Abstract:
Provided are a device and a method for stabilizing two or more vertebrae by joining the vertebrae with a flexible device. The flexible device is of unitary construction and includes anchor posts constructed and arranged for insertion into holes drilled into the vertebrae, preferably after removing all or a portion of the pedicles from the target vertebrae. Removal of the pedicles provides an acceptable fastening site, prevents interference with the device by the pedicles, and provides native donor bone tissue, thereby obviating the need for a second surgery to harvest bone tissue from a different site, such as the hip.

Description:
[0001]     This application provides a method and device useable to flexibly connect at least two vertebrae together, thereby increasing the stability of the vertebral column, and also allow for the adequate decompression of pinched nerves. The present invention improves upon related devices and methods, invented by the Applicant, and fully described in U.S. Pat. No. 4,743,260 and U.S. Pat. No. 5,282,863. The contents of these patents are incorporated by reference herein in their entireties. 
     
    
     BACKGROUND OF THE INVENTION  
       [0002]     Stabilization of the spinal vertebrae has traditionally been accomplished using fusion, a long-practiced procedure involving the permanent and rigid fixation of one or more spinal segments. Each spinal segment includes two adjacent vertebrae, their posterior bony elements, an intervertebral disc between the two vertebrae, ligaments, and two facet joint capsules. Stabilizing two or more vertebrae together is done in an attempt to improve spinal stability and prevent the occurrence of “slipped disks” and other related spinal problems, and to treat disability due to pain and/or pinched nerves.  
         [0003]     Established methods of rigid spinal fusion have significant drawbacks. When two or more vertebrae are totally fused together, and thus immobilized, the movement and stresses that the fused vertebrae once provided and absorbed are transferred to the remaining mobile vertebrae. Especially affected are those vertebrae immediately adjacent the fused section. These adjacent vertebrae are subject to inordinately high stress and degeneration often leading to the need for additional surgery. Moreover, in the typical rigid L4-S1 fusion, the L3-4 level typically undergoes stress-related degeneration of the disc and zygoapophyseal joints leading to the production of a clinical entity called the “transitional syndrome” often leading to “mechanical-type” pain or actual spinal nerve compression. The stress patterns produced by fusion often also produce additional clinical problems relating to the sacroiliac and hip joints.  
         [0004]     Safe, effective and more physiologic long-term stabilization has been difficult to accomplish. When spine fusions involve mechanical instrumentation, significant adverse forces are directly aimed at the supportive sites whether they are bone screws, hooks, or the like. This phenomenon usually wears away at the relatively soft bone matter, resulting a loosening of the attachment points for the implanted hardware and a resulting loss of support by this instrumentation. Thus, fusions involving instrumentation are often carried out in conjunction with bone fusions so that as the instrumentation loosens and fails, support can be maintained by growth of the bony counterpart. These combined procedures involve extensive surgery, substantial blood loss and high cost very often creating more problems for the patient than those solved. Further, the recovery time for such procedures is significant and debilitating and very often necessitates additional spinal surgery.  
         [0005]     Therefore, the present management of spinal instability by instrumented fusion stabilization is not optimal. The fused vertebrae become immobile, eliminating their previous natural ability to move relative to each other. Also, when fusion is combined with added internal fixation, the internal fixation parts are typically metallic. In modern medical practice, the presence of large and dense metallic devices can be a significant liability due to the scattering artifacts generated if imaging, such as MRI, is attempted. At this time MRI imaging is a preferred spinal diagnostic procedure.  
         [0006]     In 1973 scientists at the Materials Research Laboratory at Penn State University observed that in some reef building corals their microstructure was characterized by 1) a high degree of uniformity in pore diameter, 2) a pore interconnection diameter similar in size to that of the pore itself, 3) a solid-to-volume ratio of approximately one, and 4) exceptionally high permeability in which each and every pore was interconnected to all other pores. It was recognized that it would be virtually impossible to achieve these structural characteristics by artificial means. Early experiments designed to impregnate the coral with various substances, dissolve the calcium carbonate coral skeleton and then make positive casts with other materials including metal alloys, were successful and the term “the replamineform process” was coined.  
         [0007]     In addition to replamineform casting it became evident that the structural characteristics of coral itself could possibly serve as the means for bone ingrowth after a cleansing of organic materials and a chemical conversion from biogenic carbonate to hydroxyapetite.  
