Artificial expandable implant systems

Abstract

An apparatus and method for joining members together using a self-drilling screw apparatus or stapling apparatus are disclosed. The screw apparatus includes a shell and first and second first screw members having tapered ends and threaded bodies that are disposed within the shell. A drive mechanism rotatably drives the first and second screw members from the shell in opposite directions and causes the screw members to embed themselves in the members to be joined. The screw apparatus can be used to join members such as bones, portions of the spinal column, vertebral bodies, wood, building materials, metals, masonry, or plastics. The stapling apparatus includes first and second lever arms rotatably joined together at a fulcrum, and the lever arms rotate in opposite directions. First and second cartridges are disposed at the ends of the lever arms. Each cartridge is capable of holding a staple including a bracket, a nail member and an alignment slot. When the ends of the lever arms are rotated towards each other the staples from the cartridges are interlocked. The staples can be also be used to join members such as bones, portions of the spinal column, or vertebral bodies.

Description

FIELD OF INVENTION

The present invention relates to bi-directional fixating transvertebral (BDFT) screws which can be used to supplement other intervertebral spacers and/or bone fusion materials. BDFT screws can be incorporated into anterior and/or posterior cervical and lumbosacral novel zero-profile horizontal and triangular intervertebral mini-plates. In addition BDFT screws can be incorporated into two dimensional, expansile intervertebral body fusion devices (IBFDs) transforming them into stand-alone posteriorly and/or anteriorly placed cervical, thoracic and lumbar spinal fusion devices. In the lumbosacral and thoracic spine BDFT screws may obviate the need for supplemental pedicle screw fixation. In the cervical spine it obviates the need for supplemental vertically oriented anterior plating. The present invention also relates to a stand-alone or supplemental, calibrating interarticular joint stapling device which can incrementally fine-tune posterior interarticular joint motion.

DESCRIPTION OF THE RELEVANT ART

Segmental spinal fusions which stabilize two or more adjacent segments of the spine are performed for painful degenerative disc disease, recurrent disc herniations, spinal stenosis, spondylolysis and spondylolisthesis. Over the past several decades a wide variety of fusion techniques and instrumentation have evolved. One of the earliest posterior fusion techniques entails non-instrumented in-situ on-lay posteriolateral fusion utilizing autologous iliac crest bone. Because of the high rate of imperfect fusions i.e. pseudoarthroses, transpedicular pedicle screw fixation which utilizes a variety of rods and interconnectors were developed to achieve less interbody motion and hence higher fusion rates. Pedicle screw fixation was initially combined with on-lay posteriolateral fusion. Because of the poor blood supply of the transverse processes, issues still remained with pseudoarthroses. In an attempt to address this problem, pedicle screw fixation has been supplemented with a variety of interbody fusion devices. This is based on the concept that axial loading enhances fusion and that the vertebral endplates have a better blood supply. Interbody lumbar fusion devices can be placed anteriorly via an anterior lumbar interbody fusion technique (ALIF) or posteriorly via a posterior lumbar interbody fusion technique (PLIF). Material options for interbody fusion devices have included autologous iliac crest/laminar bone, cylindrical threaded titanium interbody cages, cylindrical threaded cortical bone dowels, vertebral interbody rings or boxes, carbon fiber cages, or femoral ring allograft. To lessen the complication of prolonged nerve root retraction the technique of circumferential tansforaminal lumbar interbody fusion technique (TLIF) has been introduced. This employs the transforaminal placement of an interbody spacer such as one kidney bean shaped allograft, two circular allografts, one or two titanium circular cages, a single titanium or Peek (poly-ether-ketone) boomerang spacer. The threaded spacers are usually supplemented with autologous bone and/or bone morphogenic protein (BMP), demineralized bone matrix (DBM) in the form of paste or cement, rh-BMP with collagen sponges, or similar osteoinductive biological agents which are known to enhance fusion.

Currently all lumbosacral fusion techniques, ALIF, PLIF and TLIF, are typically supplemented by pedicle screw placement. In addition posterior transfacet screws also have been used to supplement ALIF procedures. Complications of pedicle screw placement include duration of procedure, significant tissue dissection and muscle retraction, misplaced screws with neural and/or vascular injury, excessive blood loss, need for transfusions, prolonged recovery, incomplete return to work, excess rigidity leading to adjacent segmental disease requiring further fusions and re-operations. Further advances of pedicle screw fixation including minimally invasive and image-guided technology, and the development of flexible rods have imperfectly addressed some but not all of these issues. Transfacet screws entail the use of long screws which provide a static facet alignment without motion calibration.

