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Construct design is an essential part of the planning process when addressing instability or deformity of the spinal column.
Spinal implants provide internal stabilization until bony fusion occurs.
The goals of spinal instrumentation are to immediately restore stability, withstand biomechanical forces and loads, and correct deformity.
Creating a preoperative plan or blueprint ensures a definitive plan and saves time in the operating room.
Bone quality is an important factor that influences the stability of spinal implants.
The authors thank Drs. Setti S. Rengachary, Gandhivarma Subramaniam, Darrel S. Brodke, and Edward C. Benzel, who coauthored prior editions of this chapter. Their work laid the foundation for the present chapter.
Construct design is a process that formulates a specific blueprint for an orderly and thoughtful assembly of implantable spinal instrumentation designed to correct the instability or deformity of the spinal column, or both. Construct design requires a specific understanding of the deformity or instability and the biomechanical forces acting on the pathological alignment. An understanding of corrective forces and where they must be applied is also required. A keen knowledge of the anatomy and pathoanatomy is required to preserve neurological function and avoid adjacent segment injury. Although skillful assembly of the mechanical construct is a definite prerequisite, ultimate success is determined by the orderly thought process for designing the construct, based on personal experience, the experience of others, and available clinical data. Creating a preoperative plan or blueprint can focus this design process. Spinal instrumentation surgery must not be assumed to be strictly “mechanical” or “routine”; rather, it requires serious and meticulous planning to ensure success.
The nomenclature of spinal instrumentation is complex and often confusing at the outset. Factors that contribute to this complexity are the numerous components that constitute assembly, the numerous choices for purchase sites in the spine, and the variations in the mode of assembly of the hardware. There are four major categories: (1) anchors, devices that attach the construct to the bony spine (e.g., pedicle screws, cables, hooks); (2) longitudinal members (e.g., rods or plates); (3) connectors, devices that connect anchors to the longitudinal members or connect two longitudinal members (cross connectors); and (4) accessories (e.g., washers or spacers). Most spinal instrumentation systems have all four of these components. The skill in designing a construct is reflected in the optimal choice of implants that result in biomechanically stable architecture.
Spinal implants act as internal supports that immobilize the spine until bony fusion occurs. In contrast to external orthoses that serve similar functions, spinal implants provide direct control of the spinal segments and have a much broader scope.
The goals of spinal instrumentation are threefold. The first goal is immediate restoration of stability so that the patient may be prepared for early rehabilitation efforts. Immediate stability often decreases pain and may improve early function. It may also increase the success of bone union or fusion. The second goal of instrumentation is indirect decompression of neural structures, often accomplished by controlled distraction. Instrumentation may also be used to restore or maintain physiological alignment of the spine. The third goal of spinal instrumentation is correction of deformity to prevent pain or neurological compromise and neutralization of pathological, deforming forces. Surgeons designing spinal instrumentation constructs should clearly delineate which of the aforementioned goals, or which combination of goals, they are attempting to achieve. Many factors need to be considered when designing and planning a reconstruction strategy in the thoracic and lumbar spines. Some of these include the underlying pathology (infection, trauma, and tumor, among others), the preoperative alignment, the goals for correction and stabilization, the medical frailty of the patient, and the anticipated bone quality for fixation.
The six fundamental construct types are simple distraction, three-point bending, tension band fixation, fixed moment arm cantilever beam fixation, nonfixed moment arm cantilever beam fixation, and applied moment arm cantilever beam fixation ( Fig. 115.1 ).
The preoperative development of a blueprint for implant placement is based on the composite information obtained from clinical assessment and imaging studies. It ensures a definitive plan and saves time in the operating room. Some flexibility in this plan may be required after surgical exposure of the spine because of unexpected findings. For instance, minor fractures at the implant anchor site may necessitate deviation from the original plan. Assessment of bone quality is also better appreciated after exposure and actually drilling pilot holes and cannulating the pedicles before pedicle screw insertion. Preoperative x-rays and computed tomography (CT) can provide a sense of the bone quality, but qualitative descriptors of osteopenia and osteoporosis on these studies does not necessarily translate to poor bony fixation. For this reason, surgeons should keep in mind the potential for incorporating additional levels in the construct design, especially at junctional areas such as the thoracolumbar junction. This is important not only for surgical planning but also for patient counseling.
A simple scheme should be used that provides information about (1) the level of the lesion or the level of the unstable segment or segments, (2) the types of implants to be used (anchors, longitudinal members, and cross connectors), (3) the length of stabilization required on either side of the lesion, and (4) the mode of loadbearing by the construct. The scheme guides selection of the appropriate implant components in advance, improves intraoperative communication between surgeons and assistants, and enhances the chances of success.