         [0008]     Subsequent medical studies using coral with a microdiameter (200-250 microns) similar to that of the normal human bone Haversian canals (200-400 microns) were conducted by a number of physicians in the United States. Drs. Vert Mooney and David Selby in Dallas, Tex. performed 40 cases of bilateral spinal bone fusion in which one side was coral provided by Interpore International of Irvine, Calif., and the other side autogenous bone. These studies did not demonstrate significant ingrowth of osteoblasts into the coral and these observations led to the conclusion that coral showed little value in this regard. Since this work most clinicians have almost exclusively used autogenous or donor derived homologous bone.  
         [0009]     The applicant has overcome some of the aforementioned difficulties with the devices and methods described in his U.S. Pat. Nos. 4,743,260 and 5,282,863. These patents provide a device and method for stabilizing a portion of a vertebral column without fusion using a stabilization device made of a biocompatible, non-metallic material. The device includes an anchor means and a stabilization means. The anchor means includes an upper shank portion and a lower threaded portion cooperatively connected to the shank portion. The shank portion is self-tapping such that it may be screwed into the pedicle of a vertebra. The stabilization means includes a first stabilization element having first and second openings and a second stabilization element having first and second openings. The openings are arranged to be placed over the upper shank portions of the anchor means. The method involves making an incision to expose the first and second vertebrae to be stabilized. The posterior vertebral elements of each of the vertebrae to be stabilized are removed, leaving first and second pedicles of the first vertebra and first and second pedicles of the second vertebra. A bone screw is secured into at least one of the pedicles of the first and second vertebrae. The stabilization means is cooperatively connected between the bone screw of one of the first pedicles of the first vertebra to the bone screw of one of the first pedicles of the second vertebra.  
         [0010]     The device and method taught by U.S. Pat. Nos. 4,743,260 and 5,282,863 effectively provide a desired degree of flexibility. However, self-tapping bone screws, though widely used for a variety of applications, typically struggle to provide both the strength sufficient enough to drive themselves into bone, and the porosity necessary to promote ingrowth. Additionally, once the bone screws are anchored into the vertebral column, the stabilization means must be attached to the exposed ends of the screws with fasteners. Though the fasteners taught by these patents are effective, it would be advantageous to provide a device that obviates the need for fasteners and self-tapping bone screws.  
       BRIEF SUMMARY OF THE INVENTION  
       [0011]     The present invention addresses the problems associated with the prior art devices and methods for treating spinal instability, and provides for unitary flexible stabilization, rather than component flexible stabilization; meaning the spine is supported yet allowed a degree of natural movement or flex. This is accomplished with a minimal amount of metallic components. Additionally, the present invention may allow cellular infiltration by fibroblasts, osteoblasts, reticulation, or other cellular components, to occur. Included in the present invention is a device and method for stabilizing a portion of a vertebral column without fusion. In the preferred form the stabilization device of the present invention is substantially completely or completely made of non-metallic materials (e.g. plastic), which are biocompatible and designed to become integrated with normal body tissues.  
         [0012]     The vertebral column is composed of segments of adjacent vertebrae, with the first vertebra being adjacent the second vertebra. Each vertebra has a posterior vertebral element which, when removed, leaves first and second pedicles on each of the vertebra. The present device includes strong nonmetallic anchor means for securing the stabilization means to at least one of the pedicles of the first and second vertebrae and means for cooperatively connecting the stabilization means to the anchor means. In a preferred embodiment, the device further includes a means for locking the stabilization means to the anchor means.  
         [0013]     In one embodiment, the anchor means includes an upper shank portion and a lower threaded portion having a screw thread. The lower portion is cooperatively connected to the shank portion. The screw thread has segmented areas, wherein a rotary force may be applied to the shank portion whereby the threaded portion is driven into and secured into the pedicles. The screw thread may have segmented areas, wherein after a period of time the vertebra&#39;s bony re-growth encompasses the segmented areas to further secure the threaded portion to the pedicles.  
         [0014]     Preferably, the stabilization means includes a first stabilization element having first and second openings and a second stabilization element having first and second openings. The anchor means comprises four support members such that one of the support members is secured to each of the pedicles, wherein each of the openings is adapted for being positioned around one of the support members. The stabilization elements may then be aligned along the four support members in either a generally parallel relationship or in an X shape. Further, a cross support member may be used to further connect the first stabilization element to second stabilization element.  