Complications of all current interbody fusion devices is their lack of coverage of the majority of the cross sectional area of the vertebral endplates and their potential for extrusion. The recently described flexible fusion system which consists of flexible rods attached to transpedicular screws (Dionysis, Zimmer) suffers from a high pull-out rate, higher rate of re-operation than standard fusions, and does not rank high with patient satisfaction. See for example, Clinical experience with the Dynesys semirigid fixation system for the lumbar spine: Surgical and patient-oriented outcome in 50 cases after an average of 2 years; D, Grob, A. Benini and A. F. Mannion. Spine Volume 30, number 3, Feb. 1, 2005.

Single or multiple level anterior cervical spinal fusions typically employ the replacement of the cervical disc or discs with autologous or allograft bone, or an intervertebral spacer filled with autologous or allograft bone, demineralized bone matrix, BMP or rh-BMP etc. Currently these anterior cervical fusions are augmented with anterior vertical titanium plates which cross the intervertebral space or spaces and are secured to the vertebral bodies above and below the disc space or spaces with perpendicularly penetrating vertebral body screws. The purpose of these plates is to serve as a barrier to prevent extrusion of the intervertebral disc replacement. Recently anterior vertical plating has also been employed in anterior lumbar fusion.

Complications of anterior spinal plating include the potential for neurovascular injury with screw misplacement, screw and/or plate pull-out, and screw and/or plate breakage. Other complications include potential esophageal compression/injury in the cervical spine secondary to high plate profile or pullout, and to potential devastating vascular injury in the lumbar spine with plate movement and/or dislodgement into anterior iliac vasculature. Recent advances in cervical plating have therefore concentrated on the creation of lower profile plates and even resorbable plates. These advances, however, have not eliminated the-possibility of plate dislodgement and screw back out/breakage.

To achieve segmental fusion applicants propose the use of novel bidirectional fixating transvertebral (BDFT) screws which can be strategically inserted via anterior or posterior surgical spinal approaches into the anterior and middle columns of the intervertebral disc space. The BDFT mechanism employs turning one or two pinions which then turns one or two central gears which in turn simultaneously controls expansile movement of right and-left-handed bi-directional screws. The vertebral bodies above and below the disc space by virtue of their engagement and penetration by the BDFT screws are thus linked and eventually fused. The casings of the BDFT screws prevent vertebral body subsidence. The inside of the denuded intervertebral space can then be packed with autologous or allograft bone, BMP, DBX or similar osteoinductive material. Alternatively an intervertebral spacer filled with either of these substances can be inserted.

Applicants postulate that BDFT screws provide as strong or stronger segmental fusion as pedicle screws without the complications arising from pedicle screw placement which include screw misplacement with potential nerve and/or vascular injury, violation of some healthy facets, possible pedicle destruction and blood loss. By placing screws across the intervertebral space from vertebral body to vertebral body engaging anterior and middle spinal columns, and not into the vertebral bodies via the transpedicular route, some of the healthy facet joints are preserved. Because this technique accomplishes both anterior and middle column fusion, without rigidly fixing the posterior column, it in essence creates a flexible fusion. This device therefore is a flexible fusion device because the preserved posterior joints retain their function achieving at least a modicum of mobility and hence a less rigid (flexible) fusion.

The very advantage of trans-pedicular screws which facilitate a strong solid fusion by rigidly engaging all three spinal columns (anterior, middle and posterior), is the same mechanical mechanism whereby complete inflexibility of all columns is incurred thereby leading to increasing rostral and caudal segmental stress which leads to an increased rate of re-operation.

Transvertebral fusion also leads to far less muscle retraction, blood loss, and significant reduction in O.R. time. Thus the complication of pedicular screw pull-out and hence high re-operation rate associated with the current embodiment of flexible fusion pedicle screws/rods is obviated. The lumbosacral BDFT screws can be introduced via PLIF, TLIF or ALIF operative techniques. Although one can opt to supplement these screws with transpedicular screws there would be no absolute need for supplemental pedicle screw fixation with these operative techniques.

Bi-directional fixating transvertebral (BDFT) screws can also be combined with novel zero-profile horizontal cervical and lumbar mini-plates. They can also be combined with mini-plates and a cage with slots for bone material insertion. Thus this is in essence a three-in-one device; 1) cage which can be filled with bone, 2) a plate and 3) BDFT screws.

