spinal implant involves a multi-modality approach. This review outlines basic knowledge to help radiologists to approach everyday practice in clinical imaging.
I thank Dr. Abass Nour El-Din, Professor of Radiology, El-Menia University, Egypt, for his preliminary review of the manuscript
Peer reviewers: Ming-Yuan Tseng, MD, MPhil, MSc, MRCS, PhD, Department of Neurosurgery, Addenbrooke’s Hospital, University of Cambridge, 546 Derby Road, Wollaton Park, Nottingham NG7 2GY, United Kingdom; Shigeru Ehara, MD, Professor, Chair, Department of Radiology, Iwate Medical University School of Medicine, Morioka 020-8505, Japan
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