         [0015]     In a more preferred embodiment, the anchor means and the stabilization means are of one-piece unitary construction. The anchor means has an upper portion and a lower portion. The upper portion is integral with the stabilization means. The lower portion forms an elongate post, insertable into a hole drilled into the pedicle of a vertebra. To promote ingrowth, the post is porous. Additionally, the post is smaller than the diameter of the drilled hole, leaving sufficient room for a desired quantity of a slurry paste formed from ground bone tissue that includes stem cells, thereby encouraging an ingrowth of bone tissue into the post. In an alternative embodiment the post is hollow forming a channel or lumen therethrough with the outer post areas being porous. This alternative embodiment is designed to promote additional cellular ingrowth.  
         [0016]     In a preferred embodiment, the anchoring means and/or stabilization means may be made from a microporous material produced by a suitable process such as a replamineform process, wherein ingrowth by fibroblasts occur. Coral having a microdiameter of between 190-1200 microns and preferably between 190-230 microns in diameter is used and poritic corals may be used as a model for the replamineform process.  
         [0017]     The present invention also includes an activation process, which has been determined to be a key step in the successful integration of microporous system components. The activation can be internal, external or both, and is herein defined as the process of purposefully inducing and supporting local cellular proliferation to promote component integration.  
         [0018]     The present invention also comprises a surgical method for stabilizing a portion of a vertebral column without fusion. The method includes making an incision to expose the first and second vertebrae. Then, the posterior vertebral elements of each of the vertebrae to be stabilized are removed, leaving first and second pedicles of the first vertebra and first and second pedicles of the second vertebra. In order to relieve pressure from the nerves stemming from the spinal cord, a medial inferior portion of each of the remaining pedicles is also removed, thereby ensuring the nerve does not abut against the pedicle. Alternatively, if clinical presentation warrants, a full pediclectomy may be performed. A bone screw is secured into at least one of the pedicles of the first and second pedicles of the first and second vertebrae. The bone screw has a threaded bottom portion and an upper shank portion. Next, the stabilization means is cooperatively connected between the bone screw of one of the first pedicles of the first vertebra to the bone screw of one of the first pedicles of the second vertebra. It is understood that screws are not essential, but are a preferred embodiment. Other suitable anchoring means may be used to anchor the stabilization means to pedicles, such as stapling. It is also understood that multiple segments may be stabilized.  
         [0019]     A preferred embodiment of a surgical method for stabilizing a portion of a vertebral column without fusion includes making an incision to expose the first and second vertebrae. Then, the posterior vertebral elements of each of the vertebrae to be stabilized are removed, leaving first and second pedicles of the first vertebra and first and second pedicles of the second vertebra. In order to relieve pressure from the nerves stemming from the spinal cord, a medial inferior portion of each of the remaining pedicles is also removed, thereby ensuring the nerve does not abut against the pedicle. Next, holes are formed in the pedicles spaced apart a predetermined distance to accept porous anchoring posts of a unitarily constructed flexible stabilization device. Alternatively, if clinical presentation warrants, a full pediclectomy may be performed. In such a case, the holes are formed in the vertebral body at the pedicle footprint. This is a particularly strong area because of the fascicular nature of the bone fibres passing up from the vertebral body into the pedicle. If the pedicle is completely removed, i.e. flush with the vertebral body, this sit is still highly reinforced and ideal for anchoring. In both case, optimally the removed pedicles are used to create an activation slurry of milled bone and autogenous stem cells and/or bone morphogenic materials. An appropriate quantity of the slurry is placed in the holes along with the anchoring posts of the device. A temporary bond is created between the device and the vertebrae using a polymer or cement, thereby securing the device to the vertebrae while ingrowth is promoted. 