For the performance of anterior cervical, and lumbar anterior or posterior fusions one or two centrally placed BDFT screws anterior to an interverterbal graft or spacer, may be a sufficient barrier by itself to prevent device/graft extrusion. However, to further safeguard against graft/spacer extrusion applicants have devised horizontal linear mini-plates which can be incorporated into two anteriorly placed BDFT screws, as well as a linear triangulating mini-plate which can be incorporated into two anteriorly placed, and one posteriorly placed BDFT screws. The horizontal linear mini-plates or horizontal triangular mini-plate traverse the diameter of the disc space and most of the disc space height. Thus a horizontal mini-plate placed anteriorly immediately beneath the rostra! and caudal ventral vertebral body surfaces which is secured by BDFT screws which are also beneath the vertebral body surfaces, would prevent intervertebral device/graft extrusion. This mini-plate is essentially a zero- to subzero-profile plate in that it is either flush with the vertebral body surfaces or below them.

Because the BDFT screws engage a small percentage of the rostra! and caudal vertebral bodies, this plating system could be performed at multiple levels. This plating system which utilizes BDFT screws does not lead to any esophageal compression or injury in the cervical spine or vascular iliac vein injury in the lumbar spine. For the performance of two or three level intervertebral fusion with horizontal mini-plates there is virtually no possibility of plate breakage which can occur in long vertical anterior plates which are in current usage. Similarly, screw dislodgement, if it occurs would lead to minimal esophageal compression or injury compared to large vertical plate/screw dislodgement. In addition, in the cervical spine BDFT screw placement closer to the midline would avert any possibility of lateral neural or vertebral artery injury.

In copending PCT Patent Application PCT/US2005/016493, filed May 11, 2005, the entire contents of which are incorporated by reference, applicants developed an interbody expansile artificial disc device composed of an inner core artificial disc surrounded by expansile titanium shells with spikes which can expand in two or three dimensions. In yet another embodiment of tranvertebral fixation applicants propose a novel cervical and thoracic/lumbosacral intervertebral fusion device (IBFD) which combines the expansile titanium or PEEK shells or our previous artificial disc design with BDFT screws which can be inserted into the disc space.

Yet another embodiment incorporates a core expansile elastometric porous balloon sheath vulcanized to the expandable external shells which can then be filled with bone fusion material. Balloon porosity would allow fusion to occur from vertebral endplate to endplate. Bony material can be injected into this porous balloon through a port directly or through a silastic catheter (see previous patent).

If one were inclined to further enhance posterior column thoracolumbosacral fixation, applicants introduce an optional novel calibrated facet stapling device which staples the inferior articulating facet of the superior segment to the superior articulating facet of the caudal vertebral segment unilaterally or bilaterally, further minimizing motion until interbody fusion occurs. The degree of flexibility can be further modulated by varying the calibration strength and torque of facet stapling. This would be dictated by the need for greater or lesser degrees of motion preservation.

Currently, failed anterior lumbar arthoplasties are salvaged by combined anterior and posterior fusions. BDFT screws and/or IBFDs could be utilized as a one-step salvage operation for failed/extruded anteriorly placed lumbar artificial discs obviating the above salvage procedures which have greater morbidity. Likewise, for anterior cervical fusion, applying cervical BDFT screws alone or in combination with cervical mini-plates addresses the deficiencies and complications of current cervical plating technology as mentioned above.

BRIEF DESCRIPTION OF THE DRAWINGS

FIGS. 1A-D illustrate three-dimensional and cross-sectional views of the BDFT screw and its mechanism of operation (Embodiment I).

FIGS. 2A-G illustrate three-dimensional and cross-sectional views of the BDFT screw and its mechanism of operation (Embodiment II).

FIGS. 3A-E illustrate three dimensional, cross-sectional and exploded views of the BDFT screw and its mechanism of operation (Embodiment III).

FIGS. 4A-C illustrate a single or three BDFT screws inserted into adjacent vertebral bodies.

FIGS. 5A and 5B illustrate three-dimensional views of the zero-profile linear mini-plate.

FIGS. 5C and 5D illustrate the integration of BDFT screws in the zero-profile linear mini-plate.

FIGS. 6A through 6G illustrate different views of the zero-profile triangular mini-plate, its integration with BDFT screws and incorporation into the vertebral bodies.

FIGS. 6H and 61 illustrate different views of the three-in-one device combining a zero-profile horizontal mini-plate, a cage with incorporated slots for the placement of bone material, and BDFT screws

FIGS. 7A and 7B illustrate the lumbar two-dimensionally expanding intervertebral fusion device (IBFD) with incorporated BDFT screws.

FIGS. 8A-N illustrate the facet joint calibrated stapling device which staples the inferior articulating facet with the superior articulating facet. Increasing degrees of torque calibration leads to increasing posterior column rigidity, whereas decreasing degrees of calibration leads to increasing flexibility.