Although the concept of construct design encompasses similar principles in all anatomic regions of the spine, designing a thoracolumbar construct poses more challenges than most cervical constructs. Various constructs, using a variety of anchors in different bony landmarks, each used in various mechanical modes (i.e., compression, distraction, neutralization, distraction followed by compression, or distraction and compression at different segmental levels), may be used in a successful strategy. Consideration must also be given to the mechanism of injury and the biomechanical forces that led to the fracture, deformity, or issue in question. The construct needs to be designed in such a way as to counter the natural tendency for the spine to want to “fall back into” that preoperative configuration. Providing enough internal stabilization to not only withstand these forces, but also accommodate the forces associated with loadbearing, twisting, and bending in the time it takes for the area in question to heal is essential. In consideration of these complex decision-making dilemmas, this chapter focuses on thoracic and lumbar fixation design strategies.
A simple dorsoventral or lateral line drawing of the spine provides a framework for the clear definition of the operative plan. Often only a dorsoventral drawing is necessary, although clear consideration of any sagittal plane deformity is vital. The line drawing provides the blueprint for surgery ( Fig. 115.2 ). This drawing can be easily obtained from a CT scan or from radiographs.
The convention used in this chapter with regard to a dorsoventral line drawing dictates that the left side of the drawing portrays the left side of the patient (i.e., the drawing portrays the patient as viewed from behind). This portrayal is in accordance with the most common surgical approaches for complex instrumentation constructs and decreases the chance for confusion.
The designation of the level of the lesion or location of instability, the levels to be fused, and the type of fusion should be placed next on the line drawing. The level of instability or lesion is designated by an “X,” and the precise extent of proposed bony fusion is designated by a hatched outline. The number of unstable motion segments should be assessed carefully, as should associated deformity. These factors determine the number of levels to be spanned with the construct. The choice of implants also affects this decision.
Hook constructs, often used in the past throughout the spine and still used occasionally in the thoracic region, should incorporate three spinal levels above and two spinal segments below the limits of the lesion (3A-2B rule). Since the early 2000s, hooks have mainly been reserved for situations in which the pedicles are very small or for additional support along with pedicle screws in osteoporotic patients. If the patient has a marked angular kyphotic deformity, and if three-point bending is considered in an attempt to reduce the deformity, inclusion of four or more spinal levels above the lesion is common (4A-2B rule) and may provide a more functional lever arm. Such long constructs are suited mostly for lesions in the middle and upper thoracic regions, although thoracic pedicle screws are widely used even in these regions. With the use of uniplanar and fixed-head pedicle screws, correction of such kyphotic deformities can be achieved through multilevel dorsal approaches, as long as the bone quality can maintain the stresses applied to the screws during such corrective maneuvers. As such, hooks are being used less in current instrumentation systems and designs.
In the lower thoracic spine (T8‒T10), the thoracolumbar junction (T11‒L1), and the lumbar region (L2‒L5), pedicle screws are the workhorse for fixation, stabilization, and correction of deformity. The size of the pedicles at these levels and the increased stiffness of these screws provide make them an ideal choice for stabilization. In the thoracic spine, surgeons can take advantage of the costovertebral articulation with “in-out-in” technique maximizing the width of implanted screws, not relying on the width of the actual thoracic pedicles themselves. With this “in-out-in” technique, the screw traverses several cortical borders in a more lateral to medial trajectory into the thoracic vertebral body, therefore allowing not only the benefits of triangulation of the instrumentation in the axial plane, but also greater pullout strength. Short-segment fixation, meaning instrumentation of only one vertebra immediately above and below the lesion, is appropriate if the anterior, loadbearing column is intact, the kyphotic deformity is not present, and the bone structure shows sufficient strength. With increasingly sophisticated fixation choices available, it must be remembered that a rigid, stable construct is the goal with the consideration of biology and biomechanics surrounding the implants.
Both segmental pedicle screw and hook instrumentation techniques are successful in safely achieving local and global alignment goals. Balance can be accomplished without neurological injury, even in adolescent idiopathic scoliosis, where neurological risk is greatest. Segmental pedicle screw instrumentation offers significantly better overall major and minor coronal curve correction and maintenance, without neurological problems and with slightly improved pulmonary function values, for the operative treatment of adolescent idiopathic scoliosis. Pedicle screw constructs may also allow for a slightly shorter fusion length than segmental hook instrumentation.
The type of implant components used in the instrumentation construct should be delineated clearly on the blueprint. The implant component at each implant–bone juncture may be a cable, hook, or screw. The convention used is to designate hooks by a right-angled arrow, with the arrowhead pointing in the direction of the orientation of the hook. The purchase site—and the type of hook—is designated further by “P” (for pedicle), “L” (for laminar or sublaminar), or “T” (for transverse process). Screws are designated by an “X” surrounded by a circle and placed over pedicles. Cable (or wire) is depicted as a loop.
The mode of axial load application (distraction, compression, or neutral) at each implant–bone juncture is depicted as an arrow. The arrow points in the direction of force application for distraction and compression or a horizontal line for neutral. Bending moments are difficult to depict accurately on the line drawing and are described.
The modes of application of each segmental level are depicted with arrows and lines, as previously described. The arrows and lines are drawn lateral to the designations of implant types. If sagittal plane forces are to be applied, they are depicted on the lateral line drawing. Finally, cross fixator locations can be designated by rectangles with circles.
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