     
    
     BRIEF DESCRIPTION OF THE DRAWINGS  
       [0020]      FIG. 1  is a perspective view showing one embodiment of the present invention in a partially exploded perspective view;  
         [0021]      FIG. 2  is a top-plan view of the present invention shown in  FIG. 1 ;  
         [0022]      FIG. 3  is a perspective view of the bone screw of the present invention;  
         [0023]      FIG. 4  is a cross-sectional view taken generally along the lines  4 - 4  of  FIG. 3 ;  
         [0024]      FIG. 5  is a cross-sectional view of one embodiment of the locking cap as shown in  FIG. 1 ;  
         [0025]      FIG. 6  is a perspective view of a second embodiment of a locking cap;  
         [0026]      FIG. 7  is a cross-sectional view taken generally along the lines  7 - 7  of  FIG. 6 ;  
         [0027]      FIG. 8  is a partial cross-sectional view showing a bone screw being inserted into a vertebra according to the present invention;  
         [0028]      FIG. 9  is a side elevation of a vertebra before the posterior vertebral elements are removed according to the present invention;  
         [0029]      FIG. 10  is perspective view of a second embodiment of a bone screw;  
         [0030]      FIG. 11  is a perspective view of a second embodiment of a stabilization element;  
         [0031]      FIG. 12  is a perspective view of a unitary embodiment of a stabilization device with integral anchoring posts;  
         [0032]      FIG. 13  is a plan view of a unitary embodiment of a stabilization device with integral anchoring posts; and  
         [0033]      FIG. 14  is a perspective view of a unitary embodiment of a stabilization device with integral anchoring posts. 
     
    
     DETAILED DESCRIPTION OF THE INVENTION  
       [0034]     Referring to the figures, wherein like numerals represent like parts throughout the several views, there is generally illustrated a device  10  useable for stabilizing at least a portion of a vertebral column. In  FIG. 1 , a first vertebra  11  and second vertebra  12  are shown. It should be understood that when the terms “first and second” vertebrae are used in this application, reference is being made only to vertebrae that are adjacent, and not to any specific vertebrae along the vertebral column. Each vertebra has a posterior element, designated as  13  shown in  FIG. 9 . When the posterior element  13  is removed from the vertebra, a first and second vertebral pedicle is exposed in each vertebra.  FIG. 1  shows the first vertebral pedicle  11   a  and the second vertebral pedicle  11   b  of the first vertebra  11  and the first vertebral pedicle  12   a  and the second vertebral pedicle  12   b  of the second vertebra  12 . If screws are used as anchoring devices, each of the pedicles ( 11   a ,  11   b ,  12   a  or  12   b ) that are to be utilized have a hole  14  drilled into the pedicle.  
         [0035]     A bone screw, generally designated as  15 , has an upper shank portion  16 , which in a preferred embodiment has a square cross section to allow for efficient insertion and removal. A lower threaded portion  17  is cooperatively connected to the upper shank portion  16 . The threaded portion  17  has an inner shaft  17   a  and a threaded member  17   b . The threaded member  17   b  is a continuous helical member having segmented areas  17   c . The threaded member  17  provides a wide flange to give a deep bite when secured in the vertebra. While the segmented areas  17   c  are shown in  FIG. 4  as being pie-shaped, and having three per one complete circumference, it is understood that any suitable shape or number of segmented areas may be utilized. The inner shaft  17   a  and threaded member  17   b  have a generally consistent diameter throughout, except for a taper towards a point at their bottom end. Preferably, the diameter of the hole  14  is slightly smaller than the diameter of the inner shaft  17   a.    
         [0036]     A stabilization element  18 , having a first end  18   a  and a second end  18   b  has two openings  19  adapted to being placed over the upper shank  16  of the bone screw  15 . A spacer  20  may also be used if the height of the pedicle is not sufficient. The spacer  20  can be inserted between the pedicle and stabilization element  18  to avoid compression of exiting spinal nerves. In one embodiment, the element  18  is a flat strip. However, it is understood that other suitable shapes such as an hourglass shape or dumbbell shape may be used.  
         [0037]     A locking cap  21 , having an opening  21   a  has a generally downwardly depending circumferential member  21   b  that locks the rod  18  in place. A second embodiment of a locking cap is shown in  FIGS. 6 and 7 . The locking cap  22  is similar to the locking cap  21  in that it has an opening  22   a  and a generally downwardly depending circumferential member  22   b , similar to locking cap  21 . However, in addition, there are two skirt members  22   c . As will be more fully discussed hereinafter, the skirt members  22   c  limit parallelogram movement between the two stabilization elements  18  when they are in position.  