FIGS. 8O and 8P illustrate four frontal and perspective views of the facet staple with sequential increasing calibrated positions leading to decreasing increments of joint motion/flexibility.

FIGS. 8Q and 8R illustrate the stapled inferior and superior interarticulating facets by the facet stapler.

DETAILED DESCRIPTION OF THE INVENTION

1. The Medical Device

Referring to FIGS. 1A-D the above described problem can be solved in the cervical, thoracic and lumbar spine by insertion into the denuded intervertebral disc space an expansile bi-directional fixating transvertebral (BDFT) screw 100 or screws.

FIGS. 1A and 1B illustrate three-dimensional views of the screw 100 in closed and opened positions, respectively, upon its insertion into the intervertebral disc space. The screw 100 is self-drilling. The mechanism of its action entails the turning of a midline drive screw 100/pinion 104 in a clock-wise direction. This motion is bi-directionally translated via an interposing gear mechanism 105 enabling the simultaneous outward movement of left and right handed screws 102, 103 in equal and opposite directions. When the drive screw 101 and its accompanying drive screw shaft are turned clock-wise, the driving pinion 104 is likewise rotated. This motion is then translated to the driven gear 105 which is interposed between the drive screw 101 and two opposing self-drilling screws 102, 103, one left-handed and the other right-handed.

The gear ring 110 has screw coupling slots (Figures IC and 1D). There are also symmetric keyways 120 and an alignment cylinder 113. The left handed screw 102 fits into one half of the slots 114, 115 and the right handed screw 103 into the other half of the slots. This is clearly illustrated in cross sections of the screw and gear in Figures IC and ID, respectively.

FIGS. 1A-C also illustrate the external casing 111 of the device which contains the external screw threads 117, 118, against which the left and right handed internal threads interact 116, 119 with. The casing includes an upper left casing 111b and an upper right casing 111a. Below the upper casing 111b there is a surface serration pattern 118 which is part of a retaining outer shell 112.

FIGS. 2A-G illustrate Embodiment II of the BDFT 200. This design differs in two fundamental ways from Embodiment I. Firstly the driving pinion 201 accomplishes bi-directional movement by engaging left and right gears 204, 205 which simultaneously turn left and right screws 202, 203 (FIGS. 2C-G). Secondly, in it's resting closed position the solid left screw 202 with a narrower diameter is buried within the right wider diameter hollow right screw 203. This mechanism allows for greater length of screw expansion compared to Embodiment I. Maintaining alignment of screws 202, 203 and pinions 201 is accomplished by upper casings 211, outer shells 212, and left and right screw caps 209a, 209b (FIGS. 2A-G).

FIGS. 3A-E illustrate Embodiment III of the BDFT 300. This is similar to Embodiment II. The major difference is the use of two separate driving screws pinions 301a, 301b for the two separate gears 304, 305. There is one pinion 301a for the left screw 302 and another pinion 301b for the right screw 303. The left screw 302 engages the left gear 304 which engages the left screw 302. The right pinion 301a engages the right gear 305 which engages the right screw 303. Because the left and right screws 302, 303 have separate controls and are not linked by one common pinion, separate distinct motions of the screws 302, 303 can be obtained, as opposed to equal and simultaneous screw movements of Embodiments I and II. Like Embodiment II, Embodiment III consists of a smaller diameter solid left screw 302 which fits into a larger diameter hollow right screw 303. This can achieve significant screw extension length as in Embodiment II.

FIGS. 4A and 4B illustrates the placement of a single BTFD 1000 screw anteriorly into the intervertebral space between adjacent lumbar vertebrae 400. FIG. 4A illustrates the closed position. FIG. 4B illustrates the opened position. The illustrations are of a generic BDFT screw 1000 i.e. it applies to Embodiments I-Ill. Placement of a single BDFT anterior to an intervertbral spacer may be sufficient to prevent interspacer/device extrusion, and enhance spinal stability.

FIG. 4C illustrates the placement of three BTFD screws 1000 in a triangulating manner covering anterior and middle columns. The presence of three screws so situated would prevent subsidence of the screws 1000. Hence they act as a very open IBFD 1000. Bone material in the form of DBX or BMP etc. could be inserted into the intervertebral space in between the three screws 1000. This construct could be used as a supplemental or stand aloneintervertebral fusion device. Also illustrated is a cross-section of a vertebral endplate 401 demonstrating the triangular placement of screws 1000 engaging anterior and middle columns.

FIG. 5A illustrates the zero-profile horizontal linear mini-plate 500. Note the slots for placement of the BDFT screws 1000. On the anterior surface are slots 504 for the driving pinion screws. FIG. 5B illustrates that the plate 500 consists of upper and lower portions 500a, 500b which articulate with each other via interdigitation of alignment pins 502 and recesses 503. FIG. 5C illustrates the integration of the BDFT screws 1000 into the mini-plate 500. FIG. 5D illustrates the placement of the plate-BDFT construct into the intervertebral space. After the construct is placed into the intervertebral space, the screws 1000 are expanded bi-directionally in order to engage the vertebral bodies 400. This construct can be surgically placed via anterior or posterior approaches.

FIGS. 6A-G illustrate a zero-profile triangular mini-plate 600. In this embodiment the plate encompasses all three triangularly situated BDFT screws 1000. The posteriorly placed BDFT screw 1000 is expanded with a centrally placed drive screw/pinion with a long stem which extends posteriorly.

As illustrated in FIGS. 6H and 61 this embodiment 600′ could be made hollow to accommodate the packing of bone material and can actually function as a combined three-in-one fusion cage/plate/BDFT screw construct. Note that this plate embodiment 600′ also has upper and lower components similar to 600a, 600b (FIGS. 6A-C). Preferably, plates 600′a and 600′b, however, include slots 610 for placement of bone material. FIGS. 6D-F illustrate the incorporation of the BDFT screws 1000 into the triangular mini-plate 600. FIG. 6G illustrates the positioning of the triangular mini-plate 600 with incorporated expanded screws 1000 into adjacent vertebral bodies 400.

FIGS. 7A and 7B illustrate a boomerang shaped thoracolumbar IBFD 700 with ratchetable titanium or PEEK shells 710, 711 which can expand geometrically in two dimensions. FIG. 7A illustrates the BDFT screws 701, 702, 703 in partially expanded position. FIG. 7B illustrates the BDFT screws 701, 702, 703 in fully expanded position. The outer shells 710, 711 themselves when ratcheted width-wise have titanium or PEEK spikes 713 inserting themselves into and purchasing the endplates 401, thus securing permanent integration into the vertebral endplates 401. The outer shell 710, 711 surfaces can be treated with hydroxyappetite to facilitate bone incorporation. These shells are fully described in our previous PCT Patent Application PCT/US2005/016493, filed May 11, 2005.

The IBFD device 700 has four shells and a plurality of spikes 713. The height can be modified by adjusting four fixed height screws 712. Sequential turning of these screws 712 leads to height expansion between the rostra! and caudal shells 710, 711 by widening the distance between their superior and inferior shells 710a, 710b. Once the IBFD 700 is properly positioned in the interspace the spikes 713 engage and purchase the vertebral endplates 401. The three incorporated BDFT screws 701, 702, 703 are turned clockwise leading to anterior and middle column engagement of the vertebral bodies 400 above and below the disc space. The BDFT screws 701, 702, 703 are strategically placed; one on each side of the superior shell 710a and one centrally on the inferior shell 710b. This captures anterior and middle columns of the vertebral column increasing spinal stability. After the BDFT screws 701, 702, 703 are successfully purchased within the vertebral bodies 400, bone fusion substances are placed/packed or poured, into the inner aspects of the device 700 and its surrounding intervertebral space.

An alternative thoracolumbar IBFD embodiment not illustrated expands in two dimensions and has the additional feature of an incorporated expansile porous elastometric sheath molded to the inner aspects of the titanium shells. Within the balloon is a port with or without an attached micro silastic catheter through which bone fusion material can be injected. Supplemental bone fusion material can be added to the surrounding area of the device to further enhance fusion. Furthermore for certain patients where applicable, a rapid fusion can be effected by the instillation of methyl-methacrylate A similar embodiment for a cervical IBFD is based on our previously described two-dimensional cervical expansion device in PCT Patent Application PCT/US2005/016493, filed May 11, 2005.

The engagement of the IBFD shell spikes 713 and the BDFT screws 701, 702, 703 into the vertebral bodies 400 above and below the device would obviate the need for any kind of anterior plating system.

FIGS. 8A-N illustrate a calibrated facet joint stapler 800 which can be used to staple the thoracolumbar inferior and superior articulating facets with incremental torquedegrees. Incrementally increasing the degrees of calibration modulates the extent of facet joint flexibility. This can be used as an option to provide posterior column support and can be used in an open, or percutaneous, endoscopic or fluoroscopic approach. Depending on the operative approach and the individual patient, facet stapling can be performed unilaterally or bilaterally.