         [0038]     The material that the stabilization elements  18  and screws  15  are made of must provide sufficient strength, be biocompatible, and preferably non-metallic. Some non-reinforced biocompatible plastic polymers indicate a tendency to crack, fissure or shear with repeated flex or stress. A preferred material is a two-phase biocompatible plastic so as to provide adequate strength. Internal reinforcement with dissimilar polymers or filaments provide increased strength over that of a single phase plastic, but as the internal diameter of the stabilization element  18  decreases, practical fabrications become a problem. Therefore, it is preferred that internal fibers are used for reinforcement. It is desired that the material used have sufficient strength and flexibility, as well as being biocompatible.  
         [0039]     It is known that many fibers have been tested in polymers and many lightweight and remarkably strong materials have resulted. A most innovative reinforced two-phase material to date has been created for aeronautical use. Although many of these systems are attractive for their physical qualities, they are also marginal or clearly unacceptable from the standpoint of being biocompatible. It has been found that carbon fiber reinforced plastic yields adequate strength for constructing the stabilization elements  18 . However, it is sometimes preferable that the screws be made of a still stronger material so as to prevent the screws from being sheared off by the stress of the system. One such material that has been found adequate for the screws  15  is a magnamite graphite fiber or carbon reinforced plastic. The materials used for the stabilization elements  18  and screws  15  are not limited to the above noted plastics, and may also include other suitable solid materials that have the above-noted properties. Also, porous material forms in which the porosity is controlled by the replamineform process may be utilized. Polymers such as silicone, polyethylene, nylon, vinyl, methylmethacyrate, dacrons or teflon may be suitable.  
         [0040]     Applicant has made a study of small coral specimens and a study of these samples has confirmed the original observations of the Penn State researchers. By matching the physical pore size characteristics of applicant&#39;s samples with those reported in the failed medical fusion studies, two conclusions could be drawn. The first is that if coral with larger pore sizes were used (400-500 microns), it might very well be more successful for bone fusion osteoblasts ingrowth. Secondly, the previous medical research on coral, which was considered a failure, actually indicated that there was ingrowth by fibroblasts (rather than osteoblasts). However, such fibroblasts ingrowth is well suited for the flexible system of the present invention. The ingrowth of fibroblasts will further anchor and fix the device  10 , but will still allow the device  10  to retain its flexible characteristics.  
         [0041]     Further, Applicant has identified poritic coral having 190-230 micron diameter as preferred for the present flexible system rather than other corals, such as goniopera with 230-600 micron size. It is poritic coral that would serve as the replamineform model for making the screws  15  and stabilization elements  18  of the present invention. However, it has been found that pore sizes of from 190-1200 microns are suitable for the present invention.  
         [0042]     In use, only a limited surgical exposure is necessary to perform the operation necessary to incorporate the present invention. Following the removal of all or part of the posterior vertebral elements  13 , the exposed pedicles serve as the anchoring media for the bone screws  15 . In addition to removing the posterior vertebral elements  13 , medial inferior portions  38  of the remaining pedicles may be removed to alleviate pressure from swollen nerves. The removed portions  38  are shown in  FIGS. 1, 12  and  13 . The pedicles are drilled by appropriate means to create the hole  14 . A driving mechanism is placed over the upper shank  16  and the lower portion  17  is screwed completely into the vertebra. The threaded member  17   b  serves to stabilize the bone screw  15  and the segmented areas  17   c  are designed to allow bone growth to further stabilize the screw  15  in place. If only two vertebrae are to be stabilized, it is only necessary for bone screws  15  to be secured into the pedicles  11   a ,  11   b ,  12   a  and  12   b  . However, if multiple vertebrae are to be stabilized, the corresponding pedicles on the third or subsequent vertebrae also have to be provided with a bone screw  15 . The stabilization elements  18  are tapped at the appropriate position and holes  19  are made either by drilling or by a heated rod at the site of the tap. While  FIGS. 1 and 2  show that stabilization elements  18  have been placed for a one-level stabilization, the present invention is compatible with stabilizing multiple levels as well as single levels. Further, only one stabilization element  18  may be necessary for some patients. Once the screws  15  are in place, a separator instrument, not shown, may be used to distract the vertebrae, if this desired, and this separation is maintained by the placement of the stabilization elements  18  over the shank  16  of the bone screw  15 . As previously mentioned, if the height of the pedicle is not sufficient, a spacer  20  may be inserted on top of the pedicle. The spacer  20  may be constructed from a softer plastic such as polyurethane or silicone. The procedure is then completed by the application of a locking cap, either  21  or  22 , at each of the upper shanks  16  and the removal of any excess shank material above the top of the locking cap  21  or  22 .  