The stapling device 800 consists of two orthogonally placed levers 801a, 801b which open and close over a triangular fulcrum 810. The edges of the levers 801a, 801b are attached to left sand right staple cartridges 802a, 802b. Each cartridge 802a, 802b holds a titanium staple 803a, 803b in its slots. FIG. 8A illustrates an exploded view of the joint stapler 800 and its essential components. FIGS. 8B and 8C illustrate the stapler 800 in open position. FIGS. 8D and 8E illustrate the stapling device 800 and staples 803a, 803b in closed position. FIGS. 8F and 8G illustrate the stapling device 800 and 803a, 803b staples in closed, staple released, position. FIG. 8H-J illustrate the components of the lever 801a, 801b which includes the grip handle 815, arm 816, rounded wedge 817 and fulcrum screw hole 818. FIGS. 8K and 8L illustrate the details of the cartridge 802a, 802b including its slot for the fulcrum 810 and staples 803a, 803b. FIGS. 8M and 8N illustrate the details of the fulcrum 810 which include right and left cartridge slots 820a, 820b and fulcrum screw 812 and mating alignments. Most importantly it has four incremental calibration slots for incremental degrees of facet joint stapling. Also illustrated are spring anchors 814.

FIGS. 8O and 8P illustrate frontal and perspective views, respectively of the two opposing titanium facet staples 803a, 803b. Each staple 803a, 803b consists of a bracket 836, a nail 837 and an alignment pin 835. Illustrated are four sequential calibrated tightening positions of the opposing staples 803a, 803b. Increasing the calibrated opposition of the two staples 803a, 803b leads to increasing opposition of the facet joints and hence increasing rigidity, and decreasing flexibility. Each staple 803a, 803b has two alignment recesses 838. The opposition of these staples 803a, 803b around the facet joint forms a rectangular facet joint enclosure.

FIGS. 8Q ad 8R illustrate the stapled inferior and superior articulating facets 851, 852. FIG. 8R illustrates the application of the facet stapler 800 on the facets 851, 852 introducing the facet staple 803. The facet staple is used to join the exterior articulating facet 851 and the interior articulating facet 852.

2. The Surgical Method

The surgical steps necessary to practice the present invention will now be described.

The posterior lumbar spine implantation of the BDFT screws 1000, plate and IBFD can be implanted via a previously described posterior lumbar interbody fusion procedure (PLIF) or posterior transforaminal lumbar interbody fusion procedure (TLIF). The procedure can be performed open, microscopic, closed, tubular or endoscopic. Fluoroscopic guidance can be used with any of these procedures.

After the adequate induction of anesthesia, the patient is placed in the prone position.

A midline incision is made for a PLIF, and one or two parallel paramedian incisions or a midline incision is made for a TLIF. For the PLIF a unilateral or bilateral facet sparing hemi-laminotomy is created to introduce the BDFT screws 1000, plates or IBFD into the disc space after it is adequately prepared. For the TLIF procedure, after a unilateral dissection and drilling of the inferior articulating surface and the medial superior articulating facet, the far lateral disc space is entered and a circumferential discectomy is performed. The disc space is prepared and the endplates exposed.

There are then multiple embodiments to choose from for an intervertebral body fusion. With the first and simplest choice, under direct or endoscopic guidance one BDFT screw 1000 or three BDFT screws 1000 can be placed in a triangulating manner encompassing the anterior and middle vertebral columns (FIGS. 4A-C). The screws 1000 are then maximally expanded purchasing and uniting the vertebral bodies above and below the disc space. Bone material or an alternative intervertebral fusion device can then be packed into the disc space. The casing of the screws 1000 prevents subsidence of the vertebral bodies. An additional option in the posterior lumbar spine is to place a mini-plate dorsally underneath the thecal sac to prevent bone migration into the nerves. In addition via a TLIF approach a triangular mini-plate/cage construct can be inserted, and then the BDFT screws 1000 maximally expanded. This is a very simple and practical supplemental or stand-alone intervertebral fusion device.

Using an alternative IBFD option, utilizing specialized forceps the two-dimensional expanding thoracolumbar expandable IBFD 700 (FIGS. 7A and 7B) is introduced into the disc space. The final dimension expansion in all embodiments leads to purchasing of the spikes into the vertebral endplates. The BDFT screws 1000 are then driven directly into rostral and caudal vertebral bodies across the intervertebral space. Then bone fusion material; autologous, allograft, bone matrix protein, BMP, rh-BMP, paste or other similar currently available or specially designed osteoconductive substances can be placed into the device and the surrounding intervertebral space. In embodiments with an incorporated viscoelastic balloon sheath, prior to engaging the screws the expandable elastometric sheath/balloon is filled with bone fusion material as mentioned above. If desirable, further material, can be placed outside its confines within the intervertebral space.

If further posterior column stability or rigidity is required, unilateral or bilateral, single level or multiple level facet screw stapling can be performed under open, microscopic flouroscopiq or endoscopic vision. Radiographic confirmation of staple position is obtained. Calibrated stapling leads to opposition of the facet joints with incremental degrees of joint opposition. This can lead to variable degrees of posterior column rigidity and/or flexibility.

The anterior lumbar spine implantation of solitary BDFT screw(s) 1000, BDFT screws incorporated into a horizontal linear or triangular mini-plate, or the IBFD/BDFT screw embodiment for L4/5 and L5/S1 interspaces can be performed on the supine anesthetized patient via previously described open micropscopic or endoscopic techniques. Once the disc space is exposed and discectomy and space preparation is performed, placement of one, two or three BDFT screws 1000 with or without a ventral mini-plate, or placement of two dimensionally expanding IBFD with or without expansile elastometric sheaths and their incorporation is identical to that performed for the posterior approach.

The posterior placement of the BDFT screws 1000 alone or combined with mini-plates or with IBFD embodiments into the thoracic spine can be performed via previously described transpedicular approaches; open or endoscopic. The anterior placement of the IBFD 700 into the thoracic spine can be accomplished via a trans-thoracic approach. Once disc space exposure is obtained via either approach, all of the above mentioned embodiments can be inserted. Engagement of the devices is identical to what was mentioned above.

For anterior placement of the cervical embodiments of the BDFT screw(s) 1000 with or without the horizontal linear or triangular cervical mini-plate, and the IBFD embodiments the anterior spine is exposed in the anesthetized patient as previously described for anterior cervical discectomies. Once the disc space is identified, discectomy is performed and the disc space prepared. Implantation and engagement of all devices is identical to that described for the anterior lumbar and thoracic spines.

The present invention may provide an effective and safe technique that overcomes the problems associated with current tanspedicular-based thoracic and lumbar fusion technology, and with current vertical cervical plating technology, and for many degenerative stable and unstable spine diseases, and could replace many pedicle screw-based and anterior vertical-plate based instrumentation in many but not all degenerative spinal conditions. Calibrated facet joint screw staples can facilitate flexible fusions and could replace current static trans-facet screws.

To our knowledge there has not been any other previously described bidirectional screw for use in the spine, other joints, or for any commercial or carpentry application. The bi-directional screw 1000 described herein may indeed have applications in general commercial, industrial and carpentry industries. To our knowledge the description of zero to subzero profile anterior or posterior horizontal spinal plates which traverse the diameter of the disc space has not been previously described. To our knowledge an intervertebral three-inone construct combining bone cage, plate and screws has not been previously reported. To our knowledge calibrated facet joint staples 803a, 803b have not been previously described.

Claims

1. An artificial spinal implant system comprising: an artificial expansile spinal implant comprising: a first shell having a first vertebral-engaging surface and a first opposite surface, the first shell comprising a first set of engagement features extending from the first vertebral-engaging surface;a second shell having a second vertebral-engaging surface and a second opposite surface, the second shell comprising a second set of engagement features extending from the second vertebral-engaging surface; andan expansion mechanism positioned between the first shell and the second shell and configured to expand the artificial expansile spinal implant, the expansion mechanism coupled to the first opposite surface and the second opposite surface, the expansion mechanism comprising a tool-engagement surface, a threaded body, and a turning mechanism;wherein the threaded body has a first end, a second end, and a longitudinal axis between the first end and the second end, the longitudinal axis extending in a direction from the first shell to the second shell;wherein the expansion mechanism is configured to drive expansion between the first shell and the second shell in response to rotating of a tool engaged with the tool-engagement surface, wherein rotating the tool comprises rotating the tool about a longitudinal axis of the tool while the tool is engaged with the tool-engagement surface, and wherein the rotating of the tool causes a rotation of the turning mechanism;wherein the artificial expansile spinal implant is configured to be introduced into a spine with the first set of engagement features of the first vertebral-engaging surface and the second set of engagement features of the second vertebral-engaging surface engaging opposing vertebral bodies to hold the artificial expansile spinal implant in place;wherein the tool-engagement surface of the expansion mechanism is positioned and configured to be engaged by the tool extending along a direction of insertion; andwherein the first shell comprises a first cavity extending from the first vertebral-engaging surface through the first shell to the first opposite surface, and wherein the first set of engagement features are positioned on the first vertebral-engaging surface circumferentially about the first cavity.

2. The artificial spinal implant system of claim 1, wherein the first set of engagement features have substantially conical tips configured for piercing endplates of the opposing vertebral bodies when introduced into the spine and expanded.