         [0043]     While the device  10  is illustrated in  FIGS. 1 and 2  as having a stabilized means having two generally parallel stabilization elements  18 , it is understood that the stabilization means may be other suitable forms such as a single stabilization element  18 , or two stabilization elements  18  that cross to form an X shape, or two stabilization elements  18  generally parallel having across support member to form an H shape.  
         [0044]     The present invention allows for flexibility and because of the flexibility of the system, less disruptive force is applied to the screw  15 , or other anchor means, following the application of the system itself.  
         [0045]     The flexibility of the device  10  has as its lower limit no flexibility. No flexibility would have the same result as fusion and the device  10  provides for at least some flexibility more than fusion. In the preferred embodiment, the flexibility of the device  10  would stabilize with a degree that substantially equals a normal back. Too much flexibility would render the back non-functional and not stabilize the back. Any stabilization more than that present in the back of the patient before the procedure would be beneficial.  
         [0046]     Numerically, the general upper limit of flexibility for the device  10  is shown in the following table for the stabilization means:  
                                                   Stabilization   Inch-Pounds for Standard           Means Length   Deflection of ½ Inch                           1″   45 ip.           2″   32 ip.           3″   23 ip.                      
 
         [0047]     The device  10  is stiff enough to stabilize the vertebral column but flexible enough to permit at least limited normal movement of the vertebral column. The flexibility allows forces on the stabilization elements and anchors to be dissipated throughout, thereby reducing force concentrations.  
         [0048]     If locking cap  21  is used, parallelogram movement between the two stabilization elements  18  is possible. That is, there is a possibility of some relative sideways movement of the first vertebra  11  to the second vertebra  12 . If locking cap  22  is used, the locking cap  22  will limit the parallelogram movement. This is because the rod  18  is positioned inside of the skirt member  22 c such that parallelogram rotation is limited.  
         [0049]     In addition to anchoring the stabilization element  18  by means of screws  15 , it is also envisioned that other suitable methods of anchoring may be used. One such example would be to staple the stabilization element  18  to the pedicles. Another embodiment would include ribbed tabs molded to the stabilization element  18  as an integral part thereof and would be positioned approximately the same place where the bone screws  15  would be inserted in the previously discussed embodiment. The holes would then be drilled into the pedicles at the appropriate distances and the ribbed tabs could be inserted into the holes and glued in place. The ribbed tabs could be placed at varying distances along the stabilization element in various models and the appropriate length model simply chosen depending upon the spacing between the vertebrae of the patient.  
         [0050]      FIGS. 10 and 11  show another embodiment of the present invention wherein it would not be necessary to have an opening in the stabilization rod. The second embodiment of the bone screw  23  has an upper portion  24  and a lower threaded portion  25 . The lower threaded portion  25  is similar to the lower threaded section  17  in that the lower portion  25  has a shaft  25   a  about which is threaded members  25   b  having segmented areas  25   c . The upper portion  24  has a base  24   a  and two upright members  24   b  cooperatively connected thereto. The top surface of the base  24   a  has a corrugated area  24   c.    
         [0051]     The second embodiment of the stabilization element, designated as  26  has a corrugated upper surface  26   a  and a corrugated bottom surface  26   b . The corrugated surfaces  26   a ,  26   b  and  24   c  could also be described as having a vertical toothed surface. The toothed surface  26   b  meshes with the toothed surface  24   c , thereby preventing relative movement between the stabilization element  26  and the bone screw  23 . With such a vertical tooth configuration, it is not necessary to create an opening in the stabilization element  26 . The uprights  24   b  are spaced to have a distance between them the approximate width of the stabilization element  26 . Therefore the upright members  24   b  also assist in limiting relative movement of the stabilization element  26  to the bone screw  23 .  
         [0052]     A preferred embodiment of a stabilization device  30  is shown in  FIGS. 12 through 14 . The device  30  includes a stabilization means  32  and an anchoring means  34 . As shown in these Figures, the stabilization means  32  and the anchoring means  34  are of unitary construction. The anchoring means  34  are preferably elongate and extend from the stabilization means  32  at approximately 90 degrees to a longitudinal axis  36  of the stabilization means  32 . As shown in  FIG. 14 , the stabilization means and anchoring means may be channeled out to form a lumen axially disposed therethrough. Alternatively, only the anchoring means may include the lumen. The lumen promotes additional ingrowth of bone in accordance with the method of the present invention as set forth in detail below.  