3. The artificial spinal implant system of claim 2, wherein the first set of engagement features and the second set of engagement features extend from the first vertebral-engaging surface and the second vertebral-engaging surface in directions perpendicular to the first and second vertebral-engaging surfaces.

4. The artificial spinal implant system of claim 3, wherein the second shell comprises a second cavity extending from the second vertebral-engaging surface through the second shell to the second opposite surface and wherein the second set of engagement features are positioned on the second vertebral-engaging surface circumferentially about the second cavity.

5. The artificial spinal implant system of claim 4, wherein the first shell curves continuously around a first perimeter of the first shell and the second shell curves continuously around a second perimeter of the second shell.

6. The artificial spinal implant system of claim 5, wherein the first perimeter is shaped to correspond to a shape of a vertebral body.

7. The artificial spinal implant system of claim 1, wherein the expansion mechanism further comprises a ratcheting mechanism.

8. The artificial spinal implant system of claim 1, wherein the expansion mechanism further comprises a rotatable gear.

9. The artificial spinal implant system of claim 1, wherein the first shell and the second shell each comprise titanium.

10. The artificial spinal implant system of claim 1, wherein the artificial expansile spinal implant further comprises means for placement of a bone fusion material.

11. The artificial spinal implant system of claim 1, wherein the first end of the threaded body is coupled to the first shell and the second end of the threaded body is coupled to the second shell, and the turning mechanism engages threads of the threaded body.

12. An artificial spinal implant system comprising: an artificial expansile spinal implant comprising: a first shell having a first vertebral-engaging surface and a first opposite surface, the first shell comprising a first set of engagement features extending from the first vertebral-engaging surface; anda second shell having a second vertebral-engaging surface and a second opposite surface, the second shell comprising a second set of engagement features extending from the second vertebral-engaging surface; andan expansion mechanism positioned between the first shell and the second shell and configured to expand the artificial expansile spinal implant, the expansion mechanism coupled to the first opposite surface and the second opposite surface, the expansion mechanism comprising a tool-engagement surface and at least one rotating gear that is configured to rotate about an axis passing through the gear;wherein the expansion mechanism is configured to drive expansion between the first shell and the second shell in response to rotating of a tool engaged with the tool-engagement surface, wherein rotating the tool comprises rotating the tool about a longitudinal axis of the tool while the tool is engaged with the tool-engagement surface, and wherein the rotating of the tool causes a rotation of the at least one rotating gear such that the at least one rotating gear rotates about the axis passing through the gear;wherein the artificial expansile spinal implant is configured to be introduced into a spine with the first set of engagement features of the first vertebral-engaging surface and the second set of engagement features of the second vertebral-engaging surface engaging opposing vertebral bodies to hold the artificial expansile spinal implant in place;wherein the tool-engagement surface of the expansion mechanism is positioned and configured to be engaged by the tool extending along a direction of insertion; andwherein the first shell comprises a first cavity extending from the first vertebral-engaging surface through the first shell to the first opposite surface, and wherein the first set of engagement features are positioned on the first vertebral-engaging surface circumferentially about the first cavity.

13. The artificial spinal implant system of claim 12, the expansion mechanism further comprising at least one threaded body, wherein the at least one rotating gear comprise a threaded inner surface configured to engage an outer surface of the at least one threaded body, wherein the rotating of the tool and the rotation of the at least one rotating gear causes a rotation of the at least one threaded body.

14. The artificial spinal implant system of claim 13, wherein the rotating of the tool is configured to rotate the at least one rotating gear with respect to the at least one threaded body to drive expansion between the first shell and the second shell.

15. The artificial spinal implant system of claim 13, wherein the rotating of the tool leads to a height expansion between the first shell and the second shell.

16. The artificial spinal implant system of claim 15, wherein the artificial expansile spinal implant can be adjusted in at least two directions in order to engage the opposing vertebral bodies.

17. The artificial spinal implant system of claim 12, wherein the axis passing through the gear is perpendicular to the longitudinal axis of the tool.

18. The artificial spinal implant system of claim 12, wherein the first shell curves continuously around a first perimeter of the first shell.

19. The artificial spinal implant system of claim 18, wherein the first perimeter is shaped to correspond to a shape of a vertebral body.

20. The artificial spinal implant system of claim 12, wherein the first shell and the second shell each comprise titanium.

21. The artificial spinal implant system of claim 12, wherein the at least one rotating gear comprises first and second rotating gears comprising threaded inner surfaces, smooth outer surfaces, and teeth positioned between the inner and outer surfaces.