         [0053]     Preferably, the stabilization device  30  is constructed and arranged for the specific stabilization task it will perform. For example, if it is desired to stabilize three vertebrae, a pair of devices  30  will be designed to include three anchoring means  34  each. The individual posts of the anchoring means will be spaced apart to match the spacing of the pedicles of the vertebrae. If only two vertebrae are to be stabilized, such as is shown in  FIG. 12 , a pair of devices  30  are constructed to have two posts  34  extending from the stabilization means  32 , which are spaced apart to match the pedicles  11   a  and  12   a , or  11   b  and  12   b . The holes  14  are drilled in the pedicles  11  and  12  to precisely match the positions of the posts  34 .  
         [0054]     The method of the present invention begins after a determination is made that two or more vertebrae,  11  and  12 , require stabilization and the appropriate vertebrae,  11  and  12 , have been identified. Appropriate initial steps are taken to expose the spine and control the bleeding, thereby creating a suitable working environment for the procedure. Next, a posterior element  13  ( FIG. 9 ) from a first vertebra  11  is removed, thereby exposing a first and second vertebral pedicle,  11   a  and  11   b  respectively, on the first vertebra  11 . These pedicles  11   a  and  11   b  will later serve as the device anchoring point for that vertebra  11 . Similarly, the next step is to remove a posterior element  13  from a second vertebra  12 , adjacent the first vertebra  11 , thereby exposing a first and second vertebral pedicle,  12   a  and  12   b  respectively, on the second vertebra  12 . This is repeated for all of the targeted vertebrae, though for purposes of this example, only two vertebrae,  11  and  12 , will be targeted. Notably, the method of the present invention lends itself readily to nerve decompression. Removal of all or the medial inferior portion  38  of the pedicles relieves pressure placed on swollen nerves by the pedicles.  
         [0055]     Next, holes  14  must be formed in the first and second vertebral pedicles,  11   a  and  b , and  12   a  and  b , on the first and second vertebrae  11  and  12 . Care is taken to accurately measure the spacing between the holes  14 , which should closely match the distance between the centers of the posts  34  of a pre-selected stabilization device  30 . The diameter of the holes  14  should exceed the diameter of the posts  34 , thereby providing room for error as well as room for the existence of an activation slurry, which will be placed into the holes  14  with the posts  34  and promote an integration of the vertebrae  11  and  12 .  
         [0056]     The next step is to create the activation slurry (not shown), if osteoblastic induction is chosen as an external activation method. This slurry is created by milling autogenous bone, local or distal. Preferably the removed posterior elements are used, thereby obviating the need for a separate harvesting surgery. The milled bone is combined with autogenous stem cell or bone morphogenic materials. The slurry is then placed in the hole  14  to serve as an osteoblast resource.  
         [0057]     If fibroblastic induction is chosen as an external activation method, autogenous fat grafts (local or distal, but preferably local, again obviating the need for a second harvesting operation) are placed in proximity to the microporous components, such as in the hole  14 , around the post  34 , or near the union of the device  30  and the vertebrae  11  and  12 .  
         [0058]     The vertebrae  11  and  12  are now prepared to receive the stabilization device  30 . The anchoring means or posts  34  of the device  30  are simply placed into the holes  14 , giving appropriate deference to the preservation of the fat grafts, if any. A first stabilization device  30   a  is placed on one side of the vertebrae and a second stabilization device  30   b  is placed on the other side, as shown in  FIG. 12 .  
         [0059]     Measures are next taken to secure the device  30  in place until the slurry has a chance to harden and grow. Acceptable measures include applying polymers or cements. These substances may be self-curing or may require curing by irradiation, such as infrared, or thermal curing.  
         [0060]     Other modifications of the invention will be apparent to those skilled in the art in light of the foregoing description. This description is intended to provide specific examples of individual embodiments, which clearly disclose the present invention. Accordingly, the invention is not limited to these embodiments or the use of elements having specific configurations and shapes as presented herein. All alternative modifications and variations of the present invention that follow in the spirit and broad scope of the appended claims